WO2001072357A2 - Improved methods, apparatuses, and uses for infusion pump fluid pressure and force detection - Google Patents
Improved methods, apparatuses, and uses for infusion pump fluid pressure and force detection Download PDFInfo
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- WO2001072357A2 WO2001072357A2 PCT/US2001/009893 US0109893W WO0172357A2 WO 2001072357 A2 WO2001072357 A2 WO 2001072357A2 US 0109893 W US0109893 W US 0109893W WO 0172357 A2 WO0172357 A2 WO 0172357A2
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- detection system
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M5/00—Devices for bringing media into the body in a subcutaneous, intra-vascular or intramuscular way; Accessories therefor, e.g. filling or cleaning devices, arm-rests
- A61M5/14—Infusion devices, e.g. infusing by gravity; Blood infusion; Accessories therefor
- A61M5/142—Pressure infusion, e.g. using pumps
- A61M5/145—Pressure infusion, e.g. using pumps using pressurised reservoirs, e.g. pressurised by means of pistons
- A61M5/1452—Pressure infusion, e.g. using pumps using pressurised reservoirs, e.g. pressurised by means of pistons pressurised by means of pistons
- A61M5/14566—Pressure infusion, e.g. using pumps using pressurised reservoirs, e.g. pressurised by means of pistons pressurised by means of pistons with a replaceable reservoir for receiving a piston rod of the pump
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M5/00—Devices for bringing media into the body in a subcutaneous, intra-vascular or intramuscular way; Accessories therefor, e.g. filling or cleaning devices, arm-rests
- A61M5/14—Infusion devices, e.g. infusing by gravity; Blood infusion; Accessories therefor
- A61M5/142—Pressure infusion, e.g. using pumps
- A61M5/145—Pressure infusion, e.g. using pumps using pressurised reservoirs, e.g. pressurised by means of pistons
- A61M5/1452—Pressure infusion, e.g. using pumps using pressurised reservoirs, e.g. pressurised by means of pistons pressurised by means of pistons
- A61M5/1456—Pressure infusion, e.g. using pumps using pressurised reservoirs, e.g. pressurised by means of pistons pressurised by means of pistons with a replaceable reservoir comprising a piston rod to be moved into the reservoir, e.g. the piston rod is part of the removable reservoir
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M5/00—Devices for bringing media into the body in a subcutaneous, intra-vascular or intramuscular way; Accessories therefor, e.g. filling or cleaning devices, arm-rests
- A61M5/14—Infusion devices, e.g. infusing by gravity; Blood infusion; Accessories therefor
- A61M5/168—Means for controlling media flow to the body or for metering media to the body, e.g. drip meters, counters ; Monitoring media flow to the body
- A61M5/16831—Monitoring, detecting, signalling or eliminating infusion flow anomalies
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M5/00—Devices for bringing media into the body in a subcutaneous, intra-vascular or intramuscular way; Accessories therefor, e.g. filling or cleaning devices, arm-rests
- A61M5/14—Infusion devices, e.g. infusing by gravity; Blood infusion; Accessories therefor
- A61M5/168—Means for controlling media flow to the body or for metering media to the body, e.g. drip meters, counters ; Monitoring media flow to the body
- A61M5/172—Means for controlling media flow to the body or for metering media to the body, e.g. drip meters, counters ; Monitoring media flow to the body electrical or electronic
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M5/00—Devices for bringing media into the body in a subcutaneous, intra-vascular or intramuscular way; Accessories therefor, e.g. filling or cleaning devices, arm-rests
- A61M5/14—Infusion devices, e.g. infusing by gravity; Blood infusion; Accessories therefor
- A61M5/142—Pressure infusion, e.g. using pumps
- A61M5/14244—Pressure infusion, e.g. using pumps adapted to be carried by the patient, e.g. portable on the body
- A61M2005/14264—Pressure infusion, e.g. using pumps adapted to be carried by the patient, e.g. portable on the body with means for compensating influence from the environment
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M2205/00—General characteristics of the apparatus
- A61M2205/15—Detection of leaks
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M2205/00—General characteristics of the apparatus
- A61M2205/33—Controlling, regulating or measuring
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M2205/00—General characteristics of the apparatus
- A61M2205/33—Controlling, regulating or measuring
- A61M2205/3331—Pressure; Flow
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M2205/00—General characteristics of the apparatus
- A61M2205/50—General characteristics of the apparatus with microprocessors or computers
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M5/00—Devices for bringing media into the body in a subcutaneous, intra-vascular or intramuscular way; Accessories therefor, e.g. filling or cleaning devices, arm-rests
- A61M5/14—Infusion devices, e.g. infusing by gravity; Blood infusion; Accessories therefor
- A61M5/168—Means for controlling media flow to the body or for metering media to the body, e.g. drip meters, counters ; Monitoring media flow to the body
- A61M5/16831—Monitoring, detecting, signalling or eliminating infusion flow anomalies
- A61M5/1684—Monitoring, detecting, signalling or eliminating infusion flow anomalies by detecting the amount of infusate remaining, e.g. signalling end of infusion
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M5/00—Devices for bringing media into the body in a subcutaneous, intra-vascular or intramuscular way; Accessories therefor, e.g. filling or cleaning devices, arm-rests
- A61M5/14—Infusion devices, e.g. infusing by gravity; Blood infusion; Accessories therefor
- A61M5/168—Means for controlling media flow to the body or for metering media to the body, e.g. drip meters, counters ; Monitoring media flow to the body
- A61M5/16831—Monitoring, detecting, signalling or eliminating infusion flow anomalies
- A61M5/16854—Monitoring, detecting, signalling or eliminating infusion flow anomalies by monitoring line pressure
Definitions
- This invention relates generally to improvements in infusion pumps such as those used for controlled delivery of fluid to a user. More specifically, this invention relates to improved methods and apparatuses for detecting fluid pressure and occlusions in fluid delivery paths of infusion pump systems.
- Infusion pump devices and systems are relatively well-known in the medical arts, for use in delivering or dispensing a prescribed medication such as insulin to a patient.
- such devices comprise a relatively compact pump housing adapted to receive a syringe or reservoir carrying a prescribed medication for administration to the patient through infusion tubing and an associated catheter or infusion set.
- a typical infusion pump includes a housing, which encloses a pump drive system, a fluid containment assembly, electronics system, and a power supply.
- the pump drive system typically includes a small motor (DC, stepper, solenoid, or other varieties) and drive train components such as gears, screws, and levers that convert rotational motor motion to a translational displacement of a stopper in a reservoir.
- the fluid containment assembly typically includes the reservoir with the stopper, tubing, and a catheter or infusion set to create a fluid path for carrying medication from the reservoir to the body of a user.
- the electronics system regulates power from the power supply to the motor.
- the electronics system may include programmable controls to operate the motor continuously or at periodic intervals to obtain a closely controlled and accurate delivery ofthe medication over an extended period.
- Infusion pumps ofthe general type described above have provided significant advantages and benefits with respect to accurate and timely delivery of medication or other fluids over an extended period compared to manual syringe therapy.
- the infusion pump can be designed to be extremely compact as well as water resistant, and may be adapted to be carried by the user, for example, by means of a belt clip or a harness.
- precise amounts of medication may be automatically delivered to the user without significant restriction on the user's mobility or life-style, including in some cases the ability to participate in water sports.
- medication infusion pump drive systems have included alarm systems designed to detect and indicate a pump malfunction and/or non-delivery ofthe medication to the patient due to a fluid path occlusion.
- alarm systems have typically used a limit switch to detect when the force applied to the reservoir stopper reaches a set point.
- One known detector uses an "on/off limit switch. When a set point is reached, the switch changes state (from open to closed or visa versa) triggering an alarm to warn the user, h U.S. Pat. No. 4,562,751, the limit switch is positioned at one end of a rotatable lead screw. The force applied to the limit switch by the lead screw is proportional to the pressure applied to the medication as a result of power supplied to the drive system to advance the stopper.
- an on/off limit switch as an occlusion detector has several disadvantages.
- the lead screw or other drive mechanism generally moves axially some distance to actuate the limit switch. If the medication is highly concentrated, and small incremental deliveries are required, such as 0.5 micro liters, then the required stopper displacement per delivery is very small. When an occlusion develops, the lead screw displacement toward the limit switch is also small. Therefore, many deliveries may be missed before the lead screw is displaced sufficiently to actuate the limit switch.
- a limit switch typically has only one set point. Noise, temporary pressure fluctuations during a delivery, and temperature and/or humidity effects may trigger false occlusion alarms. If the set point were placed higher to avoid some ofthe false detections, additional time would be required to detect a genuine occlusion.
- the motor is contained within the housing, and the one or more drive train components react to stimulus from the motor to force fluid from a reservoir into the user.
- the sensor is positioned to measure a parameter associated with the motor or a drive train component, and the sensor produces three or more output levels across a range of measurements.
- the electronics system processes the three or more sensor output levels to declare when an occlusion exists.
- the senor measures a force proportional to a force applied to a drive train component.
- the drive train component is a lead screw, h other particular embodiments, the drive train component is a slide.
- the senor measures tension or compression on a beam proportional to a torque applied to the motor.
- the drive train component is a beam. In other particular embodiments, the drive train component is one or more mounts.
- the senor measures tension or compression proportional to a pressure applied to a drive train component.
- the drive train component is a bellows. In other particular embodiments the drive train component is a cap.
- the senor is a force sensitive resistor. In alternative embodiments, the sensor is a capacitive sensor. In other alternative embodiments, the sensor is a strain gauge. In still other alternative embodiments the sensor is a piezoelectric sensor.
- the electronics system uses a maximum measurement threshold method to declare when an occlusion exists.
- a measurement threshold is at least 2.00 pounds.
- the electronics system uses a slope threshold method to declare when an occlusion exists.
- a slope threshold is about 0.05 pounds per measurement.
- the electronics system uses a maximum measurement threshold method, and a slope threshold method to declare when an occlusion exists.
- one or more measurements must exceed a minimum level to declare that an occlusion exists.
- the measured parameter is correlated with a fluid pressure in the reservoir.
- the electronics system processes the sensor output levels to determine when the reservoir is empty. In other particular embodiments, the electronics system processes the sensor output levels to determine when a stopper contacts an end ofthe reservoir. In still other particular embodiments, the electronics system processes the sensor output levels to determine when a slide is seated in a stopper.
- the sensor is positioned between the motor and a housing component. In particular embodiments, VHB adhesive is positioned between the motor and the housing component. In other particular embodiments, one or more components including the sensor are stacked between the motor and the housing component, and the housing component is positioned to remove space between the one or more components before the housing component is attached to the housing. In alternative embodiments, one or more components including the sensor are stacked between the motor and the housing, and back-fill material is injected through the housing to remove space between the one or more components and to fill the space between the one or more components and the housing.
- a method of detecting an occlusion in an infusion pump for infusing fluid into the body of a user includes the steps of obtaining a measurement from a sensor before each fluid delivery, calculating a slope of a line generated using two or more measurements, comparing the slope to a slope threshold, incrementing a counter when the slope exceeds the slope threshold, and declaring an occlusion when the counter exceeds a detection count
- a method of detecting an occlusion in an infusion pump for infusing fluid into the body of a user includes the steps of obtaining a measurement from a sensor before each fluid delivery, calculating a current slope of a line using two or more measurements, calculating an average slope using a previous average slope and the current slope, comparing the average slope to a slope threshold, incrementing a counter when the average slope exceeds the slope threshold, and declaring an occlusion when the counter exceeds a detection count value.
- the two or more measurements are not consecutive.
- an occlusion detection system for detecting an occlusion in a fluid path of an infusion pump with a reservoir containing fluid for delivering fluid to a user includes, a housing, forcing means for forcing fluid from a reservoir containing a fluid, sensing means for sensing a parameter associated with the forcing means for forcing fluid from the reservoir containing the fluid to obtain one or more measurements, and evaluation means.
- the sensing means producing one of three or more output levels for each ofthe one or more the measurements.
- the evaluation means evaluates the one of three or more output levels associated with each ofthe one or more measurements to declare when an occlusion exists.
- Fig. 1 is a front, perspective view of an infusion pump, according to an embodiment ofthe present invention.
- Fig. 2 is a rear view ofthe infusion pump of Fig. 1, with a rear door open to illustrate particular internal components.
- Fig. 3 is an illustration view of a drive system ofthe infusion pump of Fig. 1.
- Fig. 4 is an illustration view of an infusion pump drive system with a sensor according to a second embodiment ofthe present invention.
- Fig. 5 is an illustration view of an infusion pump drive system with a sensor according to a third embodiment ofthe present invention.
- Fig. 6(a) is a cross-sectional view of a sensor mounted between a drive system component and a housing according to a first and second embodiment of the present invention as shown in Figs 3 and 4.
- Fig. 6(b) is a cross-sectional view of a force sensitive resistor style sensor according to a fourth embodiment ofthe present invention.
- Fig. 7(a) is an exploded bottom/front perspective view of an infusion pump drive system, sensing system, and fluid containing assembly, incorporating the sensor of Fig. 6(b).
- Fig. 7(b) is an exploded top/front perspective view ofthe infusion pump drive system, sensing system, and fluid containing assembly of Fig. 7(a).
- Fig. 7(c) is a cross-sectional side view of an assembled infusion pump drive system, sensing system, and fluid containing assembly of Fig. 7(b).
- Fig. 7(d) is an enlarged cross-sectional side view ofthe sensing system shown as 7(d) in Fig. 7(c).
- Fig. 8(a) is a top view of a disk ofthe sensing system of Figs. 7(a)-(d).
- Fig. 8(b) is a side view ofthe disk ofthe sensing system of Figs. 7(a)-(d).
- Fig. 8(c) is a bottom view ofthe disk ofthe sensing system of Figs. 7(a)- (d).
- Fig. 9 is an enlarged, cross-sectional view of a sensor system according to a fifth embodiment ofthe present invention.
- Fig. 10 is a graph showing measured voltage across the force sensitive resistor of Fig. 6(b) as a function of applied force.
- Fig. 11 is a graph showing measured voltage across the force sensitive resistor of Fig. 6(b) during operation ofthe drive system shown in Figs. 7(a)-(d).
- Fig. 12 is a cross sectional view of a capacitive sensor mounted between a drive system component and a housing according a sixth embodiment ofthe present invention.
- Fig. 13 is a cross-sectional view of a capacitive sensor according a seventh embodiment ofthe present invention.
- Fig. 14(a) is a side plan view of a multi-switch sensor, where the switches are mounted in series and are individually electrically monitored according to an eighth embodiment ofthe present invention.
- Fig. 14(b) is a side plan view of a multi-switch sensor, where the switches are mounted in series and are electrically connected in series according to a ninth embodiment ofthe present invention.
- Fig. 14(c) is an electrical schematic for a multi-switch sensor, where the switches are electrically connected in series according to a tenth embodiment of the present invention.
- Fig. 15(a) is a top plan view of a multi-switch sensor, where the switches are mounted in parallel.
- Fig. 15(b) is a side plan view ofthe multi-switch sensor of Fig. 15(a).
- Fig. 15(c) is an electrical schematic for a multi-switch sensor, where the switches are electrically connected in parallel.
- Fig. 16 is an illustration view of a sensor in a pump drive system according to an eleventh embodiment ofthe present invention.
- Fig. 17 is an illustration view of a sensor in a pump drive system according to a twelfth embodiment ofthe present invention.
- Fig. 18 is an illustration view of a sensor in a pump drive system according to a thirteenth embodiment ofthe present invention.
- Fig. 19 is an illustration view of a sensor in a pump drive system according to fourteenth embodiment ofthe present invention.
- Fig. 20 is an illustration view of a sensor in a pump drive system according to a twentieth embodiment ofthe present invention.
- Fig. 21 is an illustration view ofthe infusion pump drive system of Fig. 4 showing certain torque forces.
- Fig. 22(a) is a perspective view of a sensor in a portion of a drive system according to a twenty-first embodiment ofthe present invention.
- Fig. 22(b) is a rear view ofthe sensor and pump drive system of Fig.
- Fig. 23 is an illustration view of a sensor in a portion of a pump drive system according to a twenty-second embodiment ofthe present invention.
- the invention is embodied in a pressure sensing system for an infusion pump.
- the infusion pump is used for infusing fluid into the body of a user.
- the infused fluid is insulin.
- many other fluids may be administered through infusion such as, but not limited to, HIV drugs, drugs to treat pulmonary hypertension, iron chelation drugs, pain medications, anti-cancer treatments, medications, vitamins, hormones, or the like.
- a programmable controller regulates power from a power supply to a motor.
- the motor actuates a drive train to displace a slide coupled with a stopper inside a fluid filled reservoir.
- the slide forces the fluid from the reservoir, along a fluid path (including tubing and an infusion set), and into the user's body.
- the pressure sensing system is used to detect occlusions in the fluid path that slow, prevent, or otherwise degrade fluid delivery from the reservoir to the user's body.
- the pressure sensing system is used to detect when: the reservoir is empty, the slide is properly seated with the stopper, a fluid dose has been delivered, the infusion pump is subjected to shock or vibration, the infusion device requires maintenance, or the like.
- the reservoir may be a syringe, a vial, a cartridge, a bag, or the like.
- the fluid pressure increases due to force applied on the fluid by the motor and drive train.
- the fluid pressure in the reservoir grows.
- the load on the entire drive train increases as force is transferred from the motor to the slide, and the slide is constrained from movement by the stopper pressing against the fluid.
- An appropriately positioned sensor can measure variations in the force applied to one or more ofthe components within the drive train. The sensor provides at least three output levels so measurements can be used to detect an occlusion and warn the user.
- an occlusion is detected before the pressure is high enough to deliver a dose greater than a maximum allowable bolus.
- the maximum allowable bolus is the maximum amount of fluid that may be delivered safely into the user at one time, which depends on the concentration of ingredients in the fluid, the sensitivity of the user to the fluid, the amount of fluid that the user presently needs, the amount of fluid still available in the user from previous deliveries, or the like.
- an infusion pump 101 includes a reservoir 104, a slide 109, a drive system 138, a programmable controller 113, and a power supply (not shown), all contained within a housing 102.
- the housing 102 has a rear door 120, which may be pivoted open to provide access to the interior ofthe pump 101 for removing and replacing the reservoir 104 and the slide 109 (Fig. 2 shows the rear door 120 pivoted to an open position).
- the fluid-containing reservoir 104 includes a reservoir barrel 105, a neck
- the neck 106 which has a smaller diameter than the barrel 105, comiects a front end ofthe barrel 105 to the head 103.
- the neck 106 seats within an outlet port 107 formed in the housing 102.
- the head 103 which has a larger diameter than the neck 106, extends through the housingl 02.
- the head 103 mates with tubing 110 by means of a fitting 108, thereby establishing fluid communication from the barrel 105, through the housing 102, and into the tubing 110.
- the tubing 110 extends from the fitting 108 to an infusion set 136, which provides fluid communication with the body ofthe user.
- a rear end ofthe barrel 105 forms an opening to receive the slide 109. Fluid is forced from the reservoir 104 as the drive system 138 moves the slide 109 from the rear end ofthe barrel 105 toward the front end ofthe barrel 105.
- the drive system 138 includes a motor 111, a coupler 121, a lead screw 117, a drive nut 116, and one or more latch arms 119.
- the motor 111 is coupled to the lead screw 117 by the coupler 121.
- the motor rotates the coupler 121, which in turn rotates the lead screw 117.
- the drive nut 116 includes a bore with internal threads (not shown). External threads on the lead screw 117 mesh with the internal threads on the drive nut 116. As the lead screw 117 rotates in response to the motor 111, the drive nut 116 is forced to travel along the length ofthe lead screw 117 in an axial direction d.
- the one or more latch arms 119 are attached to the drive nut 116, and extend away from the drive nut 116 to engage the slide 109, thereby coupling the slide 109 to the drive nut 116.
- the slide 109 is forced to translate parallel to the lead screw 117 in an axial direction d'.
- Power is supplied to the motor 111 by the power supply (not shown), in response to commands from the programmable controller 113.
- the motor 111 is a solenoid motor.
- the motor may be a DC motor, AC motor, stepper motor, piezoelectric caterpillar drive, shape memory actuator drive, electrochemical gas cell, thermally driven gas cell, bimetallic actuator, or the like.
- the drive train includes one or more lead screws, cams, ratchets, jacks, pulleys, pawls, clamps, gears, nuts, slides, bearings, levers, beams, stoppers, plungers, sliders, brackets, guides, bearings, supports, bellows, caps, diaphragms, bags, heaters, or the like.
- the power supply is one or more batteries.
- the power supply may be a solar panel, capacitor, AC or DC power supplied through a power cord, or the like.
- the programmable controller 113 may be programmed by a care provider such as a physician or trained medical personnel, or by the user.
- programming is conducted using an array of buttons 114 and a display 115 located on a face ofthe housing 102.
- the display 115 provides information regarding program parameters, delivery profiles, pump operation, alarms, warnings, statuses, or the like.
- the programmable controller 113 operates the motor 111 in a stepwise manner, typically on an intermittent basis; to administer discrete precise doses ofthe fluid to the user according to programmed delivery profiles.
- the programmable controller operates the motor continuously.
- the lead screw 117 includes a support pin 130 that extends through one or more bearings 132 and maintains contact with a sensor 134 positioned to detect forces applied by the lead screw 117 along the axis ofthe lead screw 117.
- the one or more bearings 132 and the coupler 121 are designed to allow the lead screw some translational freedom of movement along its axis while providing lateral support.
- the sensor 134 is therefore subjected to all axial forces applied to the lead screw 117 in the direction away from the motor 111.
