WO2007041338A1 - Optically aligned pulse oximetry sensor - Google Patents
Optically aligned pulse oximetry sensor Download PDFInfo
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- WO2007041338A1 WO2007041338A1 PCT/US2006/038129 US2006038129W WO2007041338A1 WO 2007041338 A1 WO2007041338 A1 WO 2007041338A1 US 2006038129 W US2006038129 W US 2006038129W WO 2007041338 A1 WO2007041338 A1 WO 2007041338A1
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- frame
- sensor
- optical axis
- emitter
- detector
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Classifications
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/68—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient
- A61B5/6801—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient specially adapted to be attached to or worn on the body surface
- A61B5/6813—Specially adapted to be attached to a specific body part
- A61B5/6825—Hand
- A61B5/6826—Finger
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/145—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue
- A61B5/1455—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue using optical sensors, e.g. spectral photometrical oximeters
- A61B5/14551—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue using optical sensors, e.g. spectral photometrical oximeters for measuring blood gases
- A61B5/14552—Details of sensors specially adapted therefor
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/68—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient
- A61B5/6801—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient specially adapted to be attached to or worn on the body surface
- A61B5/683—Means for maintaining contact with the body
- A61B5/6838—Clamps or clips
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B2562/00—Details of sensors; Constructional details of sensor housings or probes; Accessories for sensors
- A61B2562/12—Manufacturing methods specially adapted for producing sensors for in-vivo measurements
Definitions
- the present invention relates generally to pulse oximetry and, more particularly, to sensors used for pulse oximetry.
- Pulse oximetry may be used to measure various blood flow characteristics, such as the blood-oxygen saturation of hemoglobin in arterial blood, the volume of individual blood pulsations supplying the tissue, and/or the rate of blood pulsations corresponding to each heartbeat of a patient.
- Pulse oximeters typically utilize a non-invasive sensor that is placed on or against a patient's tissue that is well perfused with blood, such as a patient's finger, toe, or earlobe.
- the pulse oximeter sensor emits light and photoelectrically senses the absorption and/or scattering of the light after passage through the perfused tissue.
- the data collected by the sensor may then be used to calculate one or more of the above physiological characteristics based upon the absorption or scattering of title light. More specifically, the emitted light is typically selected to be of one or more wavelengths that are absorbed or scattered in an amount related to the presence of oxygenated versus de-oxygenated hemoglobin in the blood.
- the amount of light absorbed and/or scattered may then be used to estimate the amount of the oxygen in the tissue using various algorithms. hi many instances, it may be desirable to employ, for cost and/or convenience, a pulse oximeter sensor that is reusable.
- Such reusable sensors should fit snugly enough that incidental patient motion will not dislodge or move the sensor yet not so tight that normal blood flow is disrupted, which may interfere with pulse oximetry measurements.
- Such a conforming fit may be difficult to achieve over a range of patient physiologies without adjustment or excessive attention on the part of medical personnel.
- transmission-type pulse oximetry sensors in which an emitter and detector are provided on opposite sides of the finger or toe
- a sensor assembly that includes: a frame comprising one or more pair of flexible elements disposed substantially symmetric relative to an optical axis; at least two optical components disposed on the frame along the optical axis; and a covering provided over at least part of the frame and the at least two optical components.
- a sensor assembly that includes: a frame; an emitter and a detector housed on the frame along an optical axis, wherein the emitter and the detector are configured to move relative to one another while remaining aligned along the optical axis; and a covering provided over the frame, the emitter, and the detector.
- a method of manufacturing a sensor that includes: situating an emitter and a detector on a frame, wherein the frame comprises one or more pair of flexible elements disposed substantially symmetric relative to an optical axis upon which the emitter and the detector are situated; and coating the frame with a coating material to form a sensor assembly.
- a method for acquiring physiological data includes: emitting two or more wavelengths of light from an emitter of a sensor assembly disposed on a patient; detecting transmitted or reflected light using a photodetector of the sensor assembly, wherein the emitter and the photodetector are maintained in optical alignment with one another along an optical axis by one or more pair of flexible elements of the sensor assembly, wherein the one or more pair of flexible elements are disposed symmetrical to the optical axis; and determining a physiological parameter based on the detected light.
- a method of manufacturing a sensor body that includes: coating a frame with a coating material to form a sensor body, wherein the frame comprises one or more pair of flexible elements disposed substantially symmetric relative to an optical axis defined by an emitter housing and a detector housing of the frame.
- a sensor body that includes: a frame comprising one or more pair of flexible elements disposed substantially symmetric relative to an optical axis defined by an emitter housing and a detector housing of the frame; and a covering provided over the frame.
- a sensor body that includes: a frame comprising an emitter housing and a detector housing which define an optical axis, wherein the emitter housing and the detector housing are configured to move relative to one another while remaining aligned along the optical axis; and a covering provided over the frame to form a sensor assembly.
- a frame of a sensor that includes: at least two optical component housings defining an optical axis; and one or more pair of flexible elements disposed substantially symmetric relative to the optical axis.
- a frame of a sensor that includes: an emitter housing and a detector housing which define an optical axis, wherein the emitter housing and the detector housing are configured to move relative to one another while remaining aligned along optical axis.
- a method for manufacturing a frame of a sensor that includes: forming at least two optical component housings of a frame of a sensor such that the at least two optical component housings define an optical axis; and providing one or more pair of flexible elements on the frame disposed substantially symmetric relative to the optical axis.
- Fig. 1 illustrates a physiological monitoring system coupled to a multi-parameter patient monitor and a patient sensor, in accordance with aspects of the present technique
- Fig. 2 illustrates a perspective view of one configuration of an internal frame for use in a patient sensor, in accordance with aspects of the present technique
- Fig. 3 illustrates the internal frame of Fig. 2 in an expanded configuration
- Fig. 4 illustrates the internal frame of Fig. 2 in a collapsed configuration
- Fig. 5 illustrates a perspective view of a covered patient sensor based upon the internal frame of Fig. 2;
- Fig. 6 illustrates a perspective view of another configuration of an internal frame for use in a patient sensor, in accordance with aspects of the present technique
- Fig. 7 illustrates the internal frame of Fig. 6 in an expanded configuration
- Fig. 8 illustrates the internal frame of Fig. 6 in a collapsed configuration
- Fig. 9 illustrates a perspective view of a covered patient sensor based upon the internal frame of Fig. 6
- Fig. 10 illustrates a perspective view of a further configuration of an internal frame for use in a patient sensor, in accordance with aspects of the present technique
- Fig. 11 illustrates the internal frame of Fig. 10 in an expanded configuration
- Fig. 12 illustrates the internal frame of Fig. 10 in a collapsed configuration
- Fig. 13 illustrates a perspective view of a covered patient sensor based upon the internal frame of Fig. 10.
- a reusable patient sensor that includes a flexible frame, such as a framework incorporating living hinges, pin hinges, bar links, bending beams, and so forth, which allows the patient sensor to conform to fingers or toes of varying sizes while maintaining alignment of the optical components.
- a sensor 10 may be used in conjunction with a patient monitor 12.
- a cable 14 connects the sensor 10 to the patient monitor 12.
- the sensor 10 and/or the cable 14 may include or incorporate one or more integrated circuit devices or electrical devices, such as a memory, processor chip, or resistor that may facilitate or enhance communication between the sensor 10 and the patient monitor 12.
- the cable 14 may be an adaptor cable, with or without an integrated circuit or electrical device, for facilitating communication between the sensor 10 and various types of monitors, including older or newer versions of the patient monitor 12 or other physiological monitors.
- the sensor 10 and the patient monitor 12 may communicate via wireless means, such as using radio, infrared, or optical signals.
- a transmission device (not shown) may be connected to the sensor 10 to facilitate wireless transmission between the sensor 10 and the patient monitor 12.
- the cable 14 (or corresponding wireless transmissions) are typically used to transmit control or timing signals from the monitor 12 to the sensor 10 and/or to transmit acquired data from the sensor 10 to the monitor 12.
- the cable 14 may be an optical fiber that allows optical signals to be conducted between the monitor 12 and the sensor 10.
- the patient monitor 12 may be a suitable pulse oximeter, such as those available from Nellcor Puritan Bennett Inc. In other embodiments, the patient monitor 12 may be a monitor suitable for measuring tissue water fractions, or other body fluid related metrics, using spectrophotometric or other techniques. Furthermore, the monitor 12 may be a multi-purpose monitor suitable for performing pulse oximetry and measurement of tissue water fraction, or other combinations of physiological and/or biochemical monitoring processes, using data acquired via the sensor 10. Furthermore, to upgrade conventional monitoring functions provided by the monitor 12 to provide additional functions, the patient monitor 12 may be coupled to a multi-parameter patient monitor 16 via a cable 18 connected to a sensor input port and/or via a cable 20 connected to a digital communication port.
- a multi-parameter patient monitor 16 via a cable 18 connected to a sensor input port and/or via a cable 20 connected to a digital communication port.
- the sensor 10, in the example depicted in Fig. 1, may be covered to provide a unitary or enclosed assembly. Such covering, however, is optional.
- the sensor 10, includes an emitter 22 and a detector 24 which may be of any suitable type.
- the emitter 22 may be one or more light emitting diodes adapted to transmit one or more wavelengths of light, such as in the red to infrared range
- the detector 24 may be a photodetector, such as a silicon photodiode package, selected to receive light in the range emitted from the emitter 22.
- the sensor 10 is coupled to a cable 14 that is responsible for transmitting electrical and/or optical signals to and from the emitter 22 and detector 24 of the sensor 10.
- the cable 14 may be permanently coupled to the sensor 10, or it may be removably coupled to the sensor 10 — the latter alternative being more useful and cost efficient in situations where the sensor 10 is disposable.
- Transmission type sensors include an emitter and detector that are typically placed on opposing sides of the sensor site. If the sensor site is a fingertip, for example, the sensor 10 is positioned over the patient's fingertip such that the emitter and detector lie on either side of the patient's nail bed. For example, the sensor 10 is positioned so that the emitter is located on the patient's fingernail and the detector is located opposite the emitter on the patient's finger pad.
- the emitter shines one or more wavelengths of light through the patient's fingertip, or other tissue, and the light received by the detector is processed to determine various physiological characteristics of the patient.
- the oxygen saturation of the patient's arterial blood may be determined using two or more wavelengths of light, most commonly red and near infrared wavelengths.
- a tissue water fraction (or other body fluid related metric) or a concentration of one or more biochemical components in an aqueous environment may be measured using two or more wavelengths of light, most commonly near infrared wavelengths between about 1,000 nm to about 2,500 nm.
- the term "light” may refer to one or more of infrared, visible, ultraviolet, or even X-ray electromagnetic radiation, and may also include any wavelength within the infrared, visible, ultraviolet, or X-ray spectra.
- Pulse oximetry and other spectrophotometric sensors are typically placed on a patient in a location conducive to measurement of the desired physiological parameters.
- pulse oximetry sensors are typically placed on a patient in a location that is normally perfused with arterial blood to facilitate measurement of the desired blood characteristics, such as arterial oxygen saturation measurement (SaO 2 ).
- SaO 2 arterial oxygen saturation measurement
- Common pulse oximetry sensor sites include a patient's fingertips, toes, forehead, or earlobes. Regardless of the placement of the sensor 10, the reliability of the pulse oximetry measurement is related to the accurate detection of transmitted light that has passed through the perfused tissue and has not been inappropriately supplemented by outside light sources or modulated by subdermal anatomic structures. Such inappropriate supplementation and/or modulation of the light transmitted by the sensor can cause variability in the resulting pulse oximetry measurements.
- a first configuration 28 of an exemplary frame 30 for a sensor 10 is depicted.
- a frame 30 may provide an internal structure that defines the general shape of the sensor 10 when covered, such as by overmolding, to form the patient sensor 10.
- the frame 30 may provide a general structure and range of motion for the patient sensor 10 while the covering may provide a surface area which contacts the patient and may protect the frame 30 and optical components of the patient sensor 10.
- different structures or regions of the frame 30 may have similar or different rigidities or other mechanical properties.
- the frame 30 may include various structural features such as a cable guide through which a cable, such as an electrical or optical cable, may pass to connect to the electrical or optical conductors attached to the emitter 22 and/or detector 24 upon assembly.
- the frame 30 may include component housings, such as the emitter housing 34 and detector housing 36.
- the frame 30 may include flexible components or elements 38, such as living hinges, pin hinges, bar links, bending beams, and so forth, which facilitate the motion of the emitter housing 34 and/or the detector housing 36 relative to one another.
- the frame 30 is constructed, in whole or in part, from polymeric materials, such as thermoplastics, capable of providing a suitable rigidity or semi-rigidity for the different portions of the frame 30.
- the frame 30 is constructed, in whole or in part, from other suitably rigid or semi-rigid materials that provide the desired support and flexibility, such as stainless steel, aluminum, magnesium, graphite, fiberglass, or other metals, alloys, or compositions that are sufficiently ductile and/or strong.
- suitable materials include polyurethane, polypropylene, and nylon, though other polymeric materials may also be suitable
- the frame 30 is constructed, in whole or in part, from other suitably rigid or semi-rigid materials that provide the desired support and flexibility, such as stainless steel, aluminum, magnesium, graphite, fiberglass, or other metals, alloys, or compositions that are sufficiently ductile and/or strong.
- metals, alloys, or compositions that are suitable for diecasting, sintering, lost wax casting, stamping and forming, and other metal or composition fabrication processes may be used to construct the frame 30.
- the frame 30 may be constructed as an integral structure or as a composite structure.
- the frame 30 may be constructed as a single piece from a single material or from different materials.
- the frame 30 may be constructed or assembled as a composite structure from two or more parts that are separately formed, hi such embodiments, the different parts may be formed from the same or different materials.
- each part may be constructed from a material having suitable mechanical and/or chemical properties for that part. The different parts may then be joined or fitted together to form the frame 30, such as by a snap fitting process, ultrasonic welding, heat staking or by application of an adhesive or mechanical fastener.
- the flexible elements 38 such as living hinges, pin hinges, bar links, bending beams, and so forth, may be constructed from the same materials and/or from different materials than the remainder of the frame 30. Furthermore, the flexible elements
- the frame 30 may be molded from polymeric materials as one piece, with the flexible elements 38 formed as living hinges molded from the polymeric material.
- the flexible elements 38 may be molded or formed as separate pieces that are attached to the remainder of the frame structure, hi such embodiments, the flexible elements 38 may be formed from the same or different materials and the remainder of the frame 30 and may serve to hold different portions of the frame structure together.
- the frame sides 42 may be formed from polymeric materials and may include annular structures along their edges that are complementary to the annular structures of an adjacent frame side 42.
- a pin such as a metal pin, may be fitted through the annular structures of two adjacent frame sides 42, thereby forming an attachment and a hinge upon which the attached frame sides 42 may be moved.
- a pin such as a metal pin
- the frame 30 may be molded, formed, or constructed in a different configuration than the final sensor configuration.
- the frame 30 for use in the sensor 10 may be initially formed, from one or more pieces, in a generally open, or flat, configuration compared to the relatively closed configuration of the frame 30 when folded to form the sensor 10.
- the frame 30 may be formed generally open or planar and then folded or bent, such as at the flexible regions 38, into the closed configuration associated with the sensor 10.
- a covering may be applied, such as by overmolding, prior to or subsequent to folding or bending the frame 30 from the open configuration to the closed configuration.
- the frame 30 may be secured together as described above, such as via a snap fitting process or via other techniques suitable for attaching the respective portions of the frame 30 including ultrasonic welding, heat staking or by application of an adhesive or mechanical fastener.
- a first configuration 28 of the frame 30 is provided, hi the first configuration 28, the flexible regions 38 are provided in pairs that are symmetric about a vertical place that coincides with the optical axis 44.
- the paired, symmetric flexible regions 38 allow lineal expansion and/or contraction along the optical axis 44, thereby maintaining optical alignment of the emitter 22 and detector 24 as the frame 30 expands or collapses to conformably fit a patient's digit, hi addition, the flexible regions 38 may allow lateral expansion (i.e., transverse to the optical axis) of the frame 30 to provide a laterally conforming fit to differently sized fingers and toes.
- lateral expansion i.e., transverse to the optical axis
- the first configuration 28 is depicted as collapsed along the optical axis 44, such as to accommodate a smaller finger or toe, while maintaining alignment of the emitter 22 and detector 24 along the optical axis 44.
- the frame 30 (such as the first configuration 28 of the frame 30) may be covered to form a unitary or integral sensor assembly or sensor body, as depicted in Fig. 5.
- Such covered embodiments may result in a sensor assembly in which the internal frame 30 is completely or substantially covered by a covering material 50.
- the covering process may be performed prior to or subsequent to bending the internal frame 30 into the closed configuration.
- the senor 10 may be formed by an injection molding process.
- the internal frame 30 may be positioned within a die or mold of the desired shape for the sensor 10.
- a molten or otherwise unset overmold material may then be injected into the die or mold.
- a molten thermoplastic elastomer at between about 400° F to about 450° F is injected into the mold.
- the coating material may then be set, such as by cooling for one or more minutes or by chemical treatment, to form the sensor body about the internal frame 30.
- other sensor components such as the emitter 22 and/or detector 24, may be attached or inserted into their respective housings or positions on the overmolded sensor body.
- the optical components such as emitter 22 and detector 24
- conductive structures such as wires or flex circuits
- the internal frame 30 and associated components may then be positioned within a die or mold and overmolded, as previously described.
- conventional techniques for protecting such components from excessive temperatures may be employed.
- the emitter 22 and/or the detector 24 may include an associated clear window, such as a plastic or crystal window, in contact with the mold to prevent coating 50 from being applied over the window
- the material in contact with such windows may be composed of a material, such as beryllium copper, which prevents the heat of the injection molding process from being conveyed through the window to the optical components.
- a beryllium copper material initially at about 40°F is contacted with the windows associated with the emitter 22 and/or detector 24 to prevent coating of the windows and heat transfer to the respective optical components.
- the injection molding process described herein is merely one technique by which the frame 30 may be covered to form a sensor body, with or without associated sensing components.
- Other techniques which may be employed include, but are not limited to, dipping the frame 30 into a molten or otherwise unset coating material to coat the frame 30 or spraying the frame 30 with a molten or otherwise unset coating material to coat the frame 30.
- the coating material may be subsequently set, such as by cooling or chemical means, to form the coating.
- Such alternative techniques to the extent that they may involve high temperatures, may include thermally protecting whatever optical components are present, such as by using beryllium copper or other suitable materials to prevent heat transfer through the windows associated with the optical components, as discussed above.
- the frame 30 may be covered by other techniques as well.
- the covering material 50 may be a sheet, a sleeve, or a film material which is applied to the frame.
- Such a covering material 50 may be bonded, such as with an adhesive material, or mechanically fastened to the frame 30.
- a suitable film material may be an extruded or laminated film that is adhesively or mechanically bonded to the frame 30.
- a suitable sheet material may be a single or multi-layer sheet material that is adhesively or mechanically bonded to the frame 30.
- Other exemplary covering material 50 include cast, foamed, or extruded materials suitable for attachment to the frame 30.
- the frame 30, as well as the optical components and associated circuitry where desired may be encased in a covering material 50 to form an integral or unitary assembly with no exposed or external moving parts of the internal frame 30.
- the sensor 10 includes features of the underlying internal frame 30 that are now completely or partially covered, such as the overmolded emitter housing 52 and detector housing 54.
- the covering material 50 is a thermoplastic elastomer or other conformable coating or material.
- the thermoplastic elastomer may include compositions such as thermoplastic polyolefins, thermoplastic vulcanizate alloys, silicone, thermoplastic polyurethane, and so forth.
- the overmolding composition may vary, depending on the varying degrees of conformability, durability, wettability, or other physical and/or chemical traits that are desired.
- the covering material 50 may be selected based upon the desirability of a chemical bond between the internal frame 30 and the covering material 50. Such a chemical bond may be desirable for durability of the resulting sensor 10.
- a covering material 50 may be selected such that the covering material 50 bonds with some or all of the internal frame 30. Li such embodiments, the covering material 50 and the portions of the internal frame 30 to which the covering material 50 is bonded are not separable, i.e., they form one continuous and generally inseparable structure.
- such a sensor 10 may be easily maintained, cleaned, and/or disinfected by immersing the sensor into a disinfectant or cleaning solution or by rinsing the sensor 10 off, such as under running water.
- a covered sensor assembly may be generally or substantially free of crevices, gaps, junctions or other surface irregularities typically associated with a multi-part construction which may normally allow the accumulation of biological detritus or residue. Such an absence of crevices and other irregularities may further facilitate the cleaning and care of the sensor 10.
- flexible regions 38 of the frame 30 incorporated into the sensor 10 provide vertical and/or lateral accommodation of a finger or other patient digit, and thereby providing a conforming fit.
- the lateral sides of the frame 30 (or the covering material 50 disposed over such lateral sides) facilitate the exclusion of environmental or ambient light from the interior of the sensor 10.
- the lateral sides of the sensor 10 therefore, help prevent or reduce the detection of light from the outside environment, which may be inappropriately detected by the sensor 10 as correlating to the SaO 2 .
- the pulse oximetry sensor may detect differences in signal modulations unrelated to the underlying SaO 2 level.
- a second frame configuration 58 is depicted.
- the exemplary second frame configuration 58 includes components noted above with regard to the first configuration 28, such as a symmetric pair of flexible regions 38, an emitter housing 34, and a detector housing 36, as well as a cable guide 60.
- the second configuration 58 of the frame 30 is provided as a semi-rigid, generally annular structure upon which the emitter housing 34 and detector housing 36 are disposed opposite one another.
- a symmetric pair of flexible regions 38 (as discussed with regard to Figs. 2-4) is disposed.
- the flexible regions 38 function as discussed above, allowing the emitter housing 34 (and associated emitter 22) and detector housing 36 (and associated detector 24) to move relative to one another along the optical axis 44. In this manner, alignment of optical components, such as an emitter 22 and detector 24 may be maintained while obtaining a conforming fit to a patient's digit.
- the second configuration of Fig. 6 is depicted with one pair of symmetrical flexible regions 38, one of ordinary skill in the art will appreciate that additional flexible regions 38 may be provided on the second configuration 58 of the frame 30 to maintain optical alignment of the emitter 22 and detector 24.
- the second configuration 58 of the frame 30 is depicted as expanded along the optical axis 44 between the emitter 22 and detector 24, such as to accommodate a large finger or toe needing greater vertical space.
- the paired, symmetric flexible regions 38 constrain the range of motion of the emitter 22 and detector 24 to linear motion along the optical axis 44, thereby maintaining the emitter 22 and detector 24 in alignment despite there motion relative to one another.
- the second configuration 58 is depicted as collapsed along the optical axis 44, such as to accommodate a smaller finger or toe, while maintaining alignment of the emitter 22 and detector 24 along the optical axis 44.
- the second configuration 58 of the frame 30 is depicted as covered in Fig. 9.
- the techniques and materials that may be used to cover the second configuration 58 of the frame 30 are the same or similar to those discussed above with regard to the covered first configuration 28 of frame 30 discussed in relation to Fig. 5.
- the covered structures and benefits are the same or similar to those discussed above with regard to the covered configuration of Fig. 5.
- a unitary sensor or sensor body may be constructed about the second configuration 58 of the frame 30 that provides a conforming fit while maintaining the optical alignment of the optical components.
- a third frame configuration 66 is depicted.
- the exemplary third frame configuration 66 includes components noted above with regard to the first and second configurations 28 and 58, such as symmetric pairs of flexible regions 38, an emitter housing 34, and a detector housing 36.
- the third configuration 66 of the frame 30 is provided as a hinged, loop structure upon which the emitter housing 34 and detector housing 36 are disposed opposite one another. Between the emitter housing 34 and detector housing 36, four symmetric pairs of flexible regions 38 is disposed.
- the flexible regions 38 function as discussed above, allowing the emitter housing 34 (and associated emitter 22) and detector housing 36 (and associated detector 24) to move relative to one another along the optical axis 44. In this manner, alignment of optical components, such as an emitter 22 and detector 24 may be maintained while obtaining a conforming fit to a patient's digit. While the third configuration of Fig. 10 is depicted with four pairs of symmetrical flexible regions 38, one of ordinary skill in the art will appreciate that less than or more than four flexible regions 38 may be provided on the third configuration 66 of the frame 30 to maintain optical alignment of the emitter 22 and detector 24.
- the third configuration 66 of the frame 30 is depicted as expanded along the optical axis 44 between the emitter 22 and detector 24, such as to accommodate a large finger or toe needing greater vertical space.
- the paired, symmetric flexible regions 38 constrain the range of motion of the emitter 22 and detector 24 to linear motion along the optical axis 44, thereby maintaining the emitter 22 and detector 24 in alignment despite there motion relative to one another.
- the third configuration 66 is depicted as collapsed along the optical axis 44, such as to accommodate a smaller finger or toe, while maintaining alignment of the emitter 22 and detector 24 along the optical axis 44.
- sensors and/or contacts applied externally to a patient may be advantageously applied using an covered sensor body as discussed herein.
- sensors or contacts may include glucose monitors or other sensors or contacts that are generally held adjacent to the skin of a patient such that a conformable and comfortable fit is desired.
- devices for measuring tissue water fraction or other body fluid related metrics may utilize a sensor as described herein.
- other spectrophotometric applications where a probe is attached to a patient may utilize a sensor as described herein.
- the frame 30 may also be used without such a covering.
- the frame 30 may itself form a sensor body, with optical components such as the emitter 22 and/or detector 24 being added to the frame 30 to form the sensor 10.
- an adhesive strip or bandage may help secure the sensor 10 to the patient.
- the present techniques may not only be applied to transmission type sensors for use in pulse oximetry, but also to retroflective and other sensor designs as well.
- the present techniques are not limited to use on fingers and toes but may also be applied to placement on other body parts such as in embodiments configured for use on the ears or nose.
Abstract
A physiological sensor is provided that includes an emitter and detector disposed on a frame such that the emitter and detector define an optical axis. The frame includes one or more pair of flexible elements disposed generally symmetric relative to the optical axis. In one embodiment, the emitter and detector remain aligned when moved relative to one another along the optical axis.
Description
OPTICALLY ALIGNED PULSE OXIMETRY SENSOR
BACKGROUND OF THE INVENTION
1. Field Of The Invention
The present invention relates generally to pulse oximetry and, more particularly, to sensors used for pulse oximetry.
2. Description Of The Related Art
This section is intended to introduce the reader to various aspects of art that may be related to various aspects of the present invention, which are described and/or claimed below. This discussion is believed to be helpful in providing the reader with background information to facilitate a better understanding of the various aspects of the present invention. Accordingly, it should be understood that these statements are to be read in this light, and not as admissions of prior art.
In the field of medicine, doctors often desire to monitor certain physiological characteristics of their patients. Accordingly, a wide variety of devices have been developed for monitoring physiological characteristics. Such devices provide doctors and other healthcare personnel with the information they need to provide the best possible healthcare for their patients. As a result, such monitoring devices have become an indispensable part of modern medicine.
One technique for monitoring certain physiological characteristics of a patient is commonly referred to as pulse oximetry, and the devices built based upon pulse oximetry techniques are commonly referred to as pulse oximeters. Pulse oximetry may be used to measure various blood flow characteristics, such as the blood-oxygen saturation of hemoglobin in arterial blood, the volume of individual blood pulsations supplying the tissue, and/or the rate of blood pulsations corresponding to each heartbeat of a patient.
Pulse oximeters typically utilize a non-invasive sensor that is placed on or against a patient's tissue that is well perfused with blood, such as a patient's finger, toe, or earlobe.
The pulse oximeter sensor emits light and photoelectrically senses the absorption and/or
scattering of the light after passage through the perfused tissue. The data collected by the sensor may then be used to calculate one or more of the above physiological characteristics based upon the absorption or scattering of title light. More specifically, the emitted light is typically selected to be of one or more wavelengths that are absorbed or scattered in an amount related to the presence of oxygenated versus de-oxygenated hemoglobin in the blood. The amount of light absorbed and/or scattered may then be used to estimate the amount of the oxygen in the tissue using various algorithms. hi many instances, it may be desirable to employ, for cost and/or convenience, a pulse oximeter sensor that is reusable. Such reusable sensors, however, should fit snugly enough that incidental patient motion will not dislodge or move the sensor yet not so tight that normal blood flow is disrupted, which may interfere with pulse oximetry measurements. Such a conforming fit may be difficult to achieve over a range of patient physiologies without adjustment or excessive attention on the part of medical personnel. In addition, for transmission-type pulse oximetry sensors (in which an emitter and detector are provided on opposite sides of the finger or toe) it may be difficult to maintain the desired alignment of optical components while obtaining a conforming fit. For example, it may be desirable to maintain the emitter and detector along a common axis, however, such alignment may be difficult to achieve or maintain while adjusting the sensor and its constituent components to fit a patient physiology.
SUMMARY
Certain aspects commensurate in scope with the originally claimed invention are set forth below. It should be understood that these aspects are presented merely to provide the reader with a brief summary of certain forms of the invention might take and that these aspects are not intended to limit the scope of the invention. Indeed, the invention may encompass a variety of aspects that may not be set forth below.
There is provided a sensor assembly that includes: a frame comprising one or more pair of flexible elements disposed substantially symmetric relative to an optical axis; at least two optical components disposed on the frame along the optical axis; and a covering provided over at least part of the frame and the at least two optical components.
There is provided a sensor assembly that includes: a frame; an emitter and a detector housed on the frame along an optical axis, wherein the emitter and the detector are configured to move relative to one another while remaining aligned along the optical axis; and a covering provided over the frame, the emitter, and the detector. There is provided a method of manufacturing a sensor that includes: situating an emitter and a detector on a frame, wherein the frame comprises one or more pair of flexible elements disposed substantially symmetric relative to an optical axis upon which the emitter and the detector are situated; and coating the frame with a coating material to form a sensor assembly. There is provided a method for acquiring physiological data that includes: emitting two or more wavelengths of light from an emitter of a sensor assembly disposed on a patient; detecting transmitted or reflected light using a photodetector of the sensor assembly, wherein the emitter and the photodetector are maintained in optical alignment with one another along an optical axis by one or more pair of flexible elements of the sensor assembly, wherein the one or more pair of flexible elements are disposed symmetrical to the optical axis; and determining a physiological parameter based on the detected light.
There is provided a method of manufacturing a sensor body that includes: coating a frame with a coating material to form a sensor body, wherein the frame comprises one or more pair of flexible elements disposed substantially symmetric relative to an optical axis defined by an emitter housing and a detector housing of the frame.
There is provided a sensor body, that includes: a frame comprising one or more pair of flexible elements disposed substantially symmetric relative to an optical axis defined by an emitter housing and a detector housing of the frame; and a covering provided over the frame. There is provided a sensor body, that includes: a frame comprising an emitter housing and a detector housing which define an optical axis, wherein the emitter housing and the detector housing are configured to move relative to one another while remaining aligned along the optical axis; and a covering provided over the frame to form a sensor assembly.
There is provided a frame of a sensor, that includes: at least two optical component housings defining an optical axis; and one or more pair of flexible elements disposed substantially symmetric relative to the optical axis.
There is provided a frame of a sensor, that includes: an emitter housing and a detector housing which define an optical axis, wherein the emitter housing and the detector housing are configured to move relative to one another while remaining aligned along optical axis.
There is provided a method for manufacturing a frame of a sensor, that includes: forming at least two optical component housings of a frame of a sensor such that the at least two optical component housings define an optical axis; and providing one or more pair of flexible elements on the frame disposed substantially symmetric relative to the optical axis.
BRIEF DESCRIPTION OF THE DRAWINGS
Advantages of the invention may become apparent upon reading the following detailed description and upon reference to the drawings in which:
Fig. 1 illustrates a physiological monitoring system coupled to a multi-parameter patient monitor and a patient sensor, in accordance with aspects of the present technique;
Fig. 2 illustrates a perspective view of one configuration of an internal frame for use in a patient sensor, in accordance with aspects of the present technique; Fig. 3 illustrates the internal frame of Fig. 2 in an expanded configuration;
Fig. 4 illustrates the internal frame of Fig. 2 in a collapsed configuration; Fig. 5 illustrates a perspective view of a covered patient sensor based upon the internal frame of Fig. 2;
Fig. 6 illustrates a perspective view of another configuration of an internal frame for use in a patient sensor, in accordance with aspects of the present technique;
Fig. 7 illustrates the internal frame of Fig. 6 in an expanded configuration; Fig. 8 illustrates the internal frame of Fig. 6 in a collapsed configuration; Fig. 9 illustrates a perspective view of a covered patient sensor based upon the internal frame of Fig. 6; Fig. 10 illustrates a perspective view of a further configuration of an internal frame for use in a patient sensor, in accordance with aspects of the present technique;
Fig. 11 illustrates the internal frame of Fig. 10 in an expanded configuration; Fig. 12 illustrates the internal frame of Fig. 10 in a collapsed configuration; and Fig. 13 illustrates a perspective view of a covered patient sensor based upon the internal frame of Fig. 10.
DETAILED DESCRIPTION OF SPECIFIC EMBODIMENTS
One or more specific embodiments of the present invention will be described below. In an effort to provide a concise description of these embodiments, not all features of an actual implementation are described in the specification. It should be appreciated that in the development of any such actual implementation, as in any engineering or design project, numerous implementation-specific decisions must be made to achieve the developers' specific goals, such as compliance with system-related and business-related constraints, which may vary from one implementation to another. Moreover, it should be appreciated that such a development effort might be complex and time consuming, but would nevertheless be a routine undertaking of design, fabrication, and manufacture for those of ordinary skill having the benefit of this disclosure.
It is desirable to provide a comfortable and conformable reusable patient sensor that is easily cleaned and that maintains alignment between optical components. In accordance with some aspects of the present technique, a reusable patient sensor is provided that includes a flexible frame, such as a framework incorporating living hinges, pin hinges, bar links, bending beams, and so forth, which allows the patient sensor to conform to fingers or toes of varying sizes while maintaining alignment of the optical components.
Prior to discussing such exemplary sensors in detail, it should be appreciated that such sensors are typically designed for use with a patient monitoring system. For example, referring now to Fig. 1, a sensor 10 according to the present invention may be used in conjunction with a patient monitor 12. In the depicted embodiment, a cable 14 connects the sensor 10 to the patient monitor 12. As will be appreciated by those of ordinary skill in the art, the sensor 10 and/or the cable 14 may include or incorporate one or more integrated circuit devices or electrical devices, such as a memory, processor chip, or resistor that may facilitate or enhance communication between the sensor 10 and the
patient monitor 12. Likewise the cable 14 may be an adaptor cable, with or without an integrated circuit or electrical device, for facilitating communication between the sensor 10 and various types of monitors, including older or newer versions of the patient monitor 12 or other physiological monitors. In other embodiments, the sensor 10 and the patient monitor 12 may communicate via wireless means, such as using radio, infrared, or optical signals. In such embodiments, a transmission device (not shown) may be connected to the sensor 10 to facilitate wireless transmission between the sensor 10 and the patient monitor 12. As will be appreciated by those of ordinary skill in the art, the cable 14 (or corresponding wireless transmissions) are typically used to transmit control or timing signals from the monitor 12 to the sensor 10 and/or to transmit acquired data from the sensor 10 to the monitor 12. In some embodiments, however, the cable 14 may be an optical fiber that allows optical signals to be conducted between the monitor 12 and the sensor 10.
In one embodiment, the patient monitor 12 may be a suitable pulse oximeter, such as those available from Nellcor Puritan Bennett Inc. In other embodiments, the patient monitor 12 may be a monitor suitable for measuring tissue water fractions, or other body fluid related metrics, using spectrophotometric or other techniques. Furthermore, the monitor 12 may be a multi-purpose monitor suitable for performing pulse oximetry and measurement of tissue water fraction, or other combinations of physiological and/or biochemical monitoring processes, using data acquired via the sensor 10. Furthermore, to upgrade conventional monitoring functions provided by the monitor 12 to provide additional functions, the patient monitor 12 may be coupled to a multi-parameter patient monitor 16 via a cable 18 connected to a sensor input port and/or via a cable 20 connected to a digital communication port. The sensor 10, in the example depicted in Fig. 1, may be covered to provide a unitary or enclosed assembly. Such covering, however, is optional. The sensor 10, includes an emitter 22 and a detector 24 which may be of any suitable type. For example, the emitter 22 may be one or more light emitting diodes adapted to transmit one or more wavelengths of light, such as in the red to infrared range, and the detector 24 may be a photodetector, such as a silicon photodiode package, selected to receive light in the range emitted from the emitter 22. In the depicted embodiment, the sensor 10 is coupled to a
cable 14 that is responsible for transmitting electrical and/or optical signals to and from the emitter 22 and detector 24 of the sensor 10. The cable 14 may be permanently coupled to the sensor 10, or it may be removably coupled to the sensor 10 — the latter alternative being more useful and cost efficient in situations where the sensor 10 is disposable.
The sensor 10 described above is generally configured for use as a "transmission type" sensor for use in spectrophotometric applications. As will be appreciated by those of ordinary skill in the art, however, such discussion is merely exemplary and is not intended to limit the scope of the present technique. Transmission type sensors include an emitter and detector that are typically placed on opposing sides of the sensor site. If the sensor site is a fingertip, for example, the sensor 10 is positioned over the patient's fingertip such that the emitter and detector lie on either side of the patient's nail bed. For example, the sensor 10 is positioned so that the emitter is located on the patient's fingernail and the detector is located opposite the emitter on the patient's finger pad. During operation, the emitter shines one or more wavelengths of light through the patient's fingertip, or other tissue, and the light received by the detector is processed to determine various physiological characteristics of the patient.
For pulse oximetry applications using transmission type sensors the oxygen saturation of the patient's arterial blood may be determined using two or more wavelengths of light, most commonly red and near infrared wavelengths. Similarly, in other applications a tissue water fraction (or other body fluid related metric) or a concentration of one or more biochemical components in an aqueous environment may be measured using two or more wavelengths of light, most commonly near infrared wavelengths between about 1,000 nm to about 2,500 nm. It should be understood that, as used herein, the term "light" may refer to one or more of infrared, visible, ultraviolet, or even X-ray electromagnetic radiation, and may also include any wavelength within the infrared, visible, ultraviolet, or X-ray spectra.
Pulse oximetry and other spectrophotometric sensors are typically placed on a patient in a location conducive to measurement of the desired physiological parameters. For example, pulse oximetry sensors are typically placed on a patient in a location that is normally perfused with arterial blood to facilitate measurement of the desired blood
characteristics, such as arterial oxygen saturation measurement (SaO2). Common pulse oximetry sensor sites include a patient's fingertips, toes, forehead, or earlobes. Regardless of the placement of the sensor 10, the reliability of the pulse oximetry measurement is related to the accurate detection of transmitted light that has passed through the perfused tissue and has not been inappropriately supplemented by outside light sources or modulated by subdermal anatomic structures. Such inappropriate supplementation and/or modulation of the light transmitted by the sensor can cause variability in the resulting pulse oximetry measurements.
Referring now to Figs. 2-13, the sensor 10 is discussed in greater detail. For example, in Figs. 2-4, a first configuration 28 of an exemplary frame 30 for a sensor 10 is depicted. Such a frame 30 may provide an internal structure that defines the general shape of the sensor 10 when covered, such as by overmolding, to form the patient sensor 10. hi such an embodiment, the frame 30 may provide a general structure and range of motion for the patient sensor 10 while the covering may provide a surface area which contacts the patient and may protect the frame 30 and optical components of the patient sensor 10. hi view of the various structural and motion functions performed by the frame 30, different structures or regions of the frame 30 may have similar or different rigidities or other mechanical properties.
The frame 30 may include various structural features such as a cable guide through which a cable, such as an electrical or optical cable, may pass to connect to the electrical or optical conductors attached to the emitter 22 and/or detector 24 upon assembly. Likewise, the frame 30 may include component housings, such as the emitter housing 34 and detector housing 36. hi addition, the frame 30 may include flexible components or elements 38, such as living hinges, pin hinges, bar links, bending beams, and so forth, which facilitate the motion of the emitter housing 34 and/or the detector housing 36 relative to one another. hi certain embodiments, the frame 30 is constructed, in whole or in part, from polymeric materials, such as thermoplastics, capable of providing a suitable rigidity or semi-rigidity for the different portions of the frame 30. Examples of such suitable materials include polyurethane, polypropylene, and nylon, though other polymeric materials may also be suitable, hi other embodiments, the frame 30 is constructed, in
whole or in part, from other suitably rigid or semi-rigid materials that provide the desired support and flexibility, such as stainless steel, aluminum, magnesium, graphite, fiberglass, or other metals, alloys, or compositions that are sufficiently ductile and/or strong. For example, metals, alloys, or compositions that are suitable for diecasting, sintering, lost wax casting, stamping and forming, and other metal or composition fabrication processes may be used to construct the frame 30.
In addition, the frame 30 may be constructed as an integral structure or as a composite structure. For example, in one embodiment, the frame 30 may be constructed as a single piece from a single material or from different materials. Alternatively, the frame 30 may be constructed or assembled as a composite structure from two or more parts that are separately formed, hi such embodiments, the different parts may be formed from the same or different materials. For example, in implementations where different parts are formed from different materials, each part may be constructed from a material having suitable mechanical and/or chemical properties for that part. The different parts may then be joined or fitted together to form the frame 30, such as by a snap fitting process, ultrasonic welding, heat staking or by application of an adhesive or mechanical fastener.
For example, the flexible elements 38, such as living hinges, pin hinges, bar links, bending beams, and so forth, may be constructed from the same materials and/or from different materials than the remainder of the frame 30. Furthermore, the flexible elements
38 may be formed integrally with the remainder of the frame 30. For example, in one embodiment, the frame 30 may be molded from polymeric materials as one piece, with the flexible elements 38 formed as living hinges molded from the polymeric material. Alternatively, some or all of the flexible elements 38 may be molded or formed as separate pieces that are attached to the remainder of the frame structure, hi such embodiments, the flexible elements 38 may be formed from the same or different materials and the remainder of the frame 30 and may serve to hold different portions of the frame structure together. For example, in an embodiment in which the flexible elements 38 are pin hinges, the frame sides 42 may be formed from polymeric materials and may include annular structures along their edges that are complementary to the annular structures of an adjacent frame side 42. In such an embodiment, a pin, such as a
metal pin, may be fitted through the annular structures of two adjacent frame sides 42, thereby forming an attachment and a hinge upon which the attached frame sides 42 may be moved. As will be appreciated by those of ordinary skill in the art, other suitable lunge and/or attachment techniques may also be applicable to construct the frame 30. Furthermore, the frame 30 may be molded, formed, or constructed in a different configuration than the final sensor configuration. For example, the frame 30 for use in the sensor 10 may be initially formed, from one or more pieces, in a generally open, or flat, configuration compared to the relatively closed configuration of the frame 30 when folded to form the sensor 10. In such embodiments, the frame 30 may be formed generally open or planar and then folded or bent, such as at the flexible regions 38, into the closed configuration associated with the sensor 10. A covering may be applied, such as by overmolding, prior to or subsequent to folding or bending the frame 30 from the open configuration to the closed configuration. In such an embodiment, the frame 30 may be secured together as described above, such as via a snap fitting process or via other techniques suitable for attaching the respective portions of the frame 30 including ultrasonic welding, heat staking or by application of an adhesive or mechanical fastener. hi the example depicted in Figs. 2-4, a first configuration 28 of the frame 30 is provided, hi the first configuration 28, the flexible regions 38 are provided in pairs that are symmetric about a vertical place that coincides with the optical axis 44. The paired, symmetric flexible regions 38 allow lineal expansion and/or contraction along the optical axis 44, thereby maintaining optical alignment of the emitter 22 and detector 24 as the frame 30 expands or collapses to conformably fit a patient's digit, hi addition, the flexible regions 38 may allow lateral expansion (i.e., transverse to the optical axis) of the frame 30 to provide a laterally conforming fit to differently sized fingers and toes. For example, referring now to Fig. 3, the first configuration 28 of Fig. 2 is depicted as expanded along the optical axis 44 between the emitter 22 and detector 24, such as to accommodate a large finger or toe needing greater vertical space. The paired, symmetric flexible regions 38 constrain the range of motion of the emitter 22 and detector 24 to linear motion along the optical axis 44, thereby maintaining the emitter 22 and detector 24 in alignment despite there motion relative to one another. Similarly, referring now to Fig. 4, the first configuration 28 is depicted as collapsed along the optical axis 44,
such as to accommodate a smaller finger or toe, while maintaining alignment of the emitter 22 and detector 24 along the optical axis 44.
As noted above, in certain embodiments of the present technique, the frame 30 (such as the first configuration 28 of the frame 30) may be covered to form a unitary or integral sensor assembly or sensor body, as depicted in Fig. 5. Such covered embodiments may result in a sensor assembly in which the internal frame 30 is completely or substantially covered by a covering material 50. hi embodiments in which the internal frame 30 is formed or molded as a relatively open or flat structure, the covering process may be performed prior to or subsequent to bending the internal frame 30 into the closed configuration.
For example, the sensor 10 may be formed by an injection molding process. In one example of such a process the internal frame 30 may be positioned within a die or mold of the desired shape for the sensor 10. A molten or otherwise unset overmold material may then be injected into the die or mold. For example, in one implementation, a molten thermoplastic elastomer at between about 400° F to about 450° F is injected into the mold. The coating material may then be set, such as by cooling for one or more minutes or by chemical treatment, to form the sensor body about the internal frame 30. hi certain embodiments, other sensor components, such as the emitter 22 and/or detector 24, may be attached or inserted into their respective housings or positions on the overmolded sensor body.
Alternatively, the optical components (such as emitter 22 and detector 24) and/ or conductive structures (such as wires or flex circuits) may be placed on the internal frame 30 prior to overmolding. The internal frame 30 and associated components may then be positioned within a die or mold and overmolded, as previously described. To protect the emitter 22, detector 24, and or other electrical components, conventional techniques for protecting such components from excessive temperatures may be employed. For example, the emitter 22 and/or the detector 24 may include an associated clear window, such as a plastic or crystal window, in contact with the mold to prevent coating 50 from being applied over the window, hi one embodiment, the material in contact with such windows may be composed of a material, such as beryllium copper, which prevents the heat of the injection molding process from being conveyed through the window to the
optical components. For example, in one embodiment, a beryllium copper material initially at about 40°F is contacted with the windows associated with the emitter 22 and/or detector 24 to prevent coating of the windows and heat transfer to the respective optical components. As will be appreciated by those of ordinary skill in the art, the injection molding process described herein is merely one technique by which the frame 30 may be covered to form a sensor body, with or without associated sensing components. Other techniques which may be employed include, but are not limited to, dipping the frame 30 into a molten or otherwise unset coating material to coat the frame 30 or spraying the frame 30 with a molten or otherwise unset coating material to coat the frame 30. In such implementations, the coating material may be subsequently set, such as by cooling or chemical means, to form the coating. Such alternative techniques, to the extent that they may involve high temperatures, may include thermally protecting whatever optical components are present, such as by using beryllium copper or other suitable materials to prevent heat transfer through the windows associated with the optical components, as discussed above.
The frame 30 may be covered by other techniques as well. For example, the covering material 50 may be a sheet, a sleeve, or a film material which is applied to the frame. Such a covering material 50 may be bonded, such as with an adhesive material, or mechanically fastened to the frame 30. For instance, a suitable film material may be an extruded or laminated film that is adhesively or mechanically bonded to the frame 30. Likewise, a suitable sheet material may be a single or multi-layer sheet material that is adhesively or mechanically bonded to the frame 30. Other exemplary covering material 50 include cast, foamed, or extruded materials suitable for attachment to the frame 30. By such techniques, the frame 30, as well as the optical components and associated circuitry where desired, may be encased in a covering material 50 to form an integral or unitary assembly with no exposed or external moving parts of the internal frame 30. For example, as depicted in Fig. 5, the sensor 10 includes features of the underlying internal frame 30 that are now completely or partially covered, such as the overmolded emitter housing 52 and detector housing 54.
In one implementation, the covering material 50 is a thermoplastic elastomer or other conformable coating or material. In such embodiments, the thermoplastic elastomer may include compositions such as thermoplastic polyolefins, thermoplastic vulcanizate alloys, silicone, thermoplastic polyurethane, and so forth. As will be appreciated by those of ordinary skill in the art, the overmolding composition may vary, depending on the varying degrees of conformability, durability, wettability, or other physical and/or chemical traits that are desired.
Furthermore, the covering material 50 may be selected based upon the desirability of a chemical bond between the internal frame 30 and the covering material 50. Such a chemical bond may be desirable for durability of the resulting sensor 10. For example, to prevent separation of the covering material 50 from the internal frame 30, a covering material 50 may be selected such that the covering material 50 bonds with some or all of the internal frame 30. Li such embodiments, the covering material 50 and the portions of the internal frame 30 to which the covering material 50 is bonded are not separable, i.e., they form one continuous and generally inseparable structure.
Furthermore, in embodiments in which the covering material 50 employed is liquid or fluid tight, such a sensor 10 may be easily maintained, cleaned, and/or disinfected by immersing the sensor into a disinfectant or cleaning solution or by rinsing the sensor 10 off, such as under running water. In particular, such an covered sensor assembly may be generally or substantially free of crevices, gaps, junctions or other surface irregularities typically associated with a multi-part construction which may normally allow the accumulation of biological detritus or residue. Such an absence of crevices and other irregularities may further facilitate the cleaning and care of the sensor 10. In the depicted example, flexible regions 38 of the frame 30 incorporated into the sensor 10 (in either coated or uncoated embodiments) provide vertical and/or lateral accommodation of a finger or other patient digit, and thereby providing a conforming fit. Furthermore, in the depicted embodiment, the lateral sides of the frame 30 (or the covering material 50 disposed over such lateral sides) facilitate the exclusion of environmental or ambient light from the interior of the sensor 10. The lateral sides of the sensor 10, therefore, help prevent or reduce the detection of light from the outside
environment, which may be inappropriately detected by the sensor 10 as correlating to the SaO2. Thus, the pulse oximetry sensor may detect differences in signal modulations unrelated to the underlying SaO2 level. In turn, this may impact the detected red-to- infrared modulation ratio and, consequently, the measured blood oxygen saturation (SpO2) value. The conformability of the fit of sensor 10 and the presence of the lateral sides on the sensor 10, therefore, may help prevent or reduce such errors.
While the frame 30 in the first configuration 28 may be used to form a covered or uncovered sensor 10, other frame configurations may also be used in accordance with the present technique. For example, referring now to Figs. 6-8, a second frame configuration 58 is depicted. The exemplary second frame configuration 58 includes components noted above with regard to the first configuration 28, such as a symmetric pair of flexible regions 38, an emitter housing 34, and a detector housing 36, as well as a cable guide 60. hi the embodiment depicted in Figs 6-8, the second configuration 58 of the frame 30 is provided as a semi-rigid, generally annular structure upon which the emitter housing 34 and detector housing 36 are disposed opposite one another. Between the emitter housing 34 and detector housing 36, a symmetric pair of flexible regions 38 (as discussed with regard to Figs. 2-4) is disposed. The flexible regions 38 function as discussed above, allowing the emitter housing 34 (and associated emitter 22) and detector housing 36 (and associated detector 24) to move relative to one another along the optical axis 44. In this manner, alignment of optical components, such as an emitter 22 and detector 24 may be maintained while obtaining a conforming fit to a patient's digit. While the second configuration of Fig. 6 is depicted with one pair of symmetrical flexible regions 38, one of ordinary skill in the art will appreciate that additional flexible regions 38 may be provided on the second configuration 58 of the frame 30 to maintain optical alignment of the emitter 22 and detector 24.
Referring now to Fig. 7, the second configuration 58 of the frame 30 is depicted as expanded along the optical axis 44 between the emitter 22 and detector 24, such as to accommodate a large finger or toe needing greater vertical space. The paired, symmetric flexible regions 38 constrain the range of motion of the emitter 22 and detector 24 to linear motion along the optical axis 44, thereby maintaining the emitter 22 and detector 24 in alignment despite there motion relative to one another. Similarly, in Fig. 8, the second
configuration 58 is depicted as collapsed along the optical axis 44, such as to accommodate a smaller finger or toe, while maintaining alignment of the emitter 22 and detector 24 along the optical axis 44.
The second configuration 58 of the frame 30 is depicted as covered in Fig. 9. The techniques and materials that may be used to cover the second configuration 58 of the frame 30 are the same or similar to those discussed above with regard to the covered first configuration 28 of frame 30 discussed in relation to Fig. 5. Likewise the covered structures and benefits are the same or similar to those discussed above with regard to the covered configuration of Fig. 5. In this manner, a unitary sensor or sensor body may be constructed about the second configuration 58 of the frame 30 that provides a conforming fit while maintaining the optical alignment of the optical components.
Other frame configurations incorporating aspects of the present technique are also possible. For example, referring now to Figs. 10-12, a third frame configuration 66 is depicted. The exemplary third frame configuration 66 includes components noted above with regard to the first and second configurations 28 and 58, such as symmetric pairs of flexible regions 38, an emitter housing 34, and a detector housing 36. hi the embodiment depicted in Figs 10-12, the third configuration 66 of the frame 30 is provided as a hinged, loop structure upon which the emitter housing 34 and detector housing 36 are disposed opposite one another. Between the emitter housing 34 and detector housing 36, four symmetric pairs of flexible regions 38 is disposed. The flexible regions 38 function as discussed above, allowing the emitter housing 34 (and associated emitter 22) and detector housing 36 (and associated detector 24) to move relative to one another along the optical axis 44. In this manner, alignment of optical components, such as an emitter 22 and detector 24 may be maintained while obtaining a conforming fit to a patient's digit. While the third configuration of Fig. 10 is depicted with four pairs of symmetrical flexible regions 38, one of ordinary skill in the art will appreciate that less than or more than four flexible regions 38 may be provided on the third configuration 66 of the frame 30 to maintain optical alignment of the emitter 22 and detector 24.
Referring now to Fig. 11, the third configuration 66 of the frame 30 is depicted as expanded along the optical axis 44 between the emitter 22 and detector 24, such as to accommodate a large finger or toe needing greater vertical space. The paired, symmetric
flexible regions 38 constrain the range of motion of the emitter 22 and detector 24 to linear motion along the optical axis 44, thereby maintaining the emitter 22 and detector 24 in alignment despite there motion relative to one another. Similarly, in Fig. 12, the third configuration 66 is depicted as collapsed along the optical axis 44, such as to accommodate a smaller finger or toe, while maintaining alignment of the emitter 22 and detector 24 along the optical axis 44.
The third configuration 66 of the frame 30 is depicted as covered in Fig. 13. The techniques and materials that may be used to cover the third configuration 66 of the frame 30 are similar to those discussed above with regard to the covered first configuration 28 of frame 30 discussed in relation to Fig. 5. Likewise the covered structures and benefits are the same or similar to those discussed above with regard to the covered configuration of Fig. 5. In this manner, a unitary sensor or sensor body may be constructed about the third configuration 66 of the frame 30 that provides a conforming fit while maintaining the optical alignment of the optical components. While the exemplary medical sensors 10 discussed herein are provided as examples, other such devices are also contemplated and fall within the scope of the present disclosure. For example, other medical sensors and/or contacts applied externally to a patient may be advantageously applied using an covered sensor body as discussed herein. Examples of such sensors or contacts may include glucose monitors or other sensors or contacts that are generally held adjacent to the skin of a patient such that a conformable and comfortable fit is desired. Similarly, and as noted above, devices for measuring tissue water fraction or other body fluid related metrics may utilize a sensor as described herein. Likewise, other spectrophotometric applications where a probe is attached to a patient may utilize a sensor as described herein. Furthermore, though the preceding discussion notes the possibility of covering the frame 30 with an overmold material to construct the sensor 10 or the sensor body, one of ordinary skill in the art will appreciate that the frame 30 may also be used without such a covering. For example, the frame 30 may itself form a sensor body, with optical components such as the emitter 22 and/or detector 24 being added to the frame 30 to form the sensor 10. In such an embodiment, an adhesive strip or bandage may help secure the sensor 10 to the patient.
While the invention may be susceptible to various modifications and alternative forms, specific embodiments have been shown by way of example in the drawings and have been described in detail herein. However, it should be understood that the invention is not intended to be limited to the particular forms disclosed. Rather, the invention is to cover all modifications, equivalents, and alternatives falling within the spirit and scope of the invention as defined by the following appended claims. Indeed, the present techniques may not only be applied to transmission type sensors for use in pulse oximetry, but also to retroflective and other sensor designs as well. Likewise, the present techniques are not limited to use on fingers and toes but may also be applied to placement on other body parts such as in embodiments configured for use on the ears or nose.
Claims
1. A sensor assembly, comprising: a frame comprising one or more pair of flexible elements disposed substantially symmetric relative to an optical axis; at least two optical components disposed on the frame along the optical axis; and a covering provided over at least part of the frame and the at least two optical components.
2. The sensor assembly of claim 1, wherein the frame comprises two or more parts joined to foπn the frame.
3. The sensor assembly of claim 1 , wherein the covering comprises a thermoplastic elastomer.
4. The sensor assembly of claim 3, wherein the thermoplastic elastomer comprises at least one of a thermoplastic polyolefm, a thermoplastic vulcanizate alloy, thermoplastic polyurethane, silicone, or a combination thereof.
5. The sensor assembly of claim 1 , wherein the covering comprises a flexible sheet, a sleeve or a film material.
6. The sensor assembly of claim 1 , wherein the covering is bonded to the frame.
7. The sensor assembly of claim 1 , wherein the covering is mechanically fastened to the frame.
8. The sensor assembly of claim 1, wherein the covering comprises a cast, foamed, or extruded material.
9. The sensor assembly of claim 1 , wherein no moving parts of the frame remain exposed from the covering.
10. The sensor assembly of claim 1 , comprising at least one integrated circuit device.
11. The sensor assembly of claim 1 , wherein the one or more pair of flexible elements comprise one or more pair of living hinges, pin hinges, bar links, or bending beams.
12. A sensor assembly, comprising: a frame; an emitter and a detector housed on the frame along an optical axis, wherein the emitter and the detector are configured to move relative to one another while remaining aligned along the optical axis; and a covering provided over the frame, the emitter, and the detector.
13. A method of manufacturing a sensor, comprising: situating an emitter and a detector on a frame, wherein the frame comprises one or more pair of flexible elements disposed substantially symmetric relative to an optical axis upon which the emitter and the detector are situated; and coating the frame with a coating material to form a sensor assembly.
14. A method for acquiring physiological data, comprising: emitting two or more wavelengths of light from an emitter of a sensor assembly disposed on a patient; detecting transmitted or reflected light using a photodetector of the sensor assembly, wherein the emitter and the photodetector are maintained in optical alignment with one another along an optical axis by one or more pair of flexible elements of the sensor assembly, wherein the one or more pair of flexible elements are disposed symmetrical to the optical axis; and determining a physiological parameter based on the detected light.
15. A method of manufacturing a sensor body, comprising: coating a frame with a coating material to form a sensor body, wherein the frame comprises one or more pair of flexible elements disposed substantially symmetric relative to an optical axis defined by an emitter housing and a detector housing of the frame.
16. A sensor body, comprising: a frame comprising one or more pair of flexible elements disposed substantially symmetric relative to an optical axis defined by an emitter housing and a detector housing of the frame; and a covering provided over the frame.
17. A sensor body, comprising: a frame comprising an emitter housing and a detector housing which define an optical axis, wherein the emitter housing and the detector housing are configured to move relative to one another while remaining aligned along the optical axis; and a covering provided over the frame to form a sensor assembly.
18. A frame of a sensor, comprising: at least two optical component housings defining an optical axis; and one or more pair of flexible elements disposed substantially symmetric relative to the optical axis.
19. A frame of a sensor, comprising: an emitter housing and a detector housing which define an optical axis, wherein the emitter housing and the detector housing are configured to move relative to one another while remaining aligned along optical axis.
20. A method for manufacturing a frame of a sensor, comprising: forming at least two optical component housings of a frame of a sensor such that the at least two optical component housings define an optical axis; and providing one or more pair of flexible elements on the frame disposed substantially symmetric relative to the optical axis.
Priority Applications (2)
Application Number | Priority Date | Filing Date | Title |
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AT06815831T ATE542475T1 (en) | 2005-09-30 | 2006-09-29 | OPTICALLY ALIGNED PULSE OXIMETRY SENSOR |
EP06815831A EP1945099B8 (en) | 2005-09-30 | 2006-09-29 | Optically aligned pulse oximetry sensor |
Applications Claiming Priority (2)
Application Number | Priority Date | Filing Date | Title |
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US11/241,031 US7486979B2 (en) | 2005-09-30 | 2005-09-30 | Optically aligned pulse oximetry sensor and technique for using the same |
US11/241,031 | 2005-09-30 |
Publications (1)
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Cited By (2)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US8692992B2 (en) | 2011-09-22 | 2014-04-08 | Covidien Lp | Faraday shield integrated into sensor bandage |
US8726496B2 (en) | 2011-09-22 | 2014-05-20 | Covidien Lp | Technique for remanufacturing a medical sensor |
Families Citing this family (49)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US7881762B2 (en) | 2005-09-30 | 2011-02-01 | Nellcor Puritan Bennett Llc | Clip-style medical sensor and technique for using the same |
US7486979B2 (en) | 2005-09-30 | 2009-02-03 | Nellcor Puritan Bennett Llc | Optically aligned pulse oximetry sensor and technique for using the same |
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US8690864B2 (en) * | 2007-03-09 | 2014-04-08 | Covidien Lp | System and method for controlling tissue treatment |
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US11607152B2 (en) * | 2007-06-12 | 2023-03-21 | Sotera Wireless, Inc. | Optical sensors for use in vital sign monitoring |
WO2009079461A1 (en) | 2007-12-14 | 2009-06-25 | Nellcor Puritan Bennett Llc | Medical sensor and technique for using the same |
US8897850B2 (en) | 2007-12-31 | 2014-11-25 | Covidien Lp | Sensor with integrated living hinge and spring |
US8199007B2 (en) | 2007-12-31 | 2012-06-12 | Nellcor Puritan Bennett Llc | Flex circuit snap track for a biometric sensor |
US20110098583A1 (en) * | 2009-09-15 | 2011-04-28 | Texas Instruments Incorporated | Heart monitors and processes with accelerometer motion artifact cancellation, and other electronic systems |
US8257274B2 (en) | 2008-09-25 | 2012-09-04 | Nellcor Puritan Bennett Llc | Medical sensor and technique for using the same |
US8417309B2 (en) | 2008-09-30 | 2013-04-09 | Covidien Lp | Medical sensor |
US20100182126A1 (en) * | 2008-12-18 | 2010-07-22 | Martis Dinesh J | Biometric sensing apparatus and methods incorporating the same |
US8515515B2 (en) | 2009-03-25 | 2013-08-20 | Covidien Lp | Medical sensor with compressible light barrier and technique for using the same |
US20110060224A1 (en) * | 2009-08-09 | 2011-03-10 | Tz Medical, Inc. | Non-invasive continuous doppler monitoring device for arterial blood flow to distal body parts |
TWI434673B (en) | 2009-11-16 | 2014-04-21 | Ind Tech Res Inst | Physiology signal sensing module |
EP2327358B1 (en) * | 2009-11-26 | 2017-01-11 | General Electric Company | Sensor holder for medical sensor |
US8798703B2 (en) * | 2010-09-07 | 2014-08-05 | Cnsystems Medizintechnik Ag | Disposable and detachable sensor for continuous non-invasive arterial blood pressure monitoring |
US8798702B2 (en) | 2011-03-31 | 2014-08-05 | Covidien Lp | Multiplexed photodetector array for optical medical sensors |
US9161722B2 (en) | 2011-09-07 | 2015-10-20 | Covidien Lp | Technique for remanufacturing a medical sensor |
US9220436B2 (en) * | 2011-09-26 | 2015-12-29 | Covidien Lp | Technique for remanufacturing a BIS sensor |
US8852095B2 (en) | 2011-10-27 | 2014-10-07 | Covidien Lp | Headband for use with medical sensor |
US9138181B2 (en) | 2011-12-16 | 2015-09-22 | Covidien Lp | Medical sensor for use with headband |
US20130294969A1 (en) | 2012-05-02 | 2013-11-07 | Nellcor Puritan Bennett Llc | Wireless, Reusable, Rechargeable Medical Sensors and System for Recharging and Disinfecting the Same |
US10881310B2 (en) | 2012-08-25 | 2021-01-05 | The Board Of Trustees Of The Leland Stanford Junior University | Motion artifact mitigation methods and devices for pulse photoplethysmography |
US10265013B2 (en) | 2013-09-06 | 2019-04-23 | Somnology, Inc. | System and method for sleep disorder diagnosis and treatment |
US10265014B2 (en) | 2013-09-06 | 2019-04-23 | Somnology, Inc. | System and method for sleep disorder diagnosis and treatment |
US9515417B2 (en) | 2014-01-14 | 2016-12-06 | Covidien Lp | Sensor interconnect for medical monitoring devices |
USD736711S1 (en) | 2014-04-24 | 2015-08-18 | Covidien Lp | Sensor connector |
USD735141S1 (en) | 2014-04-24 | 2015-07-28 | Covidien Lp | Sensor connector |
US9614337B2 (en) | 2014-06-19 | 2017-04-04 | Covidien Lp | Multiple orientation connectors for medical monitoring systems |
USD794567S1 (en) | 2014-12-18 | 2017-08-15 | Covidien Lp | Sensor cable and connector |
USD756817S1 (en) | 2015-01-06 | 2016-05-24 | Covidien Lp | Module connectable to a sensor |
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USD779433S1 (en) | 2015-09-17 | 2017-02-21 | Covidien Lp | Sensor connector cable |
USD784931S1 (en) | 2015-09-17 | 2017-04-25 | Covidien Lp | Sensor connector cable |
USD779432S1 (en) | 2015-09-17 | 2017-02-21 | Covidien Lp | Sensor and connector |
USD790069S1 (en) | 2015-11-02 | 2017-06-20 | Covidien Lp | Medical sensor |
TWI711429B (en) * | 2016-05-09 | 2020-12-01 | 香港商倍靈科技有限公司 | Wearable device for healthcare and method thereof |
WO2018007593A1 (en) * | 2016-07-08 | 2018-01-11 | Koninklijke Philips N.V. | Device and method for measuring a physiological parameter of a human limb |
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US11331019B2 (en) | 2017-08-07 | 2022-05-17 | The Research Foundation For The State University Of New York | Nanoparticle sensor having a nanofibrous membrane scaffold |
USD862709S1 (en) | 2017-09-20 | 2019-10-08 | Covidien Lp | Medical sensor |
CN107647871A (en) * | 2017-10-24 | 2018-02-02 | 成都亨通兆业精密机械有限公司 | It is a kind of to be easy to the equipment that human body physiological parameter is monitored during to plant area's Case treatment |
Citations (1)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US6654621B2 (en) * | 2001-08-29 | 2003-11-25 | Bci, Inc. | Finger oximeter with finger grip suspension system |
Family Cites Families (755)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US3403555A (en) | 1966-07-18 | 1968-10-01 | Versaci | Flowmeter |
BE661207A (en) | 1968-05-13 | 1965-07-16 | ||
US3721813A (en) | 1971-02-01 | 1973-03-20 | Perkin Elmer Corp | Analytical instrument system |
US4098772A (en) * | 1976-03-11 | 1978-07-04 | The Upjohn Company | Thermoplastic polyurethanes prepared with small amounts of monohydric alcohols |
USD250275S (en) | 1976-07-19 | 1978-11-14 | Hewlett-Packard Company | Self-attaching probe for use in photoelectric monitoring of body extremities |
USD251387S (en) | 1977-02-07 | 1979-03-20 | Component Manufacturing Service, Inc. | Electrical connector for electrocardiogram monitoring |
US4281645A (en) | 1977-06-28 | 1981-08-04 | Duke University, Inc. | Method and apparatus for monitoring metabolism in body organs |
USD262488S (en) | 1979-10-24 | 1981-12-29 | Novatec, Inc. | Pulse rate monitor |
US4353372A (en) | 1980-02-11 | 1982-10-12 | Bunker Ramo Corporation | Medical cable set and electrode therefor |
US4334544A (en) | 1980-04-28 | 1982-06-15 | Amf Incorporated | Ear lobe clip with heart beat sensor |
US4350165A (en) | 1980-05-23 | 1982-09-21 | Trw Inc. | Medical electrode assembly |
NL8005145A (en) | 1980-09-12 | 1982-04-01 | Tno | DEVICE FOR INDIRECT, NON-INVASIVE, CONTINUOUS MEASUREMENT OF BLOOD PRESSURE. |
GB8416219D0 (en) | 1984-06-26 | 1984-08-01 | Antec Systems | Patient monitoring apparatus |
JPS58143243A (en) | 1982-02-19 | 1983-08-25 | Minolta Camera Co Ltd | Measuring apparatus for coloring matter in blood without taking out blood |
US4770179A (en) | 1982-09-02 | 1988-09-13 | Nellcor Incorporated | Calibrated optical oximeter probe |
US4700708A (en) | 1982-09-02 | 1987-10-20 | Nellcor Incorporated | Calibrated optical oximeter probe |
US4621643A (en) | 1982-09-02 | 1986-11-11 | Nellcor Incorporated | Calibrated optical oximeter probe |
US4653498A (en) | 1982-09-13 | 1987-03-31 | Nellcor Incorporated | Pulse oximeter monitor |
EP0127947B1 (en) | 1983-05-11 | 1990-08-29 | Nellcor Incorporated | Sensor having cutaneous conformance |
US4830014A (en) | 1983-05-11 | 1989-05-16 | Nellcor Incorporated | Sensor having cutaneous conformance |
US5109849A (en) | 1983-08-30 | 1992-05-05 | Nellcor, Inc. | Perinatal pulse oximetry sensor |
US4938218A (en) | 1983-08-30 | 1990-07-03 | Nellcor Incorporated | Perinatal pulse oximetry sensor |
US5140989A (en) | 1983-10-14 | 1992-08-25 | Somanetics Corporation | Examination instrument for optical-response diagnostic apparatus |
US5217013A (en) | 1983-10-14 | 1993-06-08 | Somanetics Corporation | Patient sensor for optical cerebral oximeter and the like |
US4603700A (en) | 1983-12-09 | 1986-08-05 | The Boc Group, Inc. | Probe monitoring system for oximeter |
DE3405444A1 (en) | 1984-02-15 | 1985-08-22 | Kraus, Werner, Dipl.-Ing., 8000 München | Pulse sensor |
US4714341A (en) | 1984-02-23 | 1987-12-22 | Minolta Camera Kabushiki Kaisha | Multi-wavelength oximeter having a means for disregarding a poor signal |
US4510551A (en) | 1984-05-21 | 1985-04-09 | Endeco Canada Limited | Portable memory module |
US4677528A (en) | 1984-05-31 | 1987-06-30 | Motorola, Inc. | Flexible printed circuit board having integrated circuit die or the like affixed thereto |
IT1206462B (en) | 1984-08-07 | 1989-04-27 | Anic Spa | MULTI-WAVE LENGTH PULSED LIGHT PHOTOMETER FOR NON-INVASIVE MONITORING. |
US4911167A (en) | 1985-06-07 | 1990-03-27 | Nellcor Incorporated | Method and apparatus for detecting optical pulses |
US4802486A (en) | 1985-04-01 | 1989-02-07 | Nellcor Incorporated | Method and apparatus for detecting optical pulses |
US4934372A (en) | 1985-04-01 | 1990-06-19 | Nellcor Incorporated | Method and apparatus for detecting optical pulses |
US4928692A (en) | 1985-04-01 | 1990-05-29 | Goodman David E | Method and apparatus for detecting optical pulses |
DE3516338A1 (en) | 1985-05-07 | 1986-11-13 | Drägerwerk AG, 2400 Lübeck | Mounting for a measurement sensor |
CA1278044C (en) | 1985-06-06 | 1990-12-18 | The Boc Group, Inc. | Hinged finger stall with light emitter and detector |
US4685464A (en) | 1985-07-05 | 1987-08-11 | Nellcor Incorporated | Durable sensor for detecting optical pulses |
US4890619A (en) | 1986-04-15 | 1990-01-02 | Hatschek Rudolf A | System for the measurement of the content of a gas in blood, in particular the oxygen saturation of blood |
JPS6323645A (en) | 1986-05-27 | 1988-01-30 | 住友電気工業株式会社 | Reflection heating type oxymeter |
US4759369A (en) | 1986-07-07 | 1988-07-26 | Novametrix Medical Systems, Inc. | Pulse oximeter |
US4800495A (en) | 1986-08-18 | 1989-01-24 | Physio-Control Corporation | Method and apparatus for processing signals used in oximetry |
US4869253A (en) | 1986-08-18 | 1989-09-26 | Physio-Control Corporation | Method and apparatus for indicating perfusion and oxygen saturation trends in oximetry |
US4913150A (en) | 1986-08-18 | 1990-04-03 | Physio-Control Corporation | Method and apparatus for the automatic calibration of signals employed in oximetry |
US5259381A (en) | 1986-08-18 | 1993-11-09 | Physio-Control Corporation | Apparatus for the automatic calibration of signals employed in oximetry |
US4859056A (en) | 1986-08-18 | 1989-08-22 | Physio-Control Corporation | Multiple-pulse method and apparatus for use in oximetry |
US4892101A (en) | 1986-08-18 | 1990-01-09 | Physio-Control Corporation | Method and apparatus for offsetting baseline portion of oximeter signal |
US4819646A (en) | 1986-08-18 | 1989-04-11 | Physio-Control Corporation | Feedback-controlled method and apparatus for processing signals used in oximetry |
JPS6365845A (en) | 1986-09-05 | 1988-03-24 | ミノルタ株式会社 | Oximeter apparatus |
US4726382A (en) | 1986-09-17 | 1988-02-23 | The Boc Group, Inc. | Inflatable finger cuff |
US4824242A (en) | 1986-09-26 | 1989-04-25 | Sensormedics Corporation | Non-invasive oximeter and method |
US4714080A (en) | 1986-10-06 | 1987-12-22 | Nippon Colin Co., Ltd. | Method and apparatus for noninvasive monitoring of arterial blood oxygen saturation |
US4865038A (en) | 1986-10-09 | 1989-09-12 | Novametrix Medical Systems, Inc. | Sensor appliance for non-invasive monitoring |
JPS63111837A (en) | 1986-10-29 | 1988-05-17 | 日本光電工業株式会社 | Apparatus for measuring concentration of light absorbing substance in blood |
DE3639402A1 (en) | 1986-11-18 | 1988-05-19 | Siemens Ag | METHOD FOR THE PRODUCTION OF A MULTI-LAYERED CIRCUIT BOARD AND THE CIRCUIT BOARD PRODUCED THEREOF |
US5193543A (en) | 1986-12-12 | 1993-03-16 | Critikon, Inc. | Method and apparatus for measuring arterial blood constituents |
DE3703458A1 (en) | 1987-02-05 | 1988-08-18 | Hewlett Packard Gmbh | Medical oxygen saturation sensor using electromagnetic waves - has support segment for transmitter and receiver elements and clamping segment for fitting round patent |
US4776339A (en) | 1987-03-05 | 1988-10-11 | N.A.D., Inc. | Interlock for oxygen saturation monitor anesthesia apparatus |
US4880304A (en) | 1987-04-01 | 1989-11-14 | Nippon Colin Co., Ltd. | Optical sensor for pulse oximeter |
JPS63252239A (en) | 1987-04-09 | 1988-10-19 | Sumitomo Electric Ind Ltd | Reflection type oxymeter |
USRE33643E (en) | 1987-04-30 | 1991-07-23 | Nonin Medical, Inc. | Pulse oximeter with circuit leakage and ambient light compensation |
US4773422A (en) | 1987-04-30 | 1988-09-27 | Nonin Medical, Inc. | Single channel pulse oximeter |
JPS63277039A (en) | 1987-05-08 | 1988-11-15 | Hamamatsu Photonics Kk | Diagnostic apparatus |
JPS63275323A (en) | 1987-05-08 | 1988-11-14 | Hamamatsu Photonics Kk | Diagnostic apparatus |
US4722120A (en) | 1987-06-23 | 1988-02-02 | James Lu | Spring clip |
GB8719333D0 (en) | 1987-08-14 | 1987-09-23 | Swansea University College Of | Motion artefact rejection system |
DE3728109C1 (en) * | 1987-08-22 | 1989-03-16 | Telefonbau & Normalzeit Gmbh | Method for voice-controlled attenuation control in telephone transmission circuits |
US4805623A (en) | 1987-09-04 | 1989-02-21 | Vander Corporation | Spectrophotometric method for quantitatively determining the concentration of a dilute component in a light- or other radiation-scattering environment |
US4796636A (en) | 1987-09-10 | 1989-01-10 | Nippon Colin Co., Ltd. | Noninvasive reflectance oximeter |
US4819752A (en) | 1987-10-02 | 1989-04-11 | Datascope Corp. | Blood constituent measuring device and method |
US4825879A (en) | 1987-10-08 | 1989-05-02 | Critkon, Inc. | Pulse oximeter sensor |
US4848901A (en) | 1987-10-08 | 1989-07-18 | Critikon, Inc. | Pulse oximeter sensor control system |
US4807631A (en) | 1987-10-09 | 1989-02-28 | Critikon, Inc. | Pulse oximetry system |
US4807630A (en) | 1987-10-09 | 1989-02-28 | Advanced Medical Systems, Inc. | Apparatus and method for use in pulse oximeters |
US4859057A (en) | 1987-10-13 | 1989-08-22 | Lawrence Medical Systems, Inc. | Oximeter apparatus |
US4863265A (en) | 1987-10-16 | 1989-09-05 | Mine Safety Appliances Company | Apparatus and method for measuring blood constituents |
DE3877894T2 (en) | 1987-11-02 | 1993-06-24 | Sumitomo Electric Industries | ORGANIC LIGHT MEASURING PROBE. |
US4854699A (en) | 1987-11-02 | 1989-08-08 | Nippon Colin Co., Ltd. | Backscatter oximeter |
US4927264A (en) | 1987-12-02 | 1990-05-22 | Omron Tateisi Electronics Co. | Non-invasive measuring method and apparatus of blood constituents |
US4781195A (en) | 1987-12-02 | 1988-11-01 | The Boc Group, Inc. | Blood monitoring apparatus and methods with amplifier input dark current correction |
US4800885A (en) | 1987-12-02 | 1989-01-31 | The Boc Group, Inc. | Blood constituent monitoring apparatus and methods with frequency division multiplexing |
US4846183A (en) | 1987-12-02 | 1989-07-11 | The Boc Group, Inc. | Blood parameter monitoring apparatus and methods |
US4960126A (en) | 1988-01-15 | 1990-10-02 | Criticare Systems, Inc. | ECG synchronized pulse oximeter |
US4883353A (en) | 1988-02-11 | 1989-11-28 | Puritan-Bennett Corporation | Pulse oximeter |
US4883055A (en) | 1988-03-11 | 1989-11-28 | Puritan-Bennett Corporation | Artificially induced blood pulse for use with a pulse oximeter |
DE3809084C2 (en) | 1988-03-18 | 1999-01-28 | Nicolay Gmbh | Sensor for the non-invasive measurement of the pulse frequency and / or the oxygen saturation of the blood and method for its production |
DE3810411A1 (en) | 1988-03-26 | 1989-10-12 | Nicolay Gmbh | DEVICE FOR FIXING A SENSOR, IN PARTICULAR A SENSOR FOR OXIMETRIC MEASUREMENTS |
US4869254A (en) | 1988-03-30 | 1989-09-26 | Nellcor Incorporated | Method and apparatus for calculating arterial oxygen saturation |
US5078136A (en) | 1988-03-30 | 1992-01-07 | Nellcor Incorporated | Method and apparatus for calculating arterial oxygen saturation based plethysmographs including transients |
US5069213A (en) | 1988-04-29 | 1991-12-03 | Thor Technology Corporation | Oximeter sensor assembly with integral cable and encoder |
US4964408A (en) | 1988-04-29 | 1990-10-23 | Thor Technology Corporation | Oximeter sensor assembly with integral cable |
US5041187A (en) | 1988-04-29 | 1991-08-20 | Thor Technology Corporation | Oximeter sensor assembly with integral cable and method of forming the same |
JPH06169902A (en) | 1988-05-05 | 1994-06-21 | Sentinel Monitoring Inc | Pulse type non-invasion type oxymeter and technology for measuring it |
EP0341327B1 (en) | 1988-05-09 | 1993-09-15 | Hewlett-Packard GmbH | A method for processing signals, particularly for oximetric measurements on living human tissue |
US5361758A (en) | 1988-06-09 | 1994-11-08 | Cme Telemetrix Inc. | Method and device for measuring concentration levels of blood constituents non-invasively |
US4948248A (en) | 1988-07-22 | 1990-08-14 | Invivo Research Inc. | Blood constituent measuring device and method |
EP0352923A1 (en) | 1988-07-25 | 1990-01-31 | BAXTER INTERNATIONAL INC. (a Delaware corporation) | Spectrophotometric apparatus and method for monitoring oxygen saturation |
US4825872A (en) | 1988-08-05 | 1989-05-02 | Critikon, Inc. | Finger sensor for pulse oximetry system |
JPH0288041A (en) | 1988-09-24 | 1990-03-28 | Misawahoomu Sogo Kenkyusho:Kk | Finger tip pulse wave sensor |
US5099842A (en) | 1988-10-28 | 1992-03-31 | Nellcor Incorporated | Perinatal pulse oximetry probe |
US5564417A (en) | 1991-01-24 | 1996-10-15 | Non-Invasive Technology, Inc. | Pathlength corrected oximeter and the like |
US5873821A (en) | 1992-05-18 | 1999-02-23 | Non-Invasive Technology, Inc. | Lateralization spectrophotometer |
USH1039H (en) | 1988-11-14 | 1992-04-07 | The United States Of America As Represented By The Secretary Of The Air Force | Intrusion-free physiological condition monitoring |
JPH02164341A (en) | 1988-12-19 | 1990-06-25 | Nippon Koden Corp | Hemoglobin concentration measuring device |
US5553614A (en) | 1988-12-21 | 1996-09-10 | Non-Invasive Technology, Inc. | Examination of biological tissue using frequency domain spectroscopy |
US5353799A (en) | 1991-01-22 | 1994-10-11 | Non Invasive Technology, Inc. | Examination of subjects using photon migration with high directionality techniques |
US5119815A (en) | 1988-12-21 | 1992-06-09 | Nim, Incorporated | Apparatus for determining the concentration of a tissue pigment of known absorbance, in vivo, using the decay characteristics of scintered electromagnetic radiation |
US5111817A (en) | 1988-12-29 | 1992-05-12 | Medical Physics, Inc. | Noninvasive system and method for enhanced arterial oxygen saturation determination and arterial blood pressure monitoring |
US5086229A (en) | 1989-01-19 | 1992-02-04 | Futrex, Inc. | Non-invasive measurement of blood glucose |
US5365066A (en) | 1989-01-19 | 1994-11-15 | Futrex, Inc. | Low cost means for increasing measurement sensitivity in LED/IRED near-infrared instruments |
US5218207A (en) | 1989-01-19 | 1993-06-08 | Futrex, Inc. | Using led harmonic wavelengths for near-infrared quantitative |
US5028787A (en) | 1989-01-19 | 1991-07-02 | Futrex, Inc. | Non-invasive measurement of blood glucose |
FI82366C (en) | 1989-02-06 | 1991-03-11 | Instrumentarium Oy | MAETNING AV BLODETS SAMMANSAETTNING. |
US5596986A (en) * | 1989-03-17 | 1997-01-28 | Scico, Inc. | Blood oximeter |
US5902235A (en) | 1989-03-29 | 1999-05-11 | Somanetics Corporation | Optical cerebral oximeter |
USD326715S (en) | 1989-04-18 | 1992-06-02 | Hewlett-Packard Company | Medical sensors for measuring oxygen saturation or the like |
DE3912993C2 (en) | 1989-04-20 | 1998-01-29 | Nicolay Gmbh | Optoelectronic sensor for generating electrical signals based on physiological values |
US5040539A (en) | 1989-05-12 | 1991-08-20 | The United States Of America | Pulse oximeter for diagnosis of dental pulp pathology |
JP2766317B2 (en) | 1989-06-22 | 1998-06-18 | コーリン電子株式会社 | Pulse oximeter |
JPH0315502U (en) | 1989-06-28 | 1991-02-15 | ||
US5090410A (en) | 1989-06-28 | 1992-02-25 | Datascope Investment Corp. | Fastener for attaching sensor to the body |
US5299120A (en) | 1989-09-15 | 1994-03-29 | Hewlett-Packard Company | Method for digitally processing signals containing information regarding arterial blood flow |
US5058588A (en) | 1989-09-19 | 1991-10-22 | Hewlett-Packard Company | Oximeter and medical sensor therefor |
US5007423A (en) | 1989-10-04 | 1991-04-16 | Nippon Colin Company Ltd. | Oximeter sensor temperature control |
US5216598A (en) | 1989-10-04 | 1993-06-01 | Colin Electronics Co., Ltd. | System for correction of trends associated with pulse wave forms in oximeters |
US5203329A (en) | 1989-10-05 | 1993-04-20 | Colin Electronics Co., Ltd. | Noninvasive reflectance oximeter sensor providing controlled minimum optical detection depth |
US5094239A (en) | 1989-10-05 | 1992-03-10 | Colin Electronics Co., Ltd. | Composite signal implementation for acquiring oximetry signals |
US5190038A (en) | 1989-11-01 | 1993-03-02 | Novametrix Medical Systems, Inc. | Pulse oximeter with improved accuracy and response time |
DE3938759A1 (en) * | 1989-11-23 | 1991-05-29 | Philips Patentverwaltung | NON-INVASIVE OXIMETER ARRANGEMENT |
US5224478A (en) | 1989-11-25 | 1993-07-06 | Colin Electronics Co., Ltd. | Reflecting-type oxymeter probe |
KR100213554B1 (en) | 1989-11-28 | 1999-08-02 | 제이슨 오토 가도시 | Fetal probe |
US5080098A (en) * | 1989-12-18 | 1992-01-14 | Sentinel Monitoring, Inc. | Non-invasive sensor |
EP0442011A1 (en) * | 1990-02-15 | 1991-08-21 | Hewlett-Packard GmbH | Sensor, apparatus and method for non-invasive measurement of oxygen saturation |
US5152296A (en) | 1990-03-01 | 1992-10-06 | Hewlett-Packard Company | Dual-finger vital signs monitor |
US5104623A (en) | 1990-04-03 | 1992-04-14 | Minnesota Mining And Manufacturing Company | Apparatus and assembly for use in optically sensing a compositional blood parameter |
US5066859A (en) | 1990-05-18 | 1991-11-19 | Karkar Maurice N | Hematocrit and oxygen saturation blood analyzer |
GB9011887D0 (en) | 1990-05-26 | 1990-07-18 | Le Fit Ltd | Pulse responsive device |
WO1991018549A1 (en) | 1990-05-29 | 1991-12-12 | Yue Samuel K | Fetal probe apparatus |
US5239185A (en) | 1990-06-22 | 1993-08-24 | Hitachi, Ltd. | Method and equipment for measuring absorptance of light scattering materials using plural wavelengths of light |
IE77034B1 (en) | 1990-06-27 | 1997-11-19 | Futrex Inc | Non-invasive masurement of blood glucose |
US5259761A (en) | 1990-08-06 | 1993-11-09 | Jenifer M. Schnettler | Tooth vitality probe and process |
ES2128297T3 (en) | 1990-08-22 | 1999-05-16 | Nellcor Puritan Bennett Inc | APPARATUS FOR THE OXIMETRY OF THE PULSE OF A FETUS. |
US5158082A (en) | 1990-08-23 | 1992-10-27 | Spacelabs, Inc. | Apparatus for heating tissue with a photoplethysmograph sensor |
JP3329453B2 (en) | 1990-08-29 | 2002-09-30 | カデル、セオドアー・イー | Finger receiving device |
DE69119673T2 (en) * | 1990-08-31 | 1996-10-31 | New Oji Paper Co | Printer with a sheet cutter |
US5170786A (en) | 1990-09-28 | 1992-12-15 | Novametrix Medical Systems, Inc. | Reusable probe system |
US5055671A (en) | 1990-10-03 | 1991-10-08 | Spacelabs, Inc. | Apparatus for detecting transducer movement using a first and second light detector |
US6181958B1 (en) * | 1998-02-05 | 2001-01-30 | In-Line Diagnostics Corporation | Method and apparatus for non-invasive blood constituent monitoring |
US6681128B2 (en) * | 1990-10-06 | 2004-01-20 | Hema Metrics, Inc. | System for noninvasive hematocrit monitoring |
US6266546B1 (en) | 1990-10-06 | 2001-07-24 | In-Line Diagnostics Corporation | System for noninvasive hematocrit monitoring |
US5372136A (en) | 1990-10-06 | 1994-12-13 | Noninvasive Medical Technology Corporation | System and method for noninvasive hematocrit monitoring |
US5209230A (en) | 1990-10-19 | 1993-05-11 | Nellcor Incorporated | Adhesive pulse oximeter sensor with reusable portion |
US6263221B1 (en) | 1991-01-24 | 2001-07-17 | Non-Invasive Technology | Quantitative analyses of biological tissue using phase modulation spectroscopy |
US5193542A (en) | 1991-01-28 | 1993-03-16 | Missanelli John S | Peripartum oximetric monitoring apparatus |
US5291884A (en) | 1991-02-07 | 1994-03-08 | Minnesota Mining And Manufacturing Company | Apparatus for measuring a blood parameter |
JPH0614922B2 (en) * | 1991-02-15 | 1994-03-02 | 日本光電工業株式会社 | Calibration test equipment for pulse oximeter |
US5125403A (en) | 1991-02-20 | 1992-06-30 | Culp Joel B | Device and method for engagement of an oximeter probe |
US5154175A (en) | 1991-03-04 | 1992-10-13 | Gunther Ted J | Intrauterine fetal EKG-oximetry cable apparatus |
US5349953A (en) | 1991-03-05 | 1994-09-27 | Sensormedics, Corp. | Photoplethysmographics using component-amplitude-division multiplexing |
US5343818A (en) | 1991-03-05 | 1994-09-06 | Sensormedics Corp. | Photoplethysmographics using energy-reducing waveform shaping |
US5349952A (en) | 1991-03-05 | 1994-09-27 | Sensormedics Corp. | Photoplethysmographics using phase-division multiplexing |
US5267566A (en) | 1991-03-07 | 1993-12-07 | Maged Choucair | Apparatus and method for blood pressure monitoring |
MX9702434A (en) | 1991-03-07 | 1998-05-31 | Masimo Corp | Signal processing apparatus. |
EP0574509B1 (en) | 1991-03-07 | 1999-09-15 | Masimo Corporation | Signal processing apparatus and method |
US5490505A (en) | 1991-03-07 | 1996-02-13 | Masimo Corporation | Signal processing apparatus |
US5632272A (en) | 1991-03-07 | 1997-05-27 | Masimo Corporation | Signal processing apparatus |
US5226417A (en) | 1991-03-11 | 1993-07-13 | Nellcor, Inc. | Apparatus for the detection of motion transients |
US5237994A (en) | 1991-03-12 | 1993-08-24 | Square One Technology | Integrated lead frame pulse oximetry sensor |
US6541756B2 (en) | 1991-03-21 | 2003-04-01 | Masimo Corporation | Shielded optical probe having an electrical connector |
US5645440A (en) | 1995-10-16 | 1997-07-08 | Masimo Corporation | Patient cable connector |
US5995855A (en) | 1998-02-11 | 1999-11-30 | Masimo Corporation | Pulse oximetry sensor adapter |
US5638818A (en) | 1991-03-21 | 1997-06-17 | Masimo Corporation | Low noise optical probe |
US6580086B1 (en) | 1999-08-26 | 2003-06-17 | Masimo Corporation | Shielded optical probe and method |
DE4138702A1 (en) * | 1991-03-22 | 1992-09-24 | Madaus Medizin Elektronik | METHOD AND DEVICE FOR THE DIAGNOSIS AND QUANTITATIVE ANALYSIS OF APNOE AND FOR THE SIMULTANEOUS DETERMINATION OF OTHER DISEASES |
US5273036A (en) | 1991-04-03 | 1993-12-28 | Ppg Industries, Inc. | Apparatus and method for monitoring respiration |
US5218962A (en) | 1991-04-15 | 1993-06-15 | Nellcor Incorporated | Multiple region pulse oximetry probe and oximeter |
US5247932A (en) | 1991-04-15 | 1993-09-28 | Nellcor Incorporated | Sensor for intrauterine use |
US5313940A (en) | 1991-05-15 | 1994-05-24 | Nihon Kohden Corporation | Photo-electric pulse wave measuring probe |
EP0531631B1 (en) | 1991-06-19 | 1996-10-09 | Endotronics, Inc. | Cell culture apparatus |
US5402777A (en) | 1991-06-28 | 1995-04-04 | Alza Corporation | Methods and devices for facilitated non-invasive oxygen monitoring |
US5267563A (en) * | 1991-06-28 | 1993-12-07 | Nellcor Incorporated | Oximeter sensor with perfusion enhancing |
EP0522674B1 (en) * | 1991-07-12 | 1998-11-11 | Mark R. Robinson | Oximeter for reliable clinical determination of blood oxygen saturation in a fetus |
US5413100A (en) | 1991-07-17 | 1995-05-09 | Effets Biologiques Exercice | Non-invasive method for the in vivo determination of the oxygen saturation rate of arterial blood, and device for carrying out the method |
US5351685A (en) | 1991-08-05 | 1994-10-04 | Nellcor Incorporated | Condensed oximeter system with noise reduction software |
ATE124225T1 (en) | 1991-08-12 | 1995-07-15 | Avl Medical Instr Ag | DEVICE FOR MEASURING AT LEAST ONE GAS SATURATION, IN PARTICULAR THE OXYGEN SATURATION OF BLOOD. |
US5429129A (en) | 1991-08-22 | 1995-07-04 | Sensor Devices, Inc. | Apparatus for determining spectral absorption by a specific substance in a fluid |
US5217012A (en) | 1991-08-22 | 1993-06-08 | Sensor Devices Inc. | Noninvasive oximeter probe |
US5368025A (en) | 1991-08-22 | 1994-11-29 | Sensor Devices, Inc. | Non-invasive oximeter probe |
JP3124073B2 (en) | 1991-08-27 | 2001-01-15 | 日本コーリン株式会社 | Blood oxygen saturation monitor |
US5246003A (en) | 1991-08-28 | 1993-09-21 | Nellcor Incorporated | Disposable pulse oximeter sensor |
US6714803B1 (en) | 1991-09-03 | 2004-03-30 | Datex-Ohmeda, Inc. | Pulse oximetry SpO2 determination |
US5934277A (en) | 1991-09-03 | 1999-08-10 | Datex-Ohmeda, Inc. | System for pulse oximetry SpO2 determination |
US5247931A (en) | 1991-09-16 | 1993-09-28 | Mine Safety Appliances Company | Diagnostic sensor clasp utilizing a slot, pivot and spring hinge mechanism |
US5213099A (en) | 1991-09-30 | 1993-05-25 | The United States Of America As Represented By The Secretary Of The Air Force | Ear canal pulse/oxygen saturation measuring device |
JP3115374B2 (en) | 1991-10-11 | 2000-12-04 | テルモ株式会社 | Patient monitoring system |
US5249576A (en) | 1991-10-24 | 1993-10-05 | Boc Health Care, Inc. | Universal pulse oximeter probe |
US5311865A (en) * | 1991-11-07 | 1994-05-17 | Mayeux Charles D | Plastic finger oximetry probe holder |
US5253645A (en) | 1991-12-13 | 1993-10-19 | Critikon, Inc. | Method of producing an audible alarm in a blood pressure and pulse oximeter monitor |
JPH0569784U (en) | 1991-12-28 | 1993-09-21 | センチュリーメディカル株式会社 | Display device in medical equipment |
EP0549835B1 (en) | 1991-12-30 | 1996-03-13 | Hamamatsu Photonics K.K. | Diagnostic apparatus |
FR2685865B1 (en) | 1992-01-08 | 1998-04-10 | Distr App Medicaux Off | OPTICAL SENSOR, PARTICULARLY FOR MEASURING THE OXYGEN SATURATION RATE IN ARTERIAL BLOOD. |
DE69215204T2 (en) | 1992-01-29 | 1997-03-13 | Hewlett Packard Gmbh | Process and system for monitoring vital functions |
US5385143A (en) * | 1992-02-06 | 1995-01-31 | Nihon Kohden Corporation | Apparatus for measuring predetermined data of living tissue |
US5297548A (en) | 1992-02-07 | 1994-03-29 | Ohmeda Inc. | Arterial blood monitoring probe |
US5246002A (en) | 1992-02-11 | 1993-09-21 | Physio-Control Corporation | Noise insensitive pulse transmittance oximeter |
DE4210102C2 (en) | 1992-03-27 | 1999-02-25 | Rall Gerhard | Device for optically determining parameters of perfused tissue |
US5263244A (en) | 1992-04-17 | 1993-11-23 | Gould Inc. | Method of making a flexible printed circuit sensor assembly for detecting optical pulses |
JP3170866B2 (en) | 1992-04-24 | 2001-05-28 | 株式会社ノーリツ | 1 can 2 circuit type instant heating type heat exchanger |
DE69211986T2 (en) | 1992-05-15 | 1996-10-31 | Hewlett Packard Gmbh | Medical sensor |
JP3091929B2 (en) | 1992-05-28 | 2000-09-25 | 日本光電工業株式会社 | Pulse oximeter |
JP3165983B2 (en) * | 1992-06-15 | 2001-05-14 | 日本光電工業株式会社 | Light emitting element driving device for pulse oximeter |
US5377675A (en) * | 1992-06-24 | 1995-01-03 | Nellcor, Inc. | Method and apparatus for improved fetus contact with fetal probe |
US5355880A (en) | 1992-07-06 | 1994-10-18 | Sandia Corporation | Reliable noninvasive measurement of blood gases |
JP3116252B2 (en) | 1992-07-09 | 2000-12-11 | 日本光電工業株式会社 | Pulse oximeter |
US6411832B1 (en) | 1992-07-15 | 2002-06-25 | Optix Lp | Method of improving reproducibility of non-invasive measurements |
US6222189B1 (en) | 1992-07-15 | 2001-04-24 | Optix, Lp | Methods of enhancing optical signals by mechanical manipulation in non-invasive testing |
US5425360A (en) | 1992-07-24 | 1995-06-20 | Sensormedics Corporation | Molded pulse oximeter sensor |
US20050062609A9 (en) | 1992-08-19 | 2005-03-24 | Lynn Lawrence A. | Pulse oximetry relational alarm system for early recognition of instability and catastrophic occurrences |
US6342039B1 (en) * | 1992-08-19 | 2002-01-29 | Lawrence A. Lynn | Microprocessor system for the simplified diagnosis of sleep apnea |
US6223064B1 (en) | 1992-08-19 | 2001-04-24 | Lawrence A. Lynn | Microprocessor system for the simplified diagnosis of sleep apnea |
US6609016B1 (en) | 1997-07-14 | 2003-08-19 | Lawrence A. Lynn | Medical microprocessor system and method for providing a ventilation indexed oximetry value |
US5680857A (en) | 1992-08-28 | 1997-10-28 | Spacelabs Medical, Inc. | Alignment guide system for transmissive pulse oximetry sensors |
US5348003A (en) | 1992-09-03 | 1994-09-20 | Sirraya, Inc. | Method and apparatus for chemical analysis |
JP2547840Y2 (en) | 1992-09-25 | 1997-09-17 | 日本光電工業株式会社 | Oximeter probe |
US5323776A (en) | 1992-10-15 | 1994-06-28 | Picker International, Inc. | MRI compatible pulse oximetry system |
US5329922A (en) | 1992-10-19 | 1994-07-19 | Atlee Iii John L | Oximetric esophageal probe |
US5368224A (en) | 1992-10-23 | 1994-11-29 | Nellcor Incorporated | Method for reducing ambient noise effects in electronic monitoring instruments |
WO1994012096A1 (en) | 1992-12-01 | 1994-06-09 | Somanetics Corporation | Patient sensor for optical cerebral oximeters |
US5287853A (en) * | 1992-12-11 | 1994-02-22 | Hewlett-Packard Company | Adapter cable for connecting a pulsoximetry sensor unit to a medical measuring device |
US5551423A (en) | 1993-01-26 | 1996-09-03 | Nihon Kohden Corporation | Pulse oximeter probe |
DE4304693C2 (en) | 1993-02-16 | 2002-02-21 | Gerhard Rall | Sensor device for measuring vital parameters of a fetus during childbirth |
EP0615723A1 (en) | 1993-03-04 | 1994-09-21 | Hamamatsu Photonics K.K. | Method and apparatus for measuring blood flow |
JP2586392Y2 (en) | 1993-03-15 | 1998-12-02 | 日本光電工業株式会社 | Probe for pulse oximeter |
US5687719A (en) | 1993-03-25 | 1997-11-18 | Ikuo Sato | Pulse oximeter probe |
US5368026A (en) | 1993-03-26 | 1994-11-29 | Nellcor Incorporated | Oximeter with motion detection for alarm modification |
US5520177A (en) | 1993-03-26 | 1996-05-28 | Nihon Kohden Corporation | Oximeter probe |
US5676141A (en) | 1993-03-31 | 1997-10-14 | Nellcor Puritan Bennett Incorporated | Electronic processor for pulse oximeters |
US5348004A (en) | 1993-03-31 | 1994-09-20 | Nellcor Incorporated | Electronic processor for pulse oximeter |
US5497771A (en) | 1993-04-02 | 1996-03-12 | Mipm Mammendorfer Institut Fuer Physik Und Medizin Gmbh | Apparatus for measuring the oxygen saturation of fetuses during childbirth |
EP1491135A3 (en) | 1993-04-12 | 2005-09-07 | Hema Metrics, Inc. | Method and apparatus for monitoring blood constituents |
JP3173536B2 (en) | 1993-04-19 | 2001-06-04 | 日産自動車株式会社 | Vehicle steering wheel |
US5521851A (en) | 1993-04-26 | 1996-05-28 | Nihon Kohden Corporation | Noise reduction method and apparatus |
US5339810A (en) | 1993-05-03 | 1994-08-23 | Marquette Electronics, Inc. | Pulse oximetry sensor |
US5494043A (en) * | 1993-05-04 | 1996-02-27 | Vital Insite, Inc. | Arterial sensor |
WO1994027494A1 (en) | 1993-05-20 | 1994-12-08 | Somanetics Corporation | Improved electro-optical sensor for spectrophotometric medical devices |
WO1994027492A1 (en) | 1993-05-21 | 1994-12-08 | Nims, Inc. | Discriminating between valid and artifactual pulse waveforms |
JPH09501073A (en) * | 1993-05-28 | 1997-02-04 | ソマネテイツクス コーポレイシヨン | Instrument and method for measuring cerebral oxygen concentration by spectrophotometer |
JP3310390B2 (en) | 1993-06-10 | 2002-08-05 | 浜松ホトニクス株式会社 | Method and apparatus for measuring concentration of light absorbing substance in scattering medium |
US5452717A (en) | 1993-07-14 | 1995-09-26 | Masimo Corporation | Finger-cot probe |
US5337744A (en) | 1993-07-14 | 1994-08-16 | Masimo Corporation | Low noise finger cot probe |
US5425362A (en) | 1993-07-30 | 1995-06-20 | Criticare | Fetal sensor device |
EP0641543A1 (en) | 1993-09-07 | 1995-03-08 | Ohmeda Inc. | Heat-sealed neo-natal medical monitoring probe |
US5511546A (en) | 1993-09-20 | 1996-04-30 | Hon; Edward H. | Finger apparatus for measuring continuous cutaneous blood pressure and electrocardiogram electrode |
JP3345481B2 (en) | 1993-09-22 | 2002-11-18 | 興和株式会社 | Pulse wave spectrometer |
JP3387171B2 (en) | 1993-09-28 | 2003-03-17 | セイコーエプソン株式会社 | Pulse wave detection device and exercise intensity measurement device |
US5485847A (en) | 1993-10-08 | 1996-01-23 | Nellcor Puritan Bennett Incorporated | Pulse oximeter using a virtual trigger for heart rate synchronization |
US5411023A (en) | 1993-11-24 | 1995-05-02 | The Shielding Corporation | Optical sensor system |
US5417207A (en) | 1993-12-06 | 1995-05-23 | Sensor Devices, Inc. | Apparatus for the invasive use of oximeter probes |
JP3116259B2 (en) | 1993-12-07 | 2000-12-11 | 日本光電工業株式会社 | Probe for pulse oximeter |
JP2605584Y2 (en) | 1993-12-07 | 2000-07-24 | 日本光電工業株式会社 | Multi sensor |
JP3125079B2 (en) * | 1993-12-07 | 2001-01-15 | 日本光電工業株式会社 | Pulse oximeter |
DE69305178T2 (en) | 1993-12-11 | 1997-02-13 | Hewlett Packard Gmbh | Method for detecting an abnormal condition in a pulse powered oximeter system |
EP0684575A4 (en) | 1993-12-14 | 1997-05-14 | Mochida Pharm Co Ltd | Medical measuring apparatus. |
US5438986A (en) | 1993-12-14 | 1995-08-08 | Criticare Systems, Inc. | Optical sensor |
US5411024A (en) | 1993-12-15 | 1995-05-02 | Corometrics Medical Systems, Inc. | Fetal pulse oximetry sensor |
US5492118A (en) | 1993-12-16 | 1996-02-20 | Board Of Trustees Of The University Of Illinois | Determining material concentrations in tissues |
US5560355A (en) | 1993-12-17 | 1996-10-01 | Nellcor Puritan Bennett Incorporated | Medical sensor with amplitude independent output |
US5645059A (en) | 1993-12-17 | 1997-07-08 | Nellcor Incorporated | Medical sensor with modulated encoding scheme |
JP3238813B2 (en) | 1993-12-20 | 2001-12-17 | テルモ株式会社 | Pulse oximeter |
JP3464697B2 (en) | 1993-12-21 | 2003-11-10 | 興和株式会社 | Oxygen saturation meter |
US5507286A (en) | 1993-12-23 | 1996-04-16 | Medical Taping Systems, Inc. | Method and apparatus for improving the durability of a sensor |
US5553615A (en) | 1994-01-31 | 1996-09-10 | Minnesota Mining And Manufacturing Company | Method and apparatus for noninvasive prediction of hematocrit |
US5437275A (en) | 1994-02-02 | 1995-08-01 | Biochem International Inc. | Pulse oximetry sensor |
US5632273A (en) | 1994-02-04 | 1997-05-27 | Hamamatsu Photonics K.K. | Method and means for measurement of biochemical components |
US5995859A (en) | 1994-02-14 | 1999-11-30 | Nihon Kohden Corporation | Method and apparatus for accurately measuring the saturated oxygen in arterial blood by substantially eliminating noise from the measurement signal |
JP3134144B2 (en) | 1994-03-11 | 2001-02-13 | 日本光電工業株式会社 | Physiological detector |
US5830135A (en) | 1994-03-31 | 1998-11-03 | Bosque; Elena M. | Fuzzy logic alarm system for pulse oximeters |
US6662033B2 (en) | 1994-04-01 | 2003-12-09 | Nellcor Incorporated | Pulse oximeter and sensor optimized for low saturation |
US5575284A (en) * | 1994-04-01 | 1996-11-19 | University Of South Florida | Portable pulse oximeter |
US5421329A (en) | 1994-04-01 | 1995-06-06 | Nellcor, Inc. | Pulse oximeter sensor optimized for low saturation |
US6371921B1 (en) | 1994-04-15 | 2002-04-16 | Masimo Corporation | System and method of determining whether to recalibrate a blood pressure monitor |
JP3364819B2 (en) | 1994-04-28 | 2003-01-08 | 日本光電工業株式会社 | Blood absorption substance concentration measurement device |
US5402779A (en) | 1994-04-29 | 1995-04-04 | Chen; William X. | Method for the non-invasive detection of an intravascular injection of an anesthetic by the use of an indicator dye |
US5491299A (en) * | 1994-06-03 | 1996-02-13 | Siemens Medical Systems, Inc. | Flexible multi-parameter cable |
US5490523A (en) | 1994-06-29 | 1996-02-13 | Nonin Medical Inc. | Finger clip pulse oximeter |
US5912656A (en) | 1994-07-01 | 1999-06-15 | Ohmeda Inc. | Device for producing a display from monitored data |
DE4423597C1 (en) | 1994-07-06 | 1995-08-10 | Hewlett Packard Gmbh | Pulsoximetric ear sensor |
US5664270A (en) | 1994-07-19 | 1997-09-09 | Kinetic Concepts, Inc. | Patient interface system |
DE4429758A1 (en) | 1994-08-22 | 1996-02-29 | Buschmann Johannes | Method for validating devices for photometry of living tissue and device for carrying out the method |
DE4429845C1 (en) * | 1994-08-23 | 1995-10-19 | Hewlett Packard Gmbh | Pulse oximeter with flexible strap for attachment to hand or foot |
EP0702931A1 (en) | 1994-09-20 | 1996-03-27 | Ohmeda Inc. | Noninvasive medical monitoring instrument |
US5697367A (en) | 1994-10-14 | 1997-12-16 | Somanetics Corporation | Specially grounded sensor for clinical spectrophotometric procedures |
US5503148A (en) | 1994-11-01 | 1996-04-02 | Ohmeda Inc. | System for pulse oximetry SPO2 determination |
DE4442260C2 (en) | 1994-11-28 | 2000-06-08 | Mipm Mammendorfer Inst Fuer Ph | Method and arrangement for the non-invasive in vivo determination of oxygen saturation |
US5505199A (en) | 1994-12-01 | 1996-04-09 | Kim; Bill H. | Sudden infant death syndrome monitor |
DE4442855B4 (en) | 1994-12-01 | 2004-04-01 | Gerhard Dipl.-Ing. Rall | Use of a pulse oximetry sensor device |
US5676139A (en) | 1994-12-14 | 1997-10-14 | Ohmeda Inc. | Spring clip probe housing |
CA2168722A1 (en) | 1995-02-03 | 1996-08-04 | Robert William Hartwig | Self-aligning photoplethysmograph sensor |
US5673692A (en) | 1995-02-03 | 1997-10-07 | Biosignals Ltd. Co. | Single site, multi-variable patient monitor |
US5692503A (en) | 1995-03-10 | 1997-12-02 | Kuenstner; J. Todd | Method for noninvasive (in-vivo) total hemoglobin, oxyhemogolobin, deoxyhemoglobin, carboxyhemoglobin and methemoglobin concentration determination |
US5524617A (en) | 1995-03-14 | 1996-06-11 | Nellcor, Incorporated | Isolated layer pulse oximetry |
US5617852A (en) | 1995-04-06 | 1997-04-08 | Macgregor; Alastair R. | Method and apparatus for non-invasively determining blood analytes |
US5619992A (en) | 1995-04-06 | 1997-04-15 | Guthrie; Robert B. | Methods and apparatus for inhibiting contamination of reusable pulse oximetry sensors |
US5774213A (en) | 1995-04-21 | 1998-06-30 | Trebino; Rick P. | Techniques for measuring difference of an optical property at two wavelengths by modulating two sources to have opposite-phase components at a common frequency |
JP3326580B2 (en) | 1995-05-08 | 2002-09-24 | 日本光電工業株式会社 | Biological tissue transmitted light sensor |
US5662105A (en) | 1995-05-17 | 1997-09-02 | Spacelabs Medical, Inc. | System and method for the extractment of physiological signals |
US5851178A (en) | 1995-06-02 | 1998-12-22 | Ohmeda Inc. | Instrumented laser diode probe connector |
US5758644A (en) * | 1995-06-07 | 1998-06-02 | Masimo Corporation | Manual and automatic probe calibration |
US5638816A (en) * | 1995-06-07 | 1997-06-17 | Masimo Corporation | Active pulse blood constituent monitoring |
US5743262A (en) | 1995-06-07 | 1998-04-28 | Masimo Corporation | Blood glucose monitoring system |
US5760910A (en) | 1995-06-07 | 1998-06-02 | Masimo Corporation | Optical filter for spectroscopic measurement and method of producing the optical filter |
CA2221968C (en) * | 1995-06-09 | 2007-08-21 | Cybro Medical Ltd. | Sensor, method and device for optical blood oximetry |
US5645060A (en) | 1995-06-14 | 1997-07-08 | Nellcor Puritan Bennett Incorporated | Method and apparatus for removing artifact and noise from pulse oximetry |
US5685301A (en) | 1995-06-16 | 1997-11-11 | Ohmeda Inc. | Apparatus for precise determination of operating characteristics of optical devices contained in a monitoring probe |
US5829439A (en) | 1995-06-28 | 1998-11-03 | Hitachi Medical Corporation | Needle-like ultrasonic probe for ultrasonic diagnosis apparatus, method of producing same, and ultrasonic diagnosis apparatus using same |
US6055447A (en) | 1995-07-06 | 2000-04-25 | Institute Of Critical Care Medicine | Patient CO2 Measurement |
US6095974A (en) | 1995-07-21 | 2000-08-01 | Respironics, Inc. | Disposable fiber optic probe |
US5558096A (en) | 1995-07-21 | 1996-09-24 | Biochem International, Inc. | Blood pulse detection method using autocorrelation |
WO1997003603A1 (en) * | 1995-07-21 | 1997-02-06 | Respironics, Inc. | Method and apparatus for diode laser pulse oximetry using multifiber optical cables and disposable fiber optic probes |
GB9515649D0 (en) | 1995-07-31 | 1995-09-27 | Johnson & Johnson Medical | Surface sensor device |
US5853364A (en) | 1995-08-07 | 1998-12-29 | Nellcor Puritan Bennett, Inc. | Method and apparatus for estimating physiological parameters using model-based adaptive filtering |
FI111214B (en) | 1995-08-17 | 2003-06-30 | Tunturipyoerae Oy | Giver |
US5800348A (en) | 1995-08-31 | 1998-09-01 | Hewlett-Packard Company | Apparatus and method for medical monitoring, in particular pulse oximeter |
DE19537646C2 (en) | 1995-10-10 | 1998-09-17 | Hewlett Packard Gmbh | Method and device for detecting falsified measurement values in pulse oximetry for measuring oxygen saturation |
USD393830S (en) | 1995-10-16 | 1998-04-28 | Masimo Corporation | Patient cable connector |
AP931A (en) | 1995-10-23 | 2001-02-02 | Cytometrics Inc | Method and apparatus for reflected imaging analysis. |
US5626140A (en) | 1995-11-01 | 1997-05-06 | Spacelabs Medical, Inc. | System and method of multi-sensor fusion of physiological measurements |
DE19541605C2 (en) | 1995-11-08 | 1999-06-24 | Hewlett Packard Co | Sensor and method for performing medical measurements, in particular pulse oximetric measurements, on the human finger |
US5839439A (en) | 1995-11-13 | 1998-11-24 | Nellcor Puritan Bennett Incorporated | Oximeter sensor with rigid inner housing and pliable overmold |
US5660567A (en) | 1995-11-14 | 1997-08-26 | Nellcor Puritan Bennett Incorporated | Medical sensor connector with removable encoding device |
US5588427A (en) | 1995-11-20 | 1996-12-31 | Spacelabs Medical, Inc. | Enhancement of physiological signals using fractal analysis |
US5724967A (en) | 1995-11-21 | 1998-03-10 | Nellcor Puritan Bennett Incorporated | Noise reduction apparatus for low level analog signals |
US6041247A (en) | 1995-11-29 | 2000-03-21 | Instrumentarium Corp | Non-invasive optical measuring sensor and measuring method |
US5810724A (en) * | 1995-12-01 | 1998-09-22 | Nellcor Puritan Bennett Incorporated | Reusable sensor accessory containing a conformable spring activated rubber sleeved clip |
DE19651690C2 (en) | 1995-12-13 | 2001-12-13 | Bernreuter Peter | Measuring method for determining blood oxygen saturation |
US6226540B1 (en) | 1995-12-13 | 2001-05-01 | Peter Bernreuter | Measuring process for blood gas analysis sensors |
US5807247A (en) | 1995-12-20 | 1998-09-15 | Nellcor Puritan Bennett Incorporated | Method and apparatus for facilitating compatibility between pulse oximeters and sensor probes |
US5818985A (en) * | 1995-12-20 | 1998-10-06 | Nellcor Puritan Bennett Incorporated | Optical oximeter probe adapter |
AUPN740796A0 (en) | 1996-01-04 | 1996-01-25 | Circuitry Systems Limited | Biomedical data collection apparatus |
US5891026A (en) | 1996-01-29 | 1999-04-06 | Ntc Technology Inc. | Extended life disposable pulse oximetry sensor and method of making |
SE9600322L (en) | 1996-01-30 | 1997-07-31 | Hoek Instr Ab | Sensor for pulse oximetry with fiber optic signal transmission |
US5746697A (en) | 1996-02-09 | 1998-05-05 | Nellcor Puritan Bennett Incorporated | Medical diagnostic apparatus with sleep mode |
DE19609410C2 (en) | 1996-03-04 | 2002-04-25 | Biotronik Mess & Therapieg | Device for determining blood oxygen saturation |
US5797841A (en) | 1996-03-05 | 1998-08-25 | Nellcor Puritan Bennett Incorporated | Shunt barrier in pulse oximeter sensor |
US6253097B1 (en) | 1996-03-06 | 2001-06-26 | Datex-Ohmeda, Inc. | Noninvasive medical monitoring instrument using surface emitting laser devices |
JP3245042B2 (en) | 1996-03-11 | 2002-01-07 | 沖電気工業株式会社 | Tuning oscillation circuit |
WO1997036538A1 (en) * | 1996-04-01 | 1997-10-09 | Kontron Instruments Ag | Detection of parasitic signals during pulsoxymetric measurement |
US5790729A (en) | 1996-04-10 | 1998-08-04 | Ohmeda Inc. | Photoplethysmographic instrument having an integrated multimode optical coupler device |
US5766127A (en) | 1996-04-15 | 1998-06-16 | Ohmeda Inc. | Method and apparatus for improved photoplethysmographic perfusion-index monitoring |
US5692505A (en) | 1996-04-25 | 1997-12-02 | Fouts; James Michael | Data processing systems and methods for pulse oximeters |
US5919133A (en) | 1996-04-26 | 1999-07-06 | Ohmeda Inc. | Conformal wrap for pulse oximeter sensor |
US5913819A (en) | 1996-04-26 | 1999-06-22 | Datex-Ohmeda, Inc. | Injection molded, heat-sealed housing and half-etched lead frame for oximeter sensor |
US5807248A (en) | 1996-05-15 | 1998-09-15 | Ohmeda Inc. | Medical monitoring probe with modular device housing |
AU3065997A (en) | 1996-05-15 | 1997-12-05 | Nellcor Puritan Bennett Incorporated | Semi-reusable sensor with disposable sleeve |
US5752914A (en) | 1996-05-28 | 1998-05-19 | Nellcor Puritan Bennett Incorporated | Continuous mesh EMI shield for pulse oximetry sensor |
FI962448A (en) | 1996-06-12 | 1997-12-13 | Instrumentarium Oy | Method, apparatus and sensor for the determination of fractional oxygen saturation |
US5890929A (en) | 1996-06-19 | 1999-04-06 | Masimo Corporation | Shielded medical connector |
US6027452A (en) | 1996-06-26 | 2000-02-22 | Vital Insite, Inc. | Rapid non-invasive blood pressure measuring device |
US5879294A (en) | 1996-06-28 | 1999-03-09 | Hutchinson Technology Inc. | Tissue chromophore measurement system |
US5842981A (en) | 1996-07-17 | 1998-12-01 | Criticare Systems, Inc. | Direct to digital oximeter |
US6163715A (en) | 1996-07-17 | 2000-12-19 | Criticare Systems, Inc. | Direct to digital oximeter and method for calculating oxygenation levels |
EP0944347B1 (en) | 1996-07-19 | 2006-11-29 | Daedalus I, LLC | Device for noninvasive determination of blood parameters |
JP3925945B2 (en) | 1996-07-26 | 2007-06-06 | ラディオメーター・バーゼル・アクチェンゲゼルシャフト | A method for measuring oxygen saturation in tissues that are supplied with blood without damaging the specimen |
US5916155A (en) | 1996-07-30 | 1999-06-29 | Nellcor Puritan Bennett Incorporated | Fetal sensor with securing balloons remote from optics |
US5842982A (en) | 1996-08-07 | 1998-12-01 | Nellcor Puritan Bennett Incorporated | Infant neonatal pulse oximeter sensor |
US5776058A (en) | 1996-08-13 | 1998-07-07 | Nellcor Puritan Bennett Incorporated | Pressure-attached presenting part fetal pulse oximetry sensor |
US5813980A (en) | 1996-08-13 | 1998-09-29 | Nellcor Puritan Bennett Incorporated | Fetal pulse oximetry sensor with remote securing mechanism |
US5823952A (en) | 1996-08-14 | 1998-10-20 | Nellcor Incorporated | Pulse oximeter sensor with differential slip coefficient |
JP3844815B2 (en) | 1996-08-30 | 2006-11-15 | 浜松ホトニクス株式会社 | Method and apparatus for measuring absorption information of scatterers |
US5727547A (en) | 1996-09-04 | 1998-03-17 | Nellcor Puritan Bennett Incorporated | Presenting part fetal oximeter sensor with securing mechanism for providing tension to scalp attachment |
EP0875199B1 (en) | 1996-09-10 | 2004-03-10 | Seiko Epson Corporation | Organism state measuring device and relaxation state indicator device |
US5782756A (en) | 1996-09-19 | 1998-07-21 | Nellcor Puritan Bennett Incorporated | Method and apparatus for in vivo blood constituent analysis |
US5782758A (en) | 1996-09-23 | 1998-07-21 | Ohmeda Inc. | Method and apparatus for identifying the presence of noise in a time division multiplexed oximeter |
US5891022A (en) | 1996-09-25 | 1999-04-06 | Ohmeda Inc. | Apparatus for performing multiwavelength photoplethysmography |
DE19640807A1 (en) | 1996-10-02 | 1997-09-18 | Siemens Ag | Noninvasive optical detection of oxygen supply to e.g. brain or liver |
JPH10108846A (en) | 1996-10-03 | 1998-04-28 | Nippon Koden Corp | Holder for organic signal detector |
US6018673A (en) | 1996-10-10 | 2000-01-25 | Nellcor Puritan Bennett Incorporated | Motion compatible sensor for non-invasive optical blood analysis |
US5851179A (en) | 1996-10-10 | 1998-12-22 | Nellcor Puritan Bennett Incorporated | Pulse oximeter sensor with articulating head |
US5800349A (en) | 1996-10-15 | 1998-09-01 | Nonin Medical, Inc. | Offset pulse oximeter sensor |
EP0934021A2 (en) | 1996-10-24 | 1999-08-11 | Massachusetts Institute Of Technology | Patient monitoring finger ring sensor |
US5830136A (en) * | 1996-10-31 | 1998-11-03 | Nellcor Puritan Bennett Incorporated | Gel pad optical sensor |
US5817008A (en) | 1996-10-31 | 1998-10-06 | Spacelabs Medical, Inc. | Conformal pulse oximetry sensor and monitor |
US5830137A (en) | 1996-11-18 | 1998-11-03 | University Of South Florida | Green light pulse oximeter |
DE19647877C2 (en) | 1996-11-19 | 2000-06-15 | Univ Ilmenau Tech | Method and circuit arrangement for determining the oxygen saturation in the blood |
US5810723A (en) | 1996-12-05 | 1998-09-22 | Essential Medical Devices | Non-invasive carboxyhemoglobin analyer |
US6397093B1 (en) | 1996-12-05 | 2002-05-28 | Essential Medical Devices, Inc. | Non-invasive carboxyhemoglobin analyzer |
US5921921A (en) | 1996-12-18 | 1999-07-13 | Nellcor Puritan-Bennett | Pulse oximeter with sigma-delta converter |
US5842979A (en) | 1997-02-14 | 1998-12-01 | Ohmeda Inc. | Method and apparatus for improved photoplethysmographic monitoring of oxyhemoglobin, deoxyhemoglobin, carboxyhemoglobin and methemoglobin |
US6712762B1 (en) | 1997-02-28 | 2004-03-30 | Ors Diagnostic, Llc | Personal computer card for collection of real-time biological data |
US5827179A (en) | 1997-02-28 | 1998-10-27 | Qrs Diagnostic, Llc | Personal computer card for collection for real-time biological data |
US6159147A (en) | 1997-02-28 | 2000-12-12 | Qrs Diagnostics, Llc | Personal computer card for collection of real-time biological data |
US6113541A (en) | 1997-03-07 | 2000-09-05 | Agilent Technologies, Inc. | Noninvasive blood chemistry measurement method and system |
US5954644A (en) | 1997-03-24 | 1999-09-21 | Ohmeda Inc. | Method for ambient light subtraction in a photoplethysmographic measurement instrument |
US5817010A (en) | 1997-03-25 | 1998-10-06 | Ohmeda Inc. | Disposable sensor holder |
DE19880369C1 (en) | 1997-03-25 | 2002-08-08 | Siemens Ag | Method and device for the non-invasive in vivo determination of blood substances |
US5827182A (en) | 1997-03-31 | 1998-10-27 | Ohmeda Inc. | Multiple LED sets in oximetry sensors |
US6195575B1 (en) | 1997-04-02 | 2001-02-27 | Nellcor Puritan Bennett Incorporated | Fetal sensor which self-inflates using capillary force |
US5891024A (en) | 1997-04-09 | 1999-04-06 | Ohmeda Inc. | Two stage calibration and analyte measurement scheme for spectrophotomeric analysis |
EP0870465B1 (en) | 1997-04-12 | 2001-03-14 | Hewlett-Packard Company | Method and apparatus for the non-invasive determination of the concentration of a component |
DE69700253T2 (en) | 1997-04-12 | 1999-09-23 | Hewlett Packard Co | Method and device for determining the concentration of an ingredient |
US6002952A (en) | 1997-04-14 | 1999-12-14 | Masimo Corporation | Signal processing apparatus and method |
US6229856B1 (en) | 1997-04-14 | 2001-05-08 | Masimo Corporation | Method and apparatus for demodulating signals in a pulse oximetry system |
US5919134A (en) | 1997-04-14 | 1999-07-06 | Masimo Corp. | Method and apparatus for demodulating signals in a pulse oximetry system |
EP0872210B1 (en) | 1997-04-18 | 2006-01-04 | Koninklijke Philips Electronics N.V. | Intermittent measuring of arterial oxygen saturation of hemoglobin |
IL121079A0 (en) | 1997-06-15 | 1997-11-20 | Spo Medical Equipment Ltd | Physiological stress detector device and method |
AU7934498A (en) | 1997-06-27 | 1999-01-19 | Toa Medical Electronics Co., Ltd. | Living body inspecting apparatus and noninvasive blood analyzer using the same |
US6266193B1 (en) * | 1997-07-24 | 2001-07-24 | Cpfilms Inc. | Anti-reflective composite |
US5924985A (en) | 1997-07-29 | 1999-07-20 | Ohmeda Inc. | Patient probe disconnect alarm |
US6466808B1 (en) | 1999-11-22 | 2002-10-15 | Mallinckrodt Inc. | Single device for both heating and temperature measurement in an oximeter sensor |
US6115621A (en) | 1997-07-30 | 2000-09-05 | Nellcor Puritan Bennett Incorporated | Oximetry sensor with offset emitters and detector |
US5924982A (en) | 1997-07-30 | 1999-07-20 | Nellcor Puritan Bennett Incorporated | Oximeter sensor with user-modifiable color surface |
US6343223B1 (en) * | 1997-07-30 | 2002-01-29 | Mallinckrodt Inc. | Oximeter sensor with offset emitters and detector and heating device |
US6018674A (en) * | 1997-08-11 | 2000-01-25 | Datex-Ohmeda, Inc. | Fast-turnoff photodiodes with switched-gain preamplifiers in photoplethysmographic measurement instruments |
FI973454A (en) | 1997-08-22 | 1999-02-23 | Instrumentarium Oy | A resilient device in a measuring sensor for observing the properties of living tissue |
GB9717858D0 (en) | 1997-08-23 | 1997-10-29 | Electrode Company Ltd | The Electrode Company Ltd |
DE69833656T2 (en) | 1997-08-26 | 2006-08-17 | Seiko Epson Corp. | DEVICE FOR DIAGNOSIS OF PULSE WAVES |
JP3689914B2 (en) | 1997-09-05 | 2005-08-31 | セイコーエプソン株式会社 | Biological information measuring device |
GB2329015B (en) * | 1997-09-05 | 2002-02-13 | Samsung Electronics Co Ltd | Method and device for noninvasive measurement of concentrations of blood components |
US5865736A (en) * | 1997-09-30 | 1999-02-02 | Nellcor Puritan Bennett, Inc. | Method and apparatus for nuisance alarm reductions |
US5960610A (en) | 1997-10-01 | 1999-10-05 | Nellcor Puritan Bennett Incorporated | Method of curving a fetal sensor |
US5971930A (en) | 1997-10-17 | 1999-10-26 | Siemens Medical Systems, Inc. | Method and apparatus for removing artifact from physiological signals |
US5987343A (en) | 1997-11-07 | 1999-11-16 | Datascope Investment Corp. | Method for storing pulse oximetry sensor characteristics |
US6035223A (en) | 1997-11-19 | 2000-03-07 | Nellcor Puritan Bennett Inc. | Method and apparatus for determining the state of an oximetry sensor |
WO1999026528A1 (en) | 1997-11-26 | 1999-06-03 | Somanetics Corporation | Method and apparatus for monitoring fetal cerebral oxygenation during childbirth |
US5983122A (en) | 1997-12-12 | 1999-11-09 | Ohmeda Inc. | Apparatus and method for improved photoplethysmographic monitoring of multiple hemoglobin species using emitters having optimized center wavelengths |
JP3853053B2 (en) | 1997-12-17 | 2006-12-06 | 松下電器産業株式会社 | Biological information measuring device |
EP0864293B1 (en) | 1997-12-22 | 1999-08-04 | Hewlett-Packard Company | Telemetry system, in particular for medical purposes |
JP3567319B2 (en) | 1997-12-26 | 2004-09-22 | 日本光電工業株式会社 | Probe for pulse oximeter |
US6184521B1 (en) * | 1998-01-06 | 2001-02-06 | Masimo Corporation | Photodiode detector with integrated noise shielding |
US6400973B1 (en) | 1998-01-20 | 2002-06-04 | Bowden's Automated Products, Inc. | Arterial blood flow simulator |
US6179159B1 (en) * | 1998-01-26 | 2001-01-30 | Mariruth D. Gurley | Communicable disease barrier digit cover and dispensing package therefor |
US5978693A (en) | 1998-02-02 | 1999-11-02 | E.P. Limited | Apparatus and method for reduction of motion artifact |
US6014576A (en) * | 1998-02-27 | 2000-01-11 | Datex-Ohmeda, Inc. | Segmented photoplethysmographic sensor with universal probe-end |
JPH11244267A (en) | 1998-03-03 | 1999-09-14 | Fuji Photo Film Co Ltd | Blood component concentration measuring device |
US6525386B1 (en) | 1998-03-10 | 2003-02-25 | Masimo Corporation | Non-protruding optoelectronic lens |
US5924980A (en) | 1998-03-11 | 1999-07-20 | Siemens Corporate Research, Inc. | Method and apparatus for adaptively reducing the level of noise in an acquired signal |
US6165005A (en) | 1998-03-19 | 2000-12-26 | Masimo Corporation | Patient cable sensor switch |
US5997343A (en) | 1998-03-19 | 1999-12-07 | Masimo Corporation | Patient cable sensor switch |
US6078833A (en) | 1998-03-25 | 2000-06-20 | I.S.S. (Usa) Inc. | Self referencing photosensor |
US6047201A (en) | 1998-04-02 | 2000-04-04 | Jackson, Iii; William H. | Infant blood oxygen monitor and SIDS warning device |
EP0988521A1 (en) | 1998-04-14 | 2000-03-29 | Instrumentarium Corporation | Sensor assembly and method for measuring nitrogen dioxide |
US5916154A (en) | 1998-04-22 | 1999-06-29 | Nellcor Puritan Bennett | Method of enhancing performance in pulse oximetry via electrical stimulation |
US6064899A (en) | 1998-04-23 | 2000-05-16 | Nellcor Puritan Bennett Incorporated | Fiber optic oximeter connector with element indicating wavelength shift |
US6094592A (en) | 1998-05-26 | 2000-07-25 | Nellcor Puritan Bennett, Inc. | Methods and apparatus for estimating a physiological parameter using transforms |
US6334065B1 (en) | 1998-06-03 | 2001-12-25 | Masimo Corporation | Stereo pulse oximeter |
US5891021A (en) | 1998-06-03 | 1999-04-06 | Perdue Holdings, Inc. | Partially rigid-partially flexible electro-optical sensor for fingertip transillumination |
DE69800355T2 (en) * | 1998-06-05 | 2001-03-01 | Hewlett Packard Co | Pulse rate and heart rate matching detection for pulse oximetry |
IL124787A0 (en) | 1998-06-07 | 1999-01-26 | Itamar Medical C M 1997 Ltd | Pressure applicator devices particularly useful for non-invasive detection of medical conditions |
US5920263A (en) | 1998-06-11 | 1999-07-06 | Ohmeda, Inc. | De-escalation of alarm priorities in medical devices |
IL124965A (en) | 1998-06-17 | 2002-08-14 | Orsense Ltd | Non-invasive method of optical measurements for determining concentration of a substance in blood |
US5999834A (en) | 1998-06-18 | 1999-12-07 | Ntc Technology, Inc. | Disposable adhesive wrap for use with reusable pulse oximetry sensor and method of making |
US6285896B1 (en) | 1998-07-13 | 2001-09-04 | Masimo Corporation | Fetal pulse oximetry sensor |
US6671526B1 (en) | 1998-07-17 | 2003-12-30 | Nihon Kohden Corporation | Probe and apparatus for determining concentration of light-absorbing materials in living tissue |
JP2000083933A (en) | 1998-07-17 | 2000-03-28 | Nippon Koden Corp | Instrument for measuring concentration of light absorptive material in vital tissue |
EP1598003A3 (en) * | 1998-08-13 | 2006-03-01 | Whitland Research Limited | Optical device |
US6430513B1 (en) | 1998-09-04 | 2002-08-06 | Perkinelmer Instruments Llc | Monitoring constituents of an animal organ using statistical correlation |
EP1121047A1 (en) | 1998-09-09 | 2001-08-08 | U.S. Army Institute of Surgical Research | Pulse oximeter sensor combined with oropharyngeal airway and bite block |
US6266547B1 (en) | 1998-09-09 | 2001-07-24 | The United States Of America As Represented By The Secretary Of The Army | Nasopharyngeal airway with reflectance pulse oximeter sensor |
CA2343635A1 (en) | 1998-09-09 | 2000-03-16 | U.S. Army Institute Of Surgical Research | Disposable pulse oximeter assembly and protective cover therefor |
US6393310B1 (en) | 1998-09-09 | 2002-05-21 | J. Todd Kuenstner | Methods and systems for clinical analyte determination by visible and infrared spectroscopy |
JP2002524121A (en) | 1998-09-09 | 2002-08-06 | ユー.エス. アーミー インスティテュート オブ サージカル リサーチ | Methods for monitoring arterial oxygen saturation |
US20020028990A1 (en) | 1998-09-09 | 2002-03-07 | Shepherd John M. | Device and method for monitoring arterial oxygen saturation |
AU754375B2 (en) | 1998-09-18 | 2002-11-14 | Government Of The United States Of America As Represented By The Secretary Of The Army | Self-piercing pulse oximeter sensor assembly |
US6064898A (en) | 1998-09-21 | 2000-05-16 | Essential Medical Devices | Non-invasive blood component analyzer |
CA2345633A1 (en) | 1998-09-29 | 2000-04-06 | Mallinckrodt Inc. | Multiple-code oximeter calibration element |
US6298252B1 (en) | 1998-09-29 | 2001-10-02 | Mallinckrodt, Inc. | Oximeter sensor with encoder connected to detector |
US6356774B1 (en) | 1998-09-29 | 2002-03-12 | Mallinckrodt, Inc. | Oximeter sensor with encoded temperature characteristic |
JP2961608B1 (en) | 1998-10-02 | 1999-10-12 | 建夫 斎藤 | Oxygen saturation measurement device |
USRE45616E1 (en) | 1998-10-13 | 2015-07-21 | Covidien Lp | Multi-channel non-invasive tissue oximeter |
US6721585B1 (en) | 1998-10-15 | 2004-04-13 | Sensidyne, Inc. | Universal modular pulse oximeter probe for use with reusable and disposable patient attachment devices |
US6393311B1 (en) | 1998-10-15 | 2002-05-21 | Ntc Technology Inc. | Method, apparatus and system for removing motion artifacts from measurements of bodily parameters |
US6519487B1 (en) | 1998-10-15 | 2003-02-11 | Sensidyne, Inc. | Reusable pulse oximeter probe and disposable bandage apparatus |
US6343224B1 (en) * | 1998-10-15 | 2002-01-29 | Sensidyne, Inc. | Reusable pulse oximeter probe and disposable bandage apparatus |
US6144868A (en) | 1998-10-15 | 2000-11-07 | Sensidyne, Inc. | Reusable pulse oximeter probe and disposable bandage apparatus |
US6321100B1 (en) | 1999-07-13 | 2001-11-20 | Sensidyne, Inc. | Reusable pulse oximeter probe with disposable liner |
US6684091B2 (en) * | 1998-10-15 | 2004-01-27 | Sensidyne, Inc. | Reusable pulse oximeter probe and disposable bandage method |
US6519486B1 (en) | 1998-10-15 | 2003-02-11 | Ntc Technology Inc. | Method, apparatus and system for removing motion artifacts from measurements of bodily parameters |
US6006120A (en) | 1998-10-22 | 1999-12-21 | Palco Labs, Inc. | Cordless Pulse oximeter |
US6261236B1 (en) | 1998-10-26 | 2001-07-17 | Valentin Grimblatov | Bioresonance feedback method and apparatus |
US6061584A (en) | 1998-10-28 | 2000-05-09 | Lovejoy; David A. | Pulse oximetry sensor |
US6438396B1 (en) | 1998-11-05 | 2002-08-20 | Cytometrics, Inc. | Method and apparatus for providing high contrast imaging |
US6144444A (en) | 1998-11-06 | 2000-11-07 | Medtronic Avecor Cardiovascular, Inc. | Apparatus and method to determine blood parameters |
US6010938A (en) * | 1998-11-11 | 2000-01-04 | Mosel Vitelic Inc. | Method for making a load resistor on a semiconductor chip |
US7006855B1 (en) | 1998-11-16 | 2006-02-28 | S.P.O. Medical Equipment Ltd. | Sensor for radiance based diagnostics |
US6463311B1 (en) | 1998-12-30 | 2002-10-08 | Masimo Corporation | Plethysmograph pulse recognition processor |
US6606511B1 (en) | 1999-01-07 | 2003-08-12 | Masimo Corporation | Pulse oximetry pulse indicator |
US6684090B2 (en) | 1999-01-07 | 2004-01-27 | Masimo Corporation | Pulse oximetry data confidence indicator |
US6280381B1 (en) | 1999-07-22 | 2001-08-28 | Instrumentation Metrics, Inc. | Intelligent system for noninvasive blood analyte prediction |
US6770028B1 (en) | 1999-01-25 | 2004-08-03 | Masimo Corporation | Dual-mode pulse oximeter |
AU2859600A (en) | 1999-01-25 | 2000-08-07 | Masimo Corporation | Universal/upgrading pulse oximeter |
US20020140675A1 (en) | 1999-01-25 | 2002-10-03 | Ali Ammar Al | System and method for altering a display mode based on a gravity-responsive sensor |
US6658276B2 (en) | 1999-01-25 | 2003-12-02 | Masimo Corporation | Pulse oximeter user interface |
US6438399B1 (en) | 1999-02-16 | 2002-08-20 | The Children's Hospital Of Philadelphia | Multi-wavelength frequency domain near-infrared cerebral oximeter |
JP2000237170A (en) | 1999-02-17 | 2000-09-05 | Sumitomo Denko Hightecs Kk | Optical living body measuring sensor |
CA2363257C (en) | 1999-03-08 | 2010-09-07 | David B. Swedlow | Method and circuit for storing and providing historical physiological data |
IL129790A0 (en) | 1999-03-09 | 2000-02-29 | Orsense Ltd | A device for enhancement of blood-related signals |
US6360114B1 (en) | 1999-03-25 | 2002-03-19 | Masimo Corporation | Pulse oximeter probe-off detector |
US6308089B1 (en) | 1999-04-14 | 2001-10-23 | O.B. Scientific, Inc. | Limited use medical probe |
US6675031B1 (en) | 1999-04-14 | 2004-01-06 | Mallinckrodt Inc. | Method and circuit for indicating quality and accuracy of physiological measurements |
WO2000064338A2 (en) | 1999-04-23 | 2000-11-02 | Massachusetts Institute Of Technology | Isolating ring sensor design |
US6226539B1 (en) | 1999-05-26 | 2001-05-01 | Mallinckrodt, Inc. | Pulse oximeter having a low power led drive |
EP1192560A1 (en) | 1999-06-10 | 2002-04-03 | Agilent Technologies, Inc. (a Delaware corporation) | Interference suppression for measuring signals with periodic wanted signal |
WO2000077659A1 (en) | 1999-06-10 | 2000-12-21 | Koninklijke Philips Electronics N.V. | Quality indicator for measurement signals, in particular, for medical measurement signals such as those used in measuring oxygen saturation |
EP1200905B1 (en) | 1999-06-10 | 2016-08-24 | Koninklijke Philips N.V. | Recognition of a useful signal in a measurement signal |
US6587704B1 (en) | 1999-06-16 | 2003-07-01 | Orsense Ltd. | Method for non-invasive optical measurements of blood parameters |
EP1199977A2 (en) | 1999-06-18 | 2002-05-02 | Masimo Corporation | Pulse oximeter probe-off detection system |
US20030018243A1 (en) * | 1999-07-07 | 2003-01-23 | Gerhardt Thomas J. | Selