US20050096512A1 - System for monitoring physiological characteristics - Google Patents

System for monitoring physiological characteristics Download PDF

Info

Publication number
US20050096512A1
US20050096512A1 US10/999,671 US99967104A US2005096512A1 US 20050096512 A1 US20050096512 A1 US 20050096512A1 US 99967104 A US99967104 A US 99967104A US 2005096512 A1 US2005096512 A1 US 2005096512A1
Authority
US
United States
Prior art keywords
monitor
physiological characteristic
value
glucose
user
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Abandoned
Application number
US10/999,671
Inventor
James Fox
Garry Steil
Kerstin Rebrin
Mark Estes
Frank Saidara
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Individual
Original Assignee
Individual
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by Individual filed Critical Individual
Priority to US10/999,671 priority Critical patent/US20050096512A1/en
Publication of US20050096512A1 publication Critical patent/US20050096512A1/en
Abandoned legal-status Critical Current

Links

Images

Classifications

    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00Measuring for diagnostic purposes; Identification of persons
    • A61B5/72Signal processing specially adapted for physiological signals or for diagnostic purposes
    • A61B5/7271Specific aspects of physiological measurement analysis
    • A61B5/7275Determining trends in physiological measurement data; Predicting development of a medical condition based on physiological measurements, e.g. determining a risk factor
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00Measuring for diagnostic purposes; Identification of persons
    • A61B5/145Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue
    • A61B5/14532Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue for measuring glucose, e.g. by tissue impedance measurement
    • GPHYSICS
    • G16INFORMATION AND COMMUNICATION TECHNOLOGY [ICT] SPECIALLY ADAPTED FOR SPECIFIC APPLICATION FIELDS
    • G16HHEALTHCARE INFORMATICS, i.e. INFORMATION AND COMMUNICATION TECHNOLOGY [ICT] SPECIALLY ADAPTED FOR THE HANDLING OR PROCESSING OF MEDICAL OR HEALTHCARE DATA
    • G16H15/00ICT specially adapted for medical reports, e.g. generation or transmission thereof
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B2560/00Constructional details of operational features of apparatus; Accessories for medical measuring apparatus
    • A61B2560/02Operational features
    • A61B2560/0223Operational features of calibration, e.g. protocols for calibrating sensors
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B2560/00Constructional details of operational features of apparatus; Accessories for medical measuring apparatus
    • A61B2560/02Operational features
    • A61B2560/0242Operational features adapted to measure environmental factors, e.g. temperature, pollution
    • A61B2560/0247Operational features adapted to measure environmental factors, e.g. temperature, pollution for compensation or correction of the measured physiological value
    • A61B2560/0252Operational features adapted to measure environmental factors, e.g. temperature, pollution for compensation or correction of the measured physiological value using ambient temperature
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B2560/00Constructional details of operational features of apparatus; Accessories for medical measuring apparatus
    • A61B2560/04Constructional details of apparatus
    • A61B2560/0443Modular apparatus
    • A61B2560/045Modular apparatus with a separable interface unit, e.g. for communication
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00Measuring for diagnostic purposes; Identification of persons
    • A61B5/0002Remote monitoring of patients using telemetry, e.g. transmission of vital signals via a communication network
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00Measuring for diagnostic purposes; Identification of persons
    • A61B5/145Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue
    • A61B5/1468Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue using chemical or electrochemical methods, e.g. by polarographic means
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00Measuring for diagnostic purposes; Identification of persons
    • A61B5/145Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue
    • A61B5/1486Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue using enzyme electrodes, e.g. with immobilised oxidase
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00Measuring for diagnostic purposes; Identification of persons
    • A61B5/74Details of notification to user or communication with user or patient ; user input means
    • A61B5/746Alarms related to a physiological condition, e.g. details of setting alarm thresholds or avoiding false alarms
    • GPHYSICS
    • G16INFORMATION AND COMMUNICATION TECHNOLOGY [ICT] SPECIALLY ADAPTED FOR SPECIFIC APPLICATION FIELDS
    • G16HHEALTHCARE INFORMATICS, i.e. INFORMATION AND COMMUNICATION TECHNOLOGY [ICT] SPECIALLY ADAPTED FOR THE HANDLING OR PROCESSING OF MEDICAL OR HEALTHCARE DATA
    • G16H40/00ICT specially adapted for the management or administration of healthcare resources or facilities; ICT specially adapted for the management or operation of medical equipment or devices
    • G16H40/60ICT specially adapted for the management or administration of healthcare resources or facilities; ICT specially adapted for the management or operation of medical equipment or devices for the operation of medical equipment or devices
    • G16H40/63ICT specially adapted for the management or administration of healthcare resources or facilities; ICT specially adapted for the management or operation of medical equipment or devices for the operation of medical equipment or devices for local operation

Definitions

  • This invention relates generally to medical monitoring systems. More specifically, this invention relates to methods and systems for monitoring physiological characteristics in individuals including those associated with physiological conditions (e.g. monitoring blood glucose levels in diabetics).
  • a variety of electrochemical sensors have been developed for detecting and/or quantifying specific agents or compositions in a patient's blood.
  • glucose sensors have been developed for use in obtaining an indication of blood glucose levels in a diabetic patient. Such readings are useful in monitoring and/or adjusting a treatment program which typically includes the regular administration of insulin to the patient.
  • Periodic blood glucose readings significantly improve medical therapies using semi-automated medication infusion devices.
  • Some exemplary external infusion devices are described in U.S. Pat. Nos. 4,562,751, 4,678,408 and 4,685,903
  • some examples of automated implantable medication infusion devices are described in U.S. Pat. No. 4,573,994, all of which are herein incorporated by reference.
  • Electrochemical sensors can be used to obtain periodic measurements over an extended period of time.
  • Such sensors can include a plurality of exposed electrodes at one end for subcutaneous placement in contact with a user's interstitial fluid, blood, or the like.
  • a corresponding plurality of conductive contacts can be exposed at another end for convenient external electrical connection with a suitable monitoring device through a wire or cable.
  • Exemplary sensors are described in U.S. Pat. No. 5,299,571, U.S. Pat. Nos. 5,390,671; 5,391,250; 5,482,473; and 5,586,553, which are all incorporated by reference herein.
  • a glucose crash occurs when blood glucose levels of an individual are in a state of rapid decline and its symptoms are similar to those associated with hypoglycemia.
  • the symptoms are caused by the dynamics of a declining glucose level and not by an absolute glucose level.
  • Specific symptoms can include a feeling of light headedness, sweating, tremors, nervousness and/or disorientation. Disorientation is a particular risk to the patient. If the patient becomes disoriented while operating machinery, the patient could harm himself or others.
  • a glucose crash can be caused by any of the following events: excess insulin administration; an unexpected increase in insulin sensitivity; a fall of free fatty acids in the blood; heavy exercise; or mental or physical stress.
  • ordinary glucose monitors provide only for detection of hypoglycemic and hyperglycemic levels.
  • Impaired fasting glucose is another condition which is not predicted by conventional glucose monitors.
  • the American Diabetes Association (ADA) identifies IFG as an undesirable glucose condition, defined as a 126 mg/dL or higher blood glucose level at wakeup. Repeated IFG events can contribute to diabetic morbidity.
  • One cause of IFG is an inadequate nocturnal insulin basal infusion rate.
  • a patient can deal with the IFG after waking by administering an insulin bolus, it is preferable for the patient to avoid IFG incidents entirely.
  • Typical monitors provide only a single alarm to call attention to the user. This can be problematical in contexts of varying physiological states because a user is not made aware of the specific condition and/or the appropriate degree of urgency. In existing alarm systems, until the user investigates, there is no indication of the reason for the alarm or the severity of the situation.
  • Conventional monitors are designed to alert the user of unsafe conditions, however, many other factors and situations are also important to the user in managing treatment. For example, events such as meals or exercise, as well as entering calibration values are not tied to reminders issued by conventional monitors. In addition, simple alarm systems alarms can provide duplicative warnings which can frustrate users and become ignored if they are excessive.
  • the invention as embodied and disclosed herein pertains to apparatuses and methods for monitoring physiological characteristics such as blood glucose levels.
  • Embodiments of the invention include dynamic monitoring functions that can perform predictive analyses to anticipate harmful conditions, such as hyperglycemic (or hyperglycemic) incidents, before they occur. These dynamic functions can be used to monitor normal physiological functions, as well as in a variety of other contexts including the optimization of athletic performance.
  • Other embodiments of the invention include advanced alarm and reminder functions, as well as advanced data presentation tools.
  • Embodiments of the invention disclosed herein facilitate the convenient and efficient management of diseases such as diabetes.
  • One embodiment of the invention includes a method of monitoring a physiological characteristic of a user using a device including an input element capable of receiving a signal from a sensor that is based on a sensed physiological characteristic value of the user, and a processor for analyzing the received signal.
  • the processor determines a dynamic behavior of the physiological characteristic value and provides an observable indicator based upon the dynamic behavior of the physiological characteristic value so determined.
  • the physiological characteristic value is a measure of the concentration of blood glucose in the user.
  • the process of analyzing the received signal and determining a dynamic behavior includes repeatedly measuring the physiological characteristic value to obtain a series of physiological characteristic values to determine how the physiological characteristic is changing over time.
  • each of the series of physiological characteristic values includes a smoothing filtered group of repeated physiological characteristic value readings.
  • a slope of a line fit to the series of physiological characteristic values can be calculated if a most recent of the series of physiological characteristic values is within a qualifying range.
  • the physiological characteristic value readings may be decreasing and the slope is negative.
  • the indicator can also include a warning alarm that is responsive to the dynamic behavior profile of the physiological characteristic value.
  • the warning alarm can also announce an anticipated glucose crash or merely low glucose levels, depending on the operating parameters of the particular dynamic analysis, including comparison of the slope to a threshold rate (e.g., 1% to 3% per minute) and comparison of the current measured value to a qualifying range (e.g., 60 to 150 mg/dL).
  • a threshold rate e.g., 1% to 3% per minute
  • a qualifying range e.g., 60 to 150 mg/dL.
  • the series of values analyzed is taken from a defined span of time (e.g., ten to thirty minutes).
  • an anticipated physiological characteristic value is determined from an extrapolated curve based upon the series of physiological characteristic values.
  • the indicator can provide a warning of an anticipated morning glucose incident.
  • the series of values analyzed can also be taken from a defined span of time (e.g. one hour).
  • the extrapolated curve is determined from a slope of a line fit to the series of physiological characteristic values and an average of the series of physiological characteristic values.
  • the anticipated physiological characteristic value can be determined approximately three hours before an anticipated wakeup time.
  • the indicator can be provided if the anticipated value is outside a qualifying range (e.g., approximately 60 mg/dL to 126 mg/dL).
  • a slope of a line fit to the series of physiological characteristic values is calculated if a most recent of the series of physiological characteristic values exceeds a threshold value and the slope is positive.
  • the indicator can provide a warning of an anticipated hyperglycemic incident.
  • the series of physiological characteristic values spans a time period of approximately thirty minutes and the indicator will be provided if the slope is steeper than a threshold rate.
  • a typical threshold rate can be approximately 3% per minute and the threshold value can be approximately 180 mg/dL.
  • the indicator can provide a warning of an anticipated hypoglycemic incident.
  • the series of physiological characteristic values spans a time period of approximately thirty minutes and the indicator will be provided if the slope is steeper than a threshold rate.
  • a typical threshold rate can be approximately 3% per minute and the threshold value can be approximately 70 mg/dL.
  • a physiological characteristic monitor (and corresponding methods for its use) including an input device capable of receiving a signal from a sensor and a processor capable of analyzing the received signal and providing multiple alarms, each of which can be based upon different conditions associated with the physiological characteristic value of the user.
  • the signal is based on a physiological characteristic value of a user.
  • the multiple alarms are distinguishable from each other and can include any one of a wide variety of signals such as audible signals, visual signals, tactile signals, displays, and/or the like.
  • the processor determines a physiological characteristic value from the received signal and the multiple alarms are based upon that value. In such embodiments, each of the multiple alarms can then be triggered if the physiological characteristic value exceeds an associated threshold value.
  • one of a first pair of the multiple alarms can be triggered when a narrow range of physiological characteristic values is exceeded.
  • the first pair of the multiple alarms is typically associated with a first upper threshold value and a first lower threshold value, respectively.
  • a second pair of multiple alarms can be triggered by events a wide range of physiological characteristic values (e.g. exceeding a predetermined value).
  • the second pair of the multiple alarms can be associated with a second upper threshold value and a second lower threshold value, respectively.
  • a physiological characteristic monitoring method and device which include an input device capable of receiving a signal from a sensor and a processor for analyzing the received signal.
  • the signal is based on a physiological characteristic value of a user.
  • the processor initiates a timer based upon a condition associated with the physiological characteristic value of the user and provides a reminder to the user following expiration of the timer.
  • the reminder can include an alarm signal selected from the group consisting of an audible signal, a visual signal, a tactile signal, a display, and/or the like.
  • the duration of the timer is preset based upon the specific initiating condition.
  • conditions which trigger the one or more alarms can vary.
  • the conditions which trigger the one or more alarms can be an event marker such as meal markers, exercise markers, high blood glucose markers and low blood glucose markers.
  • the condition(s) which trigger the one or more alarms can further be a reference value that is entered into the monitor and the reminder can indicate that a new reference value should be entered.
  • the processor can determine a physiological characteristic value from the received signal and the triggering condition is then based upon that physiological characteristic value.
  • the triggering condition can be situations where the physiological characteristic value exceeds a predetermined threshold value.
  • a physiological characteristic monitor including an input device capable of receiving a signal from a sensor, a processor for analyzing the received signal and determining physiological characteristic value data of the user from the received signal, a memory for storing the physiological characteristic value data of the user and a display.
  • the signal is based on a physiological characteristic value of a user.
  • the display provides a retrospective display of the physiological characteristic value data.
  • the stored physiological characteristic value data includes a minimum and maximum blood glucose value and the retrospective display shows the minimum and maximum blood glucose value with a respective time and date.
  • the stored physiological characteristic value data can include a first number of excursions above an upper blood glucose value and a second number of excursions below a lower blood glucose value and the retrospective display shows the first and second number.
  • the stored physiological characteristic value data can include a distribution of blood glucose values and the retrospective display shows a first portion of the blood glucose values above an upper blood glucose value, a second portion of the blood glucose values below a lower blood glucose value and a third portion of the blood glucose values between the upper value and the lower value.
  • the portions can be shown as percentages, times or numbers of readings.
  • the display can include a total time for the physiological characteristic value data as well as the total number of readings for the physiological characteristic value data.
  • the first portion and the second portion can be shown as integrated values. The integrated values can be based on the sums of magnitude differences from the upper blood glucose value and the lower blood glucose value for the first and second portion, respectively. In such embodiments, the integrated values can be divided by a respective duration of sensor use.
  • FIG. 1 is a block diagram of a characteristic monitor embodiment of the present invention.
  • FIG. 2 is a block diagram of a telemetered characteristic monitor embodiment of the present invention
  • FIG. 3A is a flowchart of a method for anticipating a glucose crash
  • FIG. 3B is a flowchart of a method for detecting an inadequate nocturnal basal rate
  • FIG. 3C is a flowchart of a method for anticipating a hyperglycemic incident
  • FIG. 3D is a flowchart of a method for maximizing athletic performance
  • FIG. 4 illustrates a multiple alarm function of the invention
  • FIG. 5 illustrates a reminder function of the invention
  • FIG. 6A illustrates minimum and maximum data presentation
  • FIG. 6B illustrates excursion data presentation
  • FIG. 6C illustrates characteristic value distribution data presentation
  • FIG. 6D illustrates integrated characteristic value data presentation.
  • Embodiments of the present invention encompass methods and systems for the convenient operation of monitoring physiological characteristics (“characteristic monitoring systems”).
  • characteristic monitoring systems The description provided here encompasses the architecture of the apparatus as well as its control and convenience features.
  • the control and convenience features of the present invention can be implemented in a wide range of detailed characteristic monitoring system designs.
  • embodiments of the present invention are primarily described in the context of glucose monitors used in the treatment of diabetes, the embodiments of the invention are applicable to a wide variety of patient treatment programs where a physiological characteristic is periodically monitored to use in estimating the responsive treatment.
  • embodiments of the invention can be used to determine the status and/or levels of a variety of characteristics including those associated with agents such as hormones, cholesterol, medication concentrations, pH, oxygen saturation, viral loads (e.g., HIV), or the like
  • a sensor for the characteristic monitor can be implanted in and/or through subcutaneous, dermal, sub-dermal, inter-peritoneal or peritoneal tissue. Such sensors typically communicate a signal from the sensor set to the characteristic monitor.
  • General embodiments of the invention include a physiological characteristic monitor coupled to a sensor set.
  • the sensor set and monitor are for determining glucose levels in the blood and/or body fluids of the user without the use of, or necessity of, a wire or cable connection between the transmitter and the monitor.
  • Embodiments of the characteristic monitor system of the invention are primarily adapted for use in subcutaneous human tissue.
  • embodiments of the invention can be placed in a variety of other types of physiological milieus, such as muscle, lymph, organ tissue, veins, arteries or the like, as well as being used in related environments such as animal tissue.
  • Embodiments of the invention can provide sensor readings on an intermittent, near-continuous or continuous basis.
  • Embodiments of the invention include sensing and advanced predictive functions of the monitor which are designed to anticipate unsafe conditions for a user before they occur.
  • predictive functions can be employed so that a user can obtain feedback to obtain a desired physical objective, such as maximizing athletic performance.
  • Other functions of the monitor include multiple programmable alarms and reminders.
  • Embodiments of the invention can include advanced display tools to facilitate easy and quick interpretation of information related to the user's condition.
  • FIG. 1 is a block diagram of a characteristic monitoring system 100 in accordance with an embodiment of the present invention.
  • the characteristic monitoring system 100 generally includes a sensor set 102 that employs a sensor that produces a signal that corresponds to a measured characteristic of the user, such as a blood glucose level.
  • the sensor set 102 communicates these signals to a characteristic monitor 104 that is designed to interpret these signals to produce a characteristic reading or value for the user, i.e. a measurement of the characteristic.
  • the sensor signals enter the monitor 104 through a sensor input 106 and through the sensor input 106 the signals are conveyed to a processor 108 .
  • the processor 108 determines and manipulates the sensor readings within the monitor 104 .
  • the characteristic monitor 104 provides additional functions that will aid in the treatment regime to which the characteristic reading applies.
  • the monitor may track meals, exercise and other activities which affect the treatment of diabetes. These additional functions can be combined with or independent from the characteristic readings determined by the monitor 104 .
  • monitor 104 Other components of the monitor 104 support the processor 108 in performing functions.
  • a memory 110 is used to store data and instructions used by the processor 108 .
  • a data entry device 112 such as a keypad is used to receive direct input from the user and a display 114 such as a liquid crystal display (LCD), or the like, is used to relate information to the user.
  • the monitor 104 includes a data port 116 , such as a digital input/output (I/O) port.
  • I/O digital input/output
  • the data port 116 can be used for the monitor to communicate with a computer 118 .
  • the monitor may interface with the computer 118 through a communication station 120 that can serve as a docking station for the monitor 104 , for example.
  • the data port 116 within the monitor 104 can be directly connected to the computer 118 .
  • data may be downloaded from the monitor, such as stored characteristic readings, settings, programs and other information related to the monitor's function.
  • advanced analysis can be performed on a computer freeing memory 110 within the monitor 104 .
  • Data such as characteristic readings, settings and programs can also be downloaded to the monitor 104 . In this way, the monitor 104 can be conveniently reprogrammed without requiring tedious manual entry by the user.
  • FIG. 2 is a block diagram of a telemetered characteristic monitoring system embodiment of the invention.
  • the sensor input 106 of the monitor 104 is a wireless receiver, such as a radio frequency (RF) receiver.
  • the sensor set 102 provides a signal via wired link to a telemetered monitor transmitter 202 where the signal is interpreted and converted to an RF signal.
  • the wireless receiver sensor input 106 of the monitor 104 converts the signal to data understandable to the monitor processor.
  • the telemetered characteristic monitoring system can perform any or all the functions of the characteristic monitoring system of FIG. 1 .
  • a characteristic monitor system 100 in accordance with a preferred embodiment of the present invention includes a sensor set 102 , and characteristic monitor device 104 .
  • the sensor set 102 generally utilizes an electrode-type sensor.
  • the system can use other types of sensors, such as electrically based sensors, chemically based sensors, optically based sensors, or the like.
  • the sensors can be of a type that is used on the external surface of the skin or placed below the skin layer of the user. Preferred embodiments of a surface mounted sensor utilize interstitial fluid harvested from underneath the skin.
  • the sensor set 102 is connected to the monitor device 104 and provides a signal based upon the monitored characteristic (e.g., blood glucose).
  • the monitored characteristic e.g., blood glucose
  • the characteristic monitor device 104 utilizes the received signal to determine the characteristic reading or value (e.g., a blood glucose level).
  • the sensor may be placed in other parts of the body, such as, but not limited to, subcutaneous, dermal, sub-dermal, inter-peritoneal or peritoneal tissue.
  • the telemetered characteristic monitor transmitter 202 generally includes the capability to transmit data.
  • the telemetered characteristic monitor transmitter 202 can include a receiver, or the like, to facilitate two-way communication between the sensor set 102 and the characteristic monitor 104 .
  • the characteristic monitor 104 can be replaced with a data receiver, storage and/or transmitting device for later processing of the transmitted data or programming of the telemetered characteristic monitor transmitter 202 .
  • a relay or repeater (not shown) can be used with a telemetered characteristic monitor transmitter 202 and a characteristic monitor 104 to increase the distance that the telemetered characteristic monitor transmitter 202 can be used with the characteristic monitor 104 .
  • the relay can be used to provide information to parents of children using the telemetered characteristic monitor transmitter 202 and the sensor set 102 from a distance. The information can be used when children are in another room during sleep or doing activities in a location remote from the parents.
  • the relay can include the capability to sound an alarm.
  • the relay can be capable of providing telemetered characteristic monitor transmitter 202 data from the sensor set 102 , as well as other data, to a remotely located individual via a modem connected to the relay for display on a monitor, pager or the like.
  • the data can also be downloaded through the communication station 120 to a remotely located computer 118 such as a PC, lap top, or the like, over communication lines, by modem or wireless connection.
  • some embodiments of the invention can omit the communication station 120 and use a direct modem or wireless connection to the computer 118 .
  • the telemetered characteristic monitor transmitter 202 transmits to an RF programmer, which acts as a relay, or shuttle, for data transmission between the sensor set 102 and a PC, laptop, communication station 118 , a data processor, or the like.
  • the telemetered characteristic monitor transmitter 202 can transmit an alarm to a remotely located device, such as a communication station 118 , modem or the like to summon help.
  • further embodiments can include the capability for simultaneous monitoring of multiple sensors and/or include a sensor for multiple measurements.
  • a purpose of the characteristic monitor system 100 is to provide for better treatment and control in an outpatient or a home use environment.
  • the monitor systems 100 , 200 can provide indications of glucose levels, a hypoglycemia/hyperglycemia alert and outpatient diagnostics.
  • Embodiments of the invention are also useful as an evaluation tool under a physician's supervision.
  • the characteristic monitor device 104 receives characteristic information, such as glucose data or the like, from the sensor set 102 and displays and logs the received glucose readings. Logged data can be downloaded from the characteristic monitor 104 to a personal computer, laptop, or the like, for detailed data analysis.
  • the characteristic monitor system 100 , 200 can be used in a hospital environment, or the like. Still further embodiments of the present invention can include one or more buttons to record data and events for later analysis, correlation, or the like. Further buttons can include a sensor on/off button to conserve power and to assist in initializing the sensor set 102 .
  • the characteristic monitor 200 can also be employed with other medical devices to combine other patient data through a common data network system.
  • the sensor set 102 can monitor the temperature of the sensor set 102 , which can then be used to improve the calibration of the sensor.
  • the enzyme reaction activity may have a known temperature coefficient. The relationship between temperature and enzyme activity can be used to adjust the sensor values to more accurately reflect the actual characteristic levels.
  • the oxygen saturation level can be determined by measuring signals from the various electrodes of the sensor set 102 . Once obtained, the oxygen saturation level can be used in calibration of the sensor set 102 due to changes in the oxygen saturation levels, and its effects on the chemical reactions in the sensor set 102 . For example, as the oxygen level goes lower the sensor sensitivity can be lowered. The oxygen level can be utilized in calibration of the sensor set 102 by adjusting for the changing oxygen saturation.
  • temperature measurements can be used in conjunction with other readings to determine the required sensor calibration.
  • the sensor set 102 facilitates accurate placement of a flexible thin film electrochemical sensor of the type used for monitoring specific blood parameters representative of a user's condition.
  • the sensor monitors glucose levels in the body, and can be used in conjunction with automated or semi-automated medication infusion devices of the external or implantable type as described in U.S. Pat. Nos. 4,562,751; 4,678,408; 4,685,903 or 4,573,994 (which are incorporated herein by reference), to control delivery of insulin to a diabetic patient.
  • Embodiments of the flexible electrochemical sensor can be constructed in accordance with thin film mask techniques to include elongated thin film conductors embedded or encased between layers of a selected insulative material such as polyimide film or sheet, and membranes.
  • the sensor electrodes at a tip end of the sensing portion are exposed through one of the insulative layers for direct contact with patient blood or other body fluids, when the sensing portion (or active portion) of the sensor is subcutaneously placed at an insertion site.
  • the sensing portion is joined to a connection portion that terminates in conductive contact pads, or the like, which are also exposed through one of the insulative layers.
  • other types of implantable sensors such as chemical based, optical based, or the like, can be used.
  • connection portion can be conveniently connected electrically to the monitor 104 or a telemetered characteristic monitor transmitter 202 by a connector block (or the like) as shown and described in U.S. Pat. No. 5,482,473, entitled “FLEX CIRCUIT CONNECTOR”, which is also herein incorporated by reference.
  • subcutaneous sensor sets 102 are configured or formed to work with either a wired or a wireless characteristic monitor system 100 , 200 .
  • Embodiments of the present invention include different types of continuous glucose monitors that identify trends in blood glucose dynamics to facilitate enhanced treatment of diabetes.
  • a first illustrative monitor can be used to anticipate a glucose “crash” (or other hypoglycemic incident) before the onset of debilitating symptoms.
  • Another illustrative monitor can be used to detect an inadequate nocturnal basal rate and alert the patient in order to avoid an impaired fasting glucose incident.
  • Another illustrative monitor can anticipate hyperglycemic (or hypoglycemic) incidents by detecting trends toward those levels and help the patient avoid such incidents.
  • Another illustrative monitor can assist a patient in maximizing athletic performance in endurance type activities (e.g., a marathon race) by detecting trends toward hypoglycemic levels.
  • the disclosed embodiments monitor the dynamics of a physiological characteristic such as blood glucose levels. These embodiments utilize this dynamic monitoring to provide functionality including the anticipation of glucose crash and alerting the patient, the detection of inadequate nocturnal basal rate, the anticipation of hyperglycemic (or hypoglycemic) incidents and maximizing athletic performance. All of these features can be implemented in software operating in the monitor's microprocessor and/or designed into an application specific integrated circuit (ASIC) or other specialized circuitry. Also, dynamic glucose monitoring functions use periodic measurements of a glucose level.
  • ASIC application specific integrated circuit
  • a monitor anticipates a glucose crash by monitoring trends in glucose levels. For example, the monitor can alert the patient when glucose levels are rapidly decreasing. By monitoring such trends or a rate information of measured glucose levels, the monitor can provide a much better warning system to alert the user with enough time to stabilize and reverse a dangerous physiological condition.
  • the monitor measures glucose more frequently than typical glucose monitoring devices. For example, one embodiment of the invention measures approximately every minute, whereas other monitors measure a lower rate (e.g., but not limited to, once per 5 minutes). Frequent measurements are taken because of the short time intervals which are evaluated. Alternative embodiments may utilize more frequent measurements, such as, but not limited to, 10 seconds, 1 second, or the like.
  • the monitor periodically measures glucose, analyzes the present trend, determines whether a glucose crash incident is probable and appropriately alerts the patient.
  • the device measures the glucose level, applies a smoothing filter to the result, and records the filtered value.
  • the smoothing filter may take a weighted sum of past sensor values (so called finite impulse response-FIR-filter), a weighted sum of past sensor values and past filtered values (so called infinite impulse response-IIR-filters), may use simple clipping algorithms (e.g. limit the percent change in filtered output), or employ models to predict the output (e.g. Weiner and Kalman filter designs).
  • the monitor can calculate the slope of a line fit to the most recent values (most likely, but not limited to, using a Saritzky gulag filter) and determine if the slope is steeper than a selected threshold rate (e.g., but not limited to, 3% or declining at more than 30 mg/dL in ten minutes). If the slope equals or exceeds the threshold rate, a glucose crash incident is likely and the monitor alerts the patient accordingly.
  • a selected threshold rate e.g., but not limited to, 3% or declining at more than 30 mg/dL in ten minutes.
  • the qualifying range can be a closed range (e.g., but not limited to, between 100 and 150 mg/dL) and in other embodiments the qualifying range can be an open range (e.g., but not limited to, greater than 100 mg/dL).
  • the determination of a glucose crash can be unconcerned with rate magnitudes occurring when the current characteristic value is outside of the range, (of course, other alarms, which merely monitor the current characteristic value, can be triggered when the reading is too high or too low).
  • the slope can be calculated and compared to the threshold rate with every new value.
  • multiple qualifying ranges and threshold rates can be applied to evaluate the glucose dynamics and determine triggering a glucose crash warning.
  • the monitor determines that a glucose crash is likely if three criteria are met.
  • the criteria are as follows.
  • the third, G, the glucose level can be considered for example, when this value begins dropping starting within a specified range, (e.g., but not limited to, 100-150 mg/dL).
  • these criteria can be parameterized to allow the user to customize the values.
  • the qualifying range, threshold rate and period can be general values, applied to all users, or determined from factors specific to the individual user.
  • the monitor can include a feature to adjust the qualifying glucose level range, the maximum rate of glucose change, or in some embodiments, the sustained time period length.
  • any or all of the dynamic glucose monitoring functions can enabled or disabled, selectively or together.
  • control program pseudo code provides an example of a programming routine performed by the processor of the monitor to implement an embodiment of the invention.
  • REPEAT every minute ⁇ Measure glucose level g i Filter g i and store the filtered value g ′ i IF(g ′ i is in range 100-150 mg/dL) THEN Fit a line to the most recent 10 filtered (or, alternatively, unfiltered) values IF (dG/dT for that line ⁇ ( ⁇ 3% per minute ) THEN Alert the patient and record in history ENDIF ENDIF ⁇ END REPEAT
  • FIG. 3A is a flowchart of a method for anticipating a glucose crash 300 .
  • a characteristic level is repeatedly measured to obtain a group of characteristic level values.
  • a smoothing filter can be applied to the group of characteristic level values to produce a filtered measurement value.
  • the filtered measurement value is recorded at block 306 .
  • it is determined if the recorded value falls within a qualifying range e.g., but not limited to, between 100 to 150 mg/dL). If not, the process returns to block 302 . If the recorded measurement is within the range, a slope of a line fit to a recent series of recorded filtered values is calculated at block 310 .
  • the calculated slope is compared to a threshold rate (e.g., but not limited to, ⁇ 3% per minute) at block 312 . If the calculated slope is not steeper than the threshold rate the process returns to block 302 . If the slope exceeds the threshold rate, an anticipated glucose crash is indicated at block 314 .
  • a threshold rate e.g., but not limited to, ⁇ 3% per minute
  • Alternative embodiments may utilize similar logic for when the glucose level is already outside of the range and continues to drop.
  • a raw data measurement e.g. a group of characteristic level values
  • the characteristic monitor can be used to detect an inadequate nocturnal basal rate.
  • This embodiment generally applies to diabetic patients using an insulin infusion device that continually administers insulin at a patient controlled basal rate.
  • the monitor detects an inadequate basal rate (i.e., but not limited to, “low basal rate” or a “high basal rate”), by monitoring trends in glucose levels.
  • the monitor alerts a patient in the early morning, when glucose levels are high and relatively steady, low and relatively stable or changing rapidly. This gives the patient time to adjust the basal rate of the infusion device upward or downward to and avoid an impaired fasting glucose incident.
  • the monitor operates to track the characteristic level rate. For example, every 5 minutes the monitor measures and records the glucose level. Once a day (e.g., but not limited to, 3 hours before to the anticipated wakeup time), the monitor calculates the average blood glucose and the rate of blood glucose change for the previous hour. The monitor can then determine a prediction of the “morning glucose” level at wake up based upon the calculated average blood glucose and the rate of blood glucose change. In one embodiment the “morning glucose” is predicted assuming that the rate of change remains constant, however in other embodiments nonlinear characteristic curves and functions can be applied in making the prediction.
  • a high threshold value e.g., but not limited to, 126 mg/dL
  • a low threshold value e.g., but not limited to, 60 mg/dL
  • an alarm is sounded. This will allow time for the infusion device basal rate to be adjusted appropriately.
  • different times before anticipated wakeup, different high threshold values, or different low threshold values may be used.
  • the triggering criteria can also be parameterized to allow the user to customize the values.
  • the user is allowed to set the values for the controlling parameters. For example, the user can set the qualifying low and high glucose levels as well as the anticipated waking time. For each of the settings a default value can be used in the absence of a user setting. For example, a default low glucose level of 60 mg/dL, a default high glucose level of 126 mg/dL and an anticipated waking time of 7:00 AM can be used. In addition, the entire function can be enabled and disabled.
  • FIG. 3B is a flowchart of a method for detecting an inadequate nocturnal basal rate 320 .
  • the method begins by measuring a characteristic level to obtain a measurement value. The value is recorded at block 324 . Measuring and recording is repeated periodically to obtain a series of values at block 326 .
  • the average of the series of values is calculated.
  • a slope of a line fit to the series of values is calculated. The calculated slope and average of the series of values are then used to determine a predictive curve at block 332 .
  • the curve is extrapolated to predict a glucose level at wakeup.
  • the extrapolation is performed some time before wakeup (e.g., but not limited to, 3 hours prior) to provide enough time to correct any impending negative condition.
  • the predicted glucose level is compared to an acceptable range at block 336 . If the predicted glucose value falls within the range, the process ends. If the predicted glucose value falls outside the range, a morning glucose incident is reported at block 338 .
  • a glucose monitor anticipates a hyperglycemic (or hypoglycemic) incident by monitoring trends in glucose levels.
  • the monitor alerts the patient when a “relatively steady increase” (or decrease) in glucose levels occurs.
  • the monitor periodically measures glucose, analyzes the present trend, determines whether a hyperglycemic (or hypoglycemic) incident is probable and appropriately alerts the patient.
  • the device measures glucose values at a specific time interval (e.g. once every minute), and then, e.g. at 5 minute intervals, applies a smoothing filter to this group of values and records the filtered value. If the most recent (filtered) value exceeds a threshold value (e.g., but not limited to, 180 mg/dL), the monitor calculates the slope of a line fit to a recent series of recorded values (for example, but not limited to, six values). If the slope is greater than a threshold rate (e.g., but not limited to, 3% per minute), a hyperglycemic incident is likely and the monitor alerts the patient. For hypoglycemic incidents, values and thresholds corresponding to low glucose levels would be used.
  • a threshold value e.g., but not limited to, 180 mg/dL
  • a threshold rate e.g., but not limited to, 3% per minute
  • the threshold value is applied in a similar manner to the “qualifying range” applied in determining a glucose crash previously discussed.
  • the threshold value effectively operates as an open range (e.g., but not limited to, greater than 180 mg/dL).
  • the threshold value can be a closed range. Therefore, determining a hyperglycemic incident can be unconcerned with values below the threshold value (as determining a hypoglycemic incident can be unconcerned with values above a threshold value).
  • a slope calculation can be avoided if the current reading is outside the range. However, in alternate embodiments, the slope can be calculated and compared to the threshold rate with every new reading.
  • multiple qualifying ranges and threshold rates can be applied to evaluate the glucose dynamics and determine triggering a hyperglycemic (or hypoglycemic) incident warning.
  • the criteria can be parameterized to allow the user to customize the controlling values for anticipating hyperglycemic (or hypoglycemic) incidents.
  • some embodiments can allow the user to set the glucose threshold level and/or the threshold rate.
  • Embodiments of the invention can also use default parameters if no user settings are provided (e.g., but not limited to, a threshold level of 180 mg/dL and a maximal rate of 3% per minute). Embodiments of the invention can also enable and disable this function.
  • FIG. 3C is a flowchart of a method for anticipating a hyperglycemic incident 350 .
  • the method begins at block 352 by repeatedly measuring a characteristic level to obtain a group of values.
  • a smoothing filter is applied to the group of values to obtain a filtered measurement value.
  • the filtered value is recorded at block 356 .
  • the recorded value is compared to a threshold value at block 358 . If the recorded value does not exceed the threshold value (e.g., but not limited to, 180 mg/dL), the process returns to block 352 . If the recorded value does exceed the threshold value, a slope of a line fit to a recent series of values is calculated at block 354 .
  • the threshold value e.g., but not limited to, 180 mg/dL
  • Dynamic monitoring can also be used to provide feedback based upon the engaged activity of the user.
  • the monitor can be used to maximize performance during an endurance type activity (e.g., but not limited to, a marathon race).
  • the endurance athlete strives to burn glucose rather than fat and accordingly needs to anticipate low glucose levels and ingest carbohydrates early enough to avoid low glucose levels.
  • the monitor anticipates low glucose levels and alerts the athlete to ingest carbohydrates. It is important to note that this embodiment is not strictly anticipating hypoglycemic incidents. Instead it is anticipating low glucose levels where it would otherwise be too late for the athlete to compensate by ingesting carbohydrates and still perform effectively and/or at full capacity.
  • the device measures a glucose level, applies a smoothing filter and records the filtered value at 5-minute intervals. If the most recent recorded (i.e., filtered) value is in a qualifying range (e.g., but not limited to, 60-140 mg/dL), the processor calculates the slope of a line fit to the most recent six filtered values and determines if the slope is steeper than ⁇ 1% (i.e., but not limited to, 30 mg/dL in 30 minutes). If the rate of decline exceeds this threshold, a low glucose level is likely and the monitor alerts the athlete accordingly. Thus, for example, but not limited to, to trigger an alarm, the glucose level rate, dG/dT, is negative with a magnitude greater than 1% per minute for 30 minutes beginning in range 60-140 mg/dL.
  • a qualifying range e.g., but not limited to, 60-140 mg/dL
  • the qualifying range can be a closed range (e.g., but not limited to, between 60 and 140 mg/dL) or an open range (e.g., but not limited to, less than 140 mg/dL).
  • a closed range e.g., between 60 and 140 mg/dL
  • an open range e.g., but not limited to, less than 140 mg/dL.
  • the monitor will allow a user to set the qualifying glucose range and/or enable and disable the function.
  • a default qualifying range e.g., but not limited to, 60-140 mg/dL can be used.
  • FIG. 3D is a flowchart of a method for maximizing athletic performance 370 .
  • the process begins at block 372 , where a characteristic level is repeatedly measured to obtain a group of characteristic level values. Following this at block 374 , a smoothing filter can be applied to the group of characteristic level values to produce a filtered measurement value.
  • the filtered measurement value is recorded at block 376 .
  • a qualifying range e.g., but not limited to, between 60 to 140 mg/dL
  • the calculated slope is compared to a threshold rate (e.g., but not limited to, ⁇ 1% per minute) at block 382 . If the calculated slope is not steeper than the threshold rate the process returns to block 372 . If the slope exceeds the threshold rate, an anticipated low glucose level is indicated at block 384 . As noted previously, estimates of dG/dt may be calculated by slope as well as other methods known in the art.
  • a threshold rate e.g., but not limited to, ⁇ 1% per minute
  • Embodiments of the invention can also employ multiple alarms that can be independently set by the user.
  • a continuous glucose monitoring system can have multiple alarms for different glucose values.
  • the system can allow a user to set threshold glucose values that define a “narrow” glucose range (as compared to the ordinary alarm limits). If the user's glucose level passes outside the “narrow” range, an alarm can sound. This alarm alerts the user to monitor his glucose levels more closely.
  • the system can sound a second alarm (preferably having a sound distinguishable from the first “narrow” range alarm) in the even the user's glucose level reaches a more dangerous condition requiring immediate action.
  • Alarm indications may be audible, tactile, vibratory, visual, combinations of alarm indications, or the like. In the case of visual alarm indications, but not limited to, green lights can be displayed for with a range; yellow for the first alarm level; and red for the second alarm level. The visual alarm indications may flash and/or also be combined with other alarm indications.
  • the alarms can be set in ranges or separate high and low glucose level alarms can be set. Distinctive sounds can be used for each alarm. For example, each successive high glucose level alarm can have, but is not limited to having, a higher pitch. Successive low glucose level alarms can each have, but are not limited to having, lowering pitches. Alternately, intermittent or wavering volumes that also increase in pitch according to the severity of the condition can be used. In still other embodiments, the user can select or program alarm tones and other sounds and assign them to the various alarms. Also, in some embodiments, these distinguishable alarms can also be set at different volume levels. In addition, as discussed above, the alarms are not limited to audible signals; some embodiments of the invention can also utilize visual alarms, such as flashing lights or displays or tactile alarms, such as vibrating indicators.
  • threshold values and associated alarms can be set according to a schedule. For example, but not limited to, particular alarms can be set to be active only during selected portions of the day.
  • FIG. 4 illustrates a multiple alarm function of the invention.
  • a plot of the monitored characteristic value 400 e.g., blood glucose
  • a typical wide alarm range 402 is defined by an upper threshold value 404 and a lower threshold value 406 . If the monitored characteristic value 400 should exceed the defined range and cross either threshold, an alarm is initiated to indicate to the user to check his blood glucose.
  • a distinctive alarm can be associated with the alarm range 402 . Thus, the same alarm is produced whether the range 402 is exceeded by passing the upper threshold value 404 or the lower threshold value 406 .
  • distinctive alarms can be assigned to each threshold value 404 , 406 .
  • other alarm ranges can also be set.
  • a second narrower range 408 can be set with a lower upper threshold value 410 than that of the wider range 402 ; and a higher lower threshold value 412 than that of the wider range 402 .
  • an alarm is initiated if the narrower range is exceeded by the monitor characteristic value 400 .
  • alarms can be the same or different for each threshold 410 , 412 .
  • the ability to set different ranges and associated alarms allows the monitor to immediately convey some information about the condition of the user even before checking the actual readings.
  • using the narrower range 408 and associated alarms allows the user to know of a negative trend that does not require the same urgency as an alarm triggered by the wider range 402 .
  • the user is able to set multiple alarms, each indicating a different level of urgency and/or different conditions.
  • threshold values for alarms can also be set independent from ranges.
  • alarms or indicators can be set according to the direction in which a threshold value is crossed by the monitored characteristic value 400 .
  • a threshold value For example, as the monitored characteristic value 400 crosses a lower threshold value 412 from the narrow range (e.g., but not limited to, at point 414 ), one type of alarm can be provided. However, when the monitored characteristic value 400 crosses a lower threshold value 412 from the wider range 402 (e.g., but not limited to, at point 416 ), another type of alarm can be provided.
  • the difference in the alarms is appropriate because only the former case indicates a worsening of the user's condition. In the latter case, the transition actually indicates an improvement in the user's condition.
  • alarms will only be given when crossing a threshold indicates a worsening of the user's condition.
  • an indicator will also be given when a threshold has been crossed in an improving direction.
  • either the same indicator (sound, light, display or other) or different indicators can be used.
  • reminders can be set to indicate to a user various conditions (not necessarily negative) that will aid in the convenient therapy management.
  • the reminders can be alarm signals (including, but not limited to, auditory, visual, tactile, etc.) that are initiated after a timer has run to prompt the user to take action or merely inform the user of a particular status.
  • the reminder is started (i.e. the timer is initiated), when an event occurs and/or certain conditions are met.
  • the alarm signals can be the same or different based upon the triggering events or conditions.
  • reminders can be used to further assist the user in managing insulin delivery for optimum results. For example, but not limited to, reminders can be set for event markers, blood glucose values, reference values, high or low sensor measurements.
  • Characteristic monitors and infusion devices can use event markers that place tags in the data for events the user experiences (e.g., but not limited to, meals, exercise, and high or low blood glucose). For example, but not limited to, when an infusion device identifies a high or low blood glucose event marker, it can start a timer that reminds the user to check blood glucose levels. This is intended to make therapy safer by encouraging more frequent checks during times that the patient may be at risk from hypoglycemia or hyperglycemia. In addition, this feature can also be applied to characteristic monitors. For example, but not limited to, a characteristic monitor that is used to show low or high blood glucose tags can have a timer set to remind a user to check their blood glucose levels at a later time.
  • a reminder timer can be set that is triggered if a blood glucose value is entered.
  • the reminder can be if the user enters a low or high blood glucose value into the monitor as a reference or calibration value.
  • a reminder timer can also be triggered by a user providing a reference value to the monitor.
  • the user can be reminded to supply a new reference value after a minimum time period has elapsed. In this way calibration of the monitor is assured.
  • a blood glucose reminder can also be triggered by high or low measurement from the sensor.
  • the monitor will request a blood glucose reference value during an excursion away from the normal range of values.
  • the trigger for this reminder can be tempered by setting a minimum time between reminders to avoid pestering the user.
  • This reminder can be used to provide more robust data for curve fitting as correlation improves with variability in the data pairs.
  • the reminder promotes more frequent data collection during more critical periods (e.g., but not limited to, when blood glucose is too high or too low) and therefore the interpolated curve for this period is more reliably representative of the true curve.
  • reminders also serve to prevent redundant and excessive alarms for the user. For example, if the timer is removed from the previously described high or low measurement reminder, the result would be a simple hypoglycemia or hyperglycemia alarm. Using a reminder, however, the message is not that the user's blood glucose is out of range. Rather, the reminder's message is to check the user's blood glucose with a meter, or the like. If a user's blood glucose is very near an alarm triggering threshold, an alarm might be triggered repeatedly as the value passes back and forth across the threshold. A reminder will set a timer, preventing duplicative warnings for a short period of time, but reminding the user to check blood glucose again when that period has expired.
  • the alarm is triggered again, regardless of the presence of a time, if the glucose level continues to change in the direction of the trend.
  • FIG. 5 illustrates a reminder function of the invention triggered by high or low characteristic values.
  • a plot of a monitored characteristic value 500 (such as, but not limited to, blood glucose) is shown.
  • One or more ranges 502 , 504 define safe characteristic values (e.g., but not limited to, a first range 502 being a warning range and a second range 504 being a critical range), such as can be employed using multiple alarms as previously described.
  • a range is exceeded (e.g., but not limited to, at time 506 )
  • an alarm can be triggered but also a timer is started such that a reminder is also initiated after its expiration (e.g., but not limited to, at time 508 ). Over the timer period further occurrences of exceeding the threshold (e.g., but not limited to, at point 510 ) will not result in a duplicative alarm.
  • the situation can be somewhat different when the intervening triggering event is not identical to the first triggering event. For example, if a first range 502 is exceeded (e.g., but not limited to, at time 512 ) and a timer is started, but before a reminder can be issued (e.g., but not limited to, at time 514 ) a second range 504 is exceeded (e.g., but not limited to, at time 516 ), then the second alarm will be issued and the timer will be restarted.
  • a first range 502 e.g., but not limited to, at time 512
  • a timer is started, but before a reminder can be issued (e.g., but not limited to, at time 514 )
  • a second range 504 is exceeded (e.g., but not limited to, at time 516 )
  • Another aspect of the invention is to provide meaningful retrospective information to the patient using the sensor.
  • a retrospective display of one or more physiological values can provide significantly useful data.
  • the retrospective displays can be designed in a variety of ways to provide various useful information. For example, but not limited to, as the sleeping user receives no benefit from a real-time display, a retrospective view of data is important. While a simple listing of previous values has value, it can be time consuming to review, provides information that is difficult to visualize and comprehend and requires significant memory space within the device. Providing useful information that is easy to understand and that can be stored within a small memory space is very important.
  • the ability to review data from the previous sleep period is particularly helpful to a user with nocturnal hypoglycemia or “dawn effect”, as there is typically no witness to the real-time display. These measures can be even more important in cases where the alarm system can exhibit many false positives and/or false negatives, which might otherwise frustrate the user and lead to non-use of the monitor.
  • the following advanced data presentation tools can be used to conveniently and efficiently store and display useful information on a screen for a user to review while the monitor is in use.
  • the tools provide useful information while requiring only a minimal amount memory space.
  • These data presentation tools can also be used in any retrospective analysis package, such as software running on a computer or network designed to analyze trends and provide advise regarding a treatment regime.
  • the tools operate by processing that compares actual reading to high and low value limits (e.g., but not limited to, acceptable blood glucose ranges).
  • the limits can be the adjustable hypoglycemic and hyperglycemic alarm thresholds of a monitor.
  • the tools can be applied to a fixed definition of a target blood glucose range that is independent of the hyperglycemic and hypoglycemic alarm thresholds for the particular user/monitor.
  • FIG. 6A illustrates one minimum and maximum data presentation.
  • a display of the minimum and maximum values 600 of the characteristic monitor that have been measured for the user can be displayed on the monitor.
  • the minimum value and maximum values can be conveniently displayed along with the date and time of their occurrence.
  • Such a display 600 is useful, but becomes more useful when combined with an excursion count, a distribution of values, and/or integrated values as discussed below
  • FIG. 6B illustrates an excursion data presentation.
  • the number of excursions above or below the respective blood glucose limits is also very useful to have summarized for the user.
  • An excursion display 602 provides good information, particularly when there are no alarms active on the monitor (either because the monitor is not turned on or alarms are not being employed by the user).
  • a display 602 of the number of excursions above the hyperglycemic limit and the number of excursions below hypoglycemic limit give the user an idea of performance of a treatment program at a glance. A high number of incidents exceeding either limit indicate a need for improvements.
  • FIG. 6C illustrates a characteristic value distribution data presentation.
  • a simple distribution of sensor values offers a very powerful tool.
  • the distribution is described in percentages that are automatically scaled with the duration of monitor use.
  • a monitor can include the total time of use with a percentage distribution. Awareness of a total time provides perspective for reviewing the percentage distribution.
  • a time based distribution can also be used, but requires the total time to be included in the analysis as a reference.
  • a distribution can also be presented based upon the total number of readings, but requires the total time is required in the analysis.
  • the display can show a percentage of readings above a hyperglycemic alarm level, a percentage of readings below a hypoglycemic alarm level and a percentage of readings of readings within alarm range as shown in FIG. 6C .
  • the total time covered in the analysis can also be displayed.
  • an alternate display can show the time spent above a hyperglycemic alarm level, the time spent below a hypoglycemic alarm level and the time spent within alarm range (not shown).
  • the time base display requires a known total time as part of the analysis.
  • a display can also include the number of readings above hyperglycemic alarm level, the number of readings below a hypoglycemic alarm level and the number of readings within alarm range (not shown).
  • FIG. 6D illustrates an integrated characteristic value data presentation. Performing an integration of the readings outside the alarm levels with respect to time can provide a measure of the hypoglycemic and hyperglycemic events' severity. In addition, these results can also be scaled these by a total sensor time to provide a measure that is duration independent.
  • a “hyperglycemic area” can be calculated as the sum of the differences between the readings and the hyperglycemic alarm limit.
  • a “hypoglycemic area” can be calculated from the sum of all the differences between the hypoglycemic alarm limit and the readings.
  • a “hyperglycemic index” is calculated by taking the “hyperglycemic area” and dividing it by the duration of sensor use. Similarly, the “hypoglycemic index” can be calculated by taking the “hypoglycemic area” divided by the duration of sensor use.

Abstract

Apparatuses and methods for medical monitoring physiological characteristics values such as blood glucose levels for the treatment of diabetes, are presented. The apparatuses and methods provide dynamic glucose monitoring functions that perform predictive analysis to anticipate harmful conditions, such as glucose crash and hyperglycemic incidents for a patient. The dynamic functions can also be used to maximize athletic performance and warn of inadequate nocturnal basal rate. Other aspects include advanced alarm and reminder functions, as well as advanced data presentation tools to further facilitate convenient and efficient management of various physiological conditions.

Description

    BACKGROUND OF THE INVENTION
  • 1. Field of the Invention
  • This invention relates generally to medical monitoring systems. More specifically, this invention relates to methods and systems for monitoring physiological characteristics in individuals including those associated with physiological conditions (e.g. monitoring blood glucose levels in diabetics).
  • 2. Description of the Related Art
  • A variety of electrochemical sensors have been developed for detecting and/or quantifying specific agents or compositions in a patient's blood. Notably, glucose sensors have been developed for use in obtaining an indication of blood glucose levels in a diabetic patient. Such readings are useful in monitoring and/or adjusting a treatment program which typically includes the regular administration of insulin to the patient. Periodic blood glucose readings significantly improve medical therapies using semi-automated medication infusion devices. Some exemplary external infusion devices are described in U.S. Pat. Nos. 4,562,751, 4,678,408 and 4,685,903, while some examples of automated implantable medication infusion devices are described in U.S. Pat. No. 4,573,994, all of which are herein incorporated by reference.
  • Electrochemical sensors can be used to obtain periodic measurements over an extended period of time. Such sensors can include a plurality of exposed electrodes at one end for subcutaneous placement in contact with a user's interstitial fluid, blood, or the like. A corresponding plurality of conductive contacts can be exposed at another end for convenient external electrical connection with a suitable monitoring device through a wire or cable. Exemplary sensors are described in U.S. Pat. No. 5,299,571, U.S. Pat. Nos. 5,390,671; 5,391,250; 5,482,473; and 5,586,553, which are all incorporated by reference herein.
  • Conventional glucose monitoring systems are somewhat limited in features that they provide to facilitate the monitoring of blood glucose levels. Typically, a glucose monitor will take readings as directed by the user and might provide a warning if a reading is deemed at an unsafe level (e.g., a hyper- or hypoglycemic condition). However, by the time the warning occurs, the user may already be experiencing negative symptoms. Furthermore, it may be unacceptable to address this by simply reducing (or raising) the value which triggers an indicator (e.g. an display, an alarm or the like) of an unsafe condition, because this may prompt a user to take “remedial” action (such as administering an additional bolus) when no unsafe condition would have actually materialized. Such an approach merely increases the occurrence of false positive alarms. As a consequence, the unnecessary “remedial” action can actually provoke an unsafe condition. As described above, although existing glucose monitors adequately detect blood glucose levels upon entering the hyperglycemic range, they do not anticipate these conditions.
  • As is known in the art, a glucose crash occurs when blood glucose levels of an individual are in a state of rapid decline and its symptoms are similar to those associated with hypoglycemia. The symptoms are caused by the dynamics of a declining glucose level and not by an absolute glucose level. Specific symptoms can include a feeling of light headedness, sweating, tremors, nervousness and/or disorientation. Disorientation is a particular risk to the patient. If the patient becomes disoriented while operating machinery, the patient could harm himself or others. A glucose crash can be caused by any of the following events: excess insulin administration; an unexpected increase in insulin sensitivity; a fall of free fatty acids in the blood; heavy exercise; or mental or physical stress. As previously mentioned, ordinary glucose monitors provide only for detection of hypoglycemic and hyperglycemic levels.
  • Impaired fasting glucose (IFG) is another condition which is not predicted by conventional glucose monitors. The American Diabetes Association (ADA) identifies IFG as an undesirable glucose condition, defined as a 126 mg/dL or higher blood glucose level at wakeup. Repeated IFG events can contribute to diabetic morbidity. One cause of IFG is an inadequate nocturnal insulin basal infusion rate. Although a patient can deal with the IFG after waking by administering an insulin bolus, it is preferable for the patient to avoid IFG incidents entirely.
  • Typical monitors provide only a single alarm to call attention to the user. This can be problematical in contexts of varying physiological states because a user is not made aware of the specific condition and/or the appropriate degree of urgency. In existing alarm systems, until the user investigates, there is no indication of the reason for the alarm or the severity of the situation.
  • Conventional monitors are designed to alert the user of unsafe conditions, however, many other factors and situations are also important to the user in managing treatment. For example, events such as meals or exercise, as well as entering calibration values are not tied to reminders issued by conventional monitors. In addition, simple alarm systems alarms can provide duplicative warnings which can frustrate users and become ignored if they are excessive.
  • SUMMARY OF THE INVENTION
  • The invention as embodied and disclosed herein pertains to apparatuses and methods for monitoring physiological characteristics such as blood glucose levels. Embodiments of the invention include dynamic monitoring functions that can perform predictive analyses to anticipate harmful conditions, such as hyperglycemic (or hyperglycemic) incidents, before they occur. These dynamic functions can be used to monitor normal physiological functions, as well as in a variety of other contexts including the optimization of athletic performance. Other embodiments of the invention include advanced alarm and reminder functions, as well as advanced data presentation tools. Embodiments of the invention disclosed herein facilitate the convenient and efficient management of diseases such as diabetes.
  • One embodiment of the invention includes a method of monitoring a physiological characteristic of a user using a device including an input element capable of receiving a signal from a sensor that is based on a sensed physiological characteristic value of the user, and a processor for analyzing the received signal. In typical embodiments of the invention, the processor determines a dynamic behavior of the physiological characteristic value and provides an observable indicator based upon the dynamic behavior of the physiological characteristic value so determined. In a preferred embodiment, the physiological characteristic value is a measure of the concentration of blood glucose in the user. In another embodiment, the process of analyzing the received signal and determining a dynamic behavior includes repeatedly measuring the physiological characteristic value to obtain a series of physiological characteristic values to determine how the physiological characteristic is changing over time.
  • In some embodiments of the invention, each of the series of physiological characteristic values includes a smoothing filtered group of repeated physiological characteristic value readings. In such embodiments, a slope of a line fit to the series of physiological characteristic values can be calculated if a most recent of the series of physiological characteristic values is within a qualifying range. In some embodiments of the invention, the physiological characteristic value readings may be decreasing and the slope is negative. Typically, the indicator can also include a warning alarm that is responsive to the dynamic behavior profile of the physiological characteristic value. The warning alarm can also announce an anticipated glucose crash or merely low glucose levels, depending on the operating parameters of the particular dynamic analysis, including comparison of the slope to a threshold rate (e.g., 1% to 3% per minute) and comparison of the current measured value to a qualifying range (e.g., 60 to 150 mg/dL). In typical embodiments, the series of values analyzed is taken from a defined span of time (e.g., ten to thirty minutes).
  • In other typical embodiments of the invention, an anticipated physiological characteristic value is determined from an extrapolated curve based upon the series of physiological characteristic values. In such embodiments the indicator can provide a warning of an anticipated morning glucose incident. In preferred embodiments, the series of values analyzed can also be taken from a defined span of time (e.g. one hour). In one embodiments, the extrapolated curve is determined from a slope of a line fit to the series of physiological characteristic values and an average of the series of physiological characteristic values. In another illustrative embodiment, the anticipated physiological characteristic value can be determined approximately three hours before an anticipated wakeup time. In addition, in certain embodiments, the indicator can be provided if the anticipated value is outside a qualifying range (e.g., approximately 60 mg/dL to 126 mg/dL).
  • In related embodiments of the invention, a slope of a line fit to the series of physiological characteristic values is calculated if a most recent of the series of physiological characteristic values exceeds a threshold value and the slope is positive. In such embodiments, the indicator can provide a warning of an anticipated hyperglycemic incident. In an illustrative embodiment, the series of physiological characteristic values spans a time period of approximately thirty minutes and the indicator will be provided if the slope is steeper than a threshold rate. In this context a typical threshold rate can be approximately 3% per minute and the threshold value can be approximately 180 mg/dL. In such other embodiments, the indicator can provide a warning of an anticipated hypoglycemic incident. In an illustrative embodiment, the series of physiological characteristic values spans a time period of approximately thirty minutes and the indicator will be provided if the slope is steeper than a threshold rate. In this context a typical threshold rate can be approximately 3% per minute and the threshold value can be approximately 70 mg/dL.
  • Another embodiment of the invention includes a physiological characteristic monitor (and corresponding methods for its use) including an input device capable of receiving a signal from a sensor and a processor capable of analyzing the received signal and providing multiple alarms, each of which can be based upon different conditions associated with the physiological characteristic value of the user. In preferred embodiments, the signal is based on a physiological characteristic value of a user. In some embodiments, the multiple alarms are distinguishable from each other and can include any one of a wide variety of signals such as audible signals, visual signals, tactile signals, displays, and/or the like.
  • In some embodiments of the invention, the processor determines a physiological characteristic value from the received signal and the multiple alarms are based upon that value. In such embodiments, each of the multiple alarms can then be triggered if the physiological characteristic value exceeds an associated threshold value.
  • In other embodiments of the invention, one of a first pair of the multiple alarms can be triggered when a narrow range of physiological characteristic values is exceeded. The first pair of the multiple alarms is typically associated with a first upper threshold value and a first lower threshold value, respectively. In further embodiments, a second pair of multiple alarms can be triggered by events a wide range of physiological characteristic values (e.g. exceeding a predetermined value). The second pair of the multiple alarms can be associated with a second upper threshold value and a second lower threshold value, respectively.
  • In yet another embodiment of the invention, a physiological characteristic monitoring method and device are disclosed which include an input device capable of receiving a signal from a sensor and a processor for analyzing the received signal. Typically, the signal is based on a physiological characteristic value of a user. In preferred embodiments, the processor initiates a timer based upon a condition associated with the physiological characteristic value of the user and provides a reminder to the user following expiration of the timer. In some embodiments of the invention, the reminder can include an alarm signal selected from the group consisting of an audible signal, a visual signal, a tactile signal, a display, and/or the like. Typically, the duration of the timer is preset based upon the specific initiating condition.
  • In preferred embodiments of the invention, conditions which trigger the one or more alarms can vary. For example, the conditions which trigger the one or more alarms can be an event marker such as meal markers, exercise markers, high blood glucose markers and low blood glucose markers. The condition(s) which trigger the one or more alarms can further be a reference value that is entered into the monitor and the reminder can indicate that a new reference value should be entered.
  • In other embodiments of the invention, the processor can determine a physiological characteristic value from the received signal and the triggering condition is then based upon that physiological characteristic value. For example, the triggering condition can be situations where the physiological characteristic value exceeds a predetermined threshold value.
  • Other embodiments of the invention include a physiological characteristic monitor including an input device capable of receiving a signal from a sensor, a processor for analyzing the received signal and determining physiological characteristic value data of the user from the received signal, a memory for storing the physiological characteristic value data of the user and a display. Typically, the signal is based on a physiological characteristic value of a user. In preferred embodiments, the display provides a retrospective display of the physiological characteristic value data. In some embodiments of the invention, the stored physiological characteristic value data includes a minimum and maximum blood glucose value and the retrospective display shows the minimum and maximum blood glucose value with a respective time and date. In other embodiments, the stored physiological characteristic value data can include a first number of excursions above an upper blood glucose value and a second number of excursions below a lower blood glucose value and the retrospective display shows the first and second number.
  • In other embodiments of the invention, the stored physiological characteristic value data can include a distribution of blood glucose values and the retrospective display shows a first portion of the blood glucose values above an upper blood glucose value, a second portion of the blood glucose values below a lower blood glucose value and a third portion of the blood glucose values between the upper value and the lower value. In preferred embodiments, the portions can be shown as percentages, times or numbers of readings. The display can include a total time for the physiological characteristic value data as well as the total number of readings for the physiological characteristic value data. In preferred embodiments of the invention, the first portion and the second portion can be shown as integrated values. The integrated values can be based on the sums of magnitude differences from the upper blood glucose value and the lower blood glucose value for the first and second portion, respectively. In such embodiments, the integrated values can be divided by a respective duration of sensor use.
  • BRIEF DESCRIPTION OF THE DRAWINGS
  • Referring now to the drawings in which like reference numbers represent corresponding parts throughout:
  • FIG. 1 is a block diagram of a characteristic monitor embodiment of the present invention.
  • FIG. 2 is a block diagram of a telemetered characteristic monitor embodiment of the present invention;
  • FIG. 3A is a flowchart of a method for anticipating a glucose crash;
  • FIG. 3B is a flowchart of a method for detecting an inadequate nocturnal basal rate;
  • FIG. 3C is a flowchart of a method for anticipating a hyperglycemic incident;
  • FIG. 3D is a flowchart of a method for maximizing athletic performance;
  • FIG. 4 illustrates a multiple alarm function of the invention;
  • FIG. 5 illustrates a reminder function of the invention;
  • FIG. 6A illustrates minimum and maximum data presentation;
  • FIG. 6B illustrates excursion data presentation;
  • FIG. 6C illustrates characteristic value distribution data presentation; and
  • FIG. 6D illustrates integrated characteristic value data presentation.
  • DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENT
  • 1. Overview
  • Embodiments of the present invention encompass methods and systems for the convenient operation of monitoring physiological characteristics (“characteristic monitoring systems”). The description provided here encompasses the architecture of the apparatus as well as its control and convenience features. The control and convenience features of the present invention can be implemented in a wide range of detailed characteristic monitoring system designs. Although embodiments of the present invention are primarily described in the context of glucose monitors used in the treatment of diabetes, the embodiments of the invention are applicable to a wide variety of patient treatment programs where a physiological characteristic is periodically monitored to use in estimating the responsive treatment. For example, embodiments of the invention can be used to determine the status and/or levels of a variety of characteristics including those associated with agents such as hormones, cholesterol, medication concentrations, pH, oxygen saturation, viral loads (e.g., HIV), or the like As is known in the art, a sensor for the characteristic monitor can be implanted in and/or through subcutaneous, dermal, sub-dermal, inter-peritoneal or peritoneal tissue. Such sensors typically communicate a signal from the sensor set to the characteristic monitor.
  • General embodiments of the invention include a physiological characteristic monitor coupled to a sensor set. In preferred embodiments, the sensor set and monitor are for determining glucose levels in the blood and/or body fluids of the user without the use of, or necessity of, a wire or cable connection between the transmitter and the monitor.
  • Embodiments of the characteristic monitor system of the invention are primarily adapted for use in subcutaneous human tissue. Alternatively, embodiments of the invention can be placed in a variety of other types of physiological milieus, such as muscle, lymph, organ tissue, veins, arteries or the like, as well as being used in related environments such as animal tissue. Embodiments of the invention can provide sensor readings on an intermittent, near-continuous or continuous basis.
  • Embodiments of the invention include sensing and advanced predictive functions of the monitor which are designed to anticipate unsafe conditions for a user before they occur. In addition, predictive functions can be employed so that a user can obtain feedback to obtain a desired physical objective, such as maximizing athletic performance. Other functions of the monitor include multiple programmable alarms and reminders. Embodiments of the invention can include advanced display tools to facilitate easy and quick interpretation of information related to the user's condition.
  • 2. Glucose Monitor
  • FIG. 1 is a block diagram of a characteristic monitoring system 100 in accordance with an embodiment of the present invention. The characteristic monitoring system 100 generally includes a sensor set 102 that employs a sensor that produces a signal that corresponds to a measured characteristic of the user, such as a blood glucose level. The sensor set 102 communicates these signals to a characteristic monitor 104 that is designed to interpret these signals to produce a characteristic reading or value for the user, i.e. a measurement of the characteristic. The sensor signals enter the monitor 104 through a sensor input 106 and through the sensor input 106 the signals are conveyed to a processor 108. The processor 108 determines and manipulates the sensor readings within the monitor 104. In addition, but not limited to, the characteristic monitor 104 provides additional functions that will aid in the treatment regime to which the characteristic reading applies. For example, but not limited to, the monitor may track meals, exercise and other activities which affect the treatment of diabetes. These additional functions can be combined with or independent from the characteristic readings determined by the monitor 104.
  • Other components of the monitor 104 support the processor 108 in performing functions. A memory 110 is used to store data and instructions used by the processor 108. A data entry device 112 such as a keypad is used to receive direct input from the user and a display 114 such as a liquid crystal display (LCD), or the like, is used to relate information to the user. In addition, the monitor 104 includes a data port 116, such as a digital input/output (I/O) port.
  • The data port 116 can be used for the monitor to communicate with a computer 118. To facilitate communication, the monitor may interface with the computer 118 through a communication station 120 that can serve as a docking station for the monitor 104, for example. In some embodiments, the data port 116 within the monitor 104 can be directly connected to the computer 118. Through the communication link, data may be downloaded from the monitor, such as stored characteristic readings, settings, programs and other information related to the monitor's function. Thus, advanced analysis can be performed on a computer freeing memory 110 within the monitor 104. Data such as characteristic readings, settings and programs can also be downloaded to the monitor 104. In this way, the monitor 104 can be conveniently reprogrammed without requiring tedious manual entry by the user.
  • FIG. 2 is a block diagram of a telemetered characteristic monitoring system embodiment of the invention. In this system embodiment 200, the sensor input 106 of the monitor 104 is a wireless receiver, such as a radio frequency (RF) receiver. The sensor set 102 provides a signal via wired link to a telemetered monitor transmitter 202 where the signal is interpreted and converted to an RF signal. The wireless receiver sensor input 106 of the monitor 104 converts the signal to data understandable to the monitor processor. With some advantages, the telemetered characteristic monitoring system can perform any or all the functions of the characteristic monitoring system of FIG. 1.
  • A characteristic monitor system 100, in accordance with a preferred embodiment of the present invention includes a sensor set 102, and characteristic monitor device 104. The sensor set 102 generally utilizes an electrode-type sensor. However, in alternative embodiments, the system can use other types of sensors, such as electrically based sensors, chemically based sensors, optically based sensors, or the like. In further alternative embodiments, the sensors can be of a type that is used on the external surface of the skin or placed below the skin layer of the user. Preferred embodiments of a surface mounted sensor utilize interstitial fluid harvested from underneath the skin. The sensor set 102 is connected to the monitor device 104 and provides a signal based upon the monitored characteristic (e.g., blood glucose). The characteristic monitor device 104 utilizes the received signal to determine the characteristic reading or value (e.g., a blood glucose level). In still other embodiments, the sensor may be placed in other parts of the body, such as, but not limited to, subcutaneous, dermal, sub-dermal, inter-peritoneal or peritoneal tissue.
  • The telemetered characteristic monitor transmitter 202 generally includes the capability to transmit data. In alternative embodiments, the telemetered characteristic monitor transmitter 202 can include a receiver, or the like, to facilitate two-way communication between the sensor set 102 and the characteristic monitor 104. In alternative embodiments, the characteristic monitor 104 can be replaced with a data receiver, storage and/or transmitting device for later processing of the transmitted data or programming of the telemetered characteristic monitor transmitter 202. In addition, a relay or repeater (not shown) can be used with a telemetered characteristic monitor transmitter 202 and a characteristic monitor 104 to increase the distance that the telemetered characteristic monitor transmitter 202 can be used with the characteristic monitor 104. For example, the relay can be used to provide information to parents of children using the telemetered characteristic monitor transmitter 202 and the sensor set 102 from a distance. The information can be used when children are in another room during sleep or doing activities in a location remote from the parents. In further embodiments, the relay can include the capability to sound an alarm. In addition, the relay can be capable of providing telemetered characteristic monitor transmitter 202 data from the sensor set 102, as well as other data, to a remotely located individual via a modem connected to the relay for display on a monitor, pager or the like. The data can also be downloaded through the communication station 120 to a remotely located computer 118 such as a PC, lap top, or the like, over communication lines, by modem or wireless connection. As disclosed herein, some embodiments of the invention can omit the communication station 120 and use a direct modem or wireless connection to the computer 118. In further embodiments, the telemetered characteristic monitor transmitter 202 transmits to an RF programmer, which acts as a relay, or shuttle, for data transmission between the sensor set 102 and a PC, laptop, communication station 118, a data processor, or the like. In further alternatives, the telemetered characteristic monitor transmitter 202 can transmit an alarm to a remotely located device, such as a communication station 118, modem or the like to summon help.
  • In addition, further embodiments can include the capability for simultaneous monitoring of multiple sensors and/or include a sensor for multiple measurements.
  • A purpose of the characteristic monitor system 100 is to provide for better treatment and control in an outpatient or a home use environment. For example, the monitor systems 100, 200 can provide indications of glucose levels, a hypoglycemia/hyperglycemia alert and outpatient diagnostics. Embodiments of the invention are also useful as an evaluation tool under a physician's supervision.
  • The characteristic monitor device 104 receives characteristic information, such as glucose data or the like, from the sensor set 102 and displays and logs the received glucose readings. Logged data can be downloaded from the characteristic monitor 104 to a personal computer, laptop, or the like, for detailed data analysis. In further embodiments, the characteristic monitor system 100, 200 can be used in a hospital environment, or the like. Still further embodiments of the present invention can include one or more buttons to record data and events for later analysis, correlation, or the like. Further buttons can include a sensor on/off button to conserve power and to assist in initializing the sensor set 102. The characteristic monitor 200 can also be employed with other medical devices to combine other patient data through a common data network system.
  • Further embodiments of the sensor set 102 can monitor the temperature of the sensor set 102, which can then be used to improve the calibration of the sensor. For example, for a glucose sensor, the enzyme reaction activity may have a known temperature coefficient. The relationship between temperature and enzyme activity can be used to adjust the sensor values to more accurately reflect the actual characteristic levels. In addition to temperature measurements, the oxygen saturation level can be determined by measuring signals from the various electrodes of the sensor set 102. Once obtained, the oxygen saturation level can be used in calibration of the sensor set 102 due to changes in the oxygen saturation levels, and its effects on the chemical reactions in the sensor set 102. For example, as the oxygen level goes lower the sensor sensitivity can be lowered. The oxygen level can be utilized in calibration of the sensor set 102 by adjusting for the changing oxygen saturation. In alternative embodiments, temperature measurements can be used in conjunction with other readings to determine the required sensor calibration.
  • In preferred embodiments, the sensor set 102 facilitates accurate placement of a flexible thin film electrochemical sensor of the type used for monitoring specific blood parameters representative of a user's condition. Preferably, the sensor monitors glucose levels in the body, and can be used in conjunction with automated or semi-automated medication infusion devices of the external or implantable type as described in U.S. Pat. Nos. 4,562,751; 4,678,408; 4,685,903 or 4,573,994 (which are incorporated herein by reference), to control delivery of insulin to a diabetic patient.
  • Embodiments of the flexible electrochemical sensor can be constructed in accordance with thin film mask techniques to include elongated thin film conductors embedded or encased between layers of a selected insulative material such as polyimide film or sheet, and membranes. The sensor electrodes at a tip end of the sensing portion are exposed through one of the insulative layers for direct contact with patient blood or other body fluids, when the sensing portion (or active portion) of the sensor is subcutaneously placed at an insertion site. The sensing portion is joined to a connection portion that terminates in conductive contact pads, or the like, which are also exposed through one of the insulative layers. In alternative embodiments, other types of implantable sensors, such as chemical based, optical based, or the like, can be used. Further description of flexible thin film sensors of this general type are be found in U.S. Pat. No. 5,391,250, entitled “METHOD OF FABRICATING THIN FILM SENSORS”, which is herein incorporated by reference. The connection portion can be conveniently connected electrically to the monitor 104 or a telemetered characteristic monitor transmitter 202 by a connector block (or the like) as shown and described in U.S. Pat. No. 5,482,473, entitled “FLEX CIRCUIT CONNECTOR”, which is also herein incorporated by reference. Thus, in accordance with embodiments of the present invention, subcutaneous sensor sets 102 are configured or formed to work with either a wired or a wireless characteristic monitor system 100, 200.
  • 3. Dynamic Glucose Monitoring Functions
  • Embodiments of the present invention include different types of continuous glucose monitors that identify trends in blood glucose dynamics to facilitate enhanced treatment of diabetes. In general, a first illustrative monitor can be used to anticipate a glucose “crash” (or other hypoglycemic incident) before the onset of debilitating symptoms. Another illustrative monitor can be used to detect an inadequate nocturnal basal rate and alert the patient in order to avoid an impaired fasting glucose incident. Another illustrative monitor can anticipate hyperglycemic (or hypoglycemic) incidents by detecting trends toward those levels and help the patient avoid such incidents. Another illustrative monitor can assist a patient in maximizing athletic performance in endurance type activities (e.g., a marathon race) by detecting trends toward hypoglycemic levels.
  • The disclosed embodiments monitor the dynamics of a physiological characteristic such as blood glucose levels. These embodiments utilize this dynamic monitoring to provide functionality including the anticipation of glucose crash and alerting the patient, the detection of inadequate nocturnal basal rate, the anticipation of hyperglycemic (or hypoglycemic) incidents and maximizing athletic performance. All of these features can be implemented in software operating in the monitor's microprocessor and/or designed into an application specific integrated circuit (ASIC) or other specialized circuitry. Also, dynamic glucose monitoring functions use periodic measurements of a glucose level.
  • A. Monitor for Anticipating a Glucose Crash
  • In one embodiment of the invention, a monitor anticipates a glucose crash by monitoring trends in glucose levels. For example, the monitor can alert the patient when glucose levels are rapidly decreasing. By monitoring such trends or a rate information of measured glucose levels, the monitor can provide a much better warning system to alert the user with enough time to stabilize and reverse a dangerous physiological condition.
  • In some embodiments of the invention, the monitor measures glucose more frequently than typical glucose monitoring devices. For example, one embodiment of the invention measures approximately every minute, whereas other monitors measure a lower rate (e.g., but not limited to, once per 5 minutes). Frequent measurements are taken because of the short time intervals which are evaluated. Alternative embodiments may utilize more frequent measurements, such as, but not limited to, 10 seconds, 1 second, or the like.
  • In an illustrative embodiment, the monitor periodically measures glucose, analyzes the present trend, determines whether a glucose crash incident is probable and appropriately alerts the patient. At some frequent interval (e.g., but not limited to, once per minute), the device measures the glucose level, applies a smoothing filter to the result, and records the filtered value. The smoothing filter may take a weighted sum of past sensor values (so called finite impulse response-FIR-filter), a weighted sum of past sensor values and past filtered values (so called infinite impulse response-IIR-filters), may use simple clipping algorithms (e.g. limit the percent change in filtered output), or employ models to predict the output (e.g. Weiner and Kalman filter designs). For example, if the most recent (filtered) value is in the “qualifying range”, the monitor can calculate the slope of a line fit to the most recent values (most likely, but not limited to, using a Saritzky gulag filter) and determine if the slope is steeper than a selected threshold rate (e.g., but not limited to, 3% or declining at more than 30 mg/dL in ten minutes). If the slope equals or exceeds the threshold rate, a glucose crash incident is likely and the monitor alerts the patient accordingly.
  • Those skilled in the art will understand that in some embodiments the qualifying range can be a closed range (e.g., but not limited to, between 100 and 150 mg/dL) and in other embodiments the qualifying range can be an open range (e.g., but not limited to, greater than 100 mg/dL). By first identifying whether a most recent value is within the qualifying range, further calculation of the dynamic behavior of the physiologic characteristic can be avoided. Thus, the determination of a glucose crash can be unconcerned with rate magnitudes occurring when the current characteristic value is outside of the range, (of course, other alarms, which merely monitor the current characteristic value, can be triggered when the reading is too high or too low). However, in alternate embodiments, the slope can be calculated and compared to the threshold rate with every new value. In further embodiments, multiple qualifying ranges and threshold rates can be applied to evaluate the glucose dynamics and determine triggering a glucose crash warning.
  • In one preferred embodiment, the monitor determines that a glucose crash is likely if three criteria are met. The criteria are as follows. The first, dG/dT (the rate of glucose level change) is negative, can be considered for example in situations where blood glucose levels are dropping (e.g., but not limited to, when a value pertaining to the rate of glucose change is negative). The second, |dG/dT| exceeds a threshold rate, can be considered in contexts, for example where a specified blood glucose change rate is exceeded for a specified sustained period (e.g., but not limited to, greater than 3% per minute for 10 minutes). The third, G, the glucose level, can be considered for example, when this value begins dropping starting within a specified range, (e.g., but not limited to, 100-150 mg/dL).
  • In some embodiments, these criteria can be parameterized to allow the user to customize the values. The qualifying range, threshold rate and period can be general values, applied to all users, or determined from factors specific to the individual user. For example, the monitor can include a feature to adjust the qualifying glucose level range, the maximum rate of glucose change, or in some embodiments, the sustained time period length. In addition, in some embodiments, any or all of the dynamic glucose monitoring functions can enabled or disabled, selectively or together.
  • The following control program pseudo code provides an example of a programming routine performed by the processor of the monitor to implement an embodiment of the invention.
    REPEAT every minute)
    {
    Measure glucose level gi
    Filter gi and store the filtered value g ′i
    IF(g ′i is in range 100-150 mg/dL)
    THEN
    Fit a line to the most recent 10 filtered (or,
    alternatively, unfiltered) values
    IF (dG/dT for that line < ( − 3% per minute )
    THEN
    Alert the patient and record in history
    ENDIF
    ENDIF
    }
    END REPEAT
  • FIG. 3A is a flowchart of a method for anticipating a glucose crash 300. At block 302, a characteristic level is repeatedly measured to obtain a group of characteristic level values. Following this at block 304, a smoothing filter can be applied to the group of characteristic level values to produce a filtered measurement value. The filtered measurement value is recorded at block 306. At block 308 it is determined if the recorded value falls within a qualifying range (e.g., but not limited to, between 100 to 150 mg/dL). If not, the process returns to block 302. If the recorded measurement is within the range, a slope of a line fit to a recent series of recorded filtered values is calculated at block 310. The calculated slope is compared to a threshold rate (e.g., but not limited to, −3% per minute) at block 312. If the calculated slope is not steeper than the threshold rate the process returns to block 302. If the slope exceeds the threshold rate, an anticipated glucose crash is indicated at block 314. Alternative embodiments may utilize similar logic for when the glucose level is already outside of the range and continues to drop. In addition in an alternative preferred embodiment of the invention, one can utilize a raw data measurement (e.g. a group of characteristic level values) to determine a derivative as an alternative to using a filtered measurement value to determine a derivative.
  • B. Monitor for Detecting an Inadequate Nocturnal Basal Rate
  • In another embodiment of the invention, the characteristic monitor can be used to detect an inadequate nocturnal basal rate. This embodiment generally applies to diabetic patients using an insulin infusion device that continually administers insulin at a patient controlled basal rate. The monitor detects an inadequate basal rate (i.e., but not limited to, “low basal rate” or a “high basal rate”), by monitoring trends in glucose levels. The monitor then alerts a patient in the early morning, when glucose levels are high and relatively steady, low and relatively stable or changing rapidly. This gives the patient time to adjust the basal rate of the infusion device upward or downward to and avoid an impaired fasting glucose incident.
  • The monitor operates to track the characteristic level rate. For example, every 5 minutes the monitor measures and records the glucose level. Once a day (e.g., but not limited to, 3 hours before to the anticipated wakeup time), the monitor calculates the average blood glucose and the rate of blood glucose change for the previous hour. The monitor can then determine a prediction of the “morning glucose” level at wake up based upon the calculated average blood glucose and the rate of blood glucose change. In one embodiment the “morning glucose” is predicted assuming that the rate of change remains constant, however in other embodiments nonlinear characteristic curves and functions can be applied in making the prediction. If the anticipated “morning glucose” level is greater than a high threshold value (e.g., but not limited to, 126 mg/dL), or less than a low threshold value (e.g., but not limited to, 60 mg/dL), an alarm is sounded. This will allow time for the infusion device basal rate to be adjusted appropriately. In alternative embodiments, different times before anticipated wakeup, different high threshold values, or different low threshold values, may be used.
  • In some embodiments, the triggering criteria can also be parameterized to allow the user to customize the values. In some embodiments, the user is allowed to set the values for the controlling parameters. For example, the user can set the qualifying low and high glucose levels as well as the anticipated waking time. For each of the settings a default value can be used in the absence of a user setting. For example, a default low glucose level of 60 mg/dL, a default high glucose level of 126 mg/dL and an anticipated waking time of 7:00 AM can be used. In addition, the entire function can be enabled and disabled.
  • FIG. 3B is a flowchart of a method for detecting an inadequate nocturnal basal rate 320. At block 322, the method begins by measuring a characteristic level to obtain a measurement value. The value is recorded at block 324. Measuring and recording is repeated periodically to obtain a series of values at block 326. At block 328, the average of the series of values is calculated. At block 330, a slope of a line fit to the series of values is calculated. The calculated slope and average of the series of values are then used to determine a predictive curve at block 332. At block 334, the curve is extrapolated to predict a glucose level at wakeup. Those skilled in the art understand that such calculations are not limited to slope y=mx+b, and that, in this context, one can use alternative filtered arrangements as are known in the art. The extrapolation is performed some time before wakeup (e.g., but not limited to, 3 hours prior) to provide enough time to correct any impending negative condition. The predicted glucose level is compared to an acceptable range at block 336. If the predicted glucose value falls within the range, the process ends. If the predicted glucose value falls outside the range, a morning glucose incident is reported at block 338.
  • C. Monitor for Anticipating Hyperglycemic Incidents
  • In another embodiment of the invention, a glucose monitor anticipates a hyperglycemic (or hypoglycemic) incident by monitoring trends in glucose levels. The monitor alerts the patient when a “relatively steady increase” (or decrease) in glucose levels occurs. The monitor periodically measures glucose, analyzes the present trend, determines whether a hyperglycemic (or hypoglycemic) incident is probable and appropriately alerts the patient.
  • In one embodiment, the device measures glucose values at a specific time interval (e.g. once every minute), and then, e.g. at 5 minute intervals, applies a smoothing filter to this group of values and records the filtered value. If the most recent (filtered) value exceeds a threshold value (e.g., but not limited to, 180 mg/dL), the monitor calculates the slope of a line fit to a recent series of recorded values (for example, but not limited to, six values). If the slope is greater than a threshold rate (e.g., but not limited to, 3% per minute), a hyperglycemic incident is likely and the monitor alerts the patient. For hypoglycemic incidents, values and thresholds corresponding to low glucose levels would be used.
  • The threshold value is applied in a similar manner to the “qualifying range” applied in determining a glucose crash previously discussed. The threshold value effectively operates as an open range (e.g., but not limited to, greater than 180 mg/dL). In other embodiments, the threshold value can be a closed range. Therefore, determining a hyperglycemic incident can be unconcerned with values below the threshold value (as determining a hypoglycemic incident can be unconcerned with values above a threshold value). In one embodiment, a slope calculation can be avoided if the current reading is outside the range. However, in alternate embodiments, the slope can be calculated and compared to the threshold rate with every new reading. In further embodiments, multiple qualifying ranges and threshold rates can be applied to evaluate the glucose dynamics and determine triggering a hyperglycemic (or hypoglycemic) incident warning.
  • Here again, in some embodiments the criteria can be parameterized to allow the user to customize the controlling values for anticipating hyperglycemic (or hypoglycemic) incidents. For example, some embodiments can allow the user to set the glucose threshold level and/or the threshold rate. Embodiments of the invention can also use default parameters if no user settings are provided (e.g., but not limited to, a threshold level of 180 mg/dL and a maximal rate of 3% per minute). Embodiments of the invention can also enable and disable this function.
  • FIG. 3C is a flowchart of a method for anticipating a hyperglycemic incident 350. The method begins at block 352 by repeatedly measuring a characteristic level to obtain a group of values. At block 354, a smoothing filter is applied to the group of values to obtain a filtered measurement value. The filtered value is recorded at block 356. The recorded value is compared to a threshold value at block 358. If the recorded value does not exceed the threshold value (e.g., but not limited to, 180 mg/dL), the process returns to block 352. If the recorded value does exceed the threshold value, a slope of a line fit to a recent series of values is calculated at block 354. The calculated slope is compared to a threshold rate (e.g., but not limited to, +3% per minute) at block 362. If the slope is not steeper than the threshold rate, the process returns to block 352. If the slope is steeper than the threshold rate, an anticipated hyperglycemic incident is reported at block 364. For hypoglycemic incidents, corresponding steps for low glucose levels would be used. As noted previously, estimates of dG/dt may be calculated by a variety of methods known in the art including the slope (and that such calculations are not limited to, for example, determinations based on y=mx+b).
  • D. Monitor for Maximizing Athletic Performance
  • Dynamic monitoring can also be used to provide feedback based upon the engaged activity of the user. For example, the monitor can be used to maximize performance during an endurance type activity (e.g., but not limited to, a marathon race). The endurance athlete strives to burn glucose rather than fat and accordingly needs to anticipate low glucose levels and ingest carbohydrates early enough to avoid low glucose levels.
  • In such embodiments, the monitor anticipates low glucose levels and alerts the athlete to ingest carbohydrates. It is important to note that this embodiment is not strictly anticipating hypoglycemic incidents. Instead it is anticipating low glucose levels where it would otherwise be too late for the athlete to compensate by ingesting carbohydrates and still perform effectively and/or at full capacity.
  • In one embodiment, once a minute, the device measures a glucose level, applies a smoothing filter and records the filtered value at 5-minute intervals. If the most recent recorded (i.e., filtered) value is in a qualifying range (e.g., but not limited to, 60-140 mg/dL), the processor calculates the slope of a line fit to the most recent six filtered values and determines if the slope is steeper than −1% (i.e., but not limited to, 30 mg/dL in 30 minutes). If the rate of decline exceeds this threshold, a low glucose level is likely and the monitor alerts the athlete accordingly. Thus, for example, but not limited to, to trigger an alarm, the glucose level rate, dG/dT, is negative with a magnitude greater than 1% per minute for 30 minutes beginning in range 60-140 mg/dL.
  • Similar to the glucose crash monitor, in embodiments for maximizing athletic performance the qualifying range can be a closed range (e.g., but not limited to, between 60 and 140 mg/dL) or an open range (e.g., but not limited to, less than 140 mg/dL). By first identifying whether a most recent value is within the qualifying range, further calculation of the dynamic behavior of the physiologic characteristic is avoided. Although, other alarms which merely monitor the current characteristic value can be triggered when the reading is too high or too low. However, in alternate embodiments, the slope can be calculated and compared to the threshold rate with every new value. In further embodiments, multiple qualifying ranges and threshold rates can be applied to evaluate the glucose dynamics and determine triggering a low glucose warning.
  • Here too, these criteria can be parameterized to allow the user to customize the values. Typically, the monitor will allow a user to set the qualifying glucose range and/or enable and disable the function. A default qualifying range (e.g., but not limited to, 60-140 mg/dL) can be used.
  • FIG. 3D is a flowchart of a method for maximizing athletic performance 370. The process begins at block 372, where a characteristic level is repeatedly measured to obtain a group of characteristic level values. Following this at block 374, a smoothing filter can be applied to the group of characteristic level values to produce a filtered measurement value. The filtered measurement value is recorded at block 376. At block 378 it is determined if the recorded value falls within a qualifying range (e.g., but not limited to, between 60 to 140 mg/dL). If not, the process returns to block 372. If the recorded measurement is within the range, a slope of a line fitted to a recent series of recorded filtered values is calculated at block 380. The calculated slope is compared to a threshold rate (e.g., but not limited to, −1% per minute) at block 382. If the calculated slope is not steeper than the threshold rate the process returns to block 372. If the slope exceeds the threshold rate, an anticipated low glucose level is indicated at block 384. As noted previously, estimates of dG/dt may be calculated by slope as well as other methods known in the art.
  • 4. Multiple Glucose Alarm Function
  • Embodiments of the invention can also employ multiple alarms that can be independently set by the user. For example, a continuous glucose monitoring system can have multiple alarms for different glucose values. The system can allow a user to set threshold glucose values that define a “narrow” glucose range (as compared to the ordinary alarm limits). If the user's glucose level passes outside the “narrow” range, an alarm can sound. This alarm alerts the user to monitor his glucose levels more closely. The system can sound a second alarm (preferably having a sound distinguishable from the first “narrow” range alarm) in the even the user's glucose level reaches a more dangerous condition requiring immediate action. Alarm indications may be audible, tactile, vibratory, visual, combinations of alarm indications, or the like. In the case of visual alarm indications, but not limited to, green lights can be displayed for with a range; yellow for the first alarm level; and red for the second alarm level. The visual alarm indications may flash and/or also be combined with other alarm indications.
  • Although the above example describes a two-layer alarm system, further embodiments of the invention can incorporate multiple alarm layers. In addition, the alarms can be set in ranges or separate high and low glucose level alarms can be set. Distinctive sounds can be used for each alarm. For example, each successive high glucose level alarm can have, but is not limited to having, a higher pitch. Successive low glucose level alarms can each have, but are not limited to having, lowering pitches. Alternately, intermittent or wavering volumes that also increase in pitch according to the severity of the condition can be used. In still other embodiments, the user can select or program alarm tones and other sounds and assign them to the various alarms. Also, in some embodiments, these distinguishable alarms can also be set at different volume levels. In addition, as discussed above, the alarms are not limited to audible signals; some embodiments of the invention can also utilize visual alarms, such as flashing lights or displays or tactile alarms, such as vibrating indicators.
  • In still further embodiments, threshold values and associated alarms can be set according to a schedule. For example, but not limited to, particular alarms can be set to be active only during selected portions of the day.
  • FIG. 4 illustrates a multiple alarm function of the invention. A plot of the monitored characteristic value 400 (e.g., blood glucose) changing over time is shown. A typical wide alarm range 402 is defined by an upper threshold value 404 and a lower threshold value 406. If the monitored characteristic value 400 should exceed the defined range and cross either threshold, an alarm is initiated to indicate to the user to check his blood glucose. In one embodiment, a distinctive alarm can be associated with the alarm range 402. Thus, the same alarm is produced whether the range 402 is exceeded by passing the upper threshold value 404 or the lower threshold value 406. In other embodiments, distinctive alarms can be assigned to each threshold value 404, 406. In further embodiments of the invention, other alarm ranges can also be set. For example, a second narrower range 408 can be set with a lower upper threshold value 410 than that of the wider range 402; and a higher lower threshold value 412 than that of the wider range 402. As with the wider range 402, an alarm is initiated if the narrower range is exceeded by the monitor characteristic value 400. Here also, alarms can be the same or different for each threshold 410, 412.
  • The ability to set different ranges and associated alarms allows the monitor to immediately convey some information about the condition of the user even before checking the actual readings. Particularly, using the narrower range 408 and associated alarms allows the user to know of a negative trend that does not require the same urgency as an alarm triggered by the wider range 402. In effect, the user is able to set multiple alarms, each indicating a different level of urgency and/or different conditions. In some embodiments, threshold values for alarms can also be set independent from ranges.
  • In addition, in still further embodiments alarms or indicators can be set according to the direction in which a threshold value is crossed by the monitored characteristic value 400. For example, as the monitored characteristic value 400 crosses a lower threshold value 412 from the narrow range (e.g., but not limited to, at point 414), one type of alarm can be provided. However, when the monitored characteristic value 400 crosses a lower threshold value 412 from the wider range 402 (e.g., but not limited to, at point 416), another type of alarm can be provided. The difference in the alarms is appropriate because only the former case indicates a worsening of the user's condition. In the latter case, the transition actually indicates an improvement in the user's condition. Thus, in some embodiments of the invention, alarms will only be given when crossing a threshold indicates a worsening of the user's condition. In other embodiments, an indicator will also be given when a threshold has been crossed in an improving direction. In these cases, either the same indicator (sound, light, display or other) or different indicators can be used. In a similar manner, reminders can be set to indicate to a user various conditions (not necessarily negative) that will aid in the convenient therapy management.
  • 5. Advanced Blood Glucose Reminder Functions
  • Another aspect of the invention allows the user to set reminders that will be provided by the monitor. The reminders can be alarm signals (including, but not limited to, auditory, visual, tactile, etc.) that are initiated after a timer has run to prompt the user to take action or merely inform the user of a particular status. The reminder is started (i.e. the timer is initiated), when an event occurs and/or certain conditions are met. The alarm signals can be the same or different based upon the triggering events or conditions. These reminders can be used to further assist the user in managing insulin delivery for optimum results. For example, but not limited to, reminders can be set for event markers, blood glucose values, reference values, high or low sensor measurements.
  • Characteristic monitors and infusion devices can use event markers that place tags in the data for events the user experiences (e.g., but not limited to, meals, exercise, and high or low blood glucose). For example, but not limited to, when an infusion device identifies a high or low blood glucose event marker, it can start a timer that reminds the user to check blood glucose levels. This is intended to make therapy safer by encouraging more frequent checks during times that the patient may be at risk from hypoglycemia or hyperglycemia. In addition, this feature can also be applied to characteristic monitors. For example, but not limited to, a characteristic monitor that is used to show low or high blood glucose tags can have a timer set to remind a user to check their blood glucose levels at a later time.
  • In addition, a reminder timer can be set that is triggered if a blood glucose value is entered. For example, but not limited to, the reminder can be if the user enters a low or high blood glucose value into the monitor as a reference or calibration value.
  • A reminder timer can also be triggered by a user providing a reference value to the monitor. Thus, the user can be reminded to supply a new reference value after a minimum time period has elapsed. In this way calibration of the monitor is assured.
  • A blood glucose reminder can also be triggered by high or low measurement from the sensor. Thus, the monitor will request a blood glucose reference value during an excursion away from the normal range of values. The trigger for this reminder can be tempered by setting a minimum time between reminders to avoid pestering the user. This reminder can be used to provide more robust data for curve fitting as correlation improves with variability in the data pairs. The reminder promotes more frequent data collection during more critical periods (e.g., but not limited to, when blood glucose is too high or too low) and therefore the interpolated curve for this period is more reliably representative of the true curve.
  • One aspect behind the use of these reminders is that they also serve to prevent redundant and excessive alarms for the user. For example, if the timer is removed from the previously described high or low measurement reminder, the result would be a simple hypoglycemia or hyperglycemia alarm. Using a reminder, however, the message is not that the user's blood glucose is out of range. Rather, the reminder's message is to check the user's blood glucose with a meter, or the like. If a user's blood glucose is very near an alarm triggering threshold, an alarm might be triggered repeatedly as the value passes back and forth across the threshold. A reminder will set a timer, preventing duplicative warnings for a short period of time, but reminding the user to check blood glucose again when that period has expired. This can provide a better or easier path through the regulatory process. Thus, reminders are less likely to become a nuisance to the user and also prompt more useful data collection. In alternative embodiments, the alarm is triggered again, regardless of the presence of a time, if the glucose level continues to change in the direction of the trend.
  • FIG. 5 illustrates a reminder function of the invention triggered by high or low characteristic values. A plot of a monitored characteristic value 500 (such as, but not limited to, blood glucose) is shown. One or more ranges 502, 504 define safe characteristic values (e.g., but not limited to, a first range 502 being a warning range and a second range 504 being a critical range), such as can be employed using multiple alarms as previously described. When a range is exceeded (e.g., but not limited to, at time 506), an alarm can be triggered but also a timer is started such that a reminder is also initiated after its expiration (e.g., but not limited to, at time 508). Over the timer period further occurrences of exceeding the threshold (e.g., but not limited to, at point 510) will not result in a duplicative alarm.
  • However, the situation can be somewhat different when the intervening triggering event is not identical to the first triggering event. For example, if a first range 502 is exceeded (e.g., but not limited to, at time 512) and a timer is started, but before a reminder can be issued (e.g., but not limited to, at time 514) a second range 504 is exceeded (e.g., but not limited to, at time 516), then the second alarm will be issued and the timer will be restarted. No reminder will be indicated at the theoretical expiration of the first timer (e.g., but not limited to, at time 514), but a reminder will be issued at the expiration of the second timer (e.g., but not limited to, at time 518). In this case, exceeding the second range overrides the first reminder because the second alarm is a different, albeit related, condition. As previously described, however, the use of reminders is not limited to monitoring high and low characteristic values. In a similar manner, reminders can be triggered by user's supplied reference values for calibration as well as event markers entered into the monitor.
  • 6. Glucose Monitoring Information Management
  • Another aspect of the invention is to provide meaningful retrospective information to the patient using the sensor. In particular, a retrospective display of one or more physiological values can provide significantly useful data. As disclosed, the retrospective displays can be designed in a variety of ways to provide various useful information. For example, but not limited to, as the sleeping user receives no benefit from a real-time display, a retrospective view of data is important. While a simple listing of previous values has value, it can be time consuming to review, provides information that is difficult to visualize and comprehend and requires significant memory space within the device. Providing useful information that is easy to understand and that can be stored within a small memory space is very important. The ability to review data from the previous sleep period is particularly helpful to a user with nocturnal hypoglycemia or “dawn effect”, as there is typically no witness to the real-time display. These measures can be even more important in cases where the alarm system can exhibit many false positives and/or false negatives, which might otherwise frustrate the user and lead to non-use of the monitor.
  • The following advanced data presentation tools can be used to conveniently and efficiently store and display useful information on a screen for a user to review while the monitor is in use. The tools provide useful information while requiring only a minimal amount memory space. These data presentation tools can also be used in any retrospective analysis package, such as software running on a computer or network designed to analyze trends and provide advise regarding a treatment regime.
  • The tools operate by processing that compares actual reading to high and low value limits (e.g., but not limited to, acceptable blood glucose ranges). For example, but not limited to, the limits can be the adjustable hypoglycemic and hyperglycemic alarm thresholds of a monitor. Alternately, for standardization, the tools can be applied to a fixed definition of a target blood glucose range that is independent of the hyperglycemic and hypoglycemic alarm thresholds for the particular user/monitor.
  • FIG. 6A illustrates one minimum and maximum data presentation. A display of the minimum and maximum values 600 of the characteristic monitor that have been measured for the user can be displayed on the monitor. The minimum value and maximum values can be conveniently displayed along with the date and time of their occurrence. Such a display 600 is useful, but becomes more useful when combined with an excursion count, a distribution of values, and/or integrated values as discussed below
  • FIG. 6B illustrates an excursion data presentation. The number of excursions above or below the respective blood glucose limits is also very useful to have summarized for the user. An excursion display 602 provides good information, particularly when there are no alarms active on the monitor (either because the monitor is not turned on or alarms are not being employed by the user). A display 602 of the number of excursions above the hyperglycemic limit and the number of excursions below hypoglycemic limit give the user an idea of performance of a treatment program at a glance. A high number of incidents exceeding either limit indicate a need for improvements.
  • FIG. 6C illustrates a characteristic value distribution data presentation. A simple distribution of sensor values offers a very powerful tool. In a preferred embodiment, the distribution is described in percentages that are automatically scaled with the duration of monitor use. Optionally, a monitor can include the total time of use with a percentage distribution. Awareness of a total time provides perspective for reviewing the percentage distribution. A time based distribution can also be used, but requires the total time to be included in the analysis as a reference. A distribution can also be presented based upon the total number of readings, but requires the total time is required in the analysis.
  • For example, but not limited to, the display can show a percentage of readings above a hyperglycemic alarm level, a percentage of readings below a hypoglycemic alarm level and a percentage of readings of readings within alarm range as shown in FIG. 6C. Optionally, the total time covered in the analysis can also be displayed. Similarly, an alternate display can show the time spent above a hyperglycemic alarm level, the time spent below a hypoglycemic alarm level and the time spent within alarm range (not shown). As mentioned, the time base display requires a known total time as part of the analysis. Finally, a display can also include the number of readings above hyperglycemic alarm level, the number of readings below a hypoglycemic alarm level and the number of readings within alarm range (not shown).
  • FIG. 6D illustrates an integrated characteristic value data presentation. Performing an integration of the readings outside the alarm levels with respect to time can provide a measure of the hypoglycemic and hyperglycemic events' severity. In addition, these results can also be scaled these by a total sensor time to provide a measure that is duration independent.
  • For example, a “hyperglycemic area” can be calculated as the sum of the differences between the readings and the hyperglycemic alarm limit. A “hypoglycemic area” can be calculated from the sum of all the differences between the hypoglycemic alarm limit and the readings. A “hyperglycemic index” is calculated by taking the “hyperglycemic area” and dividing it by the duration of sensor use. Similarly, the “hypoglycemic index” can be calculated by taking the “hypoglycemic area” divided by the duration of sensor use.
  • CONCLUSION
  • Various alarms and/or monitoring aspects discussed above may be combined or utilized with other alarms and/or monitoring aspects. The possible embodiments and/or combinations should not be limited to the specific embodiments described above.
  • This concludes the description including the preferred embodiments of the present invention. The foregoing description including the preferred embodiment of the invention has been presented for the purposes of illustration and description. It is not intended to be exhaustive or to limit the invention to the precise form disclosed. Many equivalent modifications and variations are possible in light of the above teaching.
  • It is intended that the scope of the invention be limited not by this detailed description, but rather by the claims appended hereto. The above specification, examples and information provide a description of the manufacture and use of the apparatus and method of the invention. Since many embodiments of the invention can be made without departing from the scope of the invention, the invention resides in the claims hereinafter appended. Throughout this application, various publications are referenced. The disclosures of these publications are hereby incorporated by reference herein in their entireties.

Claims (16)

1-56. (canceled)
57. A physiological characteristic monitor, comprising:
an input device capable of receiving a signal from a sensor, the signal being based on a physiological characteristic value of a user; and
a processor capable of analyzing the received signal and providing multiple alarms each based upon different conditions associated with the physiological characteristic value of the user.
58. The physiological characteristic monitor of claim 57, wherein the multiple alarms are distinguishable from each other.
59. The physiological characteristic monitor of claim 57, wherein the multiple alarms include signals selected from the group consisting of audible signals, visual signals, tactile signals and displays.
60. The physiological characteristic monitor of claim 57, wherein the processor determines a physiological characteristic value from the received signal and the multiple alarms are based upon the physiological characteristic value.
61. The physiological characteristic monitor of claim 60, wherein each of the multiple alarms are triggered if the physiological characteristic value exceeds its associated threshold value.
62. The physiological characteristic monitor of claim 60, wherein one of a first pair of the multiple alarms is triggered when a narrow range of physiological characteristic values is exceeded, and wherein the first pair of the multiple alarms are each associated with a first upper threshold value and a first lower threshold value, respectively.
63. The physiological characteristic monitor of claim 62, wherein one of a second pair of the multiple alarms is triggered by exceeding a wide range of physiological characteristic values, and wherein the second pair of the multiple alarms are each associated with a second upper threshold value and a second lower threshold value, respectively.
64. A method of providing alarms for a physiological characteristic monitor, comprising the steps of:
receiving a signal from a sensor, the signal being based on a physiological characteristic value of a user;
analyzing the received signal; and
providing multiple alarms, where each of the multiple alarms is based upon a different physiological status or condition associated with the physiological characteristic value of the user.
65. The method of claim 64, wherein the multiple alarms are distinguishable from each other.
66. The method of claim 64, wherein the multiple alarms include signals selected from the group consisting of audible signals, visual signals, tactile signals and displays.
67. The method of claim 64, wherein the processor determines a physiological characteristic value from the received signal and the multiple alarms are based upon the physiological characteristic value.
68. The method of claim 67, wherein each of the multiple are triggered if the physiological characteristic value exceeds an associated threshold value.
69. The method of claim 67, wherein one of a first pair of the multiple alarms is triggered by exceeding a narrow range of physiological characteristic values and wherein the first pair of the multiple alarms are each associated with a first upper threshold value and a first lower threshold value, respectively.
70. The method of claim 69, wherein one of a second pair of the multiple alarms is triggered by exceeding a wide range of physiological characteristic values wherein the second pair of the multiple alarms are each associated with a second upper threshold value and a second lower threshold value, respectively.
71.-110. (canceled).
US10/999,671 2001-12-27 2004-11-30 System for monitoring physiological characteristics Abandoned US20050096512A1 (en)

Priority Applications (1)

Application Number Priority Date Filing Date Title
US10/999,671 US20050096512A1 (en) 2001-12-27 2004-11-30 System for monitoring physiological characteristics

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
US10/034,139 US7022072B2 (en) 2001-12-27 2001-12-27 System for monitoring physiological characteristics
US10/999,671 US20050096512A1 (en) 2001-12-27 2004-11-30 System for monitoring physiological characteristics

Related Parent Applications (1)

Application Number Title Priority Date Filing Date
US10/034,139 Division US7022072B2 (en) 2001-12-27 2001-12-27 System for monitoring physiological characteristics

Publications (1)

Publication Number Publication Date
US20050096512A1 true US20050096512A1 (en) 2005-05-05

Family

ID=21874554

Family Applications (4)

Application Number Title Priority Date Filing Date
US10/034,139 Expired - Lifetime US7022072B2 (en) 2001-12-27 2001-12-27 System for monitoring physiological characteristics
US10/999,671 Abandoned US20050096512A1 (en) 2001-12-27 2004-11-30 System for monitoring physiological characteristics
US10/999,658 Abandoned US20050096511A1 (en) 2001-12-27 2004-11-30 System for monitoring physiological characteristics
US10/999,491 Expired - Lifetime US7766830B2 (en) 2001-12-27 2004-11-30 System for monitoring physiological characteristics

Family Applications Before (1)

Application Number Title Priority Date Filing Date
US10/034,139 Expired - Lifetime US7022072B2 (en) 2001-12-27 2001-12-27 System for monitoring physiological characteristics

Family Applications After (2)

Application Number Title Priority Date Filing Date
US10/999,658 Abandoned US20050096511A1 (en) 2001-12-27 2004-11-30 System for monitoring physiological characteristics
US10/999,491 Expired - Lifetime US7766830B2 (en) 2001-12-27 2004-11-30 System for monitoring physiological characteristics

Country Status (4)

Country Link
US (4) US7022072B2 (en)
EP (2) EP1460931A2 (en)
AU (1) AU2002360634A1 (en)
WO (1) WO2003057027A2 (en)

Cited By (119)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20050096511A1 (en) * 2001-12-27 2005-05-05 Fox James K. System for monitoring physiological characteristics
US20080220403A1 (en) * 2007-02-16 2008-09-11 Ohio University System and method for managing diabetes
US20080228055A1 (en) * 2005-06-08 2008-09-18 Sher Philip M Fluctuating Blood Glucose Notification Threshold Profiles and Methods of Use
US20100035334A1 (en) * 2007-12-12 2010-02-11 Eiji Okuda Biological sample measurement apparatus
US7768386B2 (en) 2007-07-31 2010-08-03 Abbott Diabetes Care Inc. Method and apparatus for providing data processing and control in a medical communication system
US7768387B2 (en) 2007-04-14 2010-08-03 Abbott Diabetes Care Inc. Method and apparatus for providing dynamic multi-stage signal amplification in a medical device
US7826382B2 (en) 2008-05-30 2010-11-02 Abbott Diabetes Care Inc. Close proximity communication device and methods
US20100332445A1 (en) * 2009-06-30 2010-12-30 Lifescan, Inc. Analyte testing method and system
US20100332142A1 (en) * 2009-06-30 2010-12-30 Lifescan,Inc. Analyte testing method and device for calculating basal insulin therapy
US20100331654A1 (en) * 2009-06-30 2010-12-30 Lifescan Scotland Ltd. Systems for diabetes management and methods
US7885698B2 (en) 2006-02-28 2011-02-08 Abbott Diabetes Care Inc. Method and system for providing continuous calibration of implantable analyte sensors
US20110077493A1 (en) * 2009-09-29 2011-03-31 Lifescan Scotland Ltd. Analyte testing method and device for diabetes mangement
US7928850B2 (en) 2007-05-08 2011-04-19 Abbott Diabetes Care Inc. Analyte monitoring system and methods
US7996158B2 (en) 2007-05-14 2011-08-09 Abbott Diabetes Care Inc. Method and apparatus for providing data processing and control in a medical communication system
US20110205064A1 (en) * 2010-02-25 2011-08-25 Lifescan Scotland Ltd. Analyte testing method and system with high and low blood glucose trends notification
US8029441B2 (en) 2006-02-28 2011-10-04 Abbott Diabetes Care Inc. Analyte sensor transmitter unit configuration for a data monitoring and management system
US8066639B2 (en) 2003-06-10 2011-11-29 Abbott Diabetes Care Inc. Glucose measuring device for use in personal area network
US8103471B2 (en) 2007-05-14 2012-01-24 Abbott Diabetes Care Inc. Method and apparatus for providing data processing and control in a medical communication system
US8112240B2 (en) 2005-04-29 2012-02-07 Abbott Diabetes Care Inc. Method and apparatus for providing leak detection in data monitoring and management systems
US8116840B2 (en) 2003-10-31 2012-02-14 Abbott Diabetes Care Inc. Method of calibrating of an analyte-measurement device, and associated methods, devices and systems
US8115635B2 (en) 2005-02-08 2012-02-14 Abbott Diabetes Care Inc. RF tag on test strips, test strip vials and boxes
US8121857B2 (en) 2007-02-15 2012-02-21 Abbott Diabetes Care Inc. Device and method for automatic data acquisition and/or detection
US8123686B2 (en) 2007-03-01 2012-02-28 Abbott Diabetes Care Inc. Method and apparatus for providing rolling data in communication systems
US8135548B2 (en) 2006-10-26 2012-03-13 Abbott Diabetes Care Inc. Method, system and computer program product for real-time detection of sensitivity decline in analyte sensors
US8140312B2 (en) 2007-05-14 2012-03-20 Abbott Diabetes Care Inc. Method and system for determining analyte levels
US8140142B2 (en) 2007-04-14 2012-03-20 Abbott Diabetes Care Inc. Method and apparatus for providing data processing and control in medical communication system
US8149117B2 (en) 2007-05-08 2012-04-03 Abbott Diabetes Care Inc. Analyte monitoring system and methods
US8185181B2 (en) 2009-10-30 2012-05-22 Abbott Diabetes Care Inc. Method and apparatus for detecting false hypoglycemic conditions
US8211016B2 (en) 2006-10-25 2012-07-03 Abbott Diabetes Care Inc. Method and system for providing analyte monitoring
US8216138B1 (en) 2007-10-23 2012-07-10 Abbott Diabetes Care Inc. Correlation of alternative site blood and interstitial fluid glucose concentrations to venous glucose concentration
US8219173B2 (en) 2008-09-30 2012-07-10 Abbott Diabetes Care Inc. Optimizing analyte sensor calibration
US8224415B2 (en) 2009-01-29 2012-07-17 Abbott Diabetes Care Inc. Method and device for providing offset model based calibration for analyte sensor
US8226891B2 (en) 2006-03-31 2012-07-24 Abbott Diabetes Care Inc. Analyte monitoring devices and methods therefor
US8239166B2 (en) 2007-05-14 2012-08-07 Abbott Diabetes Care Inc. Method and apparatus for providing data processing and control in a medical communication system
US8260558B2 (en) 2007-05-14 2012-09-04 Abbott Diabetes Care Inc. Method and apparatus for providing data processing and control in a medical communication system
US8323721B2 (en) 2005-12-22 2012-12-04 Bunge Oils, Inc. Phytosterol esterification product and method of making same
US8346335B2 (en) 2008-03-28 2013-01-01 Abbott Diabetes Care Inc. Analyte sensor calibration management
US8368556B2 (en) 2009-04-29 2013-02-05 Abbott Diabetes Care Inc. Method and system for providing data communication in continuous glucose monitoring and management system
US8374668B1 (en) 2007-10-23 2013-02-12 Abbott Diabetes Care Inc. Analyte sensor with lag compensation
US8376945B2 (en) 2006-08-09 2013-02-19 Abbott Diabetes Care Inc. Method and system for providing calibration of an analyte sensor in an analyte monitoring system
US8377031B2 (en) 2007-10-23 2013-02-19 Abbott Diabetes Care Inc. Closed loop control system with safety parameters and methods
US8409093B2 (en) 2007-10-23 2013-04-02 Abbott Diabetes Care Inc. Assessing measures of glycemic variability
US8444560B2 (en) 2007-05-14 2013-05-21 Abbott Diabetes Care Inc. Method and apparatus for providing data processing and control in a medical communication system
US8456301B2 (en) 2007-05-08 2013-06-04 Abbott Diabetes Care Inc. Analyte monitoring system and methods
US8473022B2 (en) 2008-01-31 2013-06-25 Abbott Diabetes Care Inc. Analyte sensor with time lag compensation
US8478557B2 (en) 2009-07-31 2013-07-02 Abbott Diabetes Care Inc. Method and apparatus for providing analyte monitoring system calibration accuracy
US8483967B2 (en) 2009-04-29 2013-07-09 Abbott Diabetes Care Inc. Method and system for providing real time analyte sensor calibration with retrospective backfill
US8497777B2 (en) 2009-04-15 2013-07-30 Abbott Diabetes Care Inc. Analyte monitoring system having an alert
US8515517B2 (en) 2006-10-02 2013-08-20 Abbott Diabetes Care Inc. Method and system for dynamically updating calibration parameters for an analyte sensor
US8514086B2 (en) 2009-08-31 2013-08-20 Abbott Diabetes Care Inc. Displays for a medical device
US8560038B2 (en) 2007-05-14 2013-10-15 Abbott Diabetes Care Inc. Method and apparatus for providing data processing and control in a medical communication system
US8583205B2 (en) 2008-03-28 2013-11-12 Abbott Diabetes Care Inc. Analyte sensor calibration management
US8585591B2 (en) 2005-11-04 2013-11-19 Abbott Diabetes Care Inc. Method and system for providing basal profile modification in analyte monitoring and management systems
US8593109B2 (en) 2006-03-31 2013-11-26 Abbott Diabetes Care Inc. Method and system for powering an electronic device
US8597188B2 (en) 2007-06-21 2013-12-03 Abbott Diabetes Care Inc. Health management devices and methods
US8600681B2 (en) 2007-05-14 2013-12-03 Abbott Diabetes Care Inc. Method and apparatus for providing data processing and control in a medical communication system
US8615282B2 (en) 2004-07-13 2013-12-24 Dexcom, Inc. Analyte sensor
US8617069B2 (en) 2007-06-21 2013-12-31 Abbott Diabetes Care Inc. Health monitor
US8622988B2 (en) 2008-08-31 2014-01-07 Abbott Diabetes Care Inc. Variable rate closed loop control and methods
WO2014007927A1 (en) * 2012-05-29 2014-01-09 The Regents Of The University Of California Sonification system for auditory display of physiological parameters
US8635046B2 (en) 2010-06-23 2014-01-21 Abbott Diabetes Care Inc. Method and system for evaluating analyte sensor response characteristics
US8665091B2 (en) 2007-05-08 2014-03-04 Abbott Diabetes Care Inc. Method and device for determining elapsed sensor life
US8710993B2 (en) 2011-11-23 2014-04-29 Abbott Diabetes Care Inc. Mitigating single point failure of devices in an analyte monitoring system and methods thereof
US8734422B2 (en) 2008-08-31 2014-05-27 Abbott Diabetes Care Inc. Closed loop control with improved alarm functions
US8771183B2 (en) 2004-02-17 2014-07-08 Abbott Diabetes Care Inc. Method and system for providing data communication in continuous glucose monitoring and management system
US8795252B2 (en) 2008-08-31 2014-08-05 Abbott Diabetes Care Inc. Robust closed loop control and methods
US8834366B2 (en) 2007-07-31 2014-09-16 Abbott Diabetes Care Inc. Method and apparatus for providing analyte sensor calibration
US8945094B2 (en) 2010-09-08 2015-02-03 Honeywell International Inc. Apparatus and method for medication delivery using single input-single output (SISO) model predictive control
US8968198B2 (en) 2006-02-22 2015-03-03 Dexcom, Inc. Analyte sensor
US8986208B2 (en) 2008-09-30 2015-03-24 Abbott Diabetes Care Inc. Analyte sensor sensitivity attenuation mitigation
US8993331B2 (en) 2009-08-31 2015-03-31 Abbott Diabetes Care Inc. Analyte monitoring system and methods for managing power and noise
US9008743B2 (en) 2007-04-14 2015-04-14 Abbott Diabetes Care Inc. Method and apparatus for providing data processing and control in medical communication system
US9069536B2 (en) 2011-10-31 2015-06-30 Abbott Diabetes Care Inc. Electronic devices having integrated reset systems and methods thereof
US9125548B2 (en) 2007-05-14 2015-09-08 Abbott Diabetes Care Inc. Method and apparatus for providing data processing and control in a medical communication system
US9204827B2 (en) 2007-04-14 2015-12-08 Abbott Diabetes Care Inc. Method and apparatus for providing data processing and control in medical communication system
US9226701B2 (en) 2009-04-28 2016-01-05 Abbott Diabetes Care Inc. Error detection in critical repeating data in a wireless sensor system
US9247900B2 (en) 2004-07-13 2016-02-02 Dexcom, Inc. Analyte sensor
US9317656B2 (en) 2011-11-23 2016-04-19 Abbott Diabetes Care Inc. Compatibility mechanisms for devices in a continuous analyte monitoring system and methods thereof
US9314195B2 (en) 2009-08-31 2016-04-19 Abbott Diabetes Care Inc. Analyte signal processing device and methods
US9326709B2 (en) 2010-03-10 2016-05-03 Abbott Diabetes Care Inc. Systems, devices and methods for managing glucose levels
US9326707B2 (en) 2008-11-10 2016-05-03 Abbott Diabetes Care Inc. Alarm characterization for analyte monitoring devices and systems
US9339217B2 (en) 2011-11-25 2016-05-17 Abbott Diabetes Care Inc. Analyte monitoring system and methods of use
US9392969B2 (en) 2008-08-31 2016-07-19 Abbott Diabetes Care Inc. Closed loop control and signal attenuation detection
US9474475B1 (en) 2013-03-15 2016-10-25 Abbott Diabetes Care Inc. Multi-rate analyte sensor data collection with sample rate configurable signal processing
US9521968B2 (en) 2005-09-30 2016-12-20 Abbott Diabetes Care Inc. Analyte sensor retention mechanism and methods of use
US9532737B2 (en) 2011-02-28 2017-01-03 Abbott Diabetes Care Inc. Devices, systems, and methods associated with analyte monitoring devices and devices incorporating the same
US9615780B2 (en) 2007-04-14 2017-04-11 Abbott Diabetes Care Inc. Method and apparatus for providing data processing and control in medical communication system
US9622691B2 (en) 2011-10-31 2017-04-18 Abbott Diabetes Care Inc. Model based variable risk false glucose threshold alarm prevention mechanism
US9675290B2 (en) 2012-10-30 2017-06-13 Abbott Diabetes Care Inc. Sensitivity calibration of in vivo sensors used to measure analyte concentration
US9750444B2 (en) 2009-09-30 2017-09-05 Abbott Diabetes Care Inc. Interconnect for on-body analyte monitoring device
US9907492B2 (en) 2012-09-26 2018-03-06 Abbott Diabetes Care Inc. Method and apparatus for improving lag correction during in vivo measurement of analyte concentration with analyte concentration variability and range data
US9943644B2 (en) 2008-08-31 2018-04-17 Abbott Diabetes Care Inc. Closed loop control with reference measurement and methods thereof
US9962091B2 (en) 2002-12-31 2018-05-08 Abbott Diabetes Care Inc. Continuous glucose monitoring system and methods of use
US9968306B2 (en) 2012-09-17 2018-05-15 Abbott Diabetes Care Inc. Methods and apparatuses for providing adverse condition notification with enhanced wireless communication range in analyte monitoring systems
US9980669B2 (en) 2011-11-07 2018-05-29 Abbott Diabetes Care Inc. Analyte monitoring device and methods
US10002233B2 (en) 2007-05-14 2018-06-19 Abbott Diabetes Care Inc. Method and apparatus for providing data processing and control in a medical communication system
US10022499B2 (en) 2007-02-15 2018-07-17 Abbott Diabetes Care Inc. Device and method for automatic data acquisition and/or detection
US10076285B2 (en) 2013-03-15 2018-09-18 Abbott Diabetes Care Inc. Sensor fault detection using analyte sensor data pattern comparison
US10092229B2 (en) 2010-06-29 2018-10-09 Abbott Diabetes Care Inc. Calibration of analyte measurement system
US10111608B2 (en) 2007-04-14 2018-10-30 Abbott Diabetes Care Inc. Method and apparatus for providing data processing and control in medical communication system
US10132793B2 (en) 2012-08-30 2018-11-20 Abbott Diabetes Care Inc. Dropout detection in continuous analyte monitoring data during data excursions
US10136816B2 (en) 2009-08-31 2018-11-27 Abbott Diabetes Care Inc. Medical devices and methods
US10433773B1 (en) 2013-03-15 2019-10-08 Abbott Diabetes Care Inc. Noise rejection methods and apparatus for sparsely sampled analyte sensor data
US10524703B2 (en) 2004-07-13 2020-01-07 Dexcom, Inc. Transcutaneous analyte sensor
US10555695B2 (en) 2011-04-15 2020-02-11 Dexcom, Inc. Advanced analyte sensor calibration and error detection
US10610135B2 (en) 2005-03-10 2020-04-07 Dexcom, Inc. System and methods for processing analyte sensor data for sensor calibration
US10963417B2 (en) 2004-06-04 2021-03-30 Abbott Diabetes Care Inc. Systems and methods for managing diabetes care data
US11000215B1 (en) 2003-12-05 2021-05-11 Dexcom, Inc. Analyte sensor
US11006870B2 (en) 2009-02-03 2021-05-18 Abbott Diabetes Care Inc. Analyte sensor and apparatus for insertion of the sensor
US11213226B2 (en) 2010-10-07 2022-01-04 Abbott Diabetes Care Inc. Analyte monitoring devices and methods
US11229382B2 (en) 2013-12-31 2022-01-25 Abbott Diabetes Care Inc. Self-powered analyte sensor and devices using the same
US11331022B2 (en) 2017-10-24 2022-05-17 Dexcom, Inc. Pre-connected analyte sensors
US11350862B2 (en) 2017-10-24 2022-06-07 Dexcom, Inc. Pre-connected analyte sensors
US11484652B2 (en) 2017-08-02 2022-11-01 Diabeloop Closed-loop blood glucose control systems and methods
US11534089B2 (en) 2011-02-28 2022-12-27 Abbott Diabetes Care Inc. Devices, systems, and methods associated with analyte monitoring devices and devices incorporating the same
US11553883B2 (en) 2015-07-10 2023-01-17 Abbott Diabetes Care Inc. System, device and method of dynamic glucose profile response to physiological parameters
US11596330B2 (en) 2017-03-21 2023-03-07 Abbott Diabetes Care Inc. Methods, devices and system for providing diabetic condition diagnosis and therapy
US11717225B2 (en) 2014-03-30 2023-08-08 Abbott Diabetes Care Inc. Method and apparatus for determining meal start and peak events in analyte monitoring systems
US11793936B2 (en) 2009-05-29 2023-10-24 Abbott Diabetes Care Inc. Medical device antenna systems having external antenna configurations

Families Citing this family (294)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US8974386B2 (en) 1998-04-30 2015-03-10 Abbott Diabetes Care Inc. Analyte monitoring device and methods of use
US6949816B2 (en) 2003-04-21 2005-09-27 Motorola, Inc. Semiconductor component having first surface area for electrically coupling to a semiconductor chip and second surface area for electrically coupling to a substrate, and method of manufacturing same
US8465425B2 (en) 1998-04-30 2013-06-18 Abbott Diabetes Care Inc. Analyte monitoring device and methods of use
US9066695B2 (en) 1998-04-30 2015-06-30 Abbott Diabetes Care Inc. Analyte monitoring device and methods of use
US6175752B1 (en) 1998-04-30 2001-01-16 Therasense, Inc. Analyte monitoring device and methods of use
US8688188B2 (en) 1998-04-30 2014-04-01 Abbott Diabetes Care Inc. Analyte monitoring device and methods of use
US8346337B2 (en) 1998-04-30 2013-01-01 Abbott Diabetes Care Inc. Analyte monitoring device and methods of use
US8480580B2 (en) 1998-04-30 2013-07-09 Abbott Diabetes Care Inc. Analyte monitoring device and methods of use
TW495608B (en) * 1998-08-26 2002-07-21 Sensors For Med & Science Inc Optical-based sensing devices
US7553280B2 (en) * 2000-06-29 2009-06-30 Sensors For Medicine And Science, Inc. Implanted sensor processing system and method
US7584033B2 (en) 2000-08-31 2009-09-01 Strategic Design Federation W. Inc. Automobile monitoring for operation analysis
US6560471B1 (en) 2001-01-02 2003-05-06 Therasense, Inc. Analyte monitoring device and methods of use
EP1397068A2 (en) 2001-04-02 2004-03-17 Therasense, Inc. Blood glucose tracking apparatus and methods
US7135342B2 (en) * 2001-05-04 2006-11-14 Sensors For Medicine And Science, Inc. Electro-optical sensing device with reference channel
NL1018334C2 (en) * 2001-06-20 2002-12-30 Timotheus Joan Marie Lechner Device for locating a cavity in the interior of a body.
US7224281B2 (en) * 2001-08-31 2007-05-29 Draeger Medical Systems, Inc. Patient monitoring and alarm processing system and user interface
US10080529B2 (en) 2001-12-27 2018-09-25 Medtronic Minimed, Inc. System for monitoring physiological characteristics
US20080255438A1 (en) * 2001-12-27 2008-10-16 Medtronic Minimed, Inc. System for monitoring physiological characteristics
US20050027182A1 (en) 2001-12-27 2005-02-03 Uzair Siddiqui System for monitoring physiological characteristics
US7399277B2 (en) * 2001-12-27 2008-07-15 Medtronic Minimed, Inc. System for monitoring physiological characteristics
US7247162B1 (en) * 2002-01-14 2007-07-24 Edwards Lifesciences Corporation Direct access atherectomy devices
US8260393B2 (en) 2003-07-25 2012-09-04 Dexcom, Inc. Systems and methods for replacing signal data artifacts in a glucose sensor data stream
US9282925B2 (en) 2002-02-12 2016-03-15 Dexcom, Inc. Systems and methods for replacing signal artifacts in a glucose sensor data stream
US8010174B2 (en) 2003-08-22 2011-08-30 Dexcom, Inc. Systems and methods for replacing signal artifacts in a glucose sensor data stream
US9247901B2 (en) 2003-08-22 2016-02-02 Dexcom, Inc. Systems and methods for replacing signal artifacts in a glucose sensor data stream
US20080172026A1 (en) 2006-10-17 2008-07-17 Blomquist Michael L Insulin pump having a suspension bolus
US6850788B2 (en) 2002-03-25 2005-02-01 Masimo Corporation Physiological measurement communications adapter
WO2003088830A1 (en) * 2002-04-16 2003-10-30 Carematix, Inc. Method and apparatus for remotely monitoring the condition of a patient
US20030211617A1 (en) * 2002-05-07 2003-11-13 International Business Machines Corporation Blood glucose meter that reminds the user to test after a hypoglycemic event
US6825767B2 (en) 2002-05-08 2004-11-30 Charles Humbard Subscription system for monitoring user well being
CA2466772C (en) * 2002-09-11 2012-08-28 Becton, Dickinson And Company Apparatus and method for monitoring blood glucose levels including convenient display of blood glucose value average and constituent values
US7727181B2 (en) 2002-10-09 2010-06-01 Abbott Diabetes Care Inc. Fluid delivery device with autocalibration
AU2003287735A1 (en) * 2002-11-12 2004-06-03 Argose, Inc. Non-invasive measurement of analytes
US20040106163A1 (en) * 2002-11-12 2004-06-03 Workman Jerome James Non-invasive measurement of analytes
WO2004056264A1 (en) * 2002-12-19 2004-07-08 Novo Nordisk A/S Graphical display for medical devices
WO2004075782A2 (en) * 2003-02-26 2004-09-10 Alfred, E. Mann Institute For Biomedical Engineering At The University Of Southern California An implantable device with sensors for differential monitoring of internal condition
CN1806168B (en) * 2003-04-15 2010-09-29 医药及科学传感器公司 System and method for attenuating the effect of ambient light on an optical sensor
US7679407B2 (en) 2003-04-28 2010-03-16 Abbott Diabetes Care Inc. Method and apparatus for providing peak detection circuitry for data communication systems
JP3566276B1 (en) 2003-05-07 2004-09-15 株式会社日立製作所 Blood glucose meter
US8460243B2 (en) 2003-06-10 2013-06-11 Abbott Diabetes Care Inc. Glucose measuring module and insulin pump combination
US7722536B2 (en) 2003-07-15 2010-05-25 Abbott Diabetes Care Inc. Glucose measuring device integrated into a holster for a personal area network device
US8423113B2 (en) 2003-07-25 2013-04-16 Dexcom, Inc. Systems and methods for processing sensor data
US7519408B2 (en) 2003-11-19 2009-04-14 Dexcom, Inc. Integrated receiver for continuous analyte sensor
US8676287B2 (en) 2003-08-01 2014-03-18 Dexcom, Inc. System and methods for processing analyte sensor data
US8160669B2 (en) 2003-08-01 2012-04-17 Dexcom, Inc. Transcutaneous analyte sensor
US8275437B2 (en) 2003-08-01 2012-09-25 Dexcom, Inc. Transcutaneous analyte sensor
US9135402B2 (en) 2007-12-17 2015-09-15 Dexcom, Inc. Systems and methods for processing sensor data
US6931327B2 (en) * 2003-08-01 2005-08-16 Dexcom, Inc. System and methods for processing analyte sensor data
US8369919B2 (en) 2003-08-01 2013-02-05 Dexcom, Inc. Systems and methods for processing sensor data
US7774145B2 (en) 2003-08-01 2010-08-10 Dexcom, Inc. Transcutaneous analyte sensor
US8886273B2 (en) 2003-08-01 2014-11-11 Dexcom, Inc. Analyte sensor
US8285354B2 (en) 2003-08-01 2012-10-09 Dexcom, Inc. System and methods for processing analyte sensor data
US8761856B2 (en) 2003-08-01 2014-06-24 Dexcom, Inc. System and methods for processing analyte sensor data
US7591801B2 (en) 2004-02-26 2009-09-22 Dexcom, Inc. Integrated delivery device for continuous glucose sensor
US8845536B2 (en) 2003-08-01 2014-09-30 Dexcom, Inc. Transcutaneous analyte sensor
US20070066873A1 (en) 2003-08-22 2007-03-22 Apurv Kamath Systems and methods for processing analyte sensor data
US20140121989A1 (en) 2003-08-22 2014-05-01 Dexcom, Inc. Systems and methods for processing analyte sensor data
US20100056895A1 (en) * 2003-12-02 2010-03-04 Mary Darlene Temple Indicia-coded medical diagnostic apparatus
US8287453B2 (en) 2003-12-05 2012-10-16 Dexcom, Inc. Analyte sensor
US8364231B2 (en) 2006-10-04 2013-01-29 Dexcom, Inc. Analyte sensor
US11633133B2 (en) 2003-12-05 2023-04-25 Dexcom, Inc. Dual electrode system for a continuous analyte sensor
ATE480761T1 (en) * 2003-12-05 2010-09-15 Dexcom Inc CALIBRATION METHODS FOR A CONTINUOUSLY WORKING ANALYTICAL SENSOR
US8532730B2 (en) 2006-10-04 2013-09-10 Dexcom, Inc. Analyte sensor
US20100185071A1 (en) * 2003-12-05 2010-07-22 Dexcom, Inc. Dual electrode system for a continuous analyte sensor
US8423114B2 (en) 2006-10-04 2013-04-16 Dexcom, Inc. Dual electrode system for a continuous analyte sensor
WO2005057175A2 (en) 2003-12-09 2005-06-23 Dexcom, Inc. Signal processing for continuous analyte sensor
US7077810B2 (en) 2004-02-05 2006-07-18 Earlysense Ltd. Techniques for prediction and monitoring of respiration-manifested clinical episodes
US8403865B2 (en) * 2004-02-05 2013-03-26 Earlysense Ltd. Prediction and monitoring of clinical episodes
US20070118054A1 (en) * 2005-11-01 2007-05-24 Earlysense Ltd. Methods and systems for monitoring patients for clinical episodes
US8491492B2 (en) 2004-02-05 2013-07-23 Earlysense Ltd. Monitoring a condition of a subject
US8942779B2 (en) 2004-02-05 2015-01-27 Early Sense Ltd. Monitoring a condition of a subject
WO2009048462A1 (en) 2007-10-09 2009-04-16 Dexcom, Inc. Integrated insulin delivery system with continuous glucose sensor
JP3590054B1 (en) 2004-02-26 2004-11-17 株式会社日立製作所 Blood glucose measurement device
US8808228B2 (en) 2004-02-26 2014-08-19 Dexcom, Inc. Integrated medicament delivery device for use with continuous analyte sensor
US20050228242A1 (en) * 2004-04-08 2005-10-13 Tatsurou Kawamura Health management system
US20070135697A1 (en) * 2004-04-19 2007-06-14 Therasense, Inc. Method and apparatus for providing sensor guard for data monitoring and detection systems
US20070276209A1 (en) * 2004-04-30 2007-11-29 Fumiaki Emoto Blood-Sugar Level Measuring Device
US8961461B2 (en) 2004-05-27 2015-02-24 Baxter International Inc. Multi-state alarm system for a medical pump
ATE484745T1 (en) * 2004-06-03 2010-10-15 Medtronic Minimed Inc SYSTEM FOR MONITORING PHYSIOLOGICAL PROPERTIES ACCORDING TO THE BIOLOGICAL CONDITION OF THE USER
JP2008505695A (en) * 2004-07-07 2008-02-28 オブステケア インコーポレイテッド Method of measuring birth process
US8452368B2 (en) 2004-07-13 2013-05-28 Dexcom, Inc. Transcutaneous analyte sensor
US8565848B2 (en) 2004-07-13 2013-10-22 Dexcom, Inc. Transcutaneous analyte sensor
US20060016700A1 (en) 2004-07-13 2006-01-26 Dexcom, Inc. Transcutaneous analyte sensor
US7783333B2 (en) 2004-07-13 2010-08-24 Dexcom, Inc. Transcutaneous medical device with variable stiffness
EP2335584B1 (en) * 2004-07-13 2015-06-17 DexCom, Inc. Transcutaneous analyte sensor
WO2006050485A1 (en) * 2004-11-02 2006-05-11 Lifescan, Inc. Method and computer program for pattern analysis and reporting of chronic disease state management data
RU2007127254A (en) * 2004-12-17 2009-01-27 Байер Хелткэр Ллк (Us) DEVICE WITH DISPLAY DISPLAYING THE MEASUREMENT TRENDS
US9636450B2 (en) * 2007-02-19 2017-05-02 Udo Hoss Pump system modular components for delivering medication and analyte sensing at seperate insertion sites
WO2006072416A2 (en) * 2005-01-06 2006-07-13 Novo Nordisk A/S A system for analysing data and for assisting a person in navigating the data
US7547281B2 (en) * 2005-02-01 2009-06-16 Medtronic Minimed, Inc. Algorithm sensor augmented bolus estimator for semi-closed loop infusion system
US8251907B2 (en) 2005-02-14 2012-08-28 Optiscan Biomedical Corporation System and method for determining a treatment dose for a patient
CN101160090B (en) * 2005-02-22 2010-12-29 拜尔保健有限公司 Iconic display of markers for a meter
EP1863559A4 (en) 2005-03-21 2008-07-30 Abbott Diabetes Care Inc Method and system for providing integrated medication infusion and analyte monitoring system
US7308292B2 (en) 2005-04-15 2007-12-11 Sensors For Medicine And Science, Inc. Optical-based sensing devices
US7768408B2 (en) 2005-05-17 2010-08-03 Abbott Diabetes Care Inc. Method and system for providing data management in data monitoring system
US20060276771A1 (en) * 2005-06-06 2006-12-07 Galley Paul J System and method providing for user intervention in a diabetes control arrangement
EP1733677A1 (en) 2005-06-18 2006-12-20 Roche Diagnostics GmbH Blood glucose measurement apparatus with signalling device
US8740751B2 (en) * 2005-07-25 2014-06-03 Nike, Inc. Interfaces and systems for displaying athletic performance information on electronic devices
CA2620586A1 (en) 2005-08-31 2007-03-08 Boris P. Kovatchev Improving the accuracy of continuous glucose sensors
US8092379B2 (en) * 2005-09-29 2012-01-10 Nellcor Puritan Bennett Llc Method and system for determining when to reposition a physiological sensor
US8880138B2 (en) 2005-09-30 2014-11-04 Abbott Diabetes Care Inc. Device for channeling fluid and methods of use
US7962188B2 (en) * 2005-10-14 2011-06-14 Masimo Corporation Robust alarm system
US7583190B2 (en) 2005-10-31 2009-09-01 Abbott Diabetes Care Inc. Method and apparatus for providing data communication in data monitoring and management systems
US8150628B2 (en) * 2005-12-30 2012-04-03 The Invention Science Fund I, Llc Establishing a biological recording timeline by artificial marking
US20070156345A1 (en) * 2005-12-30 2007-07-05 Hyde Roderick A Modulating a biological recording with another biological recording
US20070156347A1 (en) * 2005-12-30 2007-07-05 Searete Llc Using a biological recording to obtain time values
US7736310B2 (en) 2006-01-30 2010-06-15 Abbott Diabetes Care Inc. On-body medical device securement
EP1818009A1 (en) * 2006-02-11 2007-08-15 Roche Diagnostics GmbH Portable analysis device with setting mode selection
US20090143658A1 (en) * 2006-02-27 2009-06-04 Edwards Lifesciences Corporation Analyte sensor
US7981034B2 (en) 2006-02-28 2011-07-19 Abbott Diabetes Care Inc. Smart messages and alerts for an infusion delivery and management system
US8920343B2 (en) 2006-03-23 2014-12-30 Michael Edward Sabatino Apparatus for acquiring and processing of physiological auditory signals
US20070226504A1 (en) * 2006-03-24 2007-09-27 Reconnex Corporation Signature match processing in a document registration system
US7801582B2 (en) 2006-03-31 2010-09-21 Abbott Diabetes Care Inc. Analyte monitoring and management system and methods therefor
US7920907B2 (en) 2006-06-07 2011-04-05 Abbott Diabetes Care Inc. Analyte monitoring system and method
US20080177149A1 (en) * 2006-06-16 2008-07-24 Stefan Weinert System and method for collecting patient information from which diabetes therapy may be determined
EP1870026B1 (en) * 2006-06-21 2015-09-30 Roche Diagnostics GmbH Diabetescare system for analyte detection and method to selectively transmit prioritized data.
US9119582B2 (en) 2006-06-30 2015-09-01 Abbott Diabetes Care, Inc. Integrated analyte sensor and infusion device and methods therefor
US8932216B2 (en) 2006-08-07 2015-01-13 Abbott Diabetes Care Inc. Method and system for providing data management in integrated analyte monitoring and infusion system
US8206296B2 (en) 2006-08-07 2012-06-26 Abbott Diabetes Care Inc. Method and system for providing integrated analyte monitoring and infusion system therapy management
JP5266221B2 (en) * 2006-08-08 2013-08-21 コーニンクレッカ フィリップス エレクトロニクス エヌ ヴィ Method and apparatus for monitoring physiological parameters
US9161696B2 (en) 2006-09-22 2015-10-20 Masimo Corporation Modular patient monitor
US8840549B2 (en) * 2006-09-22 2014-09-23 Masimo Corporation Modular patient monitor
US20080119710A1 (en) * 2006-10-31 2008-05-22 Abbott Diabetes Care, Inc. Medical devices and methods of using the same
US8439837B2 (en) * 2006-10-31 2013-05-14 Lifescan, Inc. Systems and methods for detecting hypoglycemic events having a reduced incidence of false alarms
EP1918837A1 (en) * 2006-10-31 2008-05-07 F. Hoffmann-La Roche AG Method for processing a chronological sequence of measurements of a time dependent parameter
US20080119702A1 (en) * 2006-10-31 2008-05-22 Abbott Diabetes Care, Inc. Analyte meter having alert, alarm and test reminder capabilities and methods of use
US8579853B2 (en) 2006-10-31 2013-11-12 Abbott Diabetes Care Inc. Infusion devices and methods
US20080306353A1 (en) * 2006-11-03 2008-12-11 Douglas Joel S Calculation device for metabolic control of critically ill and/or diabetic patients
US20080114215A1 (en) * 2006-11-09 2008-05-15 Isense Corporation Shape recognition of hypoglycemia and hyperglycemia
FI20065735A0 (en) * 2006-11-20 2006-11-20 Salla Koski Measurement, monitoring and management system and its constituent equipment
US20130324823A1 (en) * 2006-11-20 2013-12-05 Modz Oy Measurement device, system and method
US20130331659A1 (en) * 2006-11-20 2013-12-12 Modz Oy User interface of a measurement device and system
US8079955B2 (en) * 2006-11-28 2011-12-20 Isense Corporation Method and apparatus for managing glucose control
EP1933246A1 (en) * 2006-12-14 2008-06-18 F.Hoffmann-La Roche Ag A method for visualising a chronological sequence of measurements
US8092386B1 (en) * 2006-12-22 2012-01-10 Pacesetter, Inc. Method and implantable system for blood-glucose concentration monitoring
EP2109394B1 (en) 2007-01-23 2018-05-23 Ascensia Diabetes Care Holdings AG Analyte-testing device
US8732188B2 (en) 2007-02-18 2014-05-20 Abbott Diabetes Care Inc. Method and system for providing contextual based medication dosage determination
US8930203B2 (en) 2007-02-18 2015-01-06 Abbott Diabetes Care Inc. Multi-function analyte test device and methods therefor
US20080208509A1 (en) * 2007-02-27 2008-08-28 Bayer Healthcare, Llc System and method for graphically plotting and displaying analyte concentration data on a calendar
US20080228056A1 (en) 2007-03-13 2008-09-18 Michael Blomquist Basal rate testing using frequent blood glucose input
US8315709B2 (en) * 2007-03-26 2012-11-20 Medtronic, Inc. System and method for smoothing sampled digital signals
WO2009138976A2 (en) 2008-05-12 2009-11-19 Earlysense Ltd Monitoring, predicting and treating clinical episodes
US8585607B2 (en) 2007-05-02 2013-11-19 Earlysense Ltd. Monitoring, predicting and treating clinical episodes
US20090160656A1 (en) * 2007-10-11 2009-06-25 Mahesh Seetharaman Analyte monitoring system alarms
US8597190B2 (en) 2007-05-18 2013-12-03 Optiscan Biomedical Corporation Monitoring systems and methods with fast initialization
US7751907B2 (en) 2007-05-24 2010-07-06 Smiths Medical Asd, Inc. Expert system for insulin pump therapy
US8221345B2 (en) 2007-05-30 2012-07-17 Smiths Medical Asd, Inc. Insulin pump based expert system
WO2008154312A1 (en) 2007-06-08 2008-12-18 Dexcom, Inc. Integrated medicament delivery device for use with continuous analyte sensor
US9754078B2 (en) * 2007-06-21 2017-09-05 Immersion Corporation Haptic health feedback monitoring
ES2733350T3 (en) 2007-06-27 2019-11-28 Hoffmann La Roche System for medical diagnosis, treatment and prognosis for requested events and procedure
EP2562664B1 (en) * 2007-06-27 2020-11-25 Roche Diabetes Care GmbH System for determining an insulin delivery and communicating a dose in automated pancreas software
US8641618B2 (en) 2007-06-27 2014-02-04 Abbott Diabetes Care Inc. Method and structure for securing a monitoring device element
US8085151B2 (en) 2007-06-28 2011-12-27 Abbott Diabetes Care Inc. Signal converting cradle for medical condition monitoring and management system
US8160900B2 (en) 2007-06-29 2012-04-17 Abbott Diabetes Care Inc. Analyte monitoring and management device and method to analyze the frequency of user interaction with the device
US20090036753A1 (en) * 2007-07-31 2009-02-05 King Allen B Continuous glucose monitoring-directed adjustments in basal insulin rate and insulin bolus dosing formulas
US8063770B2 (en) * 2007-08-01 2011-11-22 Peter Costantino System and method for facial nerve monitoring
US8680986B2 (en) * 2007-08-01 2014-03-25 Peter Costantino System and method for facial nerve monitoring during facial surgery
US20090143725A1 (en) * 2007-08-31 2009-06-04 Abbott Diabetes Care, Inc. Method of Optimizing Efficacy of Therapeutic Agent
US8517941B1 (en) * 2007-10-23 2013-08-27 Pacesetter, Inc. Implantable cardiac device and method for monitoring blood-glucose concentration
US8000918B2 (en) * 2007-10-23 2011-08-16 Edwards Lifesciences Corporation Monitoring and compensating for temperature-related error in an electrochemical sensor
US20090247984A1 (en) * 2007-10-24 2009-10-01 Masimo Laboratories, Inc. Use of microneedles for small molecule metabolite reporter delivery
US8417312B2 (en) 2007-10-25 2013-04-09 Dexcom, Inc. Systems and methods for processing sensor data
WO2009059203A1 (en) * 2007-11-02 2009-05-07 Edwards Lifesciences Corporation Analyte monitoring system having back-up power source for use in either transport of the system or primary power loss
US20090188811A1 (en) 2007-11-28 2009-07-30 Edwards Lifesciences Corporation Preparation and maintenance of sensors
US9839395B2 (en) 2007-12-17 2017-12-12 Dexcom, Inc. Systems and methods for processing sensor data
US20090164239A1 (en) 2007-12-19 2009-06-25 Abbott Diabetes Care, Inc. Dynamic Display Of Glucose Information
USD612279S1 (en) 2008-01-18 2010-03-23 Lifescan Scotland Limited User interface in an analyte meter
US8986253B2 (en) 2008-01-25 2015-03-24 Tandem Diabetes Care, Inc. Two chamber pumps and related methods
EP2252196A4 (en) 2008-02-21 2013-05-15 Dexcom Inc Systems and methods for processing, transmitting and displaying sensor data
WO2009114678A1 (en) * 2008-03-13 2009-09-17 Carolon Company Health monitoring and management system
USD611853S1 (en) 2008-03-21 2010-03-16 Lifescan Scotland Limited Analyte test meter
USD615431S1 (en) 2008-03-21 2010-05-11 Lifescan Scotland Limited Analyte test meter
IL197532A0 (en) * 2008-03-21 2009-12-24 Lifescan Scotland Ltd Analyte testing method and system
USD612275S1 (en) 2008-03-21 2010-03-23 Lifescan Scotland, Ltd. Analyte test meter
US8396528B2 (en) 2008-03-25 2013-03-12 Dexcom, Inc. Analyte sensor
US8241616B2 (en) * 2008-04-03 2012-08-14 Rohm And Haas Company Hair styling composition
US8882684B2 (en) 2008-05-12 2014-11-11 Earlysense Ltd. Monitoring, predicting and treating clinical episodes
US9883809B2 (en) 2008-05-01 2018-02-06 Earlysense Ltd. Monitoring, predicting and treating clinical episodes
WO2009137519A1 (en) * 2008-05-05 2009-11-12 Edwards Lifesciences Corporation Membrane for use with amperometric sensors
US8591410B2 (en) 2008-05-30 2013-11-26 Abbott Diabetes Care Inc. Method and apparatus for providing glycemic control
US8924159B2 (en) * 2008-05-30 2014-12-30 Abbott Diabetes Care Inc. Method and apparatus for providing glycemic control
EP2130487A1 (en) * 2008-06-03 2009-12-09 Microlife Intellectual Property GmbH Glucose meter, a system with a glucose meter, method for operating a glucose meter and a computer program product
US20090305317A1 (en) * 2008-06-05 2009-12-10 Brauer Jacob S User interface for testing device
USD611151S1 (en) 2008-06-10 2010-03-02 Lifescan Scotland, Ltd. Test meter
AU2009268772B2 (en) * 2008-07-07 2014-06-26 Agamatrix, Inc. Integrated blood glucose measurement device
IT1396465B1 (en) * 2008-07-10 2012-12-14 B G Informatica S R L METHOD FOR THE DEFINITION AND INTERACTIVE MANAGEMENT OF A TREATMENT FOR THE CONTROL OF GLYCEMIC RATE IN THE DIABETIC PATIENT AND INTEGRATED DEVICE THAT IMPLEMENTS THIS METHOD
USD611489S1 (en) 2008-07-25 2010-03-09 Lifescan, Inc. User interface display for a glucose meter
US8454904B2 (en) * 2008-07-29 2013-06-04 Roche Diagnostics Operations, Inc. Biosensor container
US8900431B2 (en) * 2008-08-27 2014-12-02 Edwards Lifesciences Corporation Analyte sensor
WO2010025289A2 (en) * 2008-08-28 2010-03-04 Isense Corporation Method and system for communication between wireless devices
US8408421B2 (en) 2008-09-16 2013-04-02 Tandem Diabetes Care, Inc. Flow regulating stopcocks and related methods
US20100095229A1 (en) * 2008-09-18 2010-04-15 Abbott Diabetes Care, Inc. Graphical user interface for glucose monitoring system
USD611372S1 (en) 2008-09-19 2010-03-09 Lifescan Scotland Limited Analyte test meter
WO2010033878A2 (en) 2008-09-19 2010-03-25 David Brown Solute concentration measurement device and related methods
US8287487B2 (en) * 2008-10-15 2012-10-16 Asante Solutions, Inc. Infusion pump system and methods
US11478190B2 (en) 2008-10-29 2022-10-25 Flashback Technologies, Inc. Noninvasive hydration monitoring
US11857293B2 (en) 2008-10-29 2024-01-02 Flashback Technologies, Inc. Rapid detection of bleeding before, during, and after fluid resuscitation
US11395634B2 (en) 2008-10-29 2022-07-26 Flashback Technologies, Inc. Estimating physiological states based on changes in CRI
US11406269B2 (en) 2008-10-29 2022-08-09 Flashback Technologies, Inc. Rapid detection of bleeding following injury
US11395594B2 (en) 2008-10-29 2022-07-26 Flashback Technologies, Inc. Noninvasive monitoring for fluid resuscitation
US11382571B2 (en) 2008-10-29 2022-07-12 Flashback Technologies, Inc. Noninvasive predictive and/or estimative blood pressure monitoring
US8512260B2 (en) 2008-10-29 2013-08-20 The Regents Of The University Of Colorado, A Body Corporate Statistical, noninvasive measurement of intracranial pressure
EP2356579B1 (en) * 2008-10-29 2015-05-20 The Regents of the University of Colorado, a body corporate Long term active learning from large continually changing data sets
WO2010051421A2 (en) * 2008-10-31 2010-05-06 Edwards Lifesciences Corporation Analyte sensor with non-working electrode layer
US9918635B2 (en) 2008-12-23 2018-03-20 Roche Diabetes Care, Inc. Systems and methods for optimizing insulin dosage
US10437962B2 (en) 2008-12-23 2019-10-08 Roche Diabetes Care Inc Status reporting of a structured collection procedure
US9117015B2 (en) 2008-12-23 2015-08-25 Roche Diagnostics Operations, Inc. Management method and system for implementation, execution, data collection, and data analysis of a structured collection procedure which runs on a collection device
US10456036B2 (en) 2008-12-23 2019-10-29 Roche Diabetes Care, Inc. Structured tailoring
US20120011125A1 (en) 2008-12-23 2012-01-12 Roche Diagnostics Operations, Inc. Management method and system for implementation, execution, data collection, and data analysis of a structured collection procedure which runs on a collection device
US8849458B2 (en) 2008-12-23 2014-09-30 Roche Diagnostics Operations, Inc. Collection device with selective display of test results, method and computer program product thereof
CA2747332C (en) 2008-12-23 2015-01-27 F. Hoffmann-La Roche Ag Management method and system for implementation, execution, data collection, and data analysis of a structured collection procedure which runs on a collection device
US8126736B2 (en) 2009-01-23 2012-02-28 Warsaw Orthopedic, Inc. Methods and systems for diagnosing, treating, or tracking spinal disorders
US8685093B2 (en) 2009-01-23 2014-04-01 Warsaw Orthopedic, Inc. Methods and systems for diagnosing, treating, or tracking spinal disorders
US8103456B2 (en) 2009-01-29 2012-01-24 Abbott Diabetes Care Inc. Method and device for early signal attenuation detection using blood glucose measurements
US8560082B2 (en) * 2009-01-30 2013-10-15 Abbott Diabetes Care Inc. Computerized determination of insulin pump therapy parameters using real time and retrospective data processing
DK2409253T3 (en) * 2009-03-16 2019-03-25 Hoffmann La Roche METHOD OF AUTOMATICALLY CREATING A USER-SPECIFIC TARGET DATA RECORDING REGISTER FOR DISCONTINUOUS BLOOD SUGAR MEASUREMENT AND DATA PROCESSOR AND BLOOD SUCCESS MEASURER
US9446194B2 (en) 2009-03-27 2016-09-20 Dexcom, Inc. Methods and systems for promoting glucose management
US8630692B2 (en) 2009-04-30 2014-01-14 Pacesetter, Inc. Method and implantable system for blood-glucose concentration monitoring using parallel methodologies
US20100249965A1 (en) * 2009-03-31 2010-09-30 Agamatrix, Inc. Integrated Blood Glucose Measurement Device
US8467972B2 (en) 2009-04-28 2013-06-18 Abbott Diabetes Care Inc. Closed loop blood glucose control algorithm analysis
EP2432393A2 (en) * 2009-05-22 2012-03-28 Abbott Diabetes Care, Inc. Method and system for reducing false hypoglycemia alarm occurrence
US9218453B2 (en) * 2009-06-29 2015-12-22 Roche Diabetes Care, Inc. Blood glucose management and interface systems and methods
US20100331652A1 (en) * 2009-06-29 2010-12-30 Roche Diagnostics Operations, Inc. Modular diabetes management systems
EP3970610A3 (en) 2009-07-02 2022-05-18 Dexcom, Inc. Analyte sensors and methods of manufacturing same
US9351677B2 (en) 2009-07-02 2016-05-31 Dexcom, Inc. Analyte sensor with increased reference capacity
EP3932309A1 (en) 2009-07-23 2022-01-05 Abbott Diabetes Care, Inc. Continuous analyte measurement system
EP3173014B1 (en) 2009-07-23 2021-08-18 Abbott Diabetes Care, Inc. Real time management of data relating to physiological control of glucose levels
US8641671B2 (en) 2009-07-30 2014-02-04 Tandem Diabetes Care, Inc. Infusion pump system with disposable cartridge having pressure venting and pressure feedback
US20110054284A1 (en) * 2009-08-28 2011-03-03 Edwards Lifesciences Corporation Anti-Coagulant Calibrant Infusion Fluid Source
KR101632308B1 (en) * 2009-09-23 2016-06-21 삼성전자주식회사 Method and apparatus for providing blood glucose management information
US9320461B2 (en) * 2009-09-29 2016-04-26 Abbott Diabetes Care Inc. Method and apparatus for providing notification function in analyte monitoring systems
JP5909037B2 (en) * 2009-10-07 2016-04-26 日本光電工業株式会社 Biological information monitor device with alarm priority changing function and alarm control method
US20110118578A1 (en) * 2009-11-17 2011-05-19 Roche Diagnostics Operations, Inc. Hypoglycemic treatment methods and systems
US8882701B2 (en) 2009-12-04 2014-11-11 Smiths Medical Asd, Inc. Advanced step therapy delivery for an ambulatory infusion pump and system
US9153112B1 (en) 2009-12-21 2015-10-06 Masimo Corporation Modular patient monitor
US20110178382A1 (en) * 2010-01-19 2011-07-21 Topp Claire H Blood glucose ignition interlock
WO2011120018A2 (en) * 2010-03-25 2011-09-29 Rice William H Method and system for identifying volatility in medical data
EP2580589B1 (en) 2010-06-09 2016-08-31 Optiscan Biomedical Corporation Measuring analytes in a fluid sample drawn from a patient
US8532933B2 (en) 2010-06-18 2013-09-10 Roche Diagnostics Operations, Inc. Insulin optimization systems and testing methods with adjusted exit criterion accounting for system noise associated with biomarkers
US10292625B2 (en) 2010-12-07 2019-05-21 Earlysense Ltd. Monitoring a sleeping subject
US10575791B2 (en) 2010-12-22 2020-03-03 Roche Diabetes Care, Inc. Automatic recognition of known patterns in physiological measurement data
ES2864586T3 (en) * 2010-12-22 2021-10-14 Hoffmann La Roche Automatic recognition of known patterns in physiological measurement data
US20120173151A1 (en) 2010-12-29 2012-07-05 Roche Diagnostics Operations, Inc. Methods of assessing diabetes treatment protocols based on protocol complexity levels and patient proficiency levels
US8766803B2 (en) 2011-05-13 2014-07-01 Roche Diagnostics Operations, Inc. Dynamic data collection
US8755938B2 (en) 2011-05-13 2014-06-17 Roche Diagnostics Operations, Inc. Systems and methods for handling unacceptable values in structured collection protocols
US8884751B2 (en) * 2011-07-01 2014-11-11 Albert S. Baldocchi Portable monitor for elderly/infirm individuals
WO2013016212A1 (en) 2011-07-22 2013-01-31 Flashback Technologies, Inc. Hemodynamic reserve monitor and hemodialysis control
US9943269B2 (en) 2011-10-13 2018-04-17 Masimo Corporation System for displaying medical monitoring data
EP2766834B1 (en) 2011-10-13 2022-04-20 Masimo Corporation Medical monitoring hub
ES2703610T3 (en) 2011-12-15 2019-03-11 Becton Dickinson Co Near field telemetry link to pass a shared secret to establish a secure radio frequency communication link in a physiological condition monitoring system
US10149616B2 (en) 2012-02-09 2018-12-11 Masimo Corporation Wireless patient monitoring device
US10307111B2 (en) 2012-02-09 2019-06-04 Masimo Corporation Patient position detection system
WO2013138369A1 (en) 2012-03-16 2013-09-19 Dexcom, Inc. Systems and methods for processing analyte sensor data
US9180242B2 (en) 2012-05-17 2015-11-10 Tandem Diabetes Care, Inc. Methods and devices for multiple fluid transfer
US9555186B2 (en) 2012-06-05 2017-01-31 Tandem Diabetes Care, Inc. Infusion pump system with disposable cartridge having pressure venting and pressure feedback
US9956341B2 (en) 2012-07-03 2018-05-01 Milestone Scientific, Inc. Drug infusion with pressure sensing and non-continuous flow for identification of and injection into fluid-filled anatomic spaces
GB2504299B (en) * 2012-07-24 2016-09-14 Med-Bright Medical Solutions Ltd Device and method for providing information indicative of a stress situation in a human
US9749232B2 (en) 2012-09-20 2017-08-29 Masimo Corporation Intelligent medical network edge router
US9119528B2 (en) 2012-10-30 2015-09-01 Dexcom, Inc. Systems and methods for providing sensitive and specific alarms
US9173998B2 (en) 2013-03-14 2015-11-03 Tandem Diabetes Care, Inc. System and method for detecting occlusions in an infusion pump
WO2014152963A1 (en) * 2013-03-14 2014-09-25 Hodges Camille Dynamic medical ecosystems modeling
WO2015009385A1 (en) 2013-07-19 2015-01-22 Dexcom, Inc. Time averaged basal rate optimizer
WO2015035304A1 (en) 2013-09-06 2015-03-12 Tandem Diabetes Care, Inc. System and method for mitigating risk in automated medicament dosing
EP2851824A1 (en) 2013-09-20 2015-03-25 Sanofi-Aventis Deutschland GmbH Data management unit for supporting health control
EP2851823A1 (en) 2013-09-20 2015-03-25 Sanofi-Aventis Deutschland GmbH Data management unit for supporting health control
US10832818B2 (en) 2013-10-11 2020-11-10 Masimo Corporation Alarm notification system
ES2895520T3 (en) * 2013-10-21 2022-02-21 Hoffmann La Roche Control unit for infusion pump units, including a controlled intervention unit
US20150134801A1 (en) * 2013-11-14 2015-05-14 Broadcom Corporation Making policy-based decisions in a network
CA2935565A1 (en) 2013-12-31 2015-07-09 Senseonics, Incorporated Continuous analyte monitoring system
EP3434184B1 (en) * 2014-04-10 2021-10-27 DexCom, Inc. Glycemic urgency assessment and alerts interface
US10172593B2 (en) 2014-09-03 2019-01-08 Earlysense Ltd. Pregnancy state monitoring
WO2016182200A1 (en) * 2015-05-12 2016-11-17 Samsung Electronics Co., Ltd. Blood glucose measurement apparatus and blood glucose measurement method thereof
CN104921736B (en) * 2015-06-08 2017-08-04 浙江大学 A kind of continuous blood sugar monitoring device for including parameter Estimation function filtration module
US10448844B2 (en) 2015-08-31 2019-10-22 Masimo Corporation Systems and methods for patient fall detection
US10220180B2 (en) 2015-10-16 2019-03-05 Milestone Scientific, Inc. Method and apparatus for performing a peripheral nerve block
US10569016B2 (en) 2015-12-29 2020-02-25 Tandem Diabetes Care, Inc. System and method for switching between closed loop and open loop control of an ambulatory infusion pump
EP3451926A4 (en) 2016-05-02 2019-12-04 Dexcom, Inc. System and method for providing alerts optimized for a user
US10617302B2 (en) 2016-07-07 2020-04-14 Masimo Corporation Wearable pulse oximeter and respiration monitor
US11076777B2 (en) 2016-10-13 2021-08-03 Masimo Corporation Systems and methods for monitoring orientation to reduce pressure ulcer formation
US10632255B2 (en) 2017-02-15 2020-04-28 Milestone Scientific, Inc. Drug infusion device
US11471595B2 (en) 2017-05-04 2022-10-18 Milestone Scientific, Inc. Method and apparatus for performing a peripheral nerve block
EP4290320A3 (en) 2017-05-05 2024-02-21 Ypsomed AG Closed loop control of physiological glucose
CN109470677B (en) * 2017-09-08 2021-11-05 清华大学 Molecular detection device
EP3729446A1 (en) 2017-12-21 2020-10-28 Eli Lilly and Company Closed loop control of physiological glucose
CA3089642A1 (en) 2018-02-09 2019-08-15 Dexcom, Inc. System and method for decision support
EP3782165A1 (en) 2018-04-19 2021-02-24 Masimo Corporation Mobile patient alarm display
EP3574830B1 (en) * 2018-05-30 2023-12-20 Sony Group Corporation Method and device for blood glucose level monitoring
CN108876822B (en) * 2018-07-09 2020-11-20 山东大学 Behavior risk degree evaluation method and home security nursing system
US11224693B2 (en) 2018-10-10 2022-01-18 Tandem Diabetes Care, Inc. System and method for switching between medicament delivery control algorithms
US10646660B1 (en) 2019-05-16 2020-05-12 Milestone Scientific, Inc. Device and method for identification of a target region
USD980091S1 (en) 2020-07-27 2023-03-07 Masimo Corporation Wearable temperature measurement device
USD974193S1 (en) 2020-07-27 2023-01-03 Masimo Corporation Wearable temperature measurement device
CN111991003A (en) * 2020-08-12 2020-11-27 上海萌草科技有限公司 Savitzky-Golay filtering-based continuous blood glucose smoothing method, device, equipment and storage medium
USD1000975S1 (en) 2021-09-22 2023-10-10 Masimo Corporation Wearable temperature measurement device

Citations (61)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US3608542A (en) * 1970-06-12 1971-09-28 Beckman Instruments Inc Physiological monitoring system
US3701345A (en) * 1970-09-29 1972-10-31 Medrad Inc Angiographic injector equipment
US4151831A (en) * 1976-11-15 1979-05-01 Safetime Monitors, Inc. Fertility indicator
US4385272A (en) * 1980-12-24 1983-05-24 Whitehead Gary J Cable checker utilizing logic circuitry
US4444200A (en) * 1981-09-04 1984-04-24 Senoh Kabushiki Kaisha Heart pulse rate measuring system
US4498479A (en) * 1981-06-24 1985-02-12 Kone Oy Electrocardiograph (ECG) electrode testing system
US4510346A (en) * 1983-09-30 1985-04-09 At&T Bell Laboratories Shielded cable
US4562751A (en) * 1984-01-06 1986-01-07 Nason Clyde K Solenoid drive apparatus for an external infusion pump
US4573994A (en) * 1979-04-27 1986-03-04 The Johns Hopkins University Refillable medication infusion apparatus
US4619646A (en) * 1984-01-25 1986-10-28 Fernandez Tresguerres Hernande Device for the delivery-dosing of injectable products
US4676568A (en) * 1986-02-21 1987-06-30 Adc Telecommunications, Inc. Terminal test plug
US4678408A (en) * 1984-01-06 1987-07-07 Pacesetter Infusion, Ltd. Solenoid drive apparatus for an external infusion pump
US4685903A (en) * 1984-01-06 1987-08-11 Pacesetter Infusion, Ltd. External infusion pump apparatus
US4731726A (en) * 1986-05-19 1988-03-15 Healthware Corporation Patient-operated glucose monitor and diabetes management system
US4747824A (en) * 1986-05-30 1988-05-31 Spinello Ronald P Hypodermic anesthetic injection method
US4760730A (en) * 1987-07-14 1988-08-02 Medex, Inc. Calibration system for blood pressure transducer
US4857857A (en) * 1988-11-23 1989-08-15 The Research Foundation Of State University Of New York Electrode catheter testing device
US5080653A (en) * 1990-04-16 1992-01-14 Pacesetter Infusion, Ltd. Infusion pump with dual position syringe locator
US5097122A (en) * 1990-04-16 1992-03-17 Pacesetter Infusion, Ltd. Medication infusion system having optical motion sensor to detect drive mechanism malfunction
US5124661A (en) * 1990-07-23 1992-06-23 I-Stat Corporation Reusable test unit for simulating electrochemical sensor signals for quality assurance of portable blood analyzer instruments
US5219099A (en) * 1991-09-06 1993-06-15 California Institute Of Technology Coaxial lead screw drive syringe pump
US5233986A (en) * 1992-04-10 1993-08-10 Random Technologies, Inc. Time domain reflectometer-integrity testing system and method for medical device electrode
US5262944A (en) * 1992-05-15 1993-11-16 Hewlett-Packard Company Method for use of color and selective highlighting to indicate patient critical events in a centralized patient monitoring system
US5265616A (en) * 1991-11-13 1993-11-30 Fukuda Denshi Kabushiki Kaisha Biological information processing and automatically displaying apparatus
US5309908A (en) * 1991-12-13 1994-05-10 Critikon, Inc. Blood pressure and pulse oximeter monitor
US5331549A (en) * 1992-07-30 1994-07-19 Crawford Jr John M Medical monitor system
US5376070A (en) * 1992-09-29 1994-12-27 Minimed Inc. Data transfer system for an infusion pump
US5390671A (en) * 1994-03-15 1995-02-21 Minimed Inc. Transcutaneous sensor insertion set
US5391250A (en) * 1994-03-15 1995-02-21 Minimed Inc. Method of fabricating thin film sensors
US5414213A (en) * 1992-10-21 1995-05-09 Hillburn; Ralph D. Shielded electric cable
US5482473A (en) * 1994-05-09 1996-01-09 Minimed Inc. Flex circuit connector
US5523534A (en) * 1993-06-28 1996-06-04 Vital Connections, Inc. Shielded carbon lead for medical electrodes
US5557210A (en) * 1992-11-20 1996-09-17 Pacesetter, Inc. Universal cable connector for temporarily connecting implantable stimulation leads and implantable stimulation devices with a non-implantable system analyzer
US5569186A (en) * 1994-04-25 1996-10-29 Minimed Inc. Closed loop infusion pump system with removable glucose sensor
US5586553A (en) * 1995-02-16 1996-12-24 Minimed Inc. Transcutaneous sensor insertion set
US5660163A (en) * 1993-11-19 1997-08-26 Alfred E. Mann Foundation For Scientific Research Glucose sensor assembly
US5662106A (en) * 1993-03-26 1997-09-02 Nellcor Incorporated Oximeter with motion detection for alarm modification
US5665065A (en) * 1995-05-26 1997-09-09 Minimed Inc. Medication infusion device with blood glucose data input
US5683270A (en) * 1994-02-10 1997-11-04 W.W. Fischer Sa Electrical plug-type connector, particularly for medical technology
US5724025A (en) * 1993-10-21 1998-03-03 Tavori; Itzchak Portable vital signs monitor
US5781024A (en) * 1996-07-26 1998-07-14 Diametrics Medical, Inc. Instrument performance verification system
US5792068A (en) * 1992-06-23 1998-08-11 Edentec, Inc. Medical monitor with failure protection
US5822715A (en) * 1997-01-10 1998-10-13 Health Hero Network Diabetes management system and method for controlling blood glucose
US5824959A (en) * 1995-11-02 1998-10-20 Karl Mayer Textilmachinenfabrik Gmbh Flexible electrical cable and associated apparatus
US5834699A (en) * 1996-02-21 1998-11-10 The Whitaker Corporation Cable with spaced helices
US5954643A (en) * 1997-06-09 1999-09-21 Minimid Inc. Insertion set for a transcutaneous sensor
US6030346A (en) * 1996-02-21 2000-02-29 The Whitaker Corporation Ultrasound imaging probe assembly
US6113537A (en) * 1996-04-19 2000-09-05 Castano; Jaime A. Optical method and device for determining blood glucose levels
US6117083A (en) * 1996-02-21 2000-09-12 The Whitaker Corporation Ultrasound imaging probe assembly
US6134460A (en) * 1988-11-02 2000-10-17 Non-Invasive Technology, Inc. Spectrophotometers with catheters for measuring internal tissue
US6175752B1 (en) * 1998-04-30 2001-01-16 Therasense, Inc. Analyte monitoring device and methods of use
US20010011324A1 (en) * 1996-12-11 2001-08-02 Hidetoshi Sakaki Method of data migration
US6339720B1 (en) * 1999-09-20 2002-01-15 Fernando Anzellini Early warning apparatus for acute Myocardial Infarction in the first six hours of pain
US6447459B1 (en) * 2000-04-07 2002-09-10 Pds Healthcare Products, Inc. Device and method for measuring lung performance
US20030010040A1 (en) * 2001-04-27 2003-01-16 Robert Torres Method and apparatus for the delivery of liquefied gases having constant impurity levels
US6551276B1 (en) * 1998-08-18 2003-04-22 Medtronic Minimed, Inc. External infusion device with remote programming bolus estimator and/or vibration alarm capabilities
US6558351B1 (en) * 1999-06-03 2003-05-06 Medtronic Minimed, Inc. Closed loop system for controlling insulin infusion
US20030125612A1 (en) * 2001-12-27 2003-07-03 Fox James Kelly System for monitoring physiological characteristics
US20030187336A1 (en) * 2002-03-29 2003-10-02 Hiroshi Odagiri Portable device for collecting information about living body, and system and method for collecting information about living body
US20030208113A1 (en) * 2001-07-18 2003-11-06 Mault James R Closed loop glycemic index system
US6925324B2 (en) * 2000-05-30 2005-08-02 Vladimir Shusterman System and device for multi-scale analysis and representation of physiological data

Family Cites Families (50)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US3972320A (en) * 1974-08-12 1976-08-03 Gabor Ujhelyi Kalman Patient monitoring system
US4365636A (en) * 1981-06-19 1982-12-28 Medicon, Inc. Method of monitoring patient respiration and predicting apnea therefrom
US4490711A (en) * 1981-12-21 1984-12-25 Johnston Robert W Electronic programmable multiple alarm timing device and record
US4588303A (en) * 1984-06-25 1986-05-13 Mediminder Development Limited Partnership Medical timer apparatus
US5142484A (en) * 1988-05-12 1992-08-25 Health Tech Services Corporation An interactive patient assistance device for storing and dispensing prescribed medication and physical device
US5108889A (en) * 1988-10-12 1992-04-28 Thorne, Smith, Astill Technologies, Inc. Assay for determining analyte using mercury release followed by detection via interaction with aluminum
US6066847A (en) * 1989-01-19 2000-05-23 Futrex Inc. Procedure for verifying the accuracy of non-invasive blood glucose measurement instruments
US5107469A (en) * 1990-07-31 1992-04-21 Miles Inc. Digital low-power programmable alarm clock for use with reflectance photometer instruments and the like
US5251126A (en) * 1990-10-29 1993-10-05 Miles Inc. Diabetes data analysis and interpretation method
US5134661A (en) * 1991-03-04 1992-07-28 Reinsch Roger A Method of capture and analysis of digitized image data
US20010011224A1 (en) * 1995-06-07 2001-08-02 Stephen James Brown Modular microprocessor-based health monitoring system
US5299571A (en) 1993-01-22 1994-04-05 Eli Lilly And Company Apparatus and method for implantation of sensors
US5438983A (en) * 1993-09-13 1995-08-08 Hewlett-Packard Company Patient alarm detection using trend vector analysis
US5791344A (en) * 1993-11-19 1998-08-11 Alfred E. Mann Foundation For Scientific Research Patient monitoring system
US5536249A (en) * 1994-03-09 1996-07-16 Visionary Medical Products, Inc. Pen-type injector with a microprocessor and blood characteristic monitor
DE4415896A1 (en) * 1994-05-05 1995-11-09 Boehringer Mannheim Gmbh Analysis system for monitoring the concentration of an analyte in the blood of a patient
US5752512A (en) 1995-05-10 1998-05-19 Massachusetts Institute Of Technology Apparatus and method for non-invasive blood analyte measurement
US6119686A (en) * 1996-03-29 2000-09-19 Datex-Ohmeda, Inc. Apnea detection for medical ventilator
US5890929A (en) 1996-06-19 1999-04-06 Masimo Corporation Shielded medical connector
WO1998054822A1 (en) * 1997-05-26 1998-12-03 Denso Corporation Ac generator for vehicle
US5823715A (en) * 1997-09-29 1998-10-20 The United States Of America As Represented By The Secretary Of The Navy Rapidly deployed pier
EP0945962B2 (en) * 1997-10-16 2007-05-02 Denso Corporation Method and apparatus for twisting the turn portions of u-shaped stator conductorsegments
CA2547299C (en) * 1997-12-04 2009-03-03 Roche Diagnostics Corporation Instrument and method
US6579690B1 (en) * 1997-12-05 2003-06-17 Therasense, Inc. Blood analyte monitoring through subcutaneous measurement
US6047201A (en) * 1998-04-02 2000-04-04 Jackson, Iii; William H. Infant blood oxygen monitor and SIDS warning device
US7647237B2 (en) * 1998-04-29 2010-01-12 Minimed, Inc. Communication station and software for interfacing with an infusion pump, analyte monitor, analyte meter, or the like
WO1999058973A1 (en) * 1998-05-13 1999-11-18 Cygnus, Inc. Method and device for predicting physiological values
US6166644A (en) * 1998-09-10 2000-12-26 Senior Technologies, Inc. Patient monitoring system
JP3196738B2 (en) * 1998-09-11 2001-08-06 株式会社デンソー Stator manufacturing apparatus and stator manufacturing method
DE69926900T3 (en) 1998-09-30 2012-10-04 Medtronic Minimed, Inc. COMMUNICATION STATION AND SOFTWARE WITH AN INFUSION PUMP, ANALYSIS MONITORING SYSTEM, ANALYTY METER, OR SIMILAR EQUIPMENT
ATE514372T1 (en) 1998-10-08 2011-07-15 Medtronic Minimed Inc LICENSE PLATE MONITORING SYSTEM WITH REMOTE MEASUREMENT
US6398727B1 (en) * 1998-12-23 2002-06-04 Baxter International Inc. Method and apparatus for providing patient care
US6424847B1 (en) * 1999-02-25 2002-07-23 Medtronic Minimed, Inc. Glucose monitor calibration methods
US6925393B1 (en) 1999-11-18 2005-08-02 Roche Diagnostics Gmbh System for the extrapolation of glucose concentration
DE10108862A1 (en) 2000-02-15 2001-10-04 Bcs Bio Und Chemosensoren Gmbh Arrangement for support and self-treatment of ill persons, especially diabetics, ensures that persons take the correct doses and take measurements such as blood sugar level at the correct times, for entry into a computer
US6895263B2 (en) * 2000-02-23 2005-05-17 Medtronic Minimed, Inc. Real time self-adjusting calibration algorithm
FI115289B (en) 2000-02-23 2005-04-15 Polar Electro Oy Measurement of an organism's energy metabolism and glucose levels
US6572542B1 (en) * 2000-03-03 2003-06-03 Medtronic, Inc. System and method for monitoring and controlling the glycemic state of a patient
CA2408338C (en) * 2000-08-18 2009-09-08 Cygnus, Inc. Methods and devices for prediction of hypoglycemic events
KR20020072562A (en) 2000-10-27 2002-09-16 디지털 앤젤 코포레이션 Systems and methods for monitoring and tracking
US6560471B1 (en) * 2001-01-02 2003-05-06 Therasense, Inc. Analyte monitoring device and methods of use
US20020133067A1 (en) * 2001-03-15 2002-09-19 Jackson William H. New born and premature infant SIDS warning device
EP1397068A2 (en) * 2001-04-02 2004-03-17 Therasense, Inc. Blood glucose tracking apparatus and methods
US6685651B2 (en) * 2001-05-02 2004-02-03 Denise M Anker Periodic breast self-examination prompting device
US7399277B2 (en) * 2001-12-27 2008-07-15 Medtronic Minimed, Inc. System for monitoring physiological characteristics
US20050027182A1 (en) * 2001-12-27 2005-02-03 Uzair Siddiqui System for monitoring physiological characteristics
GB2418258B (en) * 2002-06-05 2006-08-23 Diabetes Diagnostics Inc Analyte testing device
US20040068230A1 (en) 2002-07-24 2004-04-08 Medtronic Minimed, Inc. System for providing blood glucose measurements to an infusion device
US7278983B2 (en) 2002-07-24 2007-10-09 Medtronic Minimed, Inc. Physiological monitoring device for controlling a medication infusion device
US7291107B2 (en) * 2004-08-26 2007-11-06 Roche Diagnostics Operations, Inc. Insulin bolus recommendation system

Patent Citations (61)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US3608542A (en) * 1970-06-12 1971-09-28 Beckman Instruments Inc Physiological monitoring system
US3701345A (en) * 1970-09-29 1972-10-31 Medrad Inc Angiographic injector equipment
US4151831A (en) * 1976-11-15 1979-05-01 Safetime Monitors, Inc. Fertility indicator
US4573994A (en) * 1979-04-27 1986-03-04 The Johns Hopkins University Refillable medication infusion apparatus
US4385272A (en) * 1980-12-24 1983-05-24 Whitehead Gary J Cable checker utilizing logic circuitry
US4498479A (en) * 1981-06-24 1985-02-12 Kone Oy Electrocardiograph (ECG) electrode testing system
US4444200A (en) * 1981-09-04 1984-04-24 Senoh Kabushiki Kaisha Heart pulse rate measuring system
US4510346A (en) * 1983-09-30 1985-04-09 At&T Bell Laboratories Shielded cable
US4562751A (en) * 1984-01-06 1986-01-07 Nason Clyde K Solenoid drive apparatus for an external infusion pump
US4678408A (en) * 1984-01-06 1987-07-07 Pacesetter Infusion, Ltd. Solenoid drive apparatus for an external infusion pump
US4685903A (en) * 1984-01-06 1987-08-11 Pacesetter Infusion, Ltd. External infusion pump apparatus
US4619646A (en) * 1984-01-25 1986-10-28 Fernandez Tresguerres Hernande Device for the delivery-dosing of injectable products
US4676568A (en) * 1986-02-21 1987-06-30 Adc Telecommunications, Inc. Terminal test plug
US4731726A (en) * 1986-05-19 1988-03-15 Healthware Corporation Patient-operated glucose monitor and diabetes management system
US4747824A (en) * 1986-05-30 1988-05-31 Spinello Ronald P Hypodermic anesthetic injection method
US4760730A (en) * 1987-07-14 1988-08-02 Medex, Inc. Calibration system for blood pressure transducer
US6134460A (en) * 1988-11-02 2000-10-17 Non-Invasive Technology, Inc. Spectrophotometers with catheters for measuring internal tissue
US4857857A (en) * 1988-11-23 1989-08-15 The Research Foundation Of State University Of New York Electrode catheter testing device
US5080653A (en) * 1990-04-16 1992-01-14 Pacesetter Infusion, Ltd. Infusion pump with dual position syringe locator
US5097122A (en) * 1990-04-16 1992-03-17 Pacesetter Infusion, Ltd. Medication infusion system having optical motion sensor to detect drive mechanism malfunction
US5124661A (en) * 1990-07-23 1992-06-23 I-Stat Corporation Reusable test unit for simulating electrochemical sensor signals for quality assurance of portable blood analyzer instruments
US5219099A (en) * 1991-09-06 1993-06-15 California Institute Of Technology Coaxial lead screw drive syringe pump
US5265616A (en) * 1991-11-13 1993-11-30 Fukuda Denshi Kabushiki Kaisha Biological information processing and automatically displaying apparatus
US5309908A (en) * 1991-12-13 1994-05-10 Critikon, Inc. Blood pressure and pulse oximeter monitor
US5233986A (en) * 1992-04-10 1993-08-10 Random Technologies, Inc. Time domain reflectometer-integrity testing system and method for medical device electrode
US5262944A (en) * 1992-05-15 1993-11-16 Hewlett-Packard Company Method for use of color and selective highlighting to indicate patient critical events in a centralized patient monitoring system
US5792068A (en) * 1992-06-23 1998-08-11 Edentec, Inc. Medical monitor with failure protection
US5331549A (en) * 1992-07-30 1994-07-19 Crawford Jr John M Medical monitor system
US5376070A (en) * 1992-09-29 1994-12-27 Minimed Inc. Data transfer system for an infusion pump
US5414213A (en) * 1992-10-21 1995-05-09 Hillburn; Ralph D. Shielded electric cable
US5557210A (en) * 1992-11-20 1996-09-17 Pacesetter, Inc. Universal cable connector for temporarily connecting implantable stimulation leads and implantable stimulation devices with a non-implantable system analyzer
US5662106A (en) * 1993-03-26 1997-09-02 Nellcor Incorporated Oximeter with motion detection for alarm modification
US5523534A (en) * 1993-06-28 1996-06-04 Vital Connections, Inc. Shielded carbon lead for medical electrodes
US5724025A (en) * 1993-10-21 1998-03-03 Tavori; Itzchak Portable vital signs monitor
US5660163A (en) * 1993-11-19 1997-08-26 Alfred E. Mann Foundation For Scientific Research Glucose sensor assembly
US5683270A (en) * 1994-02-10 1997-11-04 W.W. Fischer Sa Electrical plug-type connector, particularly for medical technology
US5390671A (en) * 1994-03-15 1995-02-21 Minimed Inc. Transcutaneous sensor insertion set
US5391250A (en) * 1994-03-15 1995-02-21 Minimed Inc. Method of fabricating thin film sensors
US5569186A (en) * 1994-04-25 1996-10-29 Minimed Inc. Closed loop infusion pump system with removable glucose sensor
US5482473A (en) * 1994-05-09 1996-01-09 Minimed Inc. Flex circuit connector
US5586553A (en) * 1995-02-16 1996-12-24 Minimed Inc. Transcutaneous sensor insertion set
US5665065A (en) * 1995-05-26 1997-09-09 Minimed Inc. Medication infusion device with blood glucose data input
US5824959A (en) * 1995-11-02 1998-10-20 Karl Mayer Textilmachinenfabrik Gmbh Flexible electrical cable and associated apparatus
US5834699A (en) * 1996-02-21 1998-11-10 The Whitaker Corporation Cable with spaced helices
US6117083A (en) * 1996-02-21 2000-09-12 The Whitaker Corporation Ultrasound imaging probe assembly
US6030346A (en) * 1996-02-21 2000-02-29 The Whitaker Corporation Ultrasound imaging probe assembly
US6113537A (en) * 1996-04-19 2000-09-05 Castano; Jaime A. Optical method and device for determining blood glucose levels
US5781024A (en) * 1996-07-26 1998-07-14 Diametrics Medical, Inc. Instrument performance verification system
US20010011324A1 (en) * 1996-12-11 2001-08-02 Hidetoshi Sakaki Method of data migration
US5822715A (en) * 1997-01-10 1998-10-13 Health Hero Network Diabetes management system and method for controlling blood glucose
US5954643A (en) * 1997-06-09 1999-09-21 Minimid Inc. Insertion set for a transcutaneous sensor
US6175752B1 (en) * 1998-04-30 2001-01-16 Therasense, Inc. Analyte monitoring device and methods of use
US6551276B1 (en) * 1998-08-18 2003-04-22 Medtronic Minimed, Inc. External infusion device with remote programming bolus estimator and/or vibration alarm capabilities
US6558351B1 (en) * 1999-06-03 2003-05-06 Medtronic Minimed, Inc. Closed loop system for controlling insulin infusion
US6339720B1 (en) * 1999-09-20 2002-01-15 Fernando Anzellini Early warning apparatus for acute Myocardial Infarction in the first six hours of pain
US6447459B1 (en) * 2000-04-07 2002-09-10 Pds Healthcare Products, Inc. Device and method for measuring lung performance
US6925324B2 (en) * 2000-05-30 2005-08-02 Vladimir Shusterman System and device for multi-scale analysis and representation of physiological data
US20030010040A1 (en) * 2001-04-27 2003-01-16 Robert Torres Method and apparatus for the delivery of liquefied gases having constant impurity levels
US20030208113A1 (en) * 2001-07-18 2003-11-06 Mault James R Closed loop glycemic index system
US20030125612A1 (en) * 2001-12-27 2003-07-03 Fox James Kelly System for monitoring physiological characteristics
US20030187336A1 (en) * 2002-03-29 2003-10-02 Hiroshi Odagiri Portable device for collecting information about living body, and system and method for collecting information about living body

Cited By (377)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20050096511A1 (en) * 2001-12-27 2005-05-05 Fox James K. System for monitoring physiological characteristics
US9962091B2 (en) 2002-12-31 2018-05-08 Abbott Diabetes Care Inc. Continuous glucose monitoring system and methods of use
US10750952B2 (en) 2002-12-31 2020-08-25 Abbott Diabetes Care Inc. Continuous glucose monitoring system and methods of use
US10039881B2 (en) 2002-12-31 2018-08-07 Abbott Diabetes Care Inc. Method and system for providing data communication in continuous glucose monitoring and management system
US8066639B2 (en) 2003-06-10 2011-11-29 Abbott Diabetes Care Inc. Glucose measuring device for use in personal area network
US9730584B2 (en) 2003-06-10 2017-08-15 Abbott Diabetes Care Inc. Glucose measuring device for use in personal area network
US8647269B2 (en) 2003-06-10 2014-02-11 Abbott Diabetes Care Inc. Glucose measuring device for use in personal area network
US8512239B2 (en) 2003-06-10 2013-08-20 Abbott Diabetes Care Inc. Glucose measuring device for use in personal area network
US8116840B2 (en) 2003-10-31 2012-02-14 Abbott Diabetes Care Inc. Method of calibrating of an analyte-measurement device, and associated methods, devices and systems
US8684930B2 (en) 2003-10-31 2014-04-01 Abbott Diabetes Care Inc. Method of calibrating an analyte-measurement device, and associated methods, devices and systems
US8219175B2 (en) 2003-10-31 2012-07-10 Abbott Diabetes Care Inc. Method of calibrating an analyte-measurement device, and associated methods, devices and systems
US8219174B2 (en) 2003-10-31 2012-07-10 Abbott Diabetes Care Inc. Method of calibrating an analyte-measurement device, and associated methods, devices and systems
US11000215B1 (en) 2003-12-05 2021-05-11 Dexcom, Inc. Analyte sensor
US11020031B1 (en) 2003-12-05 2021-06-01 Dexcom, Inc. Analyte sensor
US11627900B2 (en) 2003-12-05 2023-04-18 Dexcom, Inc. Analyte sensor
US8771183B2 (en) 2004-02-17 2014-07-08 Abbott Diabetes Care Inc. Method and system for providing data communication in continuous glucose monitoring and management system
US10963417B2 (en) 2004-06-04 2021-03-30 Abbott Diabetes Care Inc. Systems and methods for managing diabetes care data
US11507530B2 (en) 2004-06-04 2022-11-22 Abbott Diabetes Care Inc. Systems and methods for managing diabetes care data
US11182332B2 (en) 2004-06-04 2021-11-23 Abbott Diabetes Care Inc. Systems and methods for managing diabetes care data
US9668677B2 (en) 2004-07-13 2017-06-06 Dexcom, Inc. Analyte sensor
US10813576B2 (en) 2004-07-13 2020-10-27 Dexcom, Inc. Analyte sensor
US10918315B2 (en) 2004-07-13 2021-02-16 Dexcom, Inc. Analyte sensor
US10993641B2 (en) 2004-07-13 2021-05-04 Dexcom, Inc. Analyte sensor
US10799159B2 (en) 2004-07-13 2020-10-13 Dexcom, Inc. Analyte sensor
US10799158B2 (en) 2004-07-13 2020-10-13 Dexcom, Inc. Analyte sensor
US11883164B2 (en) 2004-07-13 2024-01-30 Dexcom, Inc. System and methods for processing analyte sensor data for sensor calibration
US10722152B2 (en) 2004-07-13 2020-07-28 Dexcom, Inc. Analyte sensor
US11064917B2 (en) 2004-07-13 2021-07-20 Dexcom, Inc. Analyte sensor
US10993642B2 (en) 2004-07-13 2021-05-04 Dexcom, Inc. Analyte sensor
US10709362B2 (en) 2004-07-13 2020-07-14 Dexcom, Inc. Analyte sensor
US10709363B2 (en) 2004-07-13 2020-07-14 Dexcom, Inc. Analyte sensor
US10932700B2 (en) 2004-07-13 2021-03-02 Dexcom, Inc. Analyte sensor
US10980452B2 (en) 2004-07-13 2021-04-20 Dexcom, Inc. Analyte sensor
US8615282B2 (en) 2004-07-13 2013-12-24 Dexcom, Inc. Analyte sensor
US11045120B2 (en) 2004-07-13 2021-06-29 Dexcom, Inc. Analyte sensor
US11026605B1 (en) 2004-07-13 2021-06-08 Dexcom, Inc. Analyte sensor
US10827956B2 (en) 2004-07-13 2020-11-10 Dexcom, Inc. Analyte sensor
US10918314B2 (en) 2004-07-13 2021-02-16 Dexcom, Inc. Analyte sensor
US10918313B2 (en) 2004-07-13 2021-02-16 Dexcom, Inc. Analyte sensor
US9247900B2 (en) 2004-07-13 2016-02-02 Dexcom, Inc. Analyte sensor
US10524703B2 (en) 2004-07-13 2020-01-07 Dexcom, Inc. Transcutaneous analyte sensor
US10314525B2 (en) 2004-07-13 2019-06-11 Dexcom, Inc. Analyte sensor
US8390455B2 (en) 2005-02-08 2013-03-05 Abbott Diabetes Care Inc. RF tag on test strips, test strip vials and boxes
US8223021B2 (en) 2005-02-08 2012-07-17 Abbott Diabetes Care Inc. RF tag on test strips, test strip vials and boxes
US8542122B2 (en) 2005-02-08 2013-09-24 Abbott Diabetes Care Inc. Glucose measurement device and methods using RFID
US8358210B2 (en) 2005-02-08 2013-01-22 Abbott Diabetes Care Inc. RF tag on test strips, test strip vials and boxes
US8115635B2 (en) 2005-02-08 2012-02-14 Abbott Diabetes Care Inc. RF tag on test strips, test strip vials and boxes
US11000213B2 (en) 2005-03-10 2021-05-11 Dexcom, Inc. System and methods for processing analyte sensor data for sensor calibration
US10898114B2 (en) 2005-03-10 2021-01-26 Dexcom, Inc. System and methods for processing analyte sensor data for sensor calibration
US10925524B2 (en) 2005-03-10 2021-02-23 Dexcom, Inc. System and methods for processing analyte sensor data for sensor calibration
US10610135B2 (en) 2005-03-10 2020-04-07 Dexcom, Inc. System and methods for processing analyte sensor data for sensor calibration
US10610137B2 (en) 2005-03-10 2020-04-07 Dexcom, Inc. System and methods for processing analyte sensor data for sensor calibration
US10918318B2 (en) 2005-03-10 2021-02-16 Dexcom, Inc. System and methods for processing analyte sensor data for sensor calibration
US10918316B2 (en) 2005-03-10 2021-02-16 Dexcom, Inc. System and methods for processing analyte sensor data for sensor calibration
US10856787B2 (en) 2005-03-10 2020-12-08 Dexcom, Inc. System and methods for processing analyte sensor data for sensor calibration
US10610136B2 (en) 2005-03-10 2020-04-07 Dexcom, Inc. System and methods for processing analyte sensor data for sensor calibration
US10743801B2 (en) 2005-03-10 2020-08-18 Dexcom, Inc. System and methods for processing analyte sensor data for sensor calibration
US10617336B2 (en) 2005-03-10 2020-04-14 Dexcom, Inc. System and methods for processing analyte sensor data for sensor calibration
US10918317B2 (en) 2005-03-10 2021-02-16 Dexcom, Inc. System and methods for processing analyte sensor data for sensor calibration
US11051726B2 (en) 2005-03-10 2021-07-06 Dexcom, Inc. System and methods for processing analyte sensor data for sensor calibration
US10709364B2 (en) 2005-03-10 2020-07-14 Dexcom, Inc. System and methods for processing analyte sensor data for sensor calibration
US10716498B2 (en) 2005-03-10 2020-07-21 Dexcom, Inc. System and methods for processing analyte sensor data for sensor calibration
US8112240B2 (en) 2005-04-29 2012-02-07 Abbott Diabetes Care Inc. Method and apparatus for providing leak detection in data monitoring and management systems
US7670288B2 (en) * 2005-06-08 2010-03-02 Sher Philip M Fluctuating blood glucose notification threshold profiles and methods of use
US20080228055A1 (en) * 2005-06-08 2008-09-18 Sher Philip M Fluctuating Blood Glucose Notification Threshold Profiles and Methods of Use
US10813577B2 (en) 2005-06-21 2020-10-27 Dexcom, Inc. Analyte sensor
US9521968B2 (en) 2005-09-30 2016-12-20 Abbott Diabetes Care Inc. Analyte sensor retention mechanism and methods of use
US11538580B2 (en) 2005-11-04 2022-12-27 Abbott Diabetes Care Inc. Method and system for providing basal profile modification in analyte monitoring and management systems
US9323898B2 (en) 2005-11-04 2016-04-26 Abbott Diabetes Care Inc. Method and system for providing basal profile modification in analyte monitoring and management systems
US9669162B2 (en) 2005-11-04 2017-06-06 Abbott Diabetes Care Inc. Method and system for providing basal profile modification in analyte monitoring and management systems
US8585591B2 (en) 2005-11-04 2013-11-19 Abbott Diabetes Care Inc. Method and system for providing basal profile modification in analyte monitoring and management systems
US8323721B2 (en) 2005-12-22 2012-12-04 Bunge Oils, Inc. Phytosterol esterification product and method of making same
US9724028B2 (en) 2006-02-22 2017-08-08 Dexcom, Inc. Analyte sensor
US8968198B2 (en) 2006-02-22 2015-03-03 Dexcom, Inc. Analyte sensor
US10117614B2 (en) 2006-02-28 2018-11-06 Abbott Diabetes Care Inc. Method and system for providing continuous calibration of implantable analyte sensors
US10945647B2 (en) 2006-02-28 2021-03-16 Abbott Diabetes Care Inc. Analyte sensor transmitter unit configuration for a data monitoring and management system
US8506482B2 (en) 2006-02-28 2013-08-13 Abbott Diabetes Care Inc. Method and system for providing continuous calibration of implantable analyte sensors
US10159433B2 (en) 2006-02-28 2018-12-25 Abbott Diabetes Care Inc. Analyte sensor transmitter unit configuration for a data monitoring and management system
US11872039B2 (en) 2006-02-28 2024-01-16 Abbott Diabetes Care Inc. Method and system for providing continuous calibration of implantable analyte sensors
US7885698B2 (en) 2006-02-28 2011-02-08 Abbott Diabetes Care Inc. Method and system for providing continuous calibration of implantable analyte sensors
US11064916B2 (en) 2006-02-28 2021-07-20 Abbott Diabetes Care Inc. Analyte sensor transmitter unit configuration for a data monitoring and management system
US11179072B2 (en) 2006-02-28 2021-11-23 Abbott Diabetes Care Inc. Analyte sensor transmitter unit configuration for a data monitoring and management system
US9364149B2 (en) 2006-02-28 2016-06-14 Abbott Diabetes Care Inc. Analyte sensor transmitter unit configuration for a data monitoring and management system
US11179071B2 (en) 2006-02-28 2021-11-23 Abbott Diabetes Care Inc Analyte sensor transmitter unit configuration for a data monitoring and management system
US8029441B2 (en) 2006-02-28 2011-10-04 Abbott Diabetes Care Inc. Analyte sensor transmitter unit configuration for a data monitoring and management system
US8593109B2 (en) 2006-03-31 2013-11-26 Abbott Diabetes Care Inc. Method and system for powering an electronic device
US9380971B2 (en) 2006-03-31 2016-07-05 Abbott Diabetes Care Inc. Method and system for powering an electronic device
US9625413B2 (en) 2006-03-31 2017-04-18 Abbott Diabetes Care Inc. Analyte monitoring devices and methods therefor
US8933664B2 (en) 2006-03-31 2015-01-13 Abbott Diabetes Care Inc. Method and system for powering an electronic device
US9743863B2 (en) 2006-03-31 2017-08-29 Abbott Diabetes Care Inc. Method and system for powering an electronic device
US8597575B2 (en) 2006-03-31 2013-12-03 Abbott Diabetes Care Inc. Analyte monitoring devices and methods therefor
US8226891B2 (en) 2006-03-31 2012-07-24 Abbott Diabetes Care Inc. Analyte monitoring devices and methods therefor
US9039975B2 (en) 2006-03-31 2015-05-26 Abbott Diabetes Care Inc. Analyte monitoring devices and methods therefor
US11864894B2 (en) 2006-08-09 2024-01-09 Abbott Diabetes Care Inc. Method and system for providing calibration of an analyte sensor in an analyte monitoring system
US8376945B2 (en) 2006-08-09 2013-02-19 Abbott Diabetes Care Inc. Method and system for providing calibration of an analyte sensor in an analyte monitoring system
US10278630B2 (en) 2006-08-09 2019-05-07 Abbott Diabetes Care Inc. Method and system for providing calibration of an analyte sensor in an analyte monitoring system
US9833181B2 (en) 2006-08-09 2017-12-05 Abbot Diabetes Care Inc. Method and system for providing calibration of an analyte sensor in an analyte monitoring system
US9408566B2 (en) 2006-08-09 2016-08-09 Abbott Diabetes Care Inc. Method and system for providing calibration of an analyte sensor in an analyte monitoring system
US9357959B2 (en) 2006-10-02 2016-06-07 Abbott Diabetes Care Inc. Method and system for dynamically updating calibration parameters for an analyte sensor
US10342469B2 (en) 2006-10-02 2019-07-09 Abbott Diabetes Care Inc. Method and system for dynamically updating calibration parameters for an analyte sensor
US9629578B2 (en) 2006-10-02 2017-04-25 Abbott Diabetes Care Inc. Method and system for dynamically updating calibration parameters for an analyte sensor
US8515517B2 (en) 2006-10-02 2013-08-20 Abbott Diabetes Care Inc. Method and system for dynamically updating calibration parameters for an analyte sensor
US9839383B2 (en) 2006-10-02 2017-12-12 Abbott Diabetes Care Inc. Method and system for dynamically updating calibration parameters for an analyte sensor
US10194868B2 (en) 2006-10-25 2019-02-05 Abbott Diabetes Care Inc. Method and system for providing analyte monitoring
US8211016B2 (en) 2006-10-25 2012-07-03 Abbott Diabetes Care Inc. Method and system for providing analyte monitoring
US8216137B2 (en) 2006-10-25 2012-07-10 Abbott Diabetes Care Inc. Method and system for providing analyte monitoring
US9113828B2 (en) 2006-10-25 2015-08-25 Abbott Diabetes Care Inc. Method and system for providing analyte monitoring
US9814428B2 (en) 2006-10-25 2017-11-14 Abbott Diabetes Care Inc. Method and system for providing analyte monitoring
US11282603B2 (en) 2006-10-25 2022-03-22 Abbott Diabetes Care Inc. Method and system for providing analyte monitoring
US8718958B2 (en) 2006-10-26 2014-05-06 Abbott Diabetes Care Inc. Method, system and computer program product for real-time detection of sensitivity decline in analyte sensors
US11722229B2 (en) 2006-10-26 2023-08-08 Abbott Diabetes Care Inc. Method, system and computer program product for real-time detection of sensitivity decline in analyte sensors
US10903914B2 (en) 2006-10-26 2021-01-26 Abbott Diabetes Care Inc. Method, system and computer program product for real-time detection of sensitivity decline in analyte sensors
US8135548B2 (en) 2006-10-26 2012-03-13 Abbott Diabetes Care Inc. Method, system and computer program product for real-time detection of sensitivity decline in analyte sensors
US9882660B2 (en) 2006-10-26 2018-01-30 Abbott Diabetes Care Inc. Method, system and computer program product for real-time detection of sensitivity decline in analyte sensors
US10022499B2 (en) 2007-02-15 2018-07-17 Abbott Diabetes Care Inc. Device and method for automatic data acquisition and/or detection
US8121857B2 (en) 2007-02-15 2012-02-21 Abbott Diabetes Care Inc. Device and method for automatic data acquisition and/or detection
US8417545B2 (en) 2007-02-15 2013-04-09 Abbott Diabetes Care Inc. Device and method for automatic data acquisition and/or detection
US10617823B2 (en) 2007-02-15 2020-04-14 Abbott Diabetes Care Inc. Device and method for automatic data acquisition and/or detection
US8676601B2 (en) 2007-02-15 2014-03-18 Abbott Diabetes Care Inc. Device and method for automatic data acquisition and/or detection
US20080220403A1 (en) * 2007-02-16 2008-09-11 Ohio University System and method for managing diabetes
US9801545B2 (en) 2007-03-01 2017-10-31 Abbott Diabetes Care Inc. Method and apparatus for providing rolling data in communication systems
US9095290B2 (en) 2007-03-01 2015-08-04 Abbott Diabetes Care Inc. Method and apparatus for providing rolling data in communication systems
US8123686B2 (en) 2007-03-01 2012-02-28 Abbott Diabetes Care Inc. Method and apparatus for providing rolling data in communication systems
US10349877B2 (en) 2007-04-14 2019-07-16 Abbott Diabetes Care Inc. Method and apparatus for providing data processing and control in medical communication system
US8149103B2 (en) 2007-04-14 2012-04-03 Abbott Diabetes Care Inc. Method and apparatus for providing dynamic multi-stage amplification in a medical device
US9008743B2 (en) 2007-04-14 2015-04-14 Abbott Diabetes Care Inc. Method and apparatus for providing data processing and control in medical communication system
US9204827B2 (en) 2007-04-14 2015-12-08 Abbott Diabetes Care Inc. Method and apparatus for providing data processing and control in medical communication system
US7768387B2 (en) 2007-04-14 2010-08-03 Abbott Diabetes Care Inc. Method and apparatus for providing dynamic multi-stage signal amplification in a medical device
US10111608B2 (en) 2007-04-14 2018-10-30 Abbott Diabetes Care Inc. Method and apparatus for providing data processing and control in medical communication system
US8698615B2 (en) 2007-04-14 2014-04-15 Abbott Diabetes Care Inc. Method and apparatus for providing dynamic multi-stage signal amplification in a medical device
US9615780B2 (en) 2007-04-14 2017-04-11 Abbott Diabetes Care Inc. Method and apparatus for providing data processing and control in medical communication system
US7948369B2 (en) 2007-04-14 2011-05-24 Abbott Diabetes Care Inc. Method and apparatus for providing dynamic multi-stage signal amplification in a medical device
US11039767B2 (en) 2007-04-14 2021-06-22 Abbott Diabetes Care Inc. Method and apparatus for providing data processing and control in medical communication system
US9743866B2 (en) 2007-04-14 2017-08-29 Abbott Diabetes Care Inc. Method and apparatus for providing dynamic multi-stage signal amplification in a medical device
US9402584B2 (en) 2007-04-14 2016-08-02 Abbott Diabetes Care Inc. Method and apparatus for providing dynamic multi-stage signal amplification in a medical device
US10194846B2 (en) 2007-04-14 2019-02-05 Abbott Diabetes Care Inc. Method and apparatus for providing dynamic multi-stage signal amplification in a medical device
US8427298B2 (en) 2007-04-14 2013-04-23 Abbott Diabetes Care Inc. Method and apparatus for providing dynamic multi-stage amplification in a medical device
US8937540B2 (en) 2007-04-14 2015-01-20 Abbott Diabetes Care Inc. Method and apparatus for providing dynamic multi-stage signal amplification in a medical device
US8140142B2 (en) 2007-04-14 2012-03-20 Abbott Diabetes Care Inc. Method and apparatus for providing data processing and control in medical communication system
US8461985B2 (en) 2007-05-08 2013-06-11 Abbott Diabetes Care Inc. Analyte monitoring system and methods
US8456301B2 (en) 2007-05-08 2013-06-04 Abbott Diabetes Care Inc. Analyte monitoring system and methods
US8149117B2 (en) 2007-05-08 2012-04-03 Abbott Diabetes Care Inc. Analyte monitoring system and methods
US9000929B2 (en) 2007-05-08 2015-04-07 Abbott Diabetes Care Inc. Analyte monitoring system and methods
US9177456B2 (en) 2007-05-08 2015-11-03 Abbott Diabetes Care Inc. Analyte monitoring system and methods
US8665091B2 (en) 2007-05-08 2014-03-04 Abbott Diabetes Care Inc. Method and device for determining elapsed sensor life
US9035767B2 (en) 2007-05-08 2015-05-19 Abbott Diabetes Care Inc. Analyte monitoring system and methods
US9949678B2 (en) 2007-05-08 2018-04-24 Abbott Diabetes Care Inc. Method and device for determining elapsed sensor life
US9314198B2 (en) 2007-05-08 2016-04-19 Abbott Diabetes Care Inc. Analyte monitoring system and methods
US10178954B2 (en) 2007-05-08 2019-01-15 Abbott Diabetes Care Inc. Analyte monitoring system and methods
US8593287B2 (en) 2007-05-08 2013-11-26 Abbott Diabetes Care Inc. Analyte monitoring system and methods
US8362904B2 (en) 2007-05-08 2013-01-29 Abbott Diabetes Care Inc. Analyte monitoring system and methods
US9574914B2 (en) 2007-05-08 2017-02-21 Abbott Diabetes Care Inc. Method and device for determining elapsed sensor life
US9649057B2 (en) 2007-05-08 2017-05-16 Abbott Diabetes Care Inc. Analyte monitoring system and methods
US7928850B2 (en) 2007-05-08 2011-04-19 Abbott Diabetes Care Inc. Analyte monitoring system and methods
US11696684B2 (en) 2007-05-08 2023-07-11 Abbott Diabetes Care Inc. Analyte monitoring system and methods
US10653317B2 (en) 2007-05-08 2020-05-19 Abbott Diabetes Care Inc. Analyte monitoring system and methods
US10952611B2 (en) 2007-05-08 2021-03-23 Abbott Diabetes Care Inc. Analyte monitoring system and methods
US10976304B2 (en) 2007-05-14 2021-04-13 Abbott Diabetes Care Inc. Method and apparatus for providing data processing and control in a medical communication system
US9804150B2 (en) 2007-05-14 2017-10-31 Abbott Diabetes Care Inc. Method and apparatus for providing data processing and control in a medical communication system
US9558325B2 (en) 2007-05-14 2017-01-31 Abbott Diabetes Care Inc. Method and system for determining analyte levels
US10045720B2 (en) 2007-05-14 2018-08-14 Abbott Diabetes Care Inc. Method and apparatus for providing data processing and control in a medical communication system
US11828748B2 (en) 2007-05-14 2023-11-28 Abbott Diabetes Care Inc. Method and apparatus for providing data processing and control in a medical communication system
US8239166B2 (en) 2007-05-14 2012-08-07 Abbott Diabetes Care Inc. Method and apparatus for providing data processing and control in a medical communication system
US8260558B2 (en) 2007-05-14 2012-09-04 Abbott Diabetes Care Inc. Method and apparatus for providing data processing and control in a medical communication system
US9125548B2 (en) 2007-05-14 2015-09-08 Abbott Diabetes Care Inc. Method and apparatus for providing data processing and control in a medical communication system
US9483608B2 (en) 2007-05-14 2016-11-01 Abbott Diabetes Care Inc. Method and apparatus for providing data processing and control in a medical communication system
US8484005B2 (en) 2007-05-14 2013-07-09 Abbott Diabetes Care Inc. Method and system for determining analyte levels
US10031002B2 (en) 2007-05-14 2018-07-24 Abbott Diabetes Care Inc. Method and apparatus for providing data processing and control in a medical communication system
US8612163B2 (en) 2007-05-14 2013-12-17 Abbott Diabetes Care Inc. Method and apparatus for providing data processing and control in a medical communication system
US8600681B2 (en) 2007-05-14 2013-12-03 Abbott Diabetes Care Inc. Method and apparatus for providing data processing and control in a medical communication system
US10463310B2 (en) 2007-05-14 2019-11-05 Abbott Diabetes Care Inc. Method and apparatus for providing data processing and control in a medical communication system
US10820841B2 (en) 2007-05-14 2020-11-03 Abbot Diabetes Care Inc. Method and apparatus for providing data processing and control in a medical communication system
US10991456B2 (en) 2007-05-14 2021-04-27 Abbott Diabetes Care Inc. Method and system for determining analyte levels
US10002233B2 (en) 2007-05-14 2018-06-19 Abbott Diabetes Care Inc. Method and apparatus for providing data processing and control in a medical communication system
US7996158B2 (en) 2007-05-14 2011-08-09 Abbott Diabetes Care Inc. Method and apparatus for providing data processing and control in a medical communication system
US9737249B2 (en) 2007-05-14 2017-08-22 Abbott Diabetes Care Inc. Method and apparatus for providing data processing and control in a medical communication system
US10653344B2 (en) 2007-05-14 2020-05-19 Abbott Diabetes Care Inc. Method and apparatus for providing data processing and control in a medical communication system
US11300561B2 (en) 2007-05-14 2022-04-12 Abbott Diabetes Care, Inc. Method and apparatus for providing data processing and control in a medical communication system
US11076785B2 (en) 2007-05-14 2021-08-03 Abbott Diabetes Care Inc. Method and apparatus for providing data processing and control in a medical communication system
US8571808B2 (en) 2007-05-14 2013-10-29 Abbott Diabetes Care Inc. Method and apparatus for providing data processing and control in a medical communication system
US8560038B2 (en) 2007-05-14 2013-10-15 Abbott Diabetes Care Inc. Method and apparatus for providing data processing and control in a medical communication system
US10119956B2 (en) 2007-05-14 2018-11-06 Abbott Diabetes Care Inc. Method and apparatus for providing data processing and control in a medical communication system
US9797880B2 (en) 2007-05-14 2017-10-24 Abbott Diabetes Care Inc. Method and apparatus for providing data processing and control in a medical communication system
US9801571B2 (en) 2007-05-14 2017-10-31 Abbott Diabetes Care Inc. Method and apparatus for providing data processing and control in medical communication system
US8444560B2 (en) 2007-05-14 2013-05-21 Abbott Diabetes Care Inc. Method and apparatus for providing data processing and control in a medical communication system
US10634662B2 (en) 2007-05-14 2020-04-28 Abbott Diabetes Care Inc. Method and apparatus for providing data processing and control in a medical communication system
US8103471B2 (en) 2007-05-14 2012-01-24 Abbott Diabetes Care Inc. Method and apparatus for providing data processing and control in a medical communication system
US10261069B2 (en) 2007-05-14 2019-04-16 Abbott Diabetes Care Inc. Method and apparatus for providing data processing and control in a medical communication system
US10143409B2 (en) 2007-05-14 2018-12-04 Abbott Diabetes Care Inc. Method and apparatus for providing data processing and control in a medical communication system
US8682615B2 (en) 2007-05-14 2014-03-25 Abbott Diabetes Care Inc. Method and apparatus for providing data processing and control in a medical communication system
US11119090B2 (en) 2007-05-14 2021-09-14 Abbott Diabetes Care Inc. Method and apparatus for providing data processing and control in a medical communication system
US9060719B2 (en) 2007-05-14 2015-06-23 Abbott Diabetes Care Inc. Method and apparatus for providing data processing and control in a medical communication system
US11125592B2 (en) 2007-05-14 2021-09-21 Abbott Diabetes Care Inc. Method and apparatus for providing data processing and control in a medical communication system
US8140312B2 (en) 2007-05-14 2012-03-20 Abbott Diabetes Care Inc. Method and system for determining analyte levels
US11276492B2 (en) 2007-06-21 2022-03-15 Abbott Diabetes Care Inc. Health management devices and methods
US11264133B2 (en) 2007-06-21 2022-03-01 Abbott Diabetes Care Inc. Health management devices and methods
US8617069B2 (en) 2007-06-21 2013-12-31 Abbott Diabetes Care Inc. Health monitor
US8597188B2 (en) 2007-06-21 2013-12-03 Abbott Diabetes Care Inc. Health management devices and methods
US9398872B2 (en) 2007-07-31 2016-07-26 Abbott Diabetes Care Inc. Method and apparatus for providing analyte sensor calibration
US8834366B2 (en) 2007-07-31 2014-09-16 Abbott Diabetes Care Inc. Method and apparatus for providing analyte sensor calibration
US7768386B2 (en) 2007-07-31 2010-08-03 Abbott Diabetes Care Inc. Method and apparatus for providing data processing and control in a medical communication system
US8409093B2 (en) 2007-10-23 2013-04-02 Abbott Diabetes Care Inc. Assessing measures of glycemic variability
US9804148B2 (en) 2007-10-23 2017-10-31 Abbott Diabetes Care Inc. Analyte sensor with lag compensation
US8377031B2 (en) 2007-10-23 2013-02-19 Abbott Diabetes Care Inc. Closed loop control system with safety parameters and methods
US9743865B2 (en) 2007-10-23 2017-08-29 Abbott Diabetes Care Inc. Assessing measures of glycemic variability
US8374668B1 (en) 2007-10-23 2013-02-12 Abbott Diabetes Care Inc. Analyte sensor with lag compensation
US9439586B2 (en) 2007-10-23 2016-09-13 Abbott Diabetes Care Inc. Assessing measures of glycemic variability
US10173007B2 (en) 2007-10-23 2019-01-08 Abbott Diabetes Care Inc. Closed loop control system with safety parameters and methods
US11083843B2 (en) 2007-10-23 2021-08-10 Abbott Diabetes Care Inc. Closed loop control system with safety parameters and methods
US9332934B2 (en) 2007-10-23 2016-05-10 Abbott Diabetes Care Inc. Analyte sensor with lag compensation
US8216138B1 (en) 2007-10-23 2012-07-10 Abbott Diabetes Care Inc. Correlation of alternative site blood and interstitial fluid glucose concentrations to venous glucose concentration
US8318096B2 (en) 2007-12-12 2012-11-27 Panasonic Corporation Biological sample measurement apparatus
US20100035334A1 (en) * 2007-12-12 2010-02-11 Eiji Okuda Biological sample measurement apparatus
US8473022B2 (en) 2008-01-31 2013-06-25 Abbott Diabetes Care Inc. Analyte sensor with time lag compensation
US9770211B2 (en) 2008-01-31 2017-09-26 Abbott Diabetes Care Inc. Analyte sensor with time lag compensation
US9320468B2 (en) 2008-01-31 2016-04-26 Abbott Diabetes Care Inc. Analyte sensor with time lag compensation
US8583205B2 (en) 2008-03-28 2013-11-12 Abbott Diabetes Care Inc. Analyte sensor calibration management
US11779248B2 (en) 2008-03-28 2023-10-10 Abbott Diabetes Care Inc. Analyte sensor calibration management
US9320462B2 (en) 2008-03-28 2016-04-26 Abbott Diabetes Care Inc. Analyte sensor calibration management
US9730623B2 (en) 2008-03-28 2017-08-15 Abbott Diabetes Care Inc. Analyte sensor calibration management
US10463288B2 (en) 2008-03-28 2019-11-05 Abbott Diabetes Care Inc. Analyte sensor calibration management
US8718739B2 (en) 2008-03-28 2014-05-06 Abbott Diabetes Care Inc. Analyte sensor calibration management
US8346335B2 (en) 2008-03-28 2013-01-01 Abbott Diabetes Care Inc. Analyte sensor calibration management
US7826382B2 (en) 2008-05-30 2010-11-02 Abbott Diabetes Care Inc. Close proximity communication device and methods
US8509107B2 (en) 2008-05-30 2013-08-13 Abbott Diabetes Care Inc. Close proximity communication device and methods
US11770210B2 (en) 2008-05-30 2023-09-26 Abbott Diabetes Care Inc. Close proximity communication device and methods
US8737259B2 (en) 2008-05-30 2014-05-27 Abbott Diabetes Care Inc. Close proximity communication device and methods
US9184875B2 (en) 2008-05-30 2015-11-10 Abbott Diabetes Care, Inc. Close proximity communication device and methods
US9831985B2 (en) 2008-05-30 2017-11-28 Abbott Diabetes Care Inc. Close proximity communication device and methods
US9943644B2 (en) 2008-08-31 2018-04-17 Abbott Diabetes Care Inc. Closed loop control with reference measurement and methods thereof
US8622988B2 (en) 2008-08-31 2014-01-07 Abbott Diabetes Care Inc. Variable rate closed loop control and methods
US9610046B2 (en) 2008-08-31 2017-04-04 Abbott Diabetes Care Inc. Closed loop control with improved alarm functions
US9572934B2 (en) 2008-08-31 2017-02-21 Abbott DiabetesCare Inc. Robust closed loop control and methods
US9392969B2 (en) 2008-08-31 2016-07-19 Abbott Diabetes Care Inc. Closed loop control and signal attenuation detection
US8795252B2 (en) 2008-08-31 2014-08-05 Abbott Diabetes Care Inc. Robust closed loop control and methods
US8734422B2 (en) 2008-08-31 2014-05-27 Abbott Diabetes Care Inc. Closed loop control with improved alarm functions
US9662056B2 (en) 2008-09-30 2017-05-30 Abbott Diabetes Care Inc. Optimizing analyte sensor calibration
US8744547B2 (en) 2008-09-30 2014-06-03 Abbott Diabetes Care Inc. Optimizing analyte sensor calibration
US11013439B2 (en) 2008-09-30 2021-05-25 Abbott Diabetes Care Inc. Optimizing analyte sensor calibration
US11464434B2 (en) 2008-09-30 2022-10-11 Abbott Diabetes Care Inc. Optimizing analyte sensor calibration
US11484234B2 (en) 2008-09-30 2022-11-01 Abbott Diabetes Care Inc. Optimizing analyte sensor calibration
US8986208B2 (en) 2008-09-30 2015-03-24 Abbott Diabetes Care Inc. Analyte sensor sensitivity attenuation mitigation
US8219173B2 (en) 2008-09-30 2012-07-10 Abbott Diabetes Care Inc. Optimizing analyte sensor calibration
US11202592B2 (en) 2008-09-30 2021-12-21 Abbott Diabetes Care Inc. Optimizing analyte sensor calibration
US10045739B2 (en) 2008-09-30 2018-08-14 Abbott Diabetes Care Inc. Analyte sensor sensitivity attenuation mitigation
US10980461B2 (en) 2008-11-07 2021-04-20 Dexcom, Inc. Advanced analyte sensor calibration and error detection
US9326707B2 (en) 2008-11-10 2016-05-03 Abbott Diabetes Care Inc. Alarm characterization for analyte monitoring devices and systems
US11678848B2 (en) 2008-11-10 2023-06-20 Abbott Diabetes Care Inc. Alarm characterization for analyte monitoring devices and systems
US11272890B2 (en) 2008-11-10 2022-03-15 Abbott Diabetes Care Inc. Alarm characterization for analyte monitoring devices and systems
US9730650B2 (en) 2008-11-10 2017-08-15 Abbott Diabetes Care Inc. Alarm characterization for analyte monitoring devices and systems
US10089446B2 (en) 2009-01-29 2018-10-02 Abbott Diabetes Care Inc. Method and device for providing offset model based calibration for analyte sensor
US8532935B2 (en) 2009-01-29 2013-09-10 Abbott Diabetes Care Inc. Method and device for providing offset model based calibration for analyte sensor
US8224415B2 (en) 2009-01-29 2012-07-17 Abbott Diabetes Care Inc. Method and device for providing offset model based calibration for analyte sensor
US11464430B2 (en) 2009-01-29 2022-10-11 Abbott Diabetes Care Inc. Method and device for providing offset model based calibration for analyte sensor
US11006872B2 (en) 2009-02-03 2021-05-18 Abbott Diabetes Care Inc. Analyte sensor and apparatus for insertion of the sensor
US11006871B2 (en) 2009-02-03 2021-05-18 Abbott Diabetes Care Inc. Analyte sensor and apparatus for insertion of the sensor
US11202591B2 (en) 2009-02-03 2021-12-21 Abbott Diabetes Care Inc. Analyte sensor and apparatus for insertion of the sensor
US11213229B2 (en) 2009-02-03 2022-01-04 Abbott Diabetes Care Inc. Analyte sensor and apparatus for insertion of the sensor
US11006870B2 (en) 2009-02-03 2021-05-18 Abbott Diabetes Care Inc. Analyte sensor and apparatus for insertion of the sensor
US11166656B2 (en) 2009-02-03 2021-11-09 Abbott Diabetes Care Inc. Analyte sensor and apparatus for insertion of the sensor
US9178752B2 (en) 2009-04-15 2015-11-03 Abbott Diabetes Care Inc. Analyte monitoring system having an alert
US8497777B2 (en) 2009-04-15 2013-07-30 Abbott Diabetes Care Inc. Analyte monitoring system having an alert
US10009244B2 (en) 2009-04-15 2018-06-26 Abbott Diabetes Care Inc. Analyte monitoring system having an alert
US8730058B2 (en) 2009-04-15 2014-05-20 Abbott Diabetes Care Inc. Analyte monitoring system having an alert
US9226701B2 (en) 2009-04-28 2016-01-05 Abbott Diabetes Care Inc. Error detection in critical repeating data in a wireless sensor system
US8483967B2 (en) 2009-04-29 2013-07-09 Abbott Diabetes Care Inc. Method and system for providing real time analyte sensor calibration with retrospective backfill
US9088452B2 (en) 2009-04-29 2015-07-21 Abbott Diabetes Care Inc. Method and system for providing data communication in continuous glucose monitoring and management system
US10172518B2 (en) 2009-04-29 2019-01-08 Abbott Diabetes Care Inc. Method and system for providing data communication in continuous glucose monitoring and management system
US10617296B2 (en) 2009-04-29 2020-04-14 Abbott Diabetes Care Inc. Method and system for providing data communication in continuous glucose monitoring and management system
US9693688B2 (en) 2009-04-29 2017-07-04 Abbott Diabetes Care Inc. Method and system for providing data communication in continuous glucose monitoring and management system
US8368556B2 (en) 2009-04-29 2013-02-05 Abbott Diabetes Care Inc. Method and system for providing data communication in continuous glucose monitoring and management system
US9949639B2 (en) 2009-04-29 2018-04-24 Abbott Diabetes Care Inc. Method and system for providing data communication in continuous glucose monitoring and management system
US9310230B2 (en) 2009-04-29 2016-04-12 Abbott Diabetes Care Inc. Method and system for providing real time analyte sensor calibration with retrospective backfill
US11793936B2 (en) 2009-05-29 2023-10-24 Abbott Diabetes Care Inc. Medical device antenna systems having external antenna configurations
US11872370B2 (en) 2009-05-29 2024-01-16 Abbott Diabetes Care Inc. Medical device antenna systems having external antenna configurations
US20100331654A1 (en) * 2009-06-30 2010-12-30 Lifescan Scotland Ltd. Systems for diabetes management and methods
US20100332142A1 (en) * 2009-06-30 2010-12-30 Lifescan,Inc. Analyte testing method and device for calculating basal insulin therapy
US8688386B2 (en) 2009-06-30 2014-04-01 Lifescan, Inc. Analyte testing method and device for calculating basal insulin therapy
US20100332445A1 (en) * 2009-06-30 2010-12-30 Lifescan, Inc. Analyte testing method and system
US9936910B2 (en) 2009-07-31 2018-04-10 Abbott Diabetes Care Inc. Method and apparatus for providing analyte monitoring and therapy management system accuracy
US10660554B2 (en) 2009-07-31 2020-05-26 Abbott Diabetes Care Inc. Methods and devices for analyte monitoring calibration
US11234625B2 (en) 2009-07-31 2022-02-01 Abbott Diabetes Care Inc. Method and apparatus for providing analyte monitoring and therapy management system accuracy
US8478557B2 (en) 2009-07-31 2013-07-02 Abbott Diabetes Care Inc. Method and apparatus for providing analyte monitoring system calibration accuracy
US8718965B2 (en) 2009-07-31 2014-05-06 Abbott Diabetes Care Inc. Method and apparatus for providing analyte monitoring system calibration accuracy
US9814416B2 (en) 2009-08-31 2017-11-14 Abbott Diabetes Care Inc. Displays for a medical device
US10881355B2 (en) 2009-08-31 2021-01-05 Abbott Diabetes Care Inc. Displays for a medical device
US10918342B1 (en) 2009-08-31 2021-02-16 Abbott Diabetes Care Inc. Displays for a medical device
US11150145B2 (en) 2009-08-31 2021-10-19 Abbott Diabetes Care Inc. Analyte monitoring system and methods for managing power and noise
US9549694B2 (en) 2009-08-31 2017-01-24 Abbott Diabetes Care Inc. Displays for a medical device
US9968302B2 (en) 2009-08-31 2018-05-15 Abbott Diabetes Care Inc. Analyte signal processing device and methods
US10772572B2 (en) 2009-08-31 2020-09-15 Abbott Diabetes Care Inc. Displays for a medical device
US11241175B2 (en) 2009-08-31 2022-02-08 Abbott Diabetes Care Inc. Displays for a medical device
US8514086B2 (en) 2009-08-31 2013-08-20 Abbott Diabetes Care Inc. Displays for a medical device
USD1010133S1 (en) 2009-08-31 2024-01-02 Abbott Diabetes Care Inc. Analyte sensor assembly
US9314195B2 (en) 2009-08-31 2016-04-19 Abbott Diabetes Care Inc. Analyte signal processing device and methods
US8816862B2 (en) 2009-08-31 2014-08-26 Abbott Diabetes Care Inc. Displays for a medical device
US11730429B2 (en) 2009-08-31 2023-08-22 Abbott Diabetes Care Inc. Displays for a medical device
US11045147B2 (en) 2009-08-31 2021-06-29 Abbott Diabetes Care Inc. Analyte signal processing device and methods
US10123752B2 (en) 2009-08-31 2018-11-13 Abbott Diabetes Care Inc. Displays for a medical device
US8993331B2 (en) 2009-08-31 2015-03-31 Abbott Diabetes Care Inc. Analyte monitoring system and methods for managing power and noise
US11635332B2 (en) 2009-08-31 2023-04-25 Abbott Diabetes Care Inc. Analyte monitoring system and methods for managing power and noise
US10492685B2 (en) 2009-08-31 2019-12-03 Abbott Diabetes Care Inc. Medical devices and methods
US10456091B2 (en) 2009-08-31 2019-10-29 Abbott Diabetes Care Inc. Displays for a medical device
US9226714B2 (en) 2009-08-31 2016-01-05 Abbott Diabetes Care Inc. Displays for a medical device
US10429250B2 (en) 2009-08-31 2019-10-01 Abbott Diabetes Care, Inc. Analyte monitoring system and methods for managing power and noise
US11202586B2 (en) 2009-08-31 2021-12-21 Abbott Diabetes Care Inc. Displays for a medical device
USRE47315E1 (en) 2009-08-31 2019-03-26 Abbott Diabetes Care Inc. Displays for a medical device
US9186113B2 (en) 2009-08-31 2015-11-17 Abbott Diabetes Care Inc. Displays for a medical device
US10136816B2 (en) 2009-08-31 2018-11-27 Abbott Diabetes Care Inc. Medical devices and methods
US8974387B2 (en) 2009-09-29 2015-03-10 Lifescan Scotland Limited Analyte testing method and device for diabetes management
US20110077493A1 (en) * 2009-09-29 2011-03-31 Lifescan Scotland Ltd. Analyte testing method and device for diabetes mangement
US10765351B2 (en) 2009-09-30 2020-09-08 Abbott Diabetes Care Inc. Interconnect for on-body analyte monitoring device
US9750444B2 (en) 2009-09-30 2017-09-05 Abbott Diabetes Care Inc. Interconnect for on-body analyte monitoring device
US11259725B2 (en) 2009-09-30 2022-03-01 Abbott Diabetes Care Inc. Interconnect for on-body analyte monitoring device
US10117606B2 (en) 2009-10-30 2018-11-06 Abbott Diabetes Care Inc. Method and apparatus for detecting false hypoglycemic conditions
US11207005B2 (en) 2009-10-30 2021-12-28 Abbott Diabetes Care Inc. Method and apparatus for detecting false hypoglycemic conditions
US9050041B2 (en) 2009-10-30 2015-06-09 Abbott Diabetes Care Inc. Method and apparatus for detecting false hypoglycemic conditions
US8185181B2 (en) 2009-10-30 2012-05-22 Abbott Diabetes Care Inc. Method and apparatus for detecting false hypoglycemic conditions
US20110205064A1 (en) * 2010-02-25 2011-08-25 Lifescan Scotland Ltd. Analyte testing method and system with high and low blood glucose trends notification
US9563743B2 (en) 2010-02-25 2017-02-07 Lifescan Scotland Limited Analyte testing method and system with high and low blood glucose trends notification
US9326709B2 (en) 2010-03-10 2016-05-03 Abbott Diabetes Care Inc. Systems, devices and methods for managing glucose levels
US8635046B2 (en) 2010-06-23 2014-01-21 Abbott Diabetes Care Inc. Method and system for evaluating analyte sensor response characteristics
US10092229B2 (en) 2010-06-29 2018-10-09 Abbott Diabetes Care Inc. Calibration of analyte measurement system
US11478173B2 (en) 2010-06-29 2022-10-25 Abbott Diabetes Care Inc. Calibration of analyte measurement system
US8945094B2 (en) 2010-09-08 2015-02-03 Honeywell International Inc. Apparatus and method for medication delivery using single input-single output (SISO) model predictive control
US11213226B2 (en) 2010-10-07 2022-01-04 Abbott Diabetes Care Inc. Analyte monitoring devices and methods
US11534089B2 (en) 2011-02-28 2022-12-27 Abbott Diabetes Care Inc. Devices, systems, and methods associated with analyte monitoring devices and devices incorporating the same
US9532737B2 (en) 2011-02-28 2017-01-03 Abbott Diabetes Care Inc. Devices, systems, and methods associated with analyte monitoring devices and devices incorporating the same
US10555695B2 (en) 2011-04-15 2020-02-11 Dexcom, Inc. Advanced analyte sensor calibration and error detection
US10561354B2 (en) 2011-04-15 2020-02-18 Dexcom, Inc. Advanced analyte sensor calibration and error detection
US10835162B2 (en) 2011-04-15 2020-11-17 Dexcom, Inc. Advanced analyte sensor calibration and error detection
US10722162B2 (en) 2011-04-15 2020-07-28 Dexcom, Inc. Advanced analyte sensor calibration and error detection
US10610141B2 (en) 2011-04-15 2020-04-07 Dexcom, Inc. Advanced analyte sensor calibration and error detection
US10624568B2 (en) 2011-04-15 2020-04-21 Dexcom, Inc. Advanced analyte sensor calibration and error detection
US10682084B2 (en) 2011-04-15 2020-06-16 Dexcom, Inc. Advanced analyte sensor calibration and error detection
US9465420B2 (en) 2011-10-31 2016-10-11 Abbott Diabetes Care Inc. Electronic devices having integrated reset systems and methods thereof
US9913619B2 (en) 2011-10-31 2018-03-13 Abbott Diabetes Care Inc. Model based variable risk false glucose threshold alarm prevention mechanism
US9622691B2 (en) 2011-10-31 2017-04-18 Abbott Diabetes Care Inc. Model based variable risk false glucose threshold alarm prevention mechanism
US9069536B2 (en) 2011-10-31 2015-06-30 Abbott Diabetes Care Inc. Electronic devices having integrated reset systems and methods thereof
US11406331B2 (en) 2011-10-31 2022-08-09 Abbott Diabetes Care Inc. Model based variable risk false glucose threshold alarm prevention mechanism
US9980669B2 (en) 2011-11-07 2018-05-29 Abbott Diabetes Care Inc. Analyte monitoring device and methods
US9317656B2 (en) 2011-11-23 2016-04-19 Abbott Diabetes Care Inc. Compatibility mechanisms for devices in a continuous analyte monitoring system and methods thereof
US8710993B2 (en) 2011-11-23 2014-04-29 Abbott Diabetes Care Inc. Mitigating single point failure of devices in an analyte monitoring system and methods thereof
US9743872B2 (en) 2011-11-23 2017-08-29 Abbott Diabetes Care Inc. Mitigating single point failure of devices in an analyte monitoring system and methods thereof
US9289179B2 (en) 2011-11-23 2016-03-22 Abbott Diabetes Care Inc. Mitigating single point failure of devices in an analyte monitoring system and methods thereof
US10939859B2 (en) 2011-11-23 2021-03-09 Abbott Diabetes Care Inc. Mitigating single point failure of devices in an analyte monitoring system and methods thereof
US10136847B2 (en) 2011-11-23 2018-11-27 Abbott Diabetes Care Inc. Mitigating single point failure of devices in an analyte monitoring system and methods thereof
US10082493B2 (en) 2011-11-25 2018-09-25 Abbott Diabetes Care Inc. Analyte monitoring system and methods of use
US11391723B2 (en) 2011-11-25 2022-07-19 Abbott Diabetes Care Inc. Analyte monitoring system and methods of use
US9339217B2 (en) 2011-11-25 2016-05-17 Abbott Diabetes Care Inc. Analyte monitoring system and methods of use
US9918679B2 (en) 2012-05-29 2018-03-20 The Regents Of The University Of California Sonification systems and methods for auditory display of physiological parameters
WO2014007927A1 (en) * 2012-05-29 2014-01-09 The Regents Of The University Of California Sonification system for auditory display of physiological parameters
US10132793B2 (en) 2012-08-30 2018-11-20 Abbott Diabetes Care Inc. Dropout detection in continuous analyte monitoring data during data excursions
US10345291B2 (en) 2012-08-30 2019-07-09 Abbott Diabetes Care Inc. Dropout detection in continuous analyte monitoring data during data excursions
US10942164B2 (en) 2012-08-30 2021-03-09 Abbott Diabetes Care Inc. Dropout detection in continuous analyte monitoring data during data excursions
US10656139B2 (en) 2012-08-30 2020-05-19 Abbott Diabetes Care Inc. Dropout detection in continuous analyte monitoring data during data excursions
US9968306B2 (en) 2012-09-17 2018-05-15 Abbott Diabetes Care Inc. Methods and apparatuses for providing adverse condition notification with enhanced wireless communication range in analyte monitoring systems
US11612363B2 (en) 2012-09-17 2023-03-28 Abbott Diabetes Care Inc. Methods and apparatuses for providing adverse condition notification with enhanced wireless communication range in analyte monitoring systems
US11896371B2 (en) 2012-09-26 2024-02-13 Abbott Diabetes Care Inc. Method and apparatus for improving lag correction during in vivo measurement of analyte concentration with analyte concentration variability and range data
US10842420B2 (en) 2012-09-26 2020-11-24 Abbott Diabetes Care Inc. Method and apparatus for improving lag correction during in vivo measurement of analyte concentration with analyte concentration variability and range data
US9907492B2 (en) 2012-09-26 2018-03-06 Abbott Diabetes Care Inc. Method and apparatus for improving lag correction during in vivo measurement of analyte concentration with analyte concentration variability and range data
US9675290B2 (en) 2012-10-30 2017-06-13 Abbott Diabetes Care Inc. Sensitivity calibration of in vivo sensors used to measure analyte concentration
US9801577B2 (en) 2012-10-30 2017-10-31 Abbott Diabetes Care Inc. Sensitivity calibration of in vivo sensors used to measure analyte concentration
US10188334B2 (en) 2012-10-30 2019-01-29 Abbott Diabetes Care Inc. Sensitivity calibration of in vivo sensors used to measure analyte concentration
US10874336B2 (en) 2013-03-15 2020-12-29 Abbott Diabetes Care Inc. Multi-rate analyte sensor data collection with sample rate configurable signal processing
US9474475B1 (en) 2013-03-15 2016-10-25 Abbott Diabetes Care Inc. Multi-rate analyte sensor data collection with sample rate configurable signal processing
US10433773B1 (en) 2013-03-15 2019-10-08 Abbott Diabetes Care Inc. Noise rejection methods and apparatus for sparsely sampled analyte sensor data
US10076285B2 (en) 2013-03-15 2018-09-18 Abbott Diabetes Care Inc. Sensor fault detection using analyte sensor data pattern comparison
US11229382B2 (en) 2013-12-31 2022-01-25 Abbott Diabetes Care Inc. Self-powered analyte sensor and devices using the same
US11717225B2 (en) 2014-03-30 2023-08-08 Abbott Diabetes Care Inc. Method and apparatus for determining meal start and peak events in analyte monitoring systems
US11553883B2 (en) 2015-07-10 2023-01-17 Abbott Diabetes Care Inc. System, device and method of dynamic glucose profile response to physiological parameters
US11596330B2 (en) 2017-03-21 2023-03-07 Abbott Diabetes Care Inc. Methods, devices and system for providing diabetic condition diagnosis and therapy
US11484652B2 (en) 2017-08-02 2022-11-01 Diabeloop Closed-loop blood glucose control systems and methods
US11331022B2 (en) 2017-10-24 2022-05-17 Dexcom, Inc. Pre-connected analyte sensors
US11706876B2 (en) 2017-10-24 2023-07-18 Dexcom, Inc. Pre-connected analyte sensors
US11350862B2 (en) 2017-10-24 2022-06-07 Dexcom, Inc. Pre-connected analyte sensors
US11382540B2 (en) 2017-10-24 2022-07-12 Dexcom, Inc. Pre-connected analyte sensors

Also Published As

Publication number Publication date
AU2002360634A1 (en) 2003-07-24
US20030125612A1 (en) 2003-07-03
US20050113653A1 (en) 2005-05-26
WO2003057027A3 (en) 2004-03-04
WO2003057027A2 (en) 2003-07-17
US7022072B2 (en) 2006-04-04
US20050096511A1 (en) 2005-05-05
US7766830B2 (en) 2010-08-03
EP2471456A1 (en) 2012-07-04
EP1460931A2 (en) 2004-09-29

Similar Documents

Publication Publication Date Title
US7766830B2 (en) System for monitoring physiological characteristics
US8961416B2 (en) System for monitoring physiological characteristics
US10080529B2 (en) System for monitoring physiological characteristics
US7399277B2 (en) System for monitoring physiological characteristics
CA2816310C (en) System for monitoring physiological characteristics
US20080255438A1 (en) System for monitoring physiological characteristics
US20200069184A1 (en) Smart messages and alerts for an infusion delivery and management system
JP2010510866A (en) Method and apparatus for managing glucose control
CA2567711C (en) System for monitoring physiological characteristics
US20070168136A1 (en) System and method for assessing diabetic conditions
US20230337916A1 (en) Method for transmitting and receiving unreceived biometric information based on area to which unreceived biometric information belongs

Legal Events

Date Code Title Description
STCB Information on status: application discontinuation

Free format text: ABANDONED -- FAILURE TO RESPOND TO AN OFFICE ACTION