- the axial force exerted by the lead screw 117 on the sensor 134 is generally correlated with the fluid pressure in the reservoir 109. For example, if an occlusion developed within the fluid path, blocking fluid delivery from the infusion pump to the body ofthe user, the fluid pressure would increase as the slide 109 is forced forward by the drive system 138.
- the programmable controller 113 commands power to be supplied to the motor 111, the slide 109 is driven forward into the reservoir 104, therefore increasing the fluid pressure.
- the fluid pressure is partially relieved by compliance in the system, for example, expansion ofthe tubing 110 and the reservoir 109, deformation of one or more 0-ring seals 140 on the slide 109, or the like.
- the remaining pressure is exerted against the slide 109, forcing it to back out ofthe reservoir 104.
- the slide 109 is prevented from moving by the one or more latch arms 119.
- the latch arms 119 transfer the force from the slide 109 to the drive nut 116, which in turn transfers the force, by way of thread engagement, to the lead screw 117.
- the sensor 134 is then subjected to a force with a magnitude correlated with the fluid pressure.
- the sensor 134 provides at least three output levels across the magnitude of sensed forces.
- An electronics system (not shown) supports the sensor 134 by providing power and/or signal processing, depending on the type of sensor 134.
- a motor 401 (or a motor with an attached gear box) includes a drive shaft 402, which drives a set of gears 403, as shown in Fig. 4.
- a lead screw 404 concentrically aligned with a gear 412 in the set of gears 403 is coupled to rotate with the gear 412.
- a hollow slide 405 includes an internally threaded bore 416 that passes through a rear end 418 ofthe slide 405, and engages with external threads ofthe lead screw 404.
- the axis ofthe slide 405 is generally parallel to the axis ofthe lead screw 404.
- the slide 405 further includes a tab (not shown) that engages a groove (not shown) in a housing (not shown) that runs parallel to the lead screw 404 to prevent the slide 405 from rotating when the lead screw 404 rotates.
- the slide 405 is forced to translate along the length ofthe lead screw 404.
- a front end 420 ofthe slide 405 engages a stopper 406 inside a reservoir 407.
- the stopper 406 is forced farther into the reservoir 407, thus forcing fluid from the reservoir 407, through tubing 422, and through an infusion set 408.
- the stopper and slide are formed as one piece.
- the lead screw 404 includes a support pin 414 that extends axially from an end ofthe lead screw 404 that is not enclosed within the slide 405.
- the support pin 414 passes through a bearing 409, and maintains contact with a sensor 410.
- the bearing 409 provides lateral support, and allows the lead screw 404 to have some axial translational displacement.
- the sensor 410 is positioned to prevent the lead screw 404 from translational motion away from the reservoir 407. And therefore, the sensor 410 is positioned to sense forces applied to the lead screw 404 in reaction to fluid pressure within the reservoir 407.
- the sensor provides at least three output levels based on the measurement ofthe sensed forces.
- an infusion pump 501 includes a motor 502, gear box 506, drive screw 503, slide 504, stopper 507, and a reservoir 505 generally aligned with each other to share a generally common concentric centerline, as shown in Fig. 5.
- the motor 502 rotates the drive screw 503 via a gear box 506.
- the drive screw 503 has external threads, which engage internal threads 522 on a cylindrical bore 520 running most ofthe length ofthe slide 504.
- the slide 504 further includes one or more tabs 514 that fit within one or more slots 516 in a housing 518 to prevent the slide 504 from rotating with respect to the housing 518. As the drive screw 503 rotates, the slide 504 is forced to travel along its axis.
- the slide 504 is in removable contact with a stopper 507 within the reservoir 505. And, as the slide 504 advances into the reservoir 505, the stopper 507 is displaced forcing fluid out ofthe reservoir 505, through a fitting 508, through tubing 509, and through an infusion set (not shown).
- a sensor 511 is positioned between the motor 502 in the housing 518 to detect forces translated from fluid pressure within the reservoir 505 through, the stopper 507, slide 504, drive screw 503, and the gear box 506 to the motor 502. The sensor 511 provides at least three output levels based on the detected forces. Further alternative embodiments are described in detail in co-pending application Serial No.
- a sensor is a force sensitive resistor, whose resistance changes as the force applied to the sensor changes.
- the sensor is a capacitive sensor, piezoresistive sensor, piezoelectric sensor, magnetic sensor, optical sensor, potentiometer, micro- machined sensor, linear transducer, encoder, strain gauge, and the like, which are capable of measuring compression, shear, tension, displacement, distance, rotation, torque, force, pressure, or the like.
- the sensor is capable of providing an output signal in response to a physical parameter to be measured.
- the range and resolution ofthe sensor output signal provides for at least three levels of output (three different states, values, quantities, signals, magnitudes, frequencies, steps, or the like) across the range of measurement.
- the sensor might generate a low or zero value when the measured parameter is at a minimum level, a high or maximum value when the measured parameter is at a relatively high level, and a medium value between the low value and the high value when the measured parameter is between the minimum and relatively high levels.
- the sensor provides more than three output levels, and provides a signal that corresponds to each change in resistance in a sampled, continuous, or near continuous manner.
- the sensor is distinguished from a switch, which has only two output values, and therefore can only indicate two levels of output such as, 'on' and 'off,' or 'high' and 'low.
- a force sensitive resistor as the sensor, which changes resistance as the force applied to the sensor changes.
- the electronics system maintains a constant supply voltage across the sensor.
- the output signal from the sensor is a signal current that passes through a resistive material ofthe sensor. Since the sensor resistance varies with force, and the supply voltage across the sensor is constant, the signal current varies with force.
- the signal current is converted to a signal voltage by the electronics system.
- the signal voltage is used as a measurement offeree applied to a drive train component or fluid pressure in the reservoir.
- a constant supply current is used and the signal voltage across the sensor varies with force (fluid pressure).
- other electronics systems and/or other sensors are used to convert fluid pressure or forces into a measurement used by the electronics system to detect occlusions in the fluid path.
- the force resistive sensor 706 has a substantially planar shape and is generally constructed of a layer offeree resistive material 606 sandwiched between two conductive pads 607, which are sandwiched within protective outer layers 608, as shown in Fig. 6(b). Electrical leads 605 carry a sensor signal from the conductive pads 607 to the electronics system (not shown).
- the force resistive material layer 606 is a suspension of conductive material in a polymer matrix.
- the conductive pads 607 and electrical leads 605 are formed from one or more layers of conductive ink, such as silver ink, gold ink, platinum ink, copper ink, conductive polymers, doped polymers, or the like.
- the protective outer layers 608 are polyester, which provide electrical insulation as well as protection from the elements.
- a sensor 706 ofthe type shown in Fig. 6(b) may be obtained under part number A101, from Tekscan Co. of South Boston, Massachusetts.
- the protective outer layers are made of other insulating materials such as Mylar, saran, urethane, resins, PNC, plastic, linen, cloth, glass, and the like.
- the conductive pads and/or leads are sheets of conductive material, wires, foil, or the like.
- the sensor 706 is positioned between flat rigid components to spread the force applied to the sensor 706 across the entire sensor surface area.
- the sensor 706 is located between two flat substantially rigid members, such as a housing and a motor.
- a sensor 601 is disposed between a rigid load plate 602 and a rigid back support 603, as shown in Fig. 6(a).
- the load plate 602 is in contact with an end of a lead screw 604. Examples of embodiments that use a lead screw to supply force to a sensor are shown in Figs. 3 and 4.
- the back support 603 is generally secured in place by the pump housing 609. Alternatively, a back support is not needed and the sensor is placed against the pump housing.
- the load plate is in contact with the motor or another drive train component.
- a layer of adhesive (not shown) is placed between the sensor and a plate or component, hi further alternative embodiments, force is applied to only a portion ofthe sensor.
- the design and method for mounting the sensor must: sufficiently limit unintended movement ofthe slide with respect to the reservoir; minimize space between components; be rigid enough for the sensor to immediately detect small changes in force; avoid preloading the sensor to the point that the sensor range is insufficient for occlusion, seating, and priming detection; provide sufficient resolution for early occlusion detection; compensate for sensor system and drive train component dimensional tolerance stack-up; allow sufficient movement in components ofthe drive system to compensate for misalignments, eccentricities, dimensional inconsistencies, or the like; avoid adding unnecessary friction that might increase the power required to run the drive system; and protect the sensor from shock and vibration damage.
- the slide must not be permitted to move in or out ofthe reservoir unless driven by the motor. If the motor and/or drive train components are assembled in a loose configuration that allows the slide to move within the reservoir without motor actuation, then if the infusion pump is jolted or bumped, fluid could be inadvertently delivered. Consequently, the sensor and/or components associated with mounting the sensor are generally positioned snugly against the drive train component from which force is being sensed, thus preventing the drive train component from moving when the infusion pump is subjected to shock or vibration.
- the senor is positioned so that as soon as the pump motor is loaded during operation, a drive train component applies a load to the sensor. Minimizing space between the sensor and the load-applying drive train component improves the sensor's sensitivity to load fluctuations. Small changes in load may be used to detect trends, and therefore provide an early warning that a blockage is developing before the fluid delivery is stopped entirely.
- the senor and associated electronics are intended to measure forces between 0.5 pounds (0.23 kg) and 5.0 (2.3 kg) pounds with the desired resolution of less than or equal to 0.05 pounds. Yet, the infusion pump including the sensor should survive shock levels that result in much higher forces being applied to the sensor than the intended sensor measurement range.
- the sensor range is from zero to 10 pounds (4.5 kg). In other alternative embodiments, the sensor range and/or resolution may be greater or smaller depending upon the concentration ofthe fluid being delivered, the diameter ofthe reservoir, the force required to operate the drive train, the level of sensor noise, the algorithms applied to detect trends from sensor measurements, or the like.
- the housing includes a variably positioned housing component that may be variably positioned with respect to a housing body.
- the variably positioned housing component is pressed against the sensor and/or sensor mounting components to remove gaps between the sensor, sensor mounting components and drive components before the variably positioned housing component is assembled with the housing body.
- the tolerance stack up between components is removed by adjusting the volume within the housing during assembly.
- one or more compressible components are used to compensate for tolerance stack up.
- flowable materials such as foam, adhesive, filler, liquid metal, plastic, microbeads, or the like are poured, injected, sprayed, forced, pumped, or the like, into the housing to substantially reduce space between the housing, sensor, sensor mounting components, and/or drive components.
- the infusion pump 701 includes a housing 702, and a housing bottom 703 to enclose a drive system 730, a sensing system 740, and a fluid containing assembly 750 as shown in Figs. 7(a)-(d).
- the drive system 730 includes a motor assembly 705, a drive-screw 710, and a slide 711.
- the sensing system 740 includes a sensor 706, an adhesive pad 707, a support disk 708, a housing cap 712, and an optional label 724.
- the fluid containing assembly 750 includes a stopper 714, a reservoir 715, and a reservoir connector 716.
- the drive system 730 forces fluid out ofthe reservoir 715 in a controlled and measured manner.
- the drive-screw 710 mates with threads 717 internal to the slide 711.
- One or more tangs 718 on the slide 711 ride inside groves 726 in the housing 702 that prevent the slide 711 from rotating.
- the motor assembly includes a tang 721 that prevents the motor assembly 705 from rotating within the housing 702.
- the stopper 714 is positioned to push fluid from inside the reservoir 715 through the reservoir connector 716 into tubing (not shown).
- the reservoir connector 716 seals the reservoir 715 in the housing 702.
- a shoulder 719 on the motor assembly 705 rests against a lip 720 formed on the inside ofthe housing 702.
- the lip 720 prevents the motor assembly 705 from translating along its axis in the forward direction (toward the reservoir 715).
- the components of the sensing system 740 are stacked behind the motor assembly 705, trapping the sensor 706 between the motor assembly 705 and components that are held in place by the housing bottom 703. Once the housing bottom 703 is securely attached to the housing 702, and the sensor system 740 is in place, the sensor 706 is subjected to axial forces placed on the motor assembly 705 by components of the drive system due to fluid pressure within the reservoir 715.
- the motor assembly 705 directly to the lip 720 ofthe housing 702 allows the motor assembly 705 to pitch and yaw slightly as it operates, and allows the sensor 706 to be subjected to axial forces applied to the motor assembly 705.
- the slide 711 is threaded onto the drive screw 710, then the motor assembly 705 and slide 711 are slid into the housing 702.
- the sensor 706 is then positioned on the motor assembly 705.
- the housing bottom 703 is securely welded to the housing 702.
- the housing bottom 703 is permanently attached to the housing 702 using one or more adhesives, ultrasonic welding, heat bonding, melting, snap fit, or the like.
- the remaining components ofthe sensor system 740 are installed through a hole 704 formed in the housing bottom 703.
- An adhesive pad 707 is placed on the sensor 706, followed by a rigid disk 708.
- the adhesive pad 707 serves several purposes aside from securing the disk 708 to the sensor 706.
- the adhesive pad 707 material conforms to the surface to correct for surface irregularities on the disk 708 and spread loads evenly across the sensor 706.
- the adhesive pad 707 has other properties such as a low shear strength that allows the motor assembly 705 some freedom to pitch and yaw, provides shock absorption and/or vibration dampening, and does not substantially compress under the range of forces to be measured by the sensor 706.
- the adhesive pad 707 is a 0.010-inch thick layer of very high bond (NHB) acrylic adhesive.
- one or more other materials and/or thicknesses are used that provide adhesion and/or cushioning such as tapes, epoxies, glues, foams, rubber, neoprene, plastics, hot melts, or the like, depending on the space to be filled, the forces to be measured, the size and weight of components to be stacked together, the amount of freedom of movement needed, the shock and vibration requirements, or the like.
- the disk 708 includes a generally cylindrical tang 722 extending from the center ofthe disk 708 away from the adhesive pad 707.
- the housing cap 712 includes a generally radially centered hexagonal bore 728 large enough to receive the cylindrical tang 722.
- the circumference ofthe housing cap 712 includes a beveled edge 725.
- the housing cap 712 is placed onto the disk 708 so that the tang 722 is positioned in the hexagonal bore 728, and the beveled edge 722 is facing away from the disk 708.
- the interior surface 726 (facing the disk 708) of the housing cap 712 includes ridges 723 that extend radially from one or more of the flat edges ofthe hexagonal bore 728 to the circumference ofthe housing cap 712, as shown in Figs.
- the ridges 723 hold the housing cap 712 away from the surface ofthe disk 708 to create space for adhesive.
- Adhesive is inserted through the hexagonal bore 728, at each ofthe corners, where there is space between the hexagonal bore 728 and the tang 722.
- Adhesive inserted at the hexagonal bore 728 spreads radially out to the edges ofthe disk 708 and the housing cap 712, filling the space between each ofthe ridges 723.
- the housing cap 712 is clear so that an assembler can observe the quality ofthe adhesive coverage between the housing cap 712 and the disk 708, and so that ultraviolet-light-cured adhesive may be used.
- the bore in the housing cap has a shape other than hexagonal, such as triangular, square, pentagonal, polygonal, circular, irregular, star shaped, or the like
- the tang on the disk may have other shapes, such as triangular, square, pentagonal, polygonal, circular, irregular, star shaped, or the like.
- other methods may be used to hold the housing cap off of the surface ofthe disk, such as dimples, grooves, flutes, bumps, texturing, broken ridges, or the like.
- other bonding methods may be used such as epoxy, hot melt, tape, contact cement, other adhesives, or the like.
- a force is applied to the housing cap 712 to assure that the shoulder 719 on the motor assembly 705 is seated against the lip 720 in the housing 702, and that space between components stacked between the motor assembly 705 and the housing cap 708 is substantially removed.
- the force is then removed, so that sensor 706 is not subjected to a preload, and the housing cap 712 is bonded to the housing bottom 703.
- adhesive is applied along the beveled edge 725 ofthe housing cap 712 to fill the space between the housing cap 712 and the housing bottom 703.
- a label 724 is placed over the housing cap 712. In alternative embodiments, several components are assembled together before being placed into the housing.
- the motor assembly 705, sensor 706, adhesive pad 707, and disk 708 may be assembled together and then placed into the housing 702 followed by the housing bottom 703 and then the housing cap 712.
- a sensor may include a rigid backing obviating the need for a disk.
- a housing bottom may not have an opening for a housing cap, so all ofthe components are installed into the housing and the housing bottom is positioned to remove spaces between the components and then secured to the housing.
- the force applied to remove space between components is not removed before the housing cap is secured to the housing bottom.
- the preload on the sensor is used to confirm that the space between the components is removed.
- a compressible member is used to compensate for tolerance stack-up when assembling a sensor 907 with a motor assembly 906, as shown in Fig. 9.
- An infusion pump 901 includes a housing bottom 903 attached to a housing 902, which encloses the motor assembly 906.
- the generally planar-shaped sensor 907 is positioned in direct contact with the motor assembly 906.
- the compressible member is a flexible silicone rubber seal 908 disposed between the outer edge ofthe sensor 907 and the housing bottom 903. Before assembly, the seal 908 is generally annular with a generally circular cross-section.
- the seal 908 When the seal 908 is placed on the sensor 906, and the housing bottom 903 is welded or otherwise attached to the main housing assembly 902, the seal 908 becomes deformed and adapts to the available space to form a water resistant seal between the sensor 907 and the housing bottom 903.
- the space filled by the seal 908 varies due to the dimensional tolerance stack-up of drive train components (not shown), the sensor 907, the housing 902, and the housing bottom 903.
- the housing bottom 903 includes an opening 904 generally in line with the axis of rotation ofthe motor assembly 906.
- a compliant back-fill material 909 such as silicone, urethane, hot melt adhesive, complaint epoxy, or the like, is injected through the opening 904 to fill the space between the sensor 907 and the housing bottom 903.
- the back-fill material 909 is substantially incompressible in the axial direction so that forces applied to the sensor 907 by the drive system are not relieved by the back-fill material 909. Furthermore, the back-fill material 909 mechanically isolates the drive system from shock and vibration ofthe housing 902 and housing bottom 903.
- one or more vents are provided in the housing bottom 903 to permit venting of air and improve dispersion ofthe material 909 as the material 909 is injected into the center opening 904 and flows radially outward to the seal 908.
- the seal 908 serves as a dam to prevent the material 909 from spreading around the motor assembly 906 and into other areas within the housing 902.
- the material 909 helps to absorb shock loads, dampen vibrations, compensate for tolerance stack-up, resist water penetration, and provide an even load distribution across the sensor 907.
- a label 910 is placed on the exterior of he housing bottom 903 over the opening 904.
- the senor and associated electronics provide a relatively linear voltage output in response to forces applied to the sensor by one or more drive train components.
- Particular preferred embodiments employ the sensor 706 shown in Figs. 6(b), and 7(a)-7(d).
- An example of measured voltages from the sensor 706, (and its associated electronics) in response to forces ranging from 0.5 pounds to 4.0 pounds, are shown as data points 201-208 in Fig. 10.
- each sensor is calibrated by collecting calibration points throughout a specified range of known forces, such as shown in Fig. 10.
- a measured voltage output for each known force is stored in a calibration lookup table. Then, during pump operation, the voltage output is compared to the calibration points, and linear interpolation is used convert the voltage output to a measured force.
- eight calibration points are used to create the calibration lookup table. Alternatively, more or fewer calibration points are used depending on, the sensor linearity, noise, drift rate, resolution, the required sensor accuracy, or the like, hi other alternative embodiments, other calibration methods are used such as, curve fitting, a look up table without interpolation, extrapolation, single point calibration, or the like.
- the voltage output in response to applied forces is substantially non-linear. In further alternative embodiments, no calibrations are used.
- sensor measurements are taken just prior to commanding the drive system to deliver fluid, and soon after the drive system has stopped delivering fluid
- sensor data is collected on a continuous basis at a particular sampling rate for example 10 Hz, 3 Hz, once every 10 seconds, once a minute, once every five minutes, or the like
- the sensor data is only collected just prior to commanding the drive system to deliver fluid
- sensor data is collected during fluid delivery.
- two methods are employed to declare occlusions in the fluid path, a maximum measurement tlireshold method, and a slope threshold method. Either method may independently declare an occlusion. If an occlusion is declared, commands for fluid delivery are stopped and the infusion pump provides a warning to the user. Warnings may include but are not limited to, sounds, one or more synthesized voices, vibrations, displayed symbols or messages, lights, transmitted signals, Braille output, or the like. In response to the warnings, the user may choose to replace one or more component in the fluid path including for example the infusion set, tubing, tubing connector, reservoir, stopper, or the like.
- occlusion warning Other responses that the user might have to an occlusion warning include: running a self test ofthe infusion pump, recalibrating the sensor, disregarding the warning, replacing the infusion pump, sending the infusion pump in for repair, or the like, hi alternative embodiments, when an occlusion is detected, attempts for fluid delivery are continued, and a warning is provided to the user or other individuals.
- an occlusion is declared when the measured force exceeds a threshold, h preferred embodiments, a threshold of 2.00 pounds (0.91 kg) is compared to force values measured by the sensor before delivery of fluid. If a measured force is greater than or equal to 2.00 pounds (0.91 kg), one or more confirmation measurements are taken before fluid delivery is allowed. If four consecutive force measurements exceed 2.00 pounds (0.91 kg), an occlusion is declared.
- a higher or lower threshold may be used and more or less confirmation readings may be collected before declaring an occlusion depending upon the sensor signal to noise level, the electronics signal to noise level, measurement drift, sensitivity to temperature and/or humidity, the force required to deliver fluid, the maximum allowable bolus, the sensor's susceptibility to shock and/or vibration, and the like, hi further alternative embodiments, the maximum measurement threshold method is not used.
- the use of sensors which provide a spectrum of output levels, rather than a switch, which is capable of providing only two discrete output levels, allows- the use of algorithms to detect trends in the output, and thus, declare an occlusion before the maximum measurement threshold is reached, hi preferred embodiments, the slope threshold method is used to evaluate trends to provide early occlusion detection.
- an occlusion is declared if a series of data points indicate that the force required for fluid delivery is increasing. A slope is calculated for a line passing through a series of consecutive data points. If the slope ofthe line exceeds a slope threshold, then pressure is increasing in the fluid path, and therefore, an occlusion may have developed. When nothing is blocking the fluid path, the force measured by the sensor before each delivery remains constant.
- the sawtooth appearance ofthe voltage plot is the result ofthe sharp increases and slow decay ofthe force measured by the sensor when the drive system is activated followed by fluid flowing from the infusion pump or relief due to compliance.
- the bottom of each sawtooth represents the static force measured before fluid delivery is begun. Initially, the fluid path is free of occlusions.
- Voltage samples measured before line 210 are values measured before the fluid path is blocked.
- the static force measurements taken before the fluid path is blocked are similar, and the slope of a line 212 drawn through those static force measurements is approximately or near zero. In other words, there is no occlusion in the fluid path, and the fluid pressure returns to the same offset value after each delivery. However, after line 210 (when the fluid path is blocked) the static force increases after each fluid delivery. The slope of a line 214 drawn through the static force measurements after line 210, is now greater than zero.
- the voltage output is generally proportional to the force applied to the sensor.
- an occlusion is declared.
- a voltage output of 1.0 volts is equal to or less than 1.0 pound (0.45 kg) offeree on the sensor, then it is clear that the slope threshold method is likely to declare the occlusion significantly sooner than the maximum measurement value of 2.00 pounds (0.91 kg) is obtained.
- the slope threshold method would declare an occlusion at about line 216, while the maximum measured threshold method would not have declared an occlusion even at the highest measurement on the page.
- larger or smaller changes in force over a larger or smaller number of measurements is used to declare an occlusion depending upon the force measurement resolution, the signal to noise ratio in the voltage output, friction in the drive train, the maximum allowable delivery, or the like.
- the slope is calculated from force or voltage values that are collected at times other than prior to fluid delivery such as, after fluid delivery, during fluid delivery, randomly, continuously, or the like, hi still further alternative embodiments, other algorithms may be employed to calculate a slope or evaluate the difference between one measurement and another, such as using differential values rather than actual measured values, calculating the derivative of measured values, using a subset of points across the range of points to calculate the slope, using curve fitting equations, employing smoothing, clipping or other filtering techniques, or the like.
- the static force must exceed a minimum threshold and the slope must exceed a maximum value for an occlusion to be declared.
- an occlusion is only declared if the last force measurement is greater than 1.00 pound (0.45 kg) and the slope is greater than 0.05 on average for each ofthe last 15 measurements (generally associated with the last 15 deliveries).
- an occlusion is declared if an average slope (A) exceeds a slope threshold of 0.05.
- the Current Slope (S) is calculated as:
- A A(-1) + W * (S-A(-1)).
- A(-l) is the average slope calculated at the previous force measurement
- W is a weighting factor of 0.30
- S is the current slope
- occlusion is declared if the average slope (A) is greater than a slope threshold of 0.05 for 15 measurements in a row. And if the average slope (A) drops below 0.05 for 4 measurements in a row, then restart counting. Measurements are taken just prior to each delivery. A delivery is defined as an incremental motor activation to dispense a controlled dose of fluid.
- a counter is incremented if the average slope exceeds the slope threshold. If the counter reaches a detection count value, then an occlusion is declared.
- the measured values used to calculate the current slope are separated by a greater or smaller number of measurements.
- the weighting factor W is larger or smaller depending on the previous average slope A(-l), the current force reading F(0), the accuracy ofthe measurements, and the like.
- the slope threshold is greater or smaller depending on the concentration ofthe fluid, the maximum allowable bolus, the sensor accuracy, the signal to noise ratio, and the like.
- one or more ofthe measured force values must meet or exceed 1.00 pound before the slope threshold method can declare an occlusion. For example, in some embodiments, the last four force measurements must be greater than 1.00 pound and the average slope must exceed 0.05 over the last 15 force measurements to declare an occlusion.
- the detection count value may be higher or lower depending on the sensor accuracy, the level of shock and vibration effects, the required range of measurement, and the like.
- the number of deliveries per measurement is dependent on the concentration ofthe fluid being delivered. For example, when delivering a U200 insulin formula, a measurement is taken with each delivery, when delivering a U100 insulin formula, a measurement is taken every two deliveries, and when delivering a U50 insulin formula, a measurement is taken every 4 deliveries.
- other algorithms are used to calculate a slope from the sensor measurements to compare to a slope threshold.
- Other algorithms include, but are not limited to, a least squares line fit through a number of measurements, averaging two or more groups of measurements and then calculating the slope of a line through the averaged values, regression algorithms, or the like.
- the current force measurement is compared to one or more previous force measurements, or to a trend observed from force measurements, to determine whether the current force measurement is valid (representative of a force applied to the drive train by the motor). If the cu ⁇ ent force measurement is not valid, it is ignored, replaced, re-measured, or the like.
- the senor is used to detect the removal of one or more components in the fluid path such as disconnecting the infusion set, disconnecting the tubing, or the like.
- the sensor is subjected to a nominal force due to the sum ofthe system factional components, the hydrodynamic forces associated with delivering a fluid through tubing, and the backpressure associated with the infusion set inserted in the patient.
- the nominal force is represented by a voltage offset such as represented by line 212 in Fig. 11. If a component in the fluid path were removed, the fluid backpressure would decrease thereby reducing the nominal force on the sensor.
- the infusion pump provides a warning to the user when the nominal force on the sensor decreases below a threshold, decreases by a particular percentage, decreases over a series of measurements, or the like. In alternative embodiments, larger or smaller decreases in the nominal force on the sensor are used to detect leaks in the fluid path.
- a sensor is used to detect when a reservoir is empty.
- An encoder is used to measure motor rotation. The encoder counts increase as the motor operates to move a stopper deeper into the reservoir. The encoder counts are used to estimate when the stopper is nearing the end of the reservoir. Once the encoder counts are high enough, if an occlusion is detected due to increased force on the sensor, the reservoir is declared empty, hi other particular embodiments, a sensor 706 is used to detect when a slide 711 is properly seated with a stopper 714, as shown in Fig. 7(a). The reservoir 715 containing the stopper 714 is filled with fluid before it is placed into an infusion pump 701.
- the stopper 714 has pliable internal threads 713 designed to grip external threads 712 on the slide 711.
- the stopper 714 and slide 711 do not need to rotate with respect to each other to engage the internal threads 713 with the external threads 712. hi fact, in particular embodiments, the internal threads 713, and the external threads 712, have different thread pitches so that some threads cross over others when the slide 711 and stopper 714 are forced together.
- the force continues to increase as more threads contact each other.
- the force measured by the sensor 706 increases to a level higher than the force needed to engage the internal threads 713 with the external threads 712.
- the seating threshold is generally about 1.5 pounds (0.68 kg). In alternative embodiments higher or lower seating thresholds may be used depending on the force required to mate the slide with the stopper, the force required to force fluid from the reservoir, the speed ofthe motor, the sensor accuracy and resolution, or the like. hi still other particular embodiments, other force thresholds are used for other purposes.
- a threshold of about 4 pounds (2 kg) is used.
- forces greater than about 4 pounds are used to detect shock loads that may be damaging to an infusion pump.
- drift measurements are taken though the life of a statistically significant number of sensors to generate a drift curve.
- the drift curve is used to compensate for drift in sensors used in infusion pumps.
- a lookup table offeree offset (due to drift) over operation time is stored in the infusion pump.
- the offset values are used to compensate the force measurements over time.
- the drift is characterized by an equation rather than a lookup table, hi other alternative embodiments, the sensor is periodically re-calibrated. In still other alternative embodiments, the sensor does not drift or the drift is insignificant enough that no compensation is needed.
- drift is compensated relative to the number of deliveries, the number of reservoir replacements, the integral of the forces placed on the sensor, or the like.
- the infusion pump includes humidity and/or temperature sensors. Measurements from the humidity and/or temperature sensors are used to compensate the sensor output. In alternative embodiments, humidity and/or temperature compensation is not needed.
- sensors for detecting characteristics ofthe drive system and the fluid containing assembly are not limited to the infusion pumps and drive systems shown in the figures. Moreover, the type of sensor need not be confined to a force sensitive resistor as described in prefe ⁇ ed embodiments.
- a capacitive sensor 1401 is used, such as shown in Fig. 12.
- a dielectric material 1402 is disposed between a conductive proximate plate 1403 and a conductive distal plate 1404.
- the distal plate 1404 is secured to a pump housing 1405 or alternatively, to any other stationary component of a medication infusion pump.
- the proximate plate 1403 is in contact with a drive system lead screw 1406.
- the proximate plate 1403 could be in contact with a pump motor or any other dynamic drive train component that is subjected to a reactive force co ⁇ elated to reservoir fluid pressure variations.
- the lead screw 1406 applies greater force to the proximate plate 1403 moving it closer to the distal plate 1404, and partially compressing the dielectric material 1402. As the gap across the dielectric material 1402 decreases, the sensor capacitance increases.
- the capacitance is expressed by the relationship:
- C is the capacitance
- ⁇ 0 is the permittivity constant (of free space)
- A is the surface area ofthe conductive plates
- d is the distance between the conductive plates.
- Electrical leads 1407 connect the proximate plate 1403 and the distal plate 1404 to the electronics system (not shown), which measures the varying capacitance.
- the electronics system and sensor are calibrated by applying known forces to the drive train. Once calibration is complete, the electronics system converts sensor capacitance to force measurements.
- a cylindrical capacitive sensor 1501 includes a conductive rod 1502, a dielectric inner ring 1503 and a conductive outer ring 1504, as shown in Fig. 13.
- the conductive rod 1502 is connected to a drive system lead screw (not shown).
- the conductive rod 1502 could be connected to any other dynamic drive train component that experiences movement co ⁇ elated to a reservoir fluid pressure.
- Conductive leads (not shown) electrically connect the rod 1502 and the outer ring 1504 to the system electronics.
- the lead screw is axially displaced, which in turn moves the rod 1502 further into the opening 1505 formed by the rings 1503 and 1504.
- the surface area ofthe capacitor increases, thereby increasing capacitance according to the relationship:
- C is the sensor capacitance
- / is the length ofthe rod 1502 that is enclosed by the rings 1504 and 1503
- a is the radius ofthe rod 1502
- b is the internal radius ofthe outer ring 1504
- SQ is the permittivity of free space.
- feree sensitive resistors and capacitive sensors have been described above, it should be appreciated that the embodiments disclosed herein include any type of sensor that can provide least three different levels of output signal across the range of intended use. Sensors may be positioned within various embodiments of drive trains to measure either a force applied to a drive train component, a change in position of a drive train component, a torque applied to a drive train component, or the like.
- a piezoelectric sensor is used to produce varying voltages as a function of varying forces applied to a drive train component.
- the piezoelectric sensor is made from polarized ceramic or Polyvinylidene Floride (PVDF) materials such as Kynar®, which are available from Amp Incorporated, Valley Forge, Pennsylvania.
- PVDF Polyvinylidene Floride
- multi-switch sensors are used. A distinction is made between switches, which have only two distinct output levels, versus sensors, which have more than two output levels. But, multi-switch sensors are sensors made from two or more discrete switches having different actuation set points. Thus, these multi-switch sensors have at least three output levels.
- a sensor 1601 is comprised of five series mounted switches 1602a - 1602e, each of which has a different set-point, as shown in Figs. 14(a).
- a first switch 1602a is positioned in contact with a lead screw 1603, or alternatively, any other drive train component that is subjected to a force co ⁇ elated with a reservoir fluid pressure.
- a last switch 1602e is secured to a pump housing 1604 or alternatively, to any other stationary component of an infusion pump.
- Conductive leads 1605 are attached to each ofthe switches 1602a - 1602e.
- the switchesl602a - 1602e are triggered one after another as their set points are reached.
- the electronics system (not shown) monitors each switch.
- the sensor resolution is dependent on the number of switches and the relative force required for triggering each switch, the range of measurements needed, and the like.
- the senor incorporates a multi- switch design where a series of switches 1607a - 1607e are electrically connected in series, as shown in Fig 14(b).
- An electrical lead 1608 connects a first switch 1607a to the electronics system (not shown).
- Leads 1609 connect each switch 1607a to 1607e in series.
- lead 1610 connects a last switch 1607e to the electronics system. All ofthe switches 1607a - 1607e are electrically connected such that continuity exists through each switch regardless of whether a switch is in a first position or a second position (on or off). Otherwise, the series electrical connection would be broken when a switch is opened.
- each ofthe switches 1607a - 1607e have a first position and a second position, as shown in Fig. 14(c).
- each switch When in the first position, each switch connects the circuit through a first resistor 161 la - 161 le, each of which has a value of Rl ohms.
- each switch When each switch is subjected to a force at its respective set point, it moves to its second position thereby disconnecting from the first resistor 1611a - 1611e, and closing the circuit through a second resistor 1612a - 1612e, each having a value of R2 ohms.
- Rl does not equal R2.
- a different over-all circuit resistance is measured by the electronics system co ⁇ esponding to the force applied to a drive train component.
- the resistance of all ofthe first resistors Rl is greater than or less than the resistance of all ofthe second resistors R2
- the resistance of each ofthe first resistors Rl are not equal to each other
- the resistance of each ofthe second resistors R2 are not equal to each other.
- a switch with the highest set point may not include resistors, but may simply be an on/off switch.
- other electrical components and or a ⁇ angements are used, such as a parallel circuit shown in Fig.
- an infusion pump uses a sensor made of two or more multi-switches that are a ⁇ anged in a parallel circuit.
- a sensor 1701 has five switches 1702a - 1702e a ⁇ anged in parallel, each with a different set point, as shown in Figs. 15(a) and 15(b).
- the switches 1702a - 1702e are mechanically a ⁇ anged in parallel such that one side of all five switches 1702a - 1702e is in contact with a pump housing 1703, or another member that is stationary with respect to the housing.
- the opposite side of each ofthe switches 1702a - 1702e is secured to a plate 1704.
- a drive train component such as a lead screw 1705, directly or indirectly applies force to the plate 1704.
- the force is co ⁇ elated to the fluid pressure in the reservoir (not shown).
- each one ofthe switches 1702a - 1702e will close at different set points depending upon the amount of force exerted on the plate 1704 by the lead screw 1705.
- the switches 1702a - 1702e can be electrically connected to each other and to the system electronics in any number of ways.
- each switch could be independently connected to the system electronics.
- the switches 1702a - 1702e could be electrically connected in series.
- each switch 1702a - 1702e is associated with a resistor 1707a - 1707e, and the switches are connected in parallel, as shown in Fig 15(c).
- a conductive lead 1708 provides an input signal from an electronics system (not shown) to the parallel a ⁇ ay of switches 1702a - 1702e.
- the switch closes, and cu ⁇ ent flows through the resistor 1707a - 1707e associated with the switch 1702a - 1702e through a lead 1709, and back to the electronics system.
- different resistors are placed in parallel in the network, thus changing the impedance ofthe network. The impedance is measured by the electronics system and converted to measured force that is co ⁇ elated to fluid pressure.
- a slide assembly 1807 is comprised of a thin, dome-shaped cap 1802, mounted on a support assembly 1803, and secured to a lead screw 1804, as shown in Fig. 16.
- a strain gauge sensor 1801 is mounted on the cap 1802.
- the cap 1802 is constructed of a resilient material, such as silicone, and is in contact with a stopper 1805, which is slidably positioned in a reservoir 1806. As the lead screw 1804 advances, the support assembly 1803 and cap 1802 move axially to contact the stopper 1805, and cause the stopper 1805 to move axially forcing fluid from the reservoir 1806.
- the cap 1802 deflects as it is pressed against the stopper 1805. And as the cap 1802 deflects, the dimensions ofthe strain gauge sensor 1801 are changed, thereby changing the strain gauge impedance. As fluid pressure in the reservoir 1806 increases, the cap 1802 deflection increases, which changes the impedance ofthe strain gauge sensor 1801.
- the strain gauge sensor output impedance is related to the force imposed on the stopper 1805, which is co ⁇ elated with the reservoir fluid pressure.
- the electronics system is calibrated to convert the measured strain gauge sensor output impedance to force on the drive train or fluid pressure.
- Having the sensor in direct contact with the stopper 1805 ameliorates the effects of dimensional tolerance stack-up and frictional forces within the drive train. This can allow for a more accurate measurement ofthe pressures within the reservoir 1806. Additionally, since the strain gauge sensor 1801 can provide a range of output levels, software/firmware can be used to set a threshold value that is appropriate for the particular device or drug being infused. Furthermore, over time, the system can calibrate or zero the strain gauge sensor 1801 when there is no reservoir 1806 in place in order to avoid undesirable effects from drift, creep, temperature, humidity, or the like.
- a slide 1908 includes a strain gauge sensor
- the bellows 1903 has a proximate wall 1902a, a distal wall 1902b, and a flexible sidewall 1902c.
- the strain gauge sensor 1901 is mounted on the distal wall 1902b. At least a portion ofthe perimeter ofthe distal wall 1902b supported by the support assembly 1904. And the support assembly 1904 is secured to a lead screw 1905.
- the distal wall 1902b is constructed of a deflectable resilient material, such as silicone, so that as pressure is placed against the proximate wall 1902a, the distal wall 1902b deflects toward the lead screw 1905.
- the bellows 1903 is driven forward by the lead screw 1905 and support assembly 1904 to push on a stopper 1906 that is slidably positioned in a reservoir 1907. As the lead screw 1905 continues to advance, the bellows 1903 pushes on the stopper 1906 to force fluid from the reservoir 1907.
- the bellows 1903 may be filled with a fluid to improve the transfer of pressure from the proximate wall 1902a to the distal wall 1902b.
- the amount of distal wall 1902b deflection is co ⁇ elated with the force required to move the stopper 1906.
- the strain gauge sensor output is co ⁇ elated with the amount of distal wall 1902b deflection.
- a slide 2009 is comprised of a strain gauge sensor 2001, a support assembly 2004 and a resilient bellows 2003 having a threaded member 2006, as shown in Fig. 18.
- the strain gauge sensor 2001 is mounted on a distal wall 2002 ofthe bellows 2003.
- the support assembly 2004 supports at least a portion ofthe perimeter ofthe distal wall 2002 ofthe bellows 2003, and couples a lead screw 2005 with the bellows 2003.
- the threaded member 2006 ofthe bellows 2003 is removably secured to a stopper 2007 that is slidably positioned in a reservoir 2008.
- external threads 2115 of a lead screw 2101 are engaged with the internal threads 2116 of a slide 2102 to convert the rotational motion of the lead screw 2101 to translational motion of the slide 2102, as shown in Fig. 19.
- the slide 2102 has a nose 2103 formed by a relatively stiff generally cylindrical sidewall 2117 and a proximate nose wall 2104 made of a flexible material such as silicone.
- a strain gauge sensor 2105 is secured to the proximate nose wall 2104.
- the slide 2102 is removably coupled to a stopper 2106 slidably positioned in a fluid reservoir 2107.
- the stopper 2106 has a cavity 2112 formed by an internally threaded cylindrically-shaped sidewall 2110, which forms a water-tight seal with the reservoir 2107, and a flexible proximate wall 2108.
- the cavity 2112 is adapted to receive the nose 2103, so that the proximate wall 2108 of the cavity 2112 abuts the proximate nose wall 2104 ofthe nose 2103.
- the nose sidewall 2117 has external threads 2113 for removably engaging the internal threads 2114 on the sidewall 2110 of the stopper cavity 2112. The threaded coupling between the slide 2102 and the stopper 2106 enables the drive system to move the stopper 2106 bi-directionally.
- a reinforcing ring 2109 is disposed in the stopper sidewall 2110 to provide the necessary stiffness to maintain a frictional fit between the stopper 2106 the reservoir 2107, thereby enhancing a watertight seal, hi further alternative embodiments, the reinforcing ring 2109 is not needed.
- the flexible proximate wall 2108 ofthe stopper 2106 deflects due to fluid pressure, it contacts the proximate nose wall 2104 causing it to deflect, thus deflecting the strain gauge sensor 2105.
- This provides a measurement of the pressure within the reservoir 2107 independent ofthe force used to drive the stopper 2106.
- This sensor placement provides a true indicator of pressure within the reservoir 2107. The frictional forces between the stopper 2106 and the reservoir 2107, as well as between other drive train components are not measured, and therefore do not affect the measurement ofthe fluid pressure.
- measurements from the strain gauge sensor 2105 are used to confirm co ⁇ ect reservoir 2107 installation. If the reservoir 2107 is installed into the infusion pump properly and the slide 2102 is fully engaged with the stopper 2106 within the reservoir 2107, then the stopper 2106 applies at least a slight contact with the proximate nose wall 2104 imparting a preload on the strain gauge sensor 2105. If the reservoir 2107 is not inserted (or fully inserted), then no pre-load is detected, and the electronics system provides a warning to the user. hi other embodiments, shear forces are measured to provide an indication of fluid pressure.
- a slide assembly 2207 is comprised of a support assembly 2202, piezoelectric shear sensors 2203, and a nose 2204 having a proximate nose wall 2204a and a sidewall 2204b, a shown in Fig. 20.
- a lead screw 2201 is secured to the support assembly 2202.
- the piezoelectric shear sensors 2203 are disposed between the support assembly 2202 and the sidewall 2204b ofthe nose 2204.
- a stopper 2205 is slidably mounted in a reservoir 2206.
- the stopper 2205 has a proximate wall 2209 and a generally cylindrical sidewall 2210 that form a cavity 2208 adapted to receive the nose 2204 portion ofthe slide assembly 2207.
- the stopper 2205 does not have a cavity. Rather, the nose 2204 abuts the distal wall 2210 ofthe stopper 2205.
- the force required to move the stopper 2205 is measured as shear forces placed on the piezoelectric shear sensors 2203. As the pressure on the stopper 2205 increases, the shear forces between the nose 2204 and the support assembly 2202 increase and apply shear force to the sensors 2203.
- a motor 2301 (or a motor with an attached gear box) has a drive shaft 2302 engaged to drive a set of gears 2303.
- the motor 2301 generates a torque powering the drive shaft 2302 in direction d, as shown in Fig. 21.
- the drive shaft 2302 rotates the gears 2303 to transfer the torque to a lead screw 2304, rotating the lead screw 2304 in the direction d'.
- the lead screw 2304 is mounted on a bearing 2305 for support.
- the threads ofthe lead screw 2304 are engaged with threads (not shown) in a slide 2306.
- the slide 2306 is engaged with a slot (not shown) in the housing (not shown) to prevent the slide 2306 from rotating, but allowing it to translate along the length ofthe lead screw 2304.
- the torque d' ofthe lead screw 2304 is transfe ⁇ ed to the slide 2306 causing the slide 2306 to move in an axial direction, generally parallel to the drive shaft 2302 ofthe motor 2301.
- the slide 2306 is in contact with a stopper 2307 inside a reservoir 2308.
- the stopper 2307 is forced to travel in an axial direction inside the reservoir 2308, forcing fluid from the reservoir 2308, through tubing 2309, and into an infusion set 2310.
- the stopper 2307 is forced to advance, and pressure in the reservoir 2308 increases.
- the force ofthe stopper 2307 pushing against the fluid results in a reaction torque d" acting on the motor 2 .
- sensors are used to measure the torque d" applied to the motor 2301, and the sensor measurement is used to estimate the pressure in the reservoir 2308.
- a motor 2401 has a motor case 2402, a proximate bearing 2403, a distal bearing 2404, a motor shaft 2408, and a gear
- the motor 2401 is secured to a housing (not shown) or other fixed point by a beam 2406.
- One end ofthe beam 2406 is secured to the motor case 2402 at an anchor point 2410, and the other end ofthe beam 2406 is secured to the housing (not shown) at a housing anchor point 2409.
- a strain gauge sensor 2407 is mounted on the beam 2406.
- Each end ofthe motor shaft 2408 is mounted on the bearings 2403 and 2404 that provide axial support but allow the motor shaft 2408 and motor 2401 to rotate.
- the beam 2406 supplies a counter moment in the direction d' that is equal in magnitude and opposite in direction to the motor driving torque d. As the torque produced by the motor 2401 increases, the reaction moment d" in the beam 2406 increases thereby increasing the strain within the beam 2406 and causing the beam 2406 to deflect.
- the strain gauge sensor 2407 mounted on the beam 2406 is used to measure deflection ofthe beam 2406.
- the electronics system converts the strain gauge sensor measurements to estimates of fluid pressure in a reservoir (not shown) or force acting on the drive train (not shown).
- This method of measurement provides information about the pressure within the reservoir (and frictional stack-up), as well as information about the drive train. If for example, there were a failure within the drive train such as, in the gearing, bearings, or lead screw interface, the torque measured at the strain gauge sensor 2407 would detect the failure.
- the strain gauge 2407 is used to confirm motor activation and fluid delivery. During normal fluid delivery, the measured moment increases shortly while the motor is activated, and then decreases as fluid exits the reservoir relieving pressure and therefore the moment.
- a beam provides the necessary compliance to protect a drive system from a rewind hard stop.
- a motor is used to rewind a slide in preparation to replace a reservoir.
- a hard stop at full motor speed could damage or reduce the life of drive system components.
- the beam absorbs the energy when the slide reaches the fully retracted position, without damaging the drive system.
- a strain gauge sensor can work in several modes common to strain gauge sensor technology.
- the strain gauge sensor could be mounted such that it measures tension or compression, or bending.
- a strain gauge sensor could be mounted to compensate for temperature variances and other system noises.
- the designs of Figs. 19 - 22(b) are not limited to strain gauge sensor technology. Piezoelectric, capacitive, or magnetic sensors could be used as well.
- a motor 2501 has a case 2502, a proximate bearing 2503, a distal bearing 2504, a motor shaft 2507, and a gear 2505, as shown in Fig. 23.
- the portion ofthe drive train not shown in Fig. 23 is similar to that shown in Fig. 21.
- the proximate bearing 2503 is disposed on one side ofthe pump motor 2501, and the distal bearing 2504 is disposed on the opposite side of the pump motor 2501.
- Motor mounts 2506 secure the case 2502 to the housing 2509 (or other fixed point).
- Piezoelectric shear mode sensors 2508 are secured to the mounts 2506. As the reaction torque d' increases due to an increase in the applied drive torque d, shear stress in the motor mounts 2506 increase. The sensors 2508 in turn provide a voltage co ⁇ elated to the drive torque d. As discussed previously, the drive torque d is co ⁇ elated to the fluid pressure in a reservoir (not shown).
Abstract
Description
Claims
Priority Applications (4)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
CA002406026A CA2406026C (en) | 2000-03-29 | 2001-03-28 | Improved methods, apparatuses, and uses for infusion pump fluid pressure and force detection |
EP01922776A EP1267960B1 (en) | 2000-03-29 | 2001-03-28 | Apparatus for infusion pump fluid pressure and force detection |
AU2001249540A AU2001249540A1 (en) | 2000-03-29 | 2001-03-28 | Improved methods, apparatuses, and uses for infusion pump fluid pressure and force detection |
DE60119502T DE60119502T2 (en) | 2000-03-29 | 2001-03-28 | DEVICE FOR DETERMINING THE LIQUID PRESSURE AND THE POWER CONSUMPTION IN INFUSION PUMPS |
Applications Claiming Priority (4)
Application Number | Priority Date | Filing Date | Title |
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US19290100P | 2000-03-29 | 2000-03-29 | |
US60/192,901 | 2000-03-29 | ||
US24339200P | 2000-10-26 | 2000-10-26 | |
US60/243,392 | 2000-10-26 |
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WO2001072357A2 true WO2001072357A2 (en) | 2001-10-04 |
WO2001072357A3 WO2001072357A3 (en) | 2002-05-23 |
WO2001072357A9 WO2001072357A9 (en) | 2002-12-27 |
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PCT/US2001/009893 WO2001072357A2 (en) | 2000-03-29 | 2001-03-28 | Improved methods, apparatuses, and uses for infusion pump fluid pressure and force detection |
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US (2) | US6485465B2 (en) |
EP (1) | EP1267960B1 (en) |
AT (1) | ATE325632T1 (en) |
AU (1) | AU2001249540A1 (en) |
CA (1) | CA2406026C (en) |
DE (1) | DE60119502T2 (en) |
WO (1) | WO2001072357A2 (en) |
Cited By (42)
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---|---|---|---|---|
WO2003033057A1 (en) * | 2001-10-18 | 2003-04-24 | Tecpharma Licensing Ag | Injection device comprising an energy accumulator |
KR20040003811A (en) * | 2002-07-04 | 2004-01-13 | 주식회사 옵토스타 | An injection device of Ringer's solution |
WO2004052429A1 (en) * | 2002-12-10 | 2004-06-24 | Zi Medical Plc | A syringe driver assembly |
EP1529546A1 (en) * | 2003-11-04 | 2005-05-11 | Medex, Inc. | Syringe pump rapid occlusion detection system |
WO2006015601A1 (en) * | 2004-08-13 | 2006-02-16 | Unomedical A/S | Reservoir for front end loaded infusion device |
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US7092797B2 (en) | 2004-05-25 | 2006-08-15 | Sherwood Services Ag | Flow monitoring system for a flow control apparatus |
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EP1759727A1 (en) * | 2005-09-02 | 2007-03-07 | F.Hoffmann-La Roche Ag | Infusion device having a control unit |
WO2008057223A2 (en) | 2006-10-26 | 2008-05-15 | Mallinckrodt Inc. | Medical fluid injector having a thermo-mechanical drive |
WO2008083692A1 (en) * | 2006-12-22 | 2008-07-17 | Fraunhofer-Gesellschaft zur Förderung der angewandten Forschung e.V. | Device and method for checking and monitoring the pressure in pressure pipes and/or conduits |
US7881883B2 (en) | 2004-04-20 | 2011-02-01 | Roche Diagnostics International Ag | Device and method for the detection of an occlusion |
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US8618948B2 (en) | 2007-10-22 | 2013-12-31 | Roche Diagnostics International Ag | Automatically operating injection device and method for determining an injection occlusion |
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US10086145B2 (en) | 2015-09-22 | 2018-10-02 | West Pharma Services Il, Ltd. | Rotation resistant friction adapter for plunger driver of drug delivery device |
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US10220132B2 (en) | 2014-12-19 | 2019-03-05 | Fenwal, Inc. | Biological fluid flow control apparatus and method |
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US11273261B2 (en) | 2008-01-28 | 2022-03-15 | Novo Nordisk A/S | Injection device for performing medical injections |
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US11819666B2 (en) | 2017-05-30 | 2023-11-21 | West Pharma. Services IL, Ltd. | Modular drive train for wearable injector |
Families Citing this family (630)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
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 |
US8346337B2 (en) | 1998-04-30 | 2013-01-01 | Abbott Diabetes Care 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 |
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US8480580B2 (en) | 1998-04-30 | 2013-07-09 | 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 |
US8465425B2 (en) | 1998-04-30 | 2013-06-18 | Abbott Diabetes Care Inc. | Analyte monitoring device and methods of use |
US7766873B2 (en) | 1998-10-29 | 2010-08-03 | Medtronic Minimed, Inc. | Method and apparatus for detecting occlusions in an ambulatory infusion pump |
US7621893B2 (en) | 1998-10-29 | 2009-11-24 | Medtronic Minimed, Inc. | Methods and apparatuses for detecting occlusions in an ambulatory infusion pump |
US7193521B2 (en) * | 1998-10-29 | 2007-03-20 | Medtronic Minimed, Inc. | Method and apparatus for detecting errors, fluid pressure, and occlusions in an ambulatory infusion pump |
US6645177B1 (en) * | 1999-02-09 | 2003-11-11 | Alaris Medical Systems, Inc. | Directly engaged syringe driver system |
US7063684B2 (en) * | 1999-10-28 | 2006-06-20 | Medtronic Minimed, Inc. | Drive system seal |
US6497676B1 (en) | 2000-02-10 | 2002-12-24 | Baxter International | Method and apparatus for monitoring and controlling peritoneal dialysis therapy |
WO2001070304A1 (en) * | 2000-03-22 | 2001-09-27 | Docusys, Inc. | A drug delivery and monitoring system |
US6485465B2 (en) * | 2000-03-29 | 2002-11-26 | Medtronic Minimed, Inc. | Methods, apparatuses, and uses for infusion pump fluid pressure and force detection |
US6663602B2 (en) * | 2000-06-16 | 2003-12-16 | Novo Nordisk A/S | Injection device |
GB0020060D0 (en) * | 2000-08-16 | 2000-10-04 | Smiths Industries Plc | Syringe pumps |
ATE439643T1 (en) * | 2000-11-29 | 2009-08-15 | Docusys Inc | DEVICE FOR DISPENSING A MEDICINAL PRODUCT WITH A TRACKING CODE |
US6560471B1 (en) | 2001-01-02 | 2003-05-06 | Therasense, Inc. | Analyte monitoring device and methods of use |
US20030060695A1 (en) * | 2001-03-07 | 2003-03-27 | Connelly Patrick R. | Implantable artificial organ devices |
EP1397068A2 (en) | 2001-04-02 | 2004-03-17 | Therasense, Inc. | Blood glucose tracking apparatus and methods |
WO2002083209A1 (en) * | 2001-04-13 | 2002-10-24 | Nipro Diabetes Systems | Drive system for an infusion pump |
EP2140891B1 (en) | 2001-05-18 | 2013-03-27 | DEKA Products Limited Partnership | Conduit for coupling to a fluid delivery device |
US8034026B2 (en) | 2001-05-18 | 2011-10-11 | Deka Products Limited Partnership | Infusion pump assembly |
US20120209197A1 (en) * | 2002-01-04 | 2012-08-16 | Lanigan Richard J | Infusion pump assembly |
US20030100883A1 (en) * | 2001-08-31 | 2003-05-29 | Kristensen Lars Thougaard | Cartridge for liquid insulin |
US20030055380A1 (en) * | 2001-09-19 | 2003-03-20 | Flaherty J. Christopher | Plunger for patient infusion device |
GB0201686D0 (en) * | 2002-01-25 | 2002-03-13 | Dca Design Consultants Ltd | Improvements in and relating to a medicament delivery device |
US10173008B2 (en) | 2002-01-29 | 2019-01-08 | Baxter International Inc. | System and method for communicating with a dialysis machine through a network |
US8775196B2 (en) | 2002-01-29 | 2014-07-08 | Baxter International Inc. | System and method for notification and escalation of medical data |
US7666171B2 (en) * | 2002-04-18 | 2010-02-23 | Haleys Pump Company | Portable instillation apparatus and method |
US8234128B2 (en) | 2002-04-30 | 2012-07-31 | Baxter International, Inc. | System and method for verifying medical device operational parameters |
US7175606B2 (en) | 2002-05-24 | 2007-02-13 | Baxter International Inc. | Disposable medical fluid unit having rigid frame |
AU2003233504A1 (en) * | 2002-05-24 | 2003-12-12 | Eli Lilly And Company | Medication injecting apparatus with fluid container piston-engaging drive member having internal hollow for accommodating drive member shifting mechanism |
DE10223192A1 (en) * | 2002-05-24 | 2003-12-11 | Disetronic Licensing Ag | Ampoule and delivery device |
US7153286B2 (en) | 2002-05-24 | 2006-12-26 | Baxter International Inc. | Automated dialysis system |
DE10224750A1 (en) | 2002-06-04 | 2003-12-24 | Fresenius Medical Care De Gmbh | Device for the treatment of a medical fluid |
US20040225252A1 (en) * | 2002-06-14 | 2004-11-11 | John Gillespie | System and method for operating an infusion pump |
US7018361B2 (en) | 2002-06-14 | 2006-03-28 | Baxter International Inc. | Infusion pump |
DE10226643A1 (en) * | 2002-06-14 | 2004-01-15 | Disetronic Licensing Ag | Piston stopper for injection device, product container and injection device |
US6997905B2 (en) * | 2002-06-14 | 2006-02-14 | Baxter International Inc. | Dual orientation display for a medical device |
US20030236489A1 (en) | 2002-06-21 | 2003-12-25 | Baxter International, Inc. | Method and apparatus for closed-loop flow control system |
EP1523347B1 (en) | 2002-07-19 | 2011-05-18 | Baxter International Inc. | Systems and methods for performing peritoneal dialysis |
US7238164B2 (en) | 2002-07-19 | 2007-07-03 | Baxter International Inc. | Systems, methods and apparatuses for pumping cassette-based therapies |
AU2003245872A1 (en) | 2002-07-24 | 2004-02-09 | M 2 Medical A/S | An infusion pump system, an infusion pump unit and an infusion pump |
JP2005537116A (en) * | 2002-08-31 | 2005-12-08 | ディセトロニック・ライセンシング・アクチェンゲゼルシャフト | Dosing device with temperature sensor |
US7993108B2 (en) | 2002-10-09 | 2011-08-09 | Abbott Diabetes Care Inc. | Variable volume, shape memory actuated insulin dispensing pump |
US7399401B2 (en) * | 2002-10-09 | 2008-07-15 | Abbott Diabetes Care, Inc. | Methods for use in assessing a flow condition of a fluid |
DE60336834D1 (en) | 2002-10-09 | 2011-06-01 | Abbott Diabetes Care Inc | FUEL FEEDING DEVICE, SYSTEM AND METHOD |
US7727181B2 (en) | 2002-10-09 | 2010-06-01 | Abbott Diabetes Care Inc. | Fluid delivery device with autocalibration |
US7104763B2 (en) * | 2002-10-16 | 2006-09-12 | Abbott Laboratories | Method for discriminating between operating conditions in medical pump |
US7360999B2 (en) * | 2002-10-16 | 2008-04-22 | Abbott Laboratories | Means for using single force sensor to supply all necessary information for determination of status of medical pump |
WO2004037335A1 (en) * | 2002-10-22 | 2004-05-06 | Philip Bickford Smith | Medical small-bore tubing system and kit |
AU2003280307A1 (en) | 2002-11-05 | 2004-06-07 | M 2 Medical A/S | A disposable wearable insulin dispensing device, a combination of such a device and a programming controller and a method of controlling the operation of such a device |
US20040133166A1 (en) * | 2002-11-22 | 2004-07-08 | Minimed Inc. | Methods, apparatuses, and uses for infusion pump fluid pressure and force detection |
DK1583573T3 (en) | 2002-12-23 | 2011-05-09 | Asante Solutions Inc | Flexible piston rod |
ATE385814T1 (en) | 2002-12-23 | 2008-03-15 | M2 Medical As | MEDICAL DEVICE FOR DELIVERING INSULIN |
US7294312B2 (en) * | 2003-02-20 | 2007-11-13 | Medtronic, Inc. | Test cartridge holder for blood samples |
US7390314B2 (en) * | 2003-03-05 | 2008-06-24 | Medtronic Minimed, Inc. | Lead screw driven reservoir with integral plunger nut and method of using the same |
US7715896B2 (en) * | 2003-03-21 | 2010-05-11 | Boston Scientific Scimed, Inc. | Systems and methods for internal tissue penetration |
US7198474B2 (en) * | 2003-04-07 | 2007-04-03 | Hewlett-Packard Development Company, L.P. | Pump having shape memory actuator and fuel cell system including the same |
ES2737835T3 (en) | 2003-04-23 | 2020-01-16 | Valeritas Inc | Hydraulically driven pump for long-term medication administration |
US7679407B2 (en) | 2003-04-28 | 2010-03-16 | Abbott Diabetes Care Inc. | Method and apparatus for providing peak detection circuitry for data communication systems |
US20040220551A1 (en) * | 2003-04-30 | 2004-11-04 | Flaherty J. Christopher | Low profile components for patient infusion device |
DE10325106A1 (en) * | 2003-06-03 | 2004-12-30 | Disetronic Licensing Ag | Device and method for recognizing a user of a medical device |
DE10330094B4 (en) * | 2003-07-03 | 2008-04-17 | Disetronic Licensing Ag | Device for administering a liquid product |
WO2005030034A2 (en) * | 2003-09-26 | 2005-04-07 | Depuy Spine, Inc. | Device for delivering viscous material |
US9138537B2 (en) | 2003-10-02 | 2015-09-22 | Medtronic, Inc. | Determining catheter status |
US8323244B2 (en) | 2007-03-30 | 2012-12-04 | Medtronic, Inc. | Catheter malfunction determinations using physiologic pressure |
US7320676B2 (en) | 2003-10-02 | 2008-01-22 | Medtronic, Inc. | Pressure sensing in implantable medical devices |
US9033920B2 (en) | 2003-10-02 | 2015-05-19 | Medtronic, Inc. | Determining catheter status |
EP2368589B1 (en) | 2003-10-28 | 2016-08-03 | Baxter International Inc. | Apparatuses for medical fluid systems |
US8029454B2 (en) | 2003-11-05 | 2011-10-04 | Baxter International Inc. | High convection home hemodialysis/hemofiltration and sorbent system |
WO2005072794A2 (en) | 2004-01-29 | 2005-08-11 | M 2 Medical A/S | Disposable medicine dispensing device |
US7338260B2 (en) * | 2004-03-17 | 2008-03-04 | Baxier International Inc. | System and method for controlling current provided to a stepping motor |
ITMO20040082A1 (en) * | 2004-04-13 | 2004-07-13 | Gambro Lundia Ab | CONNECTOR FOR A FLUID LINE OF AN EXTACORPOREO CIRCUIT |
ITMO20040085A1 (en) * | 2004-04-20 | 2004-07-20 | Gambro Lundia Ab | INFUSION DEVICE FOR MEDICAL FLUIDS. |
WO2006014425A1 (en) | 2004-07-02 | 2006-02-09 | Biovalve Technologies, Inc. | Methods and devices for delivering glp-1 and uses thereof |
US20090216191A1 (en) * | 2004-08-30 | 2009-08-27 | Mario Loeffel | Injection Device With Haptic Feedback |
EP1640029A1 (en) * | 2004-09-24 | 2006-03-29 | Novo Nordisk A/S | Injection device with cap |
ATE444090T1 (en) | 2004-10-21 | 2009-10-15 | Novo Nordisk As | SELECTION MECHANISM FOR A ROTARY PIN |
WO2006083876A2 (en) | 2005-02-01 | 2006-08-10 | Intelliject, Llc | Devices, systems, and methods for medicament delivery |
WO2006061027A2 (en) | 2004-12-10 | 2006-06-15 | Unomedical A/S | Cannula inserter |
US8231573B2 (en) | 2005-02-01 | 2012-07-31 | Intelliject, Inc. | Medicament delivery device having an electronic circuit system |
US8361026B2 (en) * | 2005-02-01 | 2013-01-29 | Intelliject, Inc. | Apparatus and methods for self-administration of vaccines and other medicaments |
US8206360B2 (en) | 2005-02-01 | 2012-06-26 | Intelliject, Inc. | Devices, systems and methods for medicament delivery |
US7731686B2 (en) | 2005-02-01 | 2010-06-08 | Intelliject, Inc. | Devices, systems and methods for medicament delivery |
US9022980B2 (en) | 2005-02-01 | 2015-05-05 | Kaleo, Inc. | Medical injector simulation device |
US7935074B2 (en) | 2005-02-28 | 2011-05-03 | Fresenius Medical Care Holdings, Inc. | Cassette system for peritoneal dialysis machine |
CA2601441A1 (en) | 2005-03-21 | 2006-09-28 | Abbott Diabetes Care Inc. | Method and system for providing integrated medication infusion and analyte monitoring system |
WO2006105793A1 (en) | 2005-04-06 | 2006-10-12 | M 2 Medical A/S | Method and device for dispensing liquid medicine by means of a twistable element |
WO2006114396A1 (en) | 2005-04-24 | 2006-11-02 | Novo Nordisk A/S | Injection device |
US8277415B2 (en) | 2006-08-23 | 2012-10-02 | Medtronic Minimed, Inc. | Infusion medium delivery device and method with drive device for driving plunger in reservoir |
US8512288B2 (en) * | 2006-08-23 | 2013-08-20 | Medtronic Minimed, Inc. | Infusion medium delivery device and method with drive device for driving plunger in reservoir |
US7905868B2 (en) * | 2006-08-23 | 2011-03-15 | Medtronic Minimed, Inc. | Infusion medium delivery device and method with drive device for driving plunger in reservoir |
US7768408B2 (en) | 2005-05-17 | 2010-08-03 | Abbott Diabetes Care Inc. | Method and system for providing data management in data monitoring system |
US7620437B2 (en) | 2005-06-03 | 2009-11-17 | Abbott Diabetes Care Inc. | Method and apparatus for providing rechargeable power in data monitoring and management systems |
WO2006134153A1 (en) * | 2005-06-16 | 2006-12-21 | Novo Nordisk A/S | Method and apparatus for assisting patients in self administration of medication |
US8197231B2 (en) | 2005-07-13 | 2012-06-12 | Purity Solutions Llc | Diaphragm pump and related methods |
US20070048153A1 (en) * | 2005-08-29 | 2007-03-01 | Dr.Showway Yeh | Thin and Foldable Fluid Pump Carried under User's Clothes |
WO2007035567A2 (en) * | 2005-09-19 | 2007-03-29 | Lifescan, Inc. | Infusion pump with closed loop control and algorithm |
US20070093753A1 (en) * | 2005-09-19 | 2007-04-26 | Lifescan, Inc. | Malfunction Detection Via Pressure Pulsation |
US20070066940A1 (en) * | 2005-09-19 | 2007-03-22 | Lifescan, Inc. | Systems and Methods for Detecting a Partition Position in an Infusion Pump |
US7534226B2 (en) | 2005-09-26 | 2009-05-19 | M2 Group Holdings, Inc. | Dispensing fluid from an infusion pump system |
US8057436B2 (en) | 2005-09-26 | 2011-11-15 | Asante Solutions, Inc. | Dispensing fluid from an infusion pump system |
US8551046B2 (en) | 2006-09-18 | 2013-10-08 | Asante Solutions, Inc. | Dispensing fluid from an infusion pump system |
WO2007038060A2 (en) | 2005-09-26 | 2007-04-05 | M2 Medical A/S | Modular infusion pump having two different energy sources |
US8409142B2 (en) | 2005-09-26 | 2013-04-02 | Asante Solutions, Inc. | Operating an infusion pump system |
US8105279B2 (en) | 2005-09-26 | 2012-01-31 | M2 Group Holdings, Inc. | Dispensing fluid from an infusion pump 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 |
US20070129681A1 (en) * | 2005-11-01 | 2007-06-07 | Par Technologies, Llc | Piezoelectric actuation of piston within dispensing chamber |
EP1782852A1 (en) * | 2005-11-04 | 2007-05-09 | F.Hoffmann-La Roche Ag | Device for automatic delivery of a liquid medicament into the body of a patient |
DE602006008494D1 (en) | 2005-11-08 | 2009-09-24 | M2 Medical As | INFUSION PUMP SYSTEM |
WO2007056592A2 (en) | 2005-11-08 | 2007-05-18 | M2 Medical A/S | Method and system for manual and autonomous control of an infusion pump |
US8344966B2 (en) | 2006-01-31 | 2013-01-01 | Abbott Diabetes Care Inc. | Method and system for providing a fault tolerant display unit in an electronic device |
US7931620B2 (en) * | 2006-02-01 | 2011-04-26 | Roche Diagnostics International Ag | Self-sealing connection for housing shells of an administering device |
CN104162200B (en) | 2006-02-09 | 2018-03-27 | 德卡产品有限公司 | peripheral system |
US11478623B2 (en) | 2006-02-09 | 2022-10-25 | Deka Products Limited Partnership | Infusion pump assembly |
US11364335B2 (en) | 2006-02-09 | 2022-06-21 | Deka Products Limited Partnership | Apparatus, system and method for fluid delivery |
US11497846B2 (en) | 2006-02-09 | 2022-11-15 | Deka Products Limited Partnership | Patch-sized fluid delivery systems and methods |
CN101400394B (en) * | 2006-03-10 | 2012-07-04 | 诺沃-诺迪斯克有限公司 | An injection device having a gearing arrangement |
EP1996259B1 (en) * | 2006-03-10 | 2012-08-15 | Novo Nordisk A/S | An injection device and a method of changing a cartridge in the device |
GB2477227B (en) * | 2006-03-29 | 2011-09-14 | Intelliject Inc | Devices, systems and methods for medicament delivery |
AU2007233231B2 (en) * | 2006-03-30 | 2011-02-24 | Mannkind Corporation | Multi-cartridge fluid delivery device |
WO2007123764A2 (en) | 2006-04-06 | 2007-11-01 | Medtronic, Inc. | Systems and methods of identifying catheter malfunctions using pressure sensing |
US20070255126A1 (en) | 2006-04-28 | 2007-11-01 | Moberg Sheldon B | Data communication in networked fluid infusion systems |
US8211054B2 (en) | 2006-05-01 | 2012-07-03 | Carefusion 303, Inc. | System and method for controlling administration of medical fluid |
WO2007132019A1 (en) | 2006-05-16 | 2007-11-22 | Novo Nordisk A/S | A gearing mechanism for an injection device |
JP5253387B2 (en) * | 2006-05-18 | 2013-07-31 | ノボ・ノルデイスク・エー/エス | Injection device with mode locking means |
US7920907B2 (en) | 2006-06-07 | 2011-04-05 | Abbott Diabetes Care Inc. | Analyte monitoring system and method |
US7931447B2 (en) | 2006-06-29 | 2011-04-26 | Hayward Industries, Inc. | Drain safety and pump control device |
US8025634B1 (en) | 2006-09-18 | 2011-09-27 | Baxter International Inc. | Method and system for controlled infusion of therapeutic substances |
CN102895718B (en) | 2006-09-29 | 2015-01-14 | 诺沃—诺迪斯克有限公司 | An injection device with electronic detecting means |
US8579853B2 (en) | 2006-10-31 | 2013-11-12 | Abbott Diabetes Care Inc. | Infusion devices and methods |
NZ577169A (en) | 2006-11-21 | 2011-12-22 | Baxter Healthcare Sa | System and method for remote monitoring and/or management of infusion therapies |
US20080125700A1 (en) * | 2006-11-29 | 2008-05-29 | Moberg Sheldon B | Methods and apparatuses for detecting medical device acceleration, temperature, and humidity conditions |
US7704227B2 (en) * | 2006-11-29 | 2010-04-27 | Medtronic Minimed, Inc. | Methods and apparatuses for detecting medical device acceleration, temperature, and humidity conditions |
CA2668672C (en) * | 2006-11-29 | 2011-10-25 | Medtronic Minimed, Inc. | Methods and apparatuses for detecting medical device acceleration, temperature, and humidity conditions |
US20080132843A1 (en) * | 2006-12-04 | 2008-06-05 | Animas Corporation | Syringe assembly and an infusion pump assembly incorporating such |
US7654127B2 (en) * | 2006-12-21 | 2010-02-02 | Lifescan, Inc. | Malfunction detection in infusion pumps |
US7803134B2 (en) * | 2007-01-10 | 2010-09-28 | Animas Corporation | Syringe assembly and infusion pump assembly incorporating such |
WO2008091838A2 (en) | 2007-01-22 | 2008-07-31 | Intelliject, Inc. | Medical injector with compliance tracking and monitoring |
US7644299B2 (en) * | 2007-03-02 | 2010-01-05 | Proprietary Controls Systems Corporation | Fault tolerant security system, method and apparatus |
WO2008116766A1 (en) | 2007-03-23 | 2008-10-02 | Novo Nordisk A/S | An injection device comprising a locking nut |
US9044537B2 (en) | 2007-03-30 | 2015-06-02 | Medtronic, Inc. | Devices and methods for detecting catheter complications |
US8034019B2 (en) * | 2007-04-10 | 2011-10-11 | Amrita Vishwa Vidyapeetham | Dual microcontroller-based liquid infusion system |
EP2144647B1 (en) * | 2007-04-23 | 2012-10-17 | Steadymed. Ltd. | Controllable drug delivery device driven by expandable battery |
US7963954B2 (en) | 2007-04-30 | 2011-06-21 | Medtronic Minimed, Inc. | Automated filling systems and methods |
US8613725B2 (en) | 2007-04-30 | 2013-12-24 | Medtronic Minimed, Inc. | Reservoir systems and methods |
US7959715B2 (en) * | 2007-04-30 | 2011-06-14 | Medtronic Minimed, Inc. | Systems and methods allowing for reservoir air bubble management |
JP5102350B2 (en) | 2007-04-30 | 2012-12-19 | メドトロニック ミニメド インコーポレイテッド | Reservoir filling / bubble management / infusion medium delivery system and method using the system |
US8597243B2 (en) | 2007-04-30 | 2013-12-03 | Medtronic Minimed, Inc. | Systems and methods allowing for reservoir air bubble management |
US8323250B2 (en) | 2007-04-30 | 2012-12-04 | Medtronic Minimed, Inc. | Adhesive patch systems and methods |
US8434528B2 (en) | 2007-04-30 | 2013-05-07 | Medtronic Minimed, Inc. | Systems and methods for reservoir filling |
US7833196B2 (en) | 2007-05-21 | 2010-11-16 | Asante Solutions, Inc. | Illumination instrument for an infusion pump |
US7981102B2 (en) | 2007-05-21 | 2011-07-19 | Asante Solutions, Inc. | Removable controller for an infusion pump |
US7794426B2 (en) | 2007-05-21 | 2010-09-14 | Asante Solutions, Inc. | Infusion pump system with contamination-resistant features |
US7892199B2 (en) | 2007-05-21 | 2011-02-22 | Asante Solutions, Inc. | Occlusion sensing for an infusion pump |
US20080300572A1 (en) | 2007-06-01 | 2008-12-04 | Medtronic Minimed, Inc. | Wireless monitor for a personal medical device system |
US8992516B2 (en) | 2007-07-19 | 2015-03-31 | Avedro, Inc. | Eye therapy system |
US8202272B2 (en) | 2007-07-19 | 2012-06-19 | Avedro, Inc. | Eye therapy system |
US9108006B2 (en) | 2007-08-17 | 2015-08-18 | Novo Nordisk A/S | Medical device with value sensor |
US7717903B2 (en) | 2007-09-06 | 2010-05-18 | M2 Group Holdings, Inc. | Operating an infusion pump system |
US7828528B2 (en) | 2007-09-06 | 2010-11-09 | Asante Solutions, Inc. | Occlusion sensing system for infusion pumps |
US8287514B2 (en) | 2007-09-07 | 2012-10-16 | Asante Solutions, Inc. | Power management techniques for an infusion pump system |
US7935076B2 (en) | 2007-09-07 | 2011-05-03 | Asante Solutions, Inc. | Activity sensing techniques for an infusion pump system |
US8032226B2 (en) | 2007-09-07 | 2011-10-04 | Asante Solutions, Inc. | User profile backup system for an infusion pump device |
US7879026B2 (en) | 2007-09-07 | 2011-02-01 | Asante Solutions, Inc. | Controlled adjustment of medicine dispensation from an infusion pump device |
US8012120B2 (en) * | 2007-09-13 | 2011-09-06 | Avant Medical Corp. | Device and method for the automatic initiation of an injection |
US9345836B2 (en) | 2007-10-02 | 2016-05-24 | Medimop Medical Projects Ltd. | Disengagement resistant telescoping assembly and unidirectional method of assembly for such |
US7967795B1 (en) | 2010-01-19 | 2011-06-28 | Lamodel Ltd. | Cartridge interface assembly with driving plunger |
DE102007049446A1 (en) | 2007-10-16 | 2009-04-23 | Cequr Aps | Catheter introducer |
US20090113295A1 (en) * | 2007-10-30 | 2009-04-30 | Halpern Arieh S | Graphical display for physiological patient data |
US20090157003A1 (en) * | 2007-12-14 | 2009-06-18 | Jones Daniel W | Method And Apparatus For Occlusion Prevention And Remediation |
US9026370B2 (en) | 2007-12-18 | 2015-05-05 | Hospira, Inc. | User interface improvements for medical devices |
US8313467B2 (en) | 2007-12-27 | 2012-11-20 | Medtronic Minimed, Inc. | Reservoir pressure equalization systems and methods |
CN101909673B (en) * | 2007-12-31 | 2012-12-26 | 诺沃-诺迪斯克有限公司 | Electronically monitored injection device |
US8900188B2 (en) | 2007-12-31 | 2014-12-02 | Deka Products Limited Partnership | Split ring resonator antenna adapted for use in wirelessly controlled medical device |
US9456955B2 (en) | 2007-12-31 | 2016-10-04 | Deka Products Limited Partnership | Apparatus, system and method for fluid delivery |
US10188787B2 (en) | 2007-12-31 | 2019-01-29 | Deka Products Limited Partnership | Apparatus, system and method for fluid delivery |
US8491570B2 (en) | 2007-12-31 | 2013-07-23 | Deka Products Limited Partnership | Infusion pump assembly |
MX361885B (en) | 2007-12-31 | 2018-12-18 | Deka Products Lp | Infusion pump assembly. |
US10080704B2 (en) | 2007-12-31 | 2018-09-25 | Deka Products Limited Partnership | Apparatus, system and method for fluid delivery |
US8881774B2 (en) | 2007-12-31 | 2014-11-11 | Deka Research & Development Corp. | Apparatus, system and method for fluid delivery |
US8409189B2 (en) * | 2008-01-23 | 2013-04-02 | Avedro, Inc. | System and method for reshaping an eye feature |
US8348935B2 (en) * | 2008-01-23 | 2013-01-08 | Avedro, Inc. | System and method for reshaping an eye feature |
KR20090099687A (en) * | 2008-03-18 | 2009-09-23 | 한국전자통신연구원 | Breast cancer diagnosis apparatus |
USD994111S1 (en) | 2008-05-12 | 2023-08-01 | Kaleo, Inc. | Medicament delivery device cover |
US8021344B2 (en) * | 2008-07-28 | 2011-09-20 | Intelliject, Inc. | Medicament delivery device configured to produce an audible output |
US8172811B2 (en) | 2008-05-15 | 2012-05-08 | Roche Diagnostics Operations, Inc. | Drug delivery pump drive using a shaped memory alloy wire |
US8052645B2 (en) | 2008-07-23 | 2011-11-08 | Avant Medical Corp. | System and method for an injection using a syringe needle |
US9974904B2 (en) | 2008-05-20 | 2018-05-22 | Avant Medical Corp. | Autoinjector system |
US8062513B2 (en) | 2008-07-09 | 2011-11-22 | Baxter International Inc. | Dialysis system and machine having therapy prescription recall |
US8057679B2 (en) | 2008-07-09 | 2011-11-15 | Baxter International Inc. | Dialysis system having trending and alert generation |
US9514283B2 (en) | 2008-07-09 | 2016-12-06 | Baxter International Inc. | Dialysis system having inventory management including online dextrose mixing |
US10089443B2 (en) | 2012-05-15 | 2018-10-02 | Baxter International Inc. | Home medical device systems and methods for therapy prescription and tracking, servicing and inventory |
US7959598B2 (en) | 2008-08-20 | 2011-06-14 | Asante Solutions, Inc. | Infusion pump systems and methods |
CA3132517A1 (en) | 2008-09-15 | 2010-03-18 | Deka Products Limited Partnership | Systems and methods for fluid delivery |
US9393369B2 (en) | 2008-09-15 | 2016-07-19 | Medimop Medical Projects Ltd. | Stabilized pen injector |
DK2370125T3 (en) * | 2008-10-07 | 2019-06-17 | Hoffmann La Roche | Skin-mountable drug delivery device with shock absorbing protective shield |
US9180245B2 (en) | 2008-10-10 | 2015-11-10 | Deka Products Limited Partnership | System and method for administering an infusible fluid |
US8066672B2 (en) | 2008-10-10 | 2011-11-29 | Deka Products Limited Partnership | Infusion pump assembly with a backup power supply |
US8223028B2 (en) | 2008-10-10 | 2012-07-17 | Deka Products Limited Partnership | Occlusion detection system and method |
US8262616B2 (en) | 2008-10-10 | 2012-09-11 | Deka Products Limited Partnership | Infusion pump assembly |
US8708376B2 (en) | 2008-10-10 | 2014-04-29 | Deka Products Limited Partnership | Medium connector |
US8016789B2 (en) | 2008-10-10 | 2011-09-13 | Deka Products Limited Partnership | Pump assembly with a removable cover assembly |
US8267892B2 (en) | 2008-10-10 | 2012-09-18 | Deka Products Limited Partnership | Multi-language / multi-processor infusion pump assembly |
US8554579B2 (en) | 2008-10-13 | 2013-10-08 | Fht, Inc. | Management, reporting and benchmarking of medication preparation |
US8105269B2 (en) | 2008-10-24 | 2012-01-31 | Baxter International Inc. | In situ tubing measurements for infusion pumps |
US8208973B2 (en) | 2008-11-05 | 2012-06-26 | Medtronic Minimed, Inc. | System and method for variable beacon timing with wireless devices |
JP2012508087A (en) * | 2008-11-11 | 2012-04-05 | アヴェドロ・インコーポレーテッド | Eye treatment system |
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 |
US8603051B2 (en) * | 2009-02-17 | 2013-12-10 | Kuvio, Inc. | Implantable drug delivery devices |
US8378837B2 (en) * | 2009-02-20 | 2013-02-19 | Hospira, Inc. | Occlusion detection system |
US8137083B2 (en) | 2009-03-11 | 2012-03-20 | Baxter International Inc. | Infusion pump actuators, system and method for controlling medical fluid flowrate |
US8192401B2 (en) | 2009-03-20 | 2012-06-05 | Fresenius Medical Care Holdings, Inc. | Medical fluid pump systems and related components and methods |
JP2012522602A (en) * | 2009-04-02 | 2012-09-27 | アヴェドロ・インコーポレーテッド | Eye treatment system |
WO2010115121A1 (en) | 2009-04-02 | 2010-10-07 | Avedro, Inc. | Eye therapy system |
DK2241344T3 (en) | 2009-04-16 | 2014-03-03 | Hoffmann La Roche | Portable infusion with feel-testing device |
WO2010129375A1 (en) | 2009-04-28 | 2010-11-11 | Abbott Diabetes Care Inc. | Closed loop blood glucose control algorithm analysis |
ES2606550T3 (en) | 2009-06-19 | 2017-03-24 | Alk-Abelló S.A. | New way of administering allergen in specific immunotherapy with allergens |
GR20090100384A (en) * | 2009-07-08 | 2011-02-18 | Αχιλλεας Τσουκαλης | Insulin pump |
US8344847B2 (en) | 2009-07-09 | 2013-01-01 | Medtronic Minimed, Inc. | Coordination of control commands in a medical device system having at least one therapy delivery device and at least one wireless controller device |
US20110009813A1 (en) | 2009-07-09 | 2011-01-13 | Medtronic Minimed, Inc. | Panning a display of a portable medical device |
EP2453948B1 (en) | 2009-07-15 | 2015-02-18 | DEKA Products Limited Partnership | Apparatus, systems and methods for an infusion pump assembly |
CA2767668C (en) | 2009-07-15 | 2017-03-07 | Fresenius Medical Care Holdings, Inc. | Medical fluid cassettes and related systems and methods |
EP2456351B1 (en) | 2009-07-23 | 2016-10-12 | Abbott Diabetes Care, Inc. | Real time management of data relating to physiological control of glucose levels |
AU2010278894B2 (en) | 2009-07-30 | 2014-01-30 | Tandem Diabetes Care, Inc. | Infusion pump system with disposable cartridge having pressure venting and pressure feedback |
US8720913B2 (en) | 2009-08-11 | 2014-05-13 | Fresenius Medical Care Holdings, Inc. | Portable peritoneal dialysis carts and related systems |
US8547239B2 (en) | 2009-08-18 | 2013-10-01 | Cequr Sa | Methods for detecting failure states in a medicine delivery device |
US8672873B2 (en) | 2009-08-18 | 2014-03-18 | Cequr Sa | Medicine delivery device having detachable pressure sensing unit |
US8308679B2 (en) | 2009-12-30 | 2012-11-13 | Medtronic Minimed, Inc. | Alignment systems and methods |
US8487758B2 (en) | 2009-09-02 | 2013-07-16 | Medtronic Minimed, Inc. | Medical device having an intelligent alerting scheme, and related operating methods |
US8241018B2 (en) * | 2009-09-10 | 2012-08-14 | Tyco Healthcare Group Lp | Compact peristaltic medical pump |
US10071196B2 (en) | 2012-05-15 | 2018-09-11 | West Pharma. Services IL, Ltd. | Method for selectively powering a battery-operated drug-delivery device and device therefor |
US10071198B2 (en) | 2012-11-02 | 2018-09-11 | West Pharma. Servicees IL, Ltd. | Adhesive structure for medical device |
US8157769B2 (en) | 2009-09-15 | 2012-04-17 | Medimop Medical Projects Ltd. | Cartridge insertion assembly for drug delivery system |
US8386042B2 (en) | 2009-11-03 | 2013-02-26 | Medtronic Minimed, Inc. | Omnidirectional accelerometer device and medical device incorporating same |
US8574201B2 (en) | 2009-12-22 | 2013-11-05 | Medtronic Minimed, Inc. | Syringe piston with check valve seal |
US8755269B2 (en) | 2009-12-23 | 2014-06-17 | Medtronic Minimed, Inc. | Ranking and switching of wireless channels in a body area network of medical devices |
US8858500B2 (en) | 2009-12-30 | 2014-10-14 | Medtronic Minimed, Inc. | Engagement and sensing systems and methods |
US8998840B2 (en) | 2009-12-30 | 2015-04-07 | Medtronic Minimed, Inc. | Connection and alignment systems and methods |
US8998858B2 (en) | 2009-12-29 | 2015-04-07 | Medtronic Minimed, Inc. | Alignment and connection systems and methods |
US9039653B2 (en) | 2009-12-29 | 2015-05-26 | Medtronic Minimed, Inc. | Retention systems and methods |
US8382447B2 (en) | 2009-12-31 | 2013-02-26 | Baxter International, Inc. | Shuttle pump with controlled geometry |
US8348898B2 (en) | 2010-01-19 | 2013-01-08 | Medimop Medical Projects Ltd. | Automatic needle for drug pump |
US9295778B2 (en) | 2011-12-21 | 2016-03-29 | Deka Products Limited Partnership | Syringe pump |
CA3033439C (en) | 2010-01-22 | 2021-04-06 | Deka Products Limited Partnership | Method and system for shape-memory alloy wire control |
US9744300B2 (en) | 2011-12-21 | 2017-08-29 | Deka Products Limited Partnership | Syringe pump and related method |
US9789247B2 (en) | 2011-12-21 | 2017-10-17 | Deka Products Limited Partnership | Syringe pump, and related method and system |
WO2011106530A1 (en) | 2010-02-25 | 2011-09-01 | Hayward Industries, Inc. | Universal mount for a variable speed pump drive user interface |
WO2011113806A1 (en) * | 2010-03-16 | 2011-09-22 | Sanofi-Aventis Deutschland Gmbh | Controlling a motor of an injection device |
WO2011141907A1 (en) | 2010-05-10 | 2011-11-17 | Medimop Medical Projects Ltd. | Low volume accurate injector |
USD669165S1 (en) | 2010-05-27 | 2012-10-16 | Asante Solutions, Inc. | Infusion pump |
US9737657B2 (en) | 2010-06-03 | 2017-08-22 | Medtronic, Inc. | Implantable medical pump with pressure sensor |
US8397578B2 (en) | 2010-06-03 | 2013-03-19 | Medtronic, Inc. | Capacitive pressure sensor assembly |
US8784378B2 (en) * | 2010-06-07 | 2014-07-22 | Sanofi-Aventis Deutschland Gmbh | Drug delivery device with light source |
DE202010007860U1 (en) * | 2010-06-11 | 2011-09-27 | Storz Medical Ag | Pressure wave device with pneumatic drive |
US8567235B2 (en) | 2010-06-29 | 2013-10-29 | Baxter International Inc. | Tube measurement technique using linear actuator and pressure sensor |
US9433562B2 (en) * | 2010-07-27 | 2016-09-06 | Neomed, Inc. | System for aseptic collection and enteral delivery |
US9308320B2 (en) | 2010-09-24 | 2016-04-12 | Perqflo, Llc | Infusion pumps |
US8915879B2 (en) | 2010-09-24 | 2014-12-23 | Perqflo, Llc | Infusion pumps |
US9498573B2 (en) | 2010-09-24 | 2016-11-22 | Perqflo, Llc | Infusion pumps |
US9216249B2 (en) | 2010-09-24 | 2015-12-22 | Perqflo, Llc | Infusion pumps |
US8603033B2 (en) | 2010-10-15 | 2013-12-10 | Medtronic Minimed, Inc. | Medical device and related assembly having an offset element for a piezoelectric speaker |
US8562565B2 (en) | 2010-10-15 | 2013-10-22 | Medtronic Minimed, Inc. | Battery shock absorber for a portable medical device |
US8603032B2 (en) | 2010-10-15 | 2013-12-10 | Medtronic Minimed, Inc. | Medical device with membrane keypad sealing element, and related manufacturing method |
US8495918B2 (en) | 2010-10-20 | 2013-07-30 | Medtronic Minimed, Inc. | Sensor assembly and medical device incorporating same |
US8474332B2 (en) | 2010-10-20 | 2013-07-02 | Medtronic Minimed, Inc. | Sensor assembly and medical device incorporating same |
US8479595B2 (en) | 2010-10-20 | 2013-07-09 | Medtronic Minimed, Inc. | Sensor assembly and medical device incorporating same |
US9211378B2 (en) | 2010-10-22 | 2015-12-15 | Cequr Sa | Methods and systems for dosing a medicament |
WO2012059209A1 (en) | 2010-11-01 | 2012-05-10 | Roche Diagnostics Gmbh | Fluid dispensing device with a flow detector |
US8905972B2 (en) | 2010-11-20 | 2014-12-09 | Perqflo, Llc | Infusion pumps |
DE102010053973A1 (en) | 2010-12-09 | 2012-06-14 | Fresenius Medical Care Deutschland Gmbh | Medical device with a heater |
EP2654825B1 (en) | 2010-12-20 | 2017-08-02 | Fresenius Medical Care Holdings, Inc. | Medical fluid cassettes and related systems and methods |
US8197444B1 (en) | 2010-12-22 | 2012-06-12 | Medtronic Minimed, Inc. | Monitoring the seating status of a fluid reservoir in a fluid infusion device |
US8628510B2 (en) | 2010-12-22 | 2014-01-14 | Medtronic Minimed, Inc. | Monitoring the operating health of a force sensor in a fluid infusion device |
US8690855B2 (en) | 2010-12-22 | 2014-04-08 | Medtronic Minimed, Inc. | Fluid reservoir seating procedure for a fluid infusion device |
US8469942B2 (en) * | 2010-12-22 | 2013-06-25 | Medtronic Minimed, Inc. | Occlusion detection for a fluid infusion device |
US8627816B2 (en) | 2011-02-28 | 2014-01-14 | Intelliject, Inc. | Medicament delivery device for administration of opioid antagonists including formulations for naloxone |
US8939943B2 (en) | 2011-01-26 | 2015-01-27 | Kaleo, Inc. | Medicament delivery device for administration of opioid antagonists including formulations for naloxone |
US9084849B2 (en) | 2011-01-26 | 2015-07-21 | Kaleo, Inc. | Medicament delivery devices for administration of a medicament within a prefilled syringe |
US8852152B2 (en) | 2011-02-09 | 2014-10-07 | Asante Solutions, Inc. | Infusion pump systems and methods |
US8945068B2 (en) | 2011-02-22 | 2015-02-03 | Medtronic Minimed, Inc. | Fluid reservoir having a fluid delivery needle for a fluid infusion device |
US9283318B2 (en) | 2011-02-22 | 2016-03-15 | Medtronic Minimed, Inc. | Flanged sealing element and needle guide pin assembly for a fluid infusion device having a needled fluid reservoir |
US9463309B2 (en) | 2011-02-22 | 2016-10-11 | Medtronic Minimed, Inc. | Sealing assembly and structure for a fluid infusion device having a needled fluid reservoir |
US9393399B2 (en) | 2011-02-22 | 2016-07-19 | Medtronic Minimed, Inc. | Sealing assembly for a fluid reservoir of a fluid infusion device |
US20120277155A1 (en) | 2011-02-25 | 2012-11-01 | Medtronic, Inc. | Therapy for kidney disease and/or heart failure |
EP2678028A2 (en) | 2011-02-25 | 2014-01-01 | Medtronic, Inc. | Systems and methods for therapy of kidney disease and/or heart failure using chimeric natriuretic peptides |
US8614596B2 (en) | 2011-02-28 | 2013-12-24 | Medtronic Minimed, Inc. | Systems and methods for initializing a voltage bus and medical devices incorporating same |
US9101305B2 (en) | 2011-03-09 | 2015-08-11 | Medtronic Minimed, Inc. | Glucose sensor product and related manufacturing and packaging methods |
US9624915B2 (en) | 2011-03-09 | 2017-04-18 | Fresenius Medical Care Holdings, Inc. | Medical fluid delivery sets and related systems and methods |
US8454581B2 (en) | 2011-03-16 | 2013-06-04 | Asante Solutions, Inc. | Infusion pump systems and methods |
US9018893B2 (en) | 2011-03-18 | 2015-04-28 | Medtronic Minimed, Inc. | Power control techniques for an electronic device |
US8564447B2 (en) | 2011-03-18 | 2013-10-22 | Medtronic Minimed, Inc. | Battery life indication techniques for an electronic device |
USD702834S1 (en) | 2011-03-22 | 2014-04-15 | Medimop Medical Projects Ltd. | Cartridge for use in injection device |
US8708959B2 (en) * | 2011-04-07 | 2014-04-29 | Medtronic, Inc. | Detecting fill status for medical pump reservoir |
ES2725785T3 (en) | 2011-04-20 | 2019-09-27 | Amgen Inc | Self-injector device |
EP3006059B1 (en) | 2011-04-21 | 2017-09-27 | Fresenius Medical Care Holdings, Inc. | Medical fluid pumping systems and related devices and methods |
GB201110021D0 (en) * | 2011-06-15 | 2011-07-27 | Newcastle Upon Tyne Hospitals Nhs Trust The | Apparatus for performing haemodialysis |
US8585657B2 (en) | 2011-06-21 | 2013-11-19 | Asante Solutions, Inc. | Dispensing fluid from an infusion pump system |
WO2013004308A1 (en) | 2011-07-06 | 2013-01-10 | F. Hoffmann-La Roche Ag | Device for automatic injection and occlusion detection |
EP2729200B1 (en) | 2011-07-06 | 2016-10-19 | F.Hoffmann-La Roche Ag | Automatic injection device comprising two occlusion sensors |
EP2745204A4 (en) | 2011-08-19 | 2015-01-07 | Hospira Inc | Systems and methods for a graphical interface including a graphical representation of medical data |
EP2750697A4 (en) | 2011-09-02 | 2015-03-25 | Medtronic Inc | Chimeric natriuretic peptide compositions and methods of preparation |
US8808230B2 (en) | 2011-09-07 | 2014-08-19 | Asante Solutions, Inc. | Occlusion detection for an infusion pump system |
US9186449B2 (en) | 2011-11-01 | 2015-11-17 | Fresenius Medical Care Holdings, Inc. | Dialysis machine support assemblies and related systems and methods |
US8668345B2 (en) | 2011-11-30 | 2014-03-11 | Izi Medical Products | Retro-reflective marker with snap on threaded post |
WO2013090709A1 (en) | 2011-12-16 | 2013-06-20 | Hospira, Inc. | System for monitoring and delivering medication to a patient and method of using the same to minimize the risks associated with automated therapy |
US10722645B2 (en) | 2011-12-21 | 2020-07-28 | Deka Products Limited Partnership | Syringe pump, and related method and system |
US11217340B2 (en) | 2011-12-21 | 2022-01-04 | Deka Products Limited Partnership | Syringe pump having a pressure sensor assembly |
US9533106B2 (en) | 2011-12-29 | 2017-01-03 | Novo Nordisk A/S | Torsion-spring based wind-up auto injector pen with dial-up/dial-down mechanism |
US9610401B2 (en) | 2012-01-13 | 2017-04-04 | Medtronic Minimed, Inc. | Infusion set component with modular fluid channel element |
WO2013115843A1 (en) | 2012-01-31 | 2013-08-08 | Medimop Medical Projects Ltd. | Time dependent drug delivery apparatus |
US8661573B2 (en) | 2012-02-29 | 2014-03-04 | Izi Medical Products | Protective cover for medical device having adhesive mechanism |
US11524151B2 (en) | 2012-03-07 | 2022-12-13 | Deka Products Limited Partnership | Apparatus, system and method for fluid delivery |
US8523803B1 (en) | 2012-03-20 | 2013-09-03 | Medtronic Minimed, Inc. | Motor health monitoring and medical device incorporating same |
US8603026B2 (en) | 2012-03-20 | 2013-12-10 | Medtronic Minimed, Inc. | Dynamic pulse-width modulation motor control and medical device incorporating same |
US8603027B2 (en) | 2012-03-20 | 2013-12-10 | Medtronic Minimed, Inc. | Occlusion detection using pulse-width modulation and medical device incorporating same |
US9463280B2 (en) | 2012-03-26 | 2016-10-11 | Medimop Medical Projects Ltd. | Motion activated septum puncturing drug delivery device |
US9072827B2 (en) | 2012-03-26 | 2015-07-07 | Medimop Medical Projects Ltd. | Fail safe point protector for needle safety flap |
US10668213B2 (en) | 2012-03-26 | 2020-06-02 | West Pharma. Services IL, Ltd. | Motion activated mechanisms for a drug delivery device |
EP2830687B1 (en) | 2012-03-30 | 2019-07-24 | ICU Medical, Inc. | Air detection system and method for detecting air in a pump of an infusion system |
US9180242B2 (en) | 2012-05-17 | 2015-11-10 | Tandem Diabetes Care, Inc. | Methods and devices for multiple fluid transfer |
US9522235B2 (en) | 2012-05-22 | 2016-12-20 | Kaleo, Inc. | Devices and methods for delivering medicaments from a multi-chamber container |
US10391242B2 (en) | 2012-06-07 | 2019-08-27 | Medtronic Minimed, Inc. | Diabetes therapy management system for recommending bolus calculator adjustments |
US9610392B2 (en) | 2012-06-08 | 2017-04-04 | Fresenius Medical Care Holdings, Inc. | Medical fluid cassettes and related systems and methods |
US9500188B2 (en) | 2012-06-11 | 2016-11-22 | Fresenius Medical Care Holdings, Inc. | Medical fluid cassettes and related systems and methods |
US20130338576A1 (en) * | 2012-06-15 | 2013-12-19 | Wayne C. Jaeschke, Jr. | Portable infusion pump with pressure and temperature compensation |
US9333292B2 (en) | 2012-06-26 | 2016-05-10 | Medtronic Minimed, Inc. | Mechanically actuated fluid infusion device |
US8454557B1 (en) | 2012-07-19 | 2013-06-04 | Asante Solutions, Inc. | Infusion pump system and method |
US8454562B1 (en) | 2012-07-20 | 2013-06-04 | Asante Solutions, Inc. | Infusion pump system and method |
EP3586891A1 (en) | 2012-07-31 | 2020-01-01 | ICU Medical, Inc. | Patient care system for critical medications |
EP2882476A1 (en) * | 2012-08-10 | 2015-06-17 | Sanofi-Aventis Deutschland GmbH | Pen-type drug injection device and electronic add-on monitoring module for!monitoring and logging dose setting and administration |
EP2885022A1 (en) * | 2012-08-20 | 2015-06-24 | Roche Diagnostics GmbH | Therapeutic system with an adaptor for an infusion set |
US8808269B2 (en) | 2012-08-21 | 2014-08-19 | Medtronic Minimed, Inc. | Reservoir plunger position monitoring and medical device incorporating same |
US9662445B2 (en) | 2012-08-30 | 2017-05-30 | Medtronic Minimed, Inc. | Regulating entry into a closed-loop operating mode of an insulin infusion system |
US10130767B2 (en) | 2012-08-30 | 2018-11-20 | Medtronic Minimed, Inc. | Sensor model supervisor for a closed-loop insulin infusion system |
US9878096B2 (en) | 2012-08-30 | 2018-01-30 | Medtronic Minimed, Inc. | Generation of target glucose values for a closed-loop operating mode of an insulin infusion system |
US20140066884A1 (en) | 2012-08-30 | 2014-03-06 | Medtronic Minimed, Inc. | Sensor model supervisor for a closed-loop insulin infusion system |
US9623179B2 (en) | 2012-08-30 | 2017-04-18 | Medtronic Minimed, Inc. | Safeguarding techniques for a closed-loop insulin infusion system |
US9849239B2 (en) | 2012-08-30 | 2017-12-26 | Medtronic Minimed, Inc. | Generation and application of an insulin limit for a closed-loop operating mode of an insulin infusion system |
US10496797B2 (en) | 2012-08-30 | 2019-12-03 | Medtronic Minimed, Inc. | Blood glucose validation for a closed-loop operating mode of an insulin infusion system |
KR101695119B1 (en) | 2012-10-26 | 2017-01-23 | 백스터 코포레이션 잉글우드 | Improved image acquisition for medical dose preparation system |
NZ716476A (en) | 2012-10-26 | 2018-10-26 | Baxter Corp Englewood | Improved work station for medical dose preparation system |
US8870818B2 (en) | 2012-11-15 | 2014-10-28 | Medtronic Minimed, Inc. | Systems and methods for alignment and detection of a consumable component |
US9427523B2 (en) | 2012-12-10 | 2016-08-30 | Bigfoot Biomedical, Inc. | Infusion pump system and method |
US20140276536A1 (en) | 2013-03-14 | 2014-09-18 | Asante Solutions, Inc. | Infusion Pump System and Methods |
EP2934299A1 (en) * | 2012-12-21 | 2015-10-28 | Koninklijke Philips N.V. | Plaque detection using a stream probe |
US9918814B2 (en) * | 2012-12-21 | 2018-03-20 | Koninklijke Philips N.V | Plaque detection using a stream probe |
BR112015014464A2 (en) * | 2012-12-21 | 2017-07-11 | Koninklijke Philips Nv | flow probe to detect the presence of a substance on a dental surface |
EP2938376A4 (en) | 2012-12-27 | 2017-01-25 | Kaleo, Inc. | Devices, systems and methods for locating and interacting with medicament delivery systems |
WO2014105606A1 (en) | 2012-12-31 | 2014-07-03 | Gambro Renal Products, Inc. | Occlusion detection in delivery of fluids |
US9421323B2 (en) | 2013-01-03 | 2016-08-23 | Medimop Medical Projects Ltd. | Door and doorstop for portable one use drug delivery apparatus |
US9068900B2 (en) | 2013-01-08 | 2015-06-30 | GM Global Technology Operations LLC | Deflection sensitive coolant activated drain plug detection system for high voltage battery packs |
US9522223B2 (en) | 2013-01-18 | 2016-12-20 | Medtronic Minimed, Inc. | Systems for fluid reservoir retention |
US9107994B2 (en) | 2013-01-18 | 2015-08-18 | Medtronic Minimed, Inc. | Systems for fluid reservoir retention |
US9033924B2 (en) | 2013-01-18 | 2015-05-19 | Medtronic Minimed, Inc. | Systems for fluid reservoir retention |
US9308321B2 (en) | 2013-02-18 | 2016-04-12 | Medtronic Minimed, Inc. | Infusion device having gear assembly initialization |
US9446186B2 (en) | 2013-03-01 | 2016-09-20 | Bigfoot Biomedical, Inc. | Operating an infusion pump system |
US9561323B2 (en) | 2013-03-14 | 2017-02-07 | Fresenius Medical Care Holdings, Inc. | Medical fluid cassette leak detection methods and devices |
US9173998B2 (en) | 2013-03-14 | 2015-11-03 | Tandem Diabetes Care, Inc. | System and method for detecting occlusions in an infusion pump |
AU2014228186B2 (en) | 2013-03-15 | 2019-11-07 | Hayward Industries, Inc. | Modular pool/spa control system |
TWI614041B (en) | 2013-03-15 | 2018-02-11 | 安美基公司 | Cassette for an injector |
US8920381B2 (en) | 2013-04-12 | 2014-12-30 | Medtronic Minimed, Inc. | Infusion set with improved bore configuration |
US9011164B2 (en) | 2013-04-30 | 2015-04-21 | Medimop Medical Projects Ltd. | Clip contact for easy installation of printed circuit board PCB |
US9889256B2 (en) | 2013-05-03 | 2018-02-13 | Medimop Medical Projects Ltd. | Sensing a status of an infuser based on sensing motor control and power input |
CA2913421C (en) | 2013-05-24 | 2022-02-15 | Hospira, Inc. | Multi-sensor infusion system for detecting air or an occlusion in the infusion system |
CA2913915C (en) | 2013-05-29 | 2022-03-29 | Hospira, Inc. | Infusion system which utilizes one or more sensors and additional information to make an air determination regarding the infusion system |
EP3003442B1 (en) | 2013-05-29 | 2020-12-30 | ICU Medical, Inc. | Infusion system and method of use which prevents over-saturation of an analog-to-digital converter |
US9446187B2 (en) | 2013-06-03 | 2016-09-20 | Bigfoot Biomedical, Inc. | Infusion pump system and method |
US9457141B2 (en) | 2013-06-03 | 2016-10-04 | Bigfoot Biomedical, Inc. | Infusion pump system and method |
EP3016629B1 (en) | 2013-07-03 | 2023-12-20 | DEKA Products Limited Partnership | Apparatus and system for fluid delivery |
US9561324B2 (en) | 2013-07-19 | 2017-02-07 | Bigfoot Biomedical, Inc. | Infusion pump system and method |
US9433731B2 (en) | 2013-07-19 | 2016-09-06 | Medtronic Minimed, Inc. | Detecting unintentional motor motion and infusion device incorporating same |
US9402949B2 (en) | 2013-08-13 | 2016-08-02 | Medtronic Minimed, Inc. | Detecting conditions associated with medical device operations using matched filters |
CN110047571B (en) | 2013-08-21 | 2023-10-27 | 美敦力迷你迈德公司 | Medical device and related updating method and system |
US9880528B2 (en) | 2013-08-21 | 2018-01-30 | Medtronic Minimed, Inc. | Medical devices and related updating methods and systems |
US9889257B2 (en) | 2013-08-21 | 2018-02-13 | Medtronic Minimed, Inc. | Systems and methods for updating medical devices |
US10117985B2 (en) | 2013-08-21 | 2018-11-06 | Fresenius Medical Care Holdings, Inc. | Determining a volume of medical fluid pumped into or out of a medical fluid cassette |
US9259528B2 (en) | 2013-08-22 | 2016-02-16 | Medtronic Minimed, Inc. | Fluid infusion device with safety coupling |
US10881789B2 (en) | 2013-10-24 | 2021-01-05 | Trustees Of Boston University | Infusion system for preventing mischanneling of multiple medicaments |
US10569015B2 (en) | 2013-12-02 | 2020-02-25 | Bigfoot Biomedical, Inc. | Infusion pump system and method |
US9750878B2 (en) | 2013-12-11 | 2017-09-05 | Medtronic Minimed, Inc. | Closed-loop control of glucose according to a predicted blood glucose trajectory |
US9750877B2 (en) | 2013-12-11 | 2017-09-05 | Medtronic Minimed, Inc. | Predicted time to assess and/or control a glycemic state |
US9849240B2 (en) | 2013-12-12 | 2017-12-26 | Medtronic Minimed, Inc. | Data modification for predictive operations and devices incorporating same |
US10105488B2 (en) | 2013-12-12 | 2018-10-23 | Medtronic Minimed, Inc. | Predictive infusion device operations and related methods and systems |
US9694132B2 (en) | 2013-12-19 | 2017-07-04 | Medtronic Minimed, Inc. | Insertion device for insertion set |
US20150182698A1 (en) | 2013-12-31 | 2015-07-02 | Abbvie Inc. | Pump, motor and assembly for beneficial agent delivery |
GB2523989B (en) | 2014-01-30 | 2020-07-29 | Insulet Netherlands B V | Therapeutic product delivery system and method of pairing |
EP3099220A1 (en) * | 2014-01-30 | 2016-12-07 | Koninklijke Philips N.V. | Reducing blockages of a plaque detection stream probe |
US9399096B2 (en) | 2014-02-06 | 2016-07-26 | Medtronic Minimed, Inc. | Automatic closed-loop control adjustments and infusion systems incorporating same |
US9861748B2 (en) | 2014-02-06 | 2018-01-09 | Medtronic Minimed, Inc. | User-configurable closed-loop notifications and infusion systems incorporating same |
GB201402826D0 (en) * | 2014-02-18 | 2014-04-02 | Owen Mumford Ltd | Injection device |
MX2016010876A (en) | 2014-02-21 | 2016-10-26 | Deka Products Lp | Syringe pump having a pressure sensor assembly. |
ES2776363T3 (en) | 2014-02-28 | 2020-07-30 | Icu Medical Inc | Infusion set and method using dual wavelength in-line optical air detection |
US10034976B2 (en) | 2014-03-24 | 2018-07-31 | Medtronic Minimed, Inc. | Fluid infusion patch pump device with automatic fluid system priming feature |
US10001450B2 (en) | 2014-04-18 | 2018-06-19 | Medtronic Minimed, Inc. | Nonlinear mapping technique for a physiological characteristic sensor |
US10232113B2 (en) | 2014-04-24 | 2019-03-19 | Medtronic Minimed, Inc. | Infusion devices and related methods and systems for regulating insulin on board |
US10275572B2 (en) | 2014-05-01 | 2019-04-30 | Medtronic Minimed, Inc. | Detecting blockage of a reservoir cavity during a seating operation of a fluid infusion device |
US9681828B2 (en) | 2014-05-01 | 2017-06-20 | Medtronic Minimed, Inc. | Physiological characteristic sensors and methods for forming such sensors |
US10007765B2 (en) | 2014-05-19 | 2018-06-26 | Medtronic Minimed, Inc. | Adaptive signal processing for infusion devices and related methods and systems |
US10152049B2 (en) | 2014-05-19 | 2018-12-11 | Medtronic Minimed, Inc. | Glucose sensor health monitoring and related methods and systems |
US10274349B2 (en) | 2014-05-19 | 2019-04-30 | Medtronic Minimed, Inc. | Calibration factor adjustments for infusion devices and related methods and systems |
WO2015184366A1 (en) | 2014-05-29 | 2015-12-03 | Hospira, Inc. | Infusion system and pump with configurable closed loop delivery rate catch-up |
JP2017525032A (en) | 2014-06-30 | 2017-08-31 | バクスター・コーポレーション・イングルウッドBaxter Corporation Englewood | Managed medical information exchange |
US9629901B2 (en) | 2014-07-01 | 2017-04-25 | Bigfoot Biomedical, Inc. | Glucagon administration system and methods |
US9517307B2 (en) | 2014-07-18 | 2016-12-13 | Kaleo, Inc. | Devices and methods for delivering opioid antagonists including formulations for naloxone |
US10076608B2 (en) | 2014-07-21 | 2018-09-18 | Smiths Medical Asd, Inc. | Method and apparatus for overload protection in medicament syringe pumps |
US10137246B2 (en) | 2014-08-06 | 2018-11-27 | Bigfoot Biomedical, Inc. | Infusion pump assembly and method |
US9919096B2 (en) | 2014-08-26 | 2018-03-20 | Bigfoot Biomedical, Inc. | Infusion pump system and method |
US9839753B2 (en) | 2014-09-26 | 2017-12-12 | Medtronic Minimed, Inc. | Systems for managing reservoir chamber pressure |
US9833563B2 (en) | 2014-09-26 | 2017-12-05 | Medtronic Minimed, Inc. | Systems for managing reservoir chamber pressure |
US10159786B2 (en) | 2014-09-30 | 2018-12-25 | Perqflo, Llc | Hybrid ambulatory infusion pumps |
US11575673B2 (en) | 2014-09-30 | 2023-02-07 | Baxter Corporation Englewood | Central user management in a distributed healthcare information management system |
US11107574B2 (en) | 2014-09-30 | 2021-08-31 | Baxter Corporation Englewood | Management of medication preparation with formulary management |
US10279126B2 (en) | 2014-10-07 | 2019-05-07 | Medtronic Minimed, Inc. | Fluid conduit assembly with gas trapping filter in the fluid flow path |
WO2016074002A2 (en) | 2014-10-13 | 2016-05-12 | Ramey Kirk D | Connector for medication delivery system |
US9833564B2 (en) | 2014-11-25 | 2017-12-05 | Medtronic Minimed, Inc. | Fluid conduit assembly with air venting features |
US9987420B2 (en) | 2014-11-26 | 2018-06-05 | Medtronic Minimed, Inc. | Systems and methods for fluid infusion device with automatic reservoir fill |
US10195341B2 (en) | 2014-11-26 | 2019-02-05 | Medtronic Minimed, Inc. | Systems and methods for fluid infusion device with automatic reservoir fill |
US9943645B2 (en) | 2014-12-04 | 2018-04-17 | Medtronic Minimed, Inc. | Methods for operating mode transitions and related infusion devices and systems |
US9636453B2 (en) | 2014-12-04 | 2017-05-02 | Medtronic Minimed, Inc. | Advance diagnosis of infusion device operating mode viability |
EP3937116A1 (en) | 2014-12-05 | 2022-01-12 | Baxter Corporation Englewood | Dose preparation data analytics |
US9937292B2 (en) | 2014-12-09 | 2018-04-10 | Medtronic Minimed, Inc. | Systems for filling a fluid infusion device reservoir |
US10307535B2 (en) | 2014-12-19 | 2019-06-04 | Medtronic Minimed, Inc. | Infusion devices and related methods and systems for preemptive alerting |
US11344668B2 (en) | 2014-12-19 | 2022-05-31 | Icu Medical, Inc. | Infusion system with concurrent TPN/insulin infusion |
US10265031B2 (en) | 2014-12-19 | 2019-04-23 | Medtronic Minimed, Inc. | Infusion devices and related methods and systems for automatic alert clearing |
WO2016133635A1 (en) * | 2015-02-18 | 2016-08-25 | Smiths Medical Asd, Inc. | Occlusion sensor integrated within thixo magnesium plunger driver head |
WO2016133789A2 (en) | 2015-02-18 | 2016-08-25 | Perqflo, Llc | Ambulatory infusion pump and reservoir assemblies for use with same |
CN111905188B (en) | 2015-02-18 | 2022-07-22 | 英赛罗公司 | Fluid delivery and infusion device and method of use |
US10850024B2 (en) | 2015-03-02 | 2020-12-01 | Icu Medical, Inc. | Infusion system, device, and method having advanced infusion features |
JP2018507487A (en) | 2015-03-03 | 2018-03-15 | バクスター・コーポレーション・イングルウッドBaxter Corporation Englewood | Pharmacy workflow management with alert integration |
US9795534B2 (en) | 2015-03-04 | 2017-10-24 | Medimop Medical Projects Ltd. | Compliant coupling assembly for cartridge coupling of a drug delivery device |
US10251813B2 (en) | 2015-03-04 | 2019-04-09 | West Pharma. Services IL, Ltd. | Flexibly mounted cartridge alignment collar for drug delivery device |
US9977469B2 (en) * | 2015-03-04 | 2018-05-22 | Ranch Systems Llc | Modular computing node |
US10307528B2 (en) | 2015-03-09 | 2019-06-04 | Medtronic Minimed, Inc. | Extensible infusion devices and related methods |
AU2016235054B2 (en) | 2015-03-24 | 2020-07-16 | Kaleo, Inc. | Devices and methods for delivering a lyophilized medicament |
US10449298B2 (en) | 2015-03-26 | 2019-10-22 | Medtronic Minimed, Inc. | Fluid injection devices and related methods |
US9744297B2 (en) | 2015-04-10 | 2017-08-29 | Medimop Medical Projects Ltd. | Needle cannula position as an input to operational control of an injection device |
US10293120B2 (en) | 2015-04-10 | 2019-05-21 | West Pharma. Services IL, Ltd. | Redundant injection device status indication |
BR112017020735A2 (en) | 2015-04-15 | 2018-07-17 | Gambro Lundia Ab | infusion set pressure booster treatment system |
US9878097B2 (en) | 2015-04-29 | 2018-01-30 | Bigfoot Biomedical, Inc. | Operating an infusion pump system |
US9999721B2 (en) | 2015-05-26 | 2018-06-19 | Medtronic Minimed, Inc. | Error handling in infusion devices with distributed motor control and related operating methods |
US10137243B2 (en) | 2015-05-26 | 2018-11-27 | Medtronic Minimed, Inc. | Infusion devices with distributed motor control and related operating methods |
US10575767B2 (en) | 2015-05-29 | 2020-03-03 | Medtronic Minimed, Inc. | Method for monitoring an analyte, analyte sensor and analyte monitoring apparatus |
WO2016196934A1 (en) | 2015-06-04 | 2016-12-08 | Medimop Medical Projects Ltd. | Cartridge insertion for drug delivery device |
EP3302621A4 (en) | 2015-06-04 | 2019-05-08 | Smiths Medical ASD, Inc. | Procedure-based programming for infusion pumps |
US9993594B2 (en) | 2015-06-22 | 2018-06-12 | Medtronic Minimed, Inc. | Occlusion detection techniques for a fluid infusion device having a rotary pump mechanism and rotor position sensors |
US10010668B2 (en) | 2015-06-22 | 2018-07-03 | Medtronic Minimed, Inc. | Occlusion detection techniques for a fluid infusion device having a rotary pump mechanism and a force sensor |
US9879668B2 (en) | 2015-06-22 | 2018-01-30 | Medtronic Minimed, Inc. | Occlusion detection techniques for a fluid infusion device having a rotary pump mechanism and an optical sensor |
US9878095B2 (en) | 2015-06-22 | 2018-01-30 | Medtronic Minimed, Inc. | Occlusion detection techniques for a fluid infusion device having a rotary pump mechanism and multiple sensor contact elements |
US9987425B2 (en) | 2015-06-22 | 2018-06-05 | Medtronic Minimed, Inc. | Occlusion detection techniques for a fluid infusion device having a rotary pump mechanism and sensor contact elements |
CN116206744A (en) | 2015-06-25 | 2023-06-02 | 甘布罗伦迪亚股份公司 | Medical device systems and methods with distributed databases |
GB2556479B (en) | 2015-06-30 | 2022-09-07 | Kaleo Inc | Auto-injectors for administration of a medicament within a prefilled syringe |
WO2017007968A1 (en) | 2015-07-08 | 2017-01-12 | Trustees Of Boston University | Infusion system and components thereof |
CN108348677B (en) | 2015-08-20 | 2020-10-27 | 坦德姆糖尿病护理股份有限公司 | Drive mechanism for a perfusion pump |
US10463297B2 (en) | 2015-08-21 | 2019-11-05 | Medtronic Minimed, Inc. | Personalized event detection methods and related devices and systems |
US20170053084A1 (en) | 2015-08-21 | 2017-02-23 | Medtronic Minimed, Inc. | Data analytics and reporting of glucose-related information |
US10293108B2 (en) | 2015-08-21 | 2019-05-21 | Medtronic Minimed, Inc. | Infusion devices and related patient ratio adjustment methods |
WO2017035024A1 (en) | 2015-08-21 | 2017-03-02 | Medtronic Minimed, Inc. | Data analytics and insight delivery for the management and control of diabetes |
WO2017035022A1 (en) | 2015-08-21 | 2017-03-02 | Medtronic Minimed, Inc. | Personalized parameter modeling methods and related devices and systems |
US10478557B2 (en) | 2015-08-21 | 2019-11-19 | Medtronic Minimed, Inc. | Personalized parameter modeling methods and related devices and systems |
US10201657B2 (en) | 2015-08-21 | 2019-02-12 | Medtronic Minimed, Inc. | Methods for providing sensor site rotation feedback and related infusion devices and systems |
US10117992B2 (en) | 2015-09-29 | 2018-11-06 | Medtronic Minimed, Inc. | Infusion devices and related rescue detection methods |
US11501867B2 (en) | 2015-10-19 | 2022-11-15 | Medtronic Minimed, Inc. | Medical devices and related event pattern presentation methods |
US11666702B2 (en) | 2015-10-19 | 2023-06-06 | Medtronic Minimed, Inc. | Medical devices and related event pattern treatment recommendation methods |
US10146911B2 (en) | 2015-10-23 | 2018-12-04 | Medtronic Minimed, Inc. | Medical devices and related methods and systems for data transfer |
US10037722B2 (en) | 2015-11-03 | 2018-07-31 | Medtronic Minimed, Inc. | Detecting breakage in a display element |
US10449306B2 (en) | 2015-11-25 | 2019-10-22 | Medtronics Minimed, Inc. | Systems for fluid delivery with wicking membrane |
US10449294B1 (en) | 2016-01-05 | 2019-10-22 | Bigfoot Biomedical, Inc. | Operating an infusion pump system |
EP3374900A1 (en) | 2016-01-05 | 2018-09-19 | Bigfoot Biomedical, Inc. | Operating multi-modal medicine delivery systems |
EP3374905A1 (en) | 2016-01-13 | 2018-09-19 | Bigfoot Biomedical, Inc. | User interface for diabetes management system |
CN112933333B (en) | 2016-01-14 | 2023-03-28 | 比格福特生物医药公司 | Adjusting insulin delivery rate |
WO2017123703A2 (en) | 2016-01-14 | 2017-07-20 | Bigfoot Biomedical, Inc. | Occlusion resolution in medication delivery devices, systems, and methods |
US11720085B2 (en) | 2016-01-22 | 2023-08-08 | Hayward Industries, Inc. | Systems and methods for providing network connectivity and remote monitoring, optimization, and control of pool/spa equipment |
EP3405629A4 (en) | 2016-01-22 | 2020-01-22 | Hayward Industries, Inc. | Systems and methods for providing network connectivity and remote monitoring, optimization, and control of pool/spa equipment |
CA3013053A1 (en) | 2016-01-28 | 2017-08-03 | Savor Labs, Inc. | Method and apparatus for tracking of food intake and other behaviors and providing relevant feedback |
CN115607768A (en) | 2016-02-12 | 2023-01-17 | 美敦力米尼梅德有限公司 | Portable infusion pump and assembly for use therewith |
USD809134S1 (en) | 2016-03-10 | 2018-01-30 | Bigfoot Biomedical, Inc. | Infusion pump assembly |
US10589038B2 (en) | 2016-04-27 | 2020-03-17 | Medtronic Minimed, Inc. | Set connector systems for venting a fluid reservoir |
USD831820S1 (en) * | 2016-04-29 | 2018-10-23 | Csl Behring Recombinant Facility Ag | Syringe pump housing |
USD829434S1 (en) * | 2016-04-29 | 2018-10-02 | Csl Behring Recombinant Facility Ag | Syringe pump housing |
USD831821S1 (en) * | 2016-04-29 | 2018-10-23 | Csl Behring Recombinant Facility Ag | Syringe pump housing |
USD831194S1 (en) * | 2016-04-29 | 2018-10-16 | Csl Behring Recombinant Facility Ag | Syringe pump housing |
AU2017264784B2 (en) | 2016-05-13 | 2022-04-21 | Icu Medical, Inc. | Infusion pump system and method with common line auto flush |
DK3760274T3 (en) | 2016-05-26 | 2023-06-19 | Medtronic Minimed Inc | SYSTEMS FOR FIXED CONNECTOR ASSEMBLY WITH LOCK |
US9968737B2 (en) | 2016-05-26 | 2018-05-15 | Medtronic Minimed, Inc. | Systems for set connector assembly with lock |
US10086134B2 (en) | 2016-05-26 | 2018-10-02 | Medtronic Minimed, Inc. | Systems for set connector assembly with lock |
US10086133B2 (en) | 2016-05-26 | 2018-10-02 | Medtronic Minimed, Inc. | Systems for set connector assembly with lock |
CN109195646B (en) * | 2016-06-01 | 2023-04-25 | 费森尤斯维尔公司 | Infusion device and method allowing detection of drift of sensor signal |
JP6957525B2 (en) | 2016-06-02 | 2021-11-02 | ウェスト ファーマ サービシーズ イスラエル リミテッド | Needle evacuation by 3 positions |
US10773024B2 (en) * | 2016-06-09 | 2020-09-15 | Becton, Dickinson And Company | Drive assembly for drug delivery system |
US10751476B2 (en) | 2016-06-09 | 2020-08-25 | Becton, Dickinson And Company | Actuator assembly for drug delivery system |
WO2017214441A1 (en) | 2016-06-10 | 2017-12-14 | Icu Medical, Inc. | Acoustic flow sensor for continuous medication flow measurements and feedback control of infusion |
EP3260147A1 (en) * | 2016-06-23 | 2017-12-27 | TecPharma Licensing AG | A segmented piston rod for a medication delivery device |
EP3490635B1 (en) | 2016-08-01 | 2021-11-17 | West Pharma. Services Il, Ltd. | Partial door closure prevention spring |
KR101839809B1 (en) * | 2016-08-12 | 2018-03-19 | (주)포인트엔지니어링 | Micro sensor |
US10449291B2 (en) | 2016-09-06 | 2019-10-22 | Medtronic Minimed, Inc. | Pump clip for a fluid infusion device |
US10718337B2 (en) | 2016-09-22 | 2020-07-21 | Hayward Industries, Inc. | Self-priming dedicated water feature pump |
WO2018058041A1 (en) * | 2016-09-23 | 2018-03-29 | Insulet Corporation | Fluid delivery device with sensor |
CN109789264B (en) | 2016-09-27 | 2021-06-22 | 比格福特生物医药公司 | Drug injection and disease management systems, devices and methods |
US10561788B2 (en) | 2016-10-06 | 2020-02-18 | Medtronic Minimed, Inc. | Infusion systems and methods for automated exercise mitigation |
US11097051B2 (en) | 2016-11-04 | 2021-08-24 | Medtronic Minimed, Inc. | Methods and apparatus for detecting and reacting to insufficient hypoglycemia response |
WO2018096534A1 (en) | 2016-11-22 | 2018-05-31 | Sorrel Medical Ltd. | Apparatus for delivering a therapeutic substance |
US10238030B2 (en) | 2016-12-06 | 2019-03-26 | Medtronic Minimed, Inc. | Wireless medical device with a complementary split ring resonator arrangement for suppression of electromagnetic interference |
US11096624B2 (en) | 2016-12-12 | 2021-08-24 | Bigfoot Biomedical, Inc. | Alarms and alerts for medication delivery devices and systems |
USD836769S1 (en) | 2016-12-12 | 2018-12-25 | Bigfoot Biomedical, Inc. | Insulin delivery controller |
AU2017381172A1 (en) | 2016-12-21 | 2019-06-13 | Gambro Lundia Ab | Medical device system including information technology infrastructure having secure cluster domain supporting external domain |
US10854322B2 (en) | 2016-12-21 | 2020-12-01 | Medtronic Minimed, Inc. | Infusion systems and methods for patient activity adjustments |
US10709834B2 (en) | 2016-12-21 | 2020-07-14 | Medtronic Minimed, Inc. | Medication fluid infusion set component with integrated physiological analyte sensor, and corresponding fluid infusion device |
US10272201B2 (en) | 2016-12-22 | 2019-04-30 | Medtronic Minimed, Inc. | Insertion site monitoring methods and related infusion devices and systems |
JP7175898B2 (en) | 2017-01-06 | 2022-11-21 | トラスティーズ オブ ボストン ユニバーシティ | Injection system and its components |
AU2018210313A1 (en) | 2017-01-17 | 2019-06-20 | Kaleo, Inc. | Medicament delivery devices with wireless connectivity and event detection |
US10532165B2 (en) | 2017-01-30 | 2020-01-14 | Medtronic Minimed, Inc. | Fluid reservoir and systems for filling a fluid reservoir of a fluid infusion device |
US10500135B2 (en) | 2017-01-30 | 2019-12-10 | Medtronic Minimed, Inc. | Fluid reservoir and systems for filling a fluid reservoir of a fluid infusion device |
US10552580B2 (en) | 2017-02-07 | 2020-02-04 | Medtronic Minimed, Inc. | Infusion system consumables and related calibration methods |
US10363365B2 (en) | 2017-02-07 | 2019-07-30 | Medtronic Minimed, Inc. | Infusion devices and related consumable calibration methods |
US11207463B2 (en) | 2017-02-21 | 2021-12-28 | Medtronic Minimed, Inc. | Apparatuses, systems, and methods for identifying an infusate in a reservoir of an infusion device |
US10646649B2 (en) | 2017-02-21 | 2020-05-12 | Medtronic Minimed, Inc. | Infusion devices and fluid identification apparatuses and methods |
US20180272064A1 (en) | 2017-03-24 | 2018-09-27 | Medtronic Minimed, Inc. | Patient management systems and prospective risk management methods |
JP6810816B2 (en) * | 2017-05-30 | 2021-01-06 | ウェスト ファーマ サービシーズ イスラエル リミテッド | Syringe noise and vibration damping mount module |
USD839294S1 (en) | 2017-06-16 | 2019-01-29 | Bigfoot Biomedical, Inc. | Display screen with graphical user interface for closed-loop medication delivery |
US20180361066A1 (en) * | 2017-06-20 | 2018-12-20 | Accugentix, LLC | Hand-held volume displacement dosage dispenser |
US11179516B2 (en) | 2017-06-22 | 2021-11-23 | Baxter International Inc. | Systems and methods for incorporating patient pressure into medical fluid delivery |
CN107091948A (en) * | 2017-06-29 | 2017-08-25 | 桐乡昊屹电子有限公司 | The blockage detector and detection method of electronic infusion pump |
US11260171B2 (en) | 2017-07-04 | 2022-03-01 | Medtronic Minimed, Inc. | Ambulatory infusion pumps and assemblies for use with same |
EP3651647A1 (en) | 2017-07-13 | 2020-05-20 | Bigfoot Biomedical, Inc. | Multi-scale display of blood glucose information |
EP3689465A3 (en) | 2017-07-27 | 2020-11-04 | Biomérieux Inc. | Isolation tube |
EP3675936A1 (en) | 2017-08-31 | 2020-07-08 | Eli Lilly and Company | Dose detection with piezoelectric sensing for a medication delivery device |
WO2019052111A1 (en) * | 2017-09-12 | 2019-03-21 | 美敦力公司 | Fluid infusion device and driving system therefor |
US10525244B2 (en) | 2017-09-28 | 2020-01-07 | Medtronic Minimed, Inc. | Microneedle arrays and methods for fabricating microneedle arrays |
US10524730B2 (en) | 2017-09-28 | 2020-01-07 | Medtronic Minimed, Inc. | Medical devices with microneedle arrays and methods for operating such medical devices |
US20190148025A1 (en) | 2017-11-15 | 2019-05-16 | Medtronic Minimed, Inc. | Patient therapy management and coaching system |
US11676734B2 (en) | 2017-11-15 | 2023-06-13 | Medtronic Minimed, Inc. | Patient therapy management system that leverages aggregated patient population data |
US11857767B2 (en) | 2017-12-22 | 2024-01-02 | West Pharma. Services IL, Ltd. | Injector usable with different dimension cartridges |
US10089055B1 (en) | 2017-12-27 | 2018-10-02 | Icu Medical, Inc. | Synchronized display of screen content on networked devices |
US11439352B2 (en) | 2018-01-17 | 2022-09-13 | Medtronic Minimed, Inc. | Medical device with adhesive patch longevity |
WO2019152908A1 (en) | 2018-02-05 | 2019-08-08 | Tandem Diabetes Care, Inc. | Methods and systems for detecting infusion pump conditions |
USD911355S1 (en) | 2018-03-29 | 2021-02-23 | Bigfoot Biomedical, Inc. | Display screen or portion thereof with graphical user interface |
USD928199S1 (en) | 2018-04-02 | 2021-08-17 | Bigfoot Biomedical, Inc. | Medication delivery device with icons |
US11158413B2 (en) | 2018-04-23 | 2021-10-26 | Medtronic Minimed, Inc. | Personalized closed loop medication delivery system that utilizes a digital twin of the patient |
US11147919B2 (en) | 2018-04-23 | 2021-10-19 | Medtronic Minimed, Inc. | Methodology to recommend and implement adjustments to a fluid infusion device of a medication delivery system |
WO2019209963A1 (en) | 2018-04-24 | 2019-10-31 | Deka Products Limited Partnership | Apparatus and system for fluid delivery |
US20190336078A1 (en) | 2018-05-04 | 2019-11-07 | Medtronic Minimed, Inc. | Medical device with extended wear adhesive patch |
CA3099113A1 (en) | 2018-05-04 | 2019-11-07 | Insulet Corporation | Safety constraints for a control algorithm-based drug delivery system |
US11367526B2 (en) | 2018-05-07 | 2022-06-21 | Medtronic Minimed, Inc. | Proactive patient guidance using augmented reality |
US11458250B2 (en) * | 2018-05-31 | 2022-10-04 | Insulet Corporation | System and techniques for drug reservoir volume detection |
US11441550B2 (en) * | 2018-06-29 | 2022-09-13 | Norgren Kloehn Llc | Self-aligning power screw for syringe pump |
CH715144A1 (en) * | 2018-07-02 | 2020-01-15 | Edelweiss Dr Ag | Extrusion device and composite distribution system. |
WO2020018433A1 (en) | 2018-07-16 | 2020-01-23 | Kaleo, Inc. | Medicament delivery devices with wireless connectivity and compliance detection |
CA3051543A1 (en) | 2018-08-30 | 2020-02-29 | Becton, Dickinson And Company | Liquid medicament reservoir empty detection sensor and occlusion sensor for medicament delivery device |
US10828419B2 (en) | 2018-09-04 | 2020-11-10 | Medtronic Minimed, Inc. | Infusion set with pivoting metal cannula and strain relief |
US11547799B2 (en) | 2018-09-20 | 2023-01-10 | Medtronic Minimed, Inc. | Patient day planning systems and methods |
CN112714936A (en) | 2018-09-20 | 2021-04-27 | 美敦力泌力美公司 | Patient monitoring system and related recommendation method |
US11097052B2 (en) | 2018-09-28 | 2021-08-24 | Medtronic Minimed, Inc. | Insulin infusion device with configurable target blood glucose value for automatic basal insulin delivery operation |
US10980942B2 (en) | 2018-09-28 | 2021-04-20 | Medtronic Minimed, Inc. | Infusion devices and related meal bolus adjustment methods |
US11071821B2 (en) | 2018-09-28 | 2021-07-27 | Medtronic Minimed, Inc. | Insulin infusion device with efficient confirmation routine for blood glucose measurements |
US10894126B2 (en) | 2018-09-28 | 2021-01-19 | Medtronic Minimed, Inc. | Fluid infusion system that automatically determines and delivers a correction bolus |
CN112789070A (en) | 2018-09-28 | 2021-05-11 | 英赛罗公司 | Mode of activity of the artificial pancreas System |
US11357909B2 (en) | 2018-10-05 | 2022-06-14 | Eitan Medical Ltd. | Triggering sequence |
US10946140B2 (en) | 2018-10-11 | 2021-03-16 | Medtronic Minimed, Inc. | Systems and methods for measurement of fluid delivery |
US20200116748A1 (en) | 2018-10-11 | 2020-04-16 | Medtronic Minimed, Inc. | Systems and methods for measurement of fluid delivery |
US11565039B2 (en) | 2018-10-11 | 2023-01-31 | Insulet Corporation | Event detection for drug delivery system |
US20200135320A1 (en) | 2018-10-31 | 2020-04-30 | Medtronic Minimed, Inc. | Automated detection of a physical behavior event and corresponding adjustment of a medication dispensing system based on historical events |
US20200202997A1 (en) | 2018-12-19 | 2020-06-25 | Nutrino Health Ltd. | Automated method and system for generating personalized dietary and health advice or recommendations for individual users |
US11439752B2 (en) | 2019-02-01 | 2022-09-13 | Medtronic Minimed, Inc. | Methods and devices for occlusion detection using actuator sensors |
US11389587B2 (en) | 2019-02-06 | 2022-07-19 | Medtronic Minimed, Inc. | Patient monitoring systems and related presentation methods |
US11191899B2 (en) | 2019-02-12 | 2021-12-07 | Medtronic Minimed, Inc. | Infusion systems and related personalized bolusing methods |
EP3935646A1 (en) | 2019-04-16 | 2022-01-12 | Medtronic MiniMed, Inc. | Personalized closed loop optimization systems and methods |
DE102019112792A1 (en) * | 2019-05-15 | 2020-11-19 | Leistritz Pumpen Gmbh | Method for determining a flow volume of a fluid conveyed by a pump |
US10939488B2 (en) | 2019-05-20 | 2021-03-02 | Medtronic Minimed, Inc. | Method and system for controlling communication between devices of a wireless body area network for an medical device system |
US11642454B2 (en) | 2019-06-06 | 2023-05-09 | Medtronic Minimed, Inc. | Fluid infusion systems |
MX2022000668A (en) | 2019-07-16 | 2022-05-20 | Beta Bionics Inc | Ambulatory device and components thereof. |
WO2021026399A1 (en) | 2019-08-06 | 2021-02-11 | Medtronic Minimed, Inc. | Machine learning-based system for estimating glucose values |
US11883208B2 (en) | 2019-08-06 | 2024-01-30 | Medtronic Minimed, Inc. | Machine learning-based system for estimating glucose values based on blood glucose measurements and contextual activity data |
JP2022543523A (en) | 2019-08-09 | 2022-10-13 | カレオ,インコーポレイテッド | Device and method for delivery of substances in pre-filled syringes |
US11724045B2 (en) | 2019-08-21 | 2023-08-15 | Medtronic Minimed, Inc. | Connection of a stopper and piston in a fluid delivery device |
US20210060244A1 (en) | 2019-08-28 | 2021-03-04 | Medtronic Minimed, Inc. | Method and system for verifying whether a non-medical client device is operating correctly with a medical device controlled by the non-medical client device and causing a notification to be generated |
US20210060249A1 (en) | 2019-08-29 | 2021-03-04 | Medtronic Minimed, Inc. | Controlling medical infusion device operation and features based on detected patient sleeping status |
US11565044B2 (en) | 2019-09-12 | 2023-01-31 | Medtronic Minimed, Inc. | Manufacturing controls for sensor calibration using fabrication measurements |
US11654235B2 (en) | 2019-09-12 | 2023-05-23 | Medtronic Minimed, Inc. | Sensor calibration using fabrication measurements |
US11801344B2 (en) | 2019-09-13 | 2023-10-31 | Insulet Corporation | Blood glucose rate of change modulation of meal and correction insulin bolus quantity |
US11213623B2 (en) | 2019-09-20 | 2022-01-04 | Medtronic Minimed, Inc. | Infusion systems and related personalized bolusing methods |
US11241537B2 (en) | 2019-09-20 | 2022-02-08 | Medtronic Minimed, Inc. | Contextual personalized closed-loop adjustment methods and systems |
US11935637B2 (en) | 2019-09-27 | 2024-03-19 | Insulet Corporation | Onboarding and total daily insulin adaptivity |
US11496083B2 (en) | 2019-11-15 | 2022-11-08 | Medtronic Minimed, Inc. | Devices and methods for controlling electromechanical actuators |
US11278671B2 (en) | 2019-12-04 | 2022-03-22 | Icu Medical, Inc. | Infusion pump with safety sequence keypad |
US11670425B2 (en) | 2019-12-09 | 2023-06-06 | Medtronic Minimed, Inc. | Translation modeling methods and systems for simulating sensor measurements |
US11786655B2 (en) | 2019-12-13 | 2023-10-17 | Medtronic Minimed, Inc. | Context-sensitive predictive operation of a medication delivery system in response to gesture-indicated activity changes |
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US20210281092A1 (en) | 2020-03-09 | 2021-09-09 | Medtronic Minimed, Inc. | Networked dynamic management of charge |
US11278661B2 (en) | 2020-03-10 | 2022-03-22 | Beta Bionics, Inc. | Infusion system and components thereof |
US11607493B2 (en) | 2020-04-06 | 2023-03-21 | Insulet Corporation | Initial total daily insulin setting for user onboarding |
US11596359B2 (en) | 2020-04-09 | 2023-03-07 | Medtronic Minimed, Inc. | Methods and systems for mitigating sensor error propagation |
US11583631B2 (en) | 2020-04-23 | 2023-02-21 | Medtronic Minimed, Inc. | Intuitive user interface features and related functionality for a therapy delivery system |
US11690955B2 (en) | 2020-04-23 | 2023-07-04 | Medtronic Minimed, Inc. | Continuous analyte sensor quality measures and related therapy actions for an automated therapy delivery system |
CN115426946A (en) | 2020-04-23 | 2022-12-02 | 美敦力迷你迈德公司 | Analyte sensor quality metrics and related therapeutic actions for automated therapeutic delivery systems |
US20210377726A1 (en) | 2020-05-27 | 2021-12-02 | Medtronic Minimed, Inc. | Method and system for automatically associating a non-medical device with a medical device |
US20210393876A1 (en) | 2020-06-19 | 2021-12-23 | Medtronic Minimed, Inc. | Default carbohydrate consumption counts based on characteristics of persons |
US11735305B2 (en) | 2020-06-26 | 2023-08-22 | Medtronic Minimed, Inc. | Automatic configuration of user-specific data based on placement into service |
WO2022020184A1 (en) | 2020-07-21 | 2022-01-27 | Icu Medical, Inc. | Fluid transfer devices and methods of use |
CN116097370A (en) | 2020-07-30 | 2023-05-09 | 美敦力迷你迈德公司 | Automatic device configuration |
US11445807B2 (en) | 2020-07-31 | 2022-09-20 | Medtronic Minimed, Inc. | Pump clip with tube clamp for a fluid infusion device |
US11684716B2 (en) | 2020-07-31 | 2023-06-27 | Insulet Corporation | Techniques to reduce risk of occlusions in drug delivery systems |
WO2022081298A1 (en) | 2020-09-18 | 2022-04-21 | Medtronic Minimed, Inc. | Ketone body sensing device |
US11839743B2 (en) | 2020-10-07 | 2023-12-12 | Medtronic Minimed, Inc. | Graphic user interface for automated infusate delivery |
US11737783B2 (en) | 2020-10-16 | 2023-08-29 | Medtronic Minimed, Inc. | Disposable medical device introduction system |
US11135360B1 (en) | 2020-12-07 | 2021-10-05 | Icu Medical, Inc. | Concurrent infusion with common line auto flush |
FR3118104B1 (en) * | 2020-12-21 | 2023-02-10 | Zynnon GmbH | Improved pump device. |
EP4288971A1 (en) | 2021-02-02 | 2023-12-13 | Medtronic MiniMed, Inc. | Dynamic adjustments of physiological data |
US11744946B2 (en) | 2021-02-18 | 2023-09-05 | Medtronic Minimed, Inc. | Dynamic super bolus generation |
US11839744B2 (en) | 2021-02-18 | 2023-12-12 | Medtronic Minimed, Inc. | Automated super bolus generation |
US11904140B2 (en) | 2021-03-10 | 2024-02-20 | Insulet Corporation | Adaptable asymmetric medicament cost component in a control system for medicament delivery |
US11904139B2 (en) | 2021-04-05 | 2024-02-20 | Medtronic Minimed, Inc. | Closed-loop control in steady-state conditions |
US20230000447A1 (en) | 2021-06-30 | 2023-01-05 | Medtronic Minimed, Inc. | Event-oriented predictions of glycemic responses |
WO2023036832A1 (en) | 2021-09-10 | 2023-03-16 | Fresenius Vial Sas | Infusion device having a processing device configured to determine a value indicative of a sensitivity of a sensor device |
US11738144B2 (en) | 2021-09-27 | 2023-08-29 | Insulet Corporation | Techniques enabling adaptation of parameters in aid systems by user input |
US20230149637A1 (en) | 2021-11-12 | 2023-05-18 | Medtronic Minimed, Inc. | Fluid reservoir cap with gas trapping filter and associated retaining feature |
US11439754B1 (en) | 2021-12-01 | 2022-09-13 | Insulet Corporation | Optimizing embedded formulations for drug delivery |
WO2023102147A1 (en) | 2021-12-01 | 2023-06-08 | Medtronic Minimed, Inc. | Mealtime delivery of correction boluses |
WO2023102498A1 (en) | 2021-12-01 | 2023-06-08 | Medtronic Minimed, Inc. | Real-time meal detection based on sensor glucose and estimated plasma insulin levels |
Citations (6)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
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 |
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 |
WO2001030421A2 (en) | 1999-10-28 | 2001-05-03 | Minimed, Inc. | Plunger plug with stiffening insert |
Family Cites Families (6)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US4747828A (en) | 1986-12-09 | 1988-05-31 | Fisher Scientific Group | IV fluid line occlusion detector |
US5096385A (en) * | 1989-11-08 | 1992-03-17 | Ivac Corporation | Method and system for upstream occlusion detection |
FR2710537B1 (en) | 1993-09-30 | 1995-12-01 | Becton Dickinson Co | Method and device for detecting occlusions in a perfusion line. |
US5695473A (en) | 1994-07-27 | 1997-12-09 | Sims Deltec, Inc. | Occlusion detection system for an infusion pump |
US5647853A (en) | 1995-03-03 | 1997-07-15 | Minimed Inc. | Rapid response occlusion detector for a medication infusion pump |
US6485465B2 (en) * | 2000-03-29 | 2002-11-26 | Medtronic Minimed, Inc. | Methods, apparatuses, and uses for infusion pump fluid pressure and force detection |
-
2001
- 2001-03-27 US US09/819,208 patent/US6485465B2/en not_active Expired - Lifetime
- 2001-03-28 AT AT01922776T patent/ATE325632T1/en not_active IP Right Cessation
- 2001-03-28 EP EP01922776A patent/EP1267960B1/en not_active Expired - Lifetime
- 2001-03-28 WO PCT/US2001/009893 patent/WO2001072357A2/en active IP Right Grant
- 2001-03-28 DE DE60119502T patent/DE60119502T2/en not_active Expired - Lifetime
- 2001-03-28 CA CA002406026A patent/CA2406026C/en not_active Expired - Fee Related
- 2001-03-28 AU AU2001249540A patent/AU2001249540A1/en not_active Abandoned
-
2002
- 2002-11-22 US US10/302,002 patent/US6659980B2/en not_active Expired - Lifetime
Patent Citations (6)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
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 |
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 |
WO2001030421A2 (en) | 1999-10-28 | 2001-05-03 | Minimed, Inc. | Plunger plug with stiffening insert |
Cited By (75)
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---|---|---|---|---|
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AU2002328764B2 (en) * | 2001-10-18 | 2007-06-28 | Tecpharma Licensing Ag | Injection device comprising an energy accumulator |
WO2003033057A1 (en) * | 2001-10-18 | 2003-04-24 | Tecpharma Licensing Ag | Injection device comprising an energy accumulator |
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US8900213B2 (en) | 2003-11-04 | 2014-12-02 | Brian Pope | Syringe pump rapid occlusion detection system |
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EP1616589A3 (en) * | 2003-11-04 | 2006-03-15 | Medex, Inc. | Syringe pump rapid occlusion detection system |
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US8182461B2 (en) | 2003-11-04 | 2012-05-22 | Smiths Medical Asd, Inc. | Syringe pump rapid occlusion detection system |
US9427521B2 (en) | 2003-11-04 | 2016-08-30 | Smiths Medical Asd, Inc. | Syringe pump rapid occlusion detection system |
CN103990203A (en) * | 2003-11-04 | 2014-08-20 | 史密斯医疗Asd公司 | Syringe pump rapid occlusion detection system |
WO2005046768A1 (en) * | 2003-11-04 | 2005-05-26 | Medex, Inc. | Syringe pump rapid occlusion detection system |
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US7881883B2 (en) | 2004-04-20 | 2011-02-01 | Roche Diagnostics International Ag | Device and method for the detection of an occlusion |
US7092797B2 (en) | 2004-05-25 | 2006-08-15 | Sherwood Services Ag | Flow monitoring system for a flow control apparatus |
US7447566B2 (en) | 2004-05-25 | 2008-11-04 | Covidien Ag | Occlusion system and method for a flow control apparatus |
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Also Published As
Publication number | Publication date |
---|---|
CA2406026C (en) | 2006-07-25 |
EP1267960A2 (en) | 2003-01-02 |
DE60119502T2 (en) | 2007-05-03 |
WO2001072357A9 (en) | 2002-12-27 |
CA2406026A1 (en) | 2001-10-04 |
US20010034502A1 (en) | 2001-10-25 |
WO2001072357A3 (en) | 2002-05-23 |
AU2001249540A1 (en) | 2001-10-08 |
DE60119502D1 (en) | 2006-06-14 |
EP1267960B1 (en) | 2006-05-10 |
US20030073954A1 (en) | 2003-04-17 |
ATE325632T1 (en) | 2006-06-15 |
US6659980B2 (en) | 2003-12-09 |
US6485465B2 (en) | 2002-11-26 |
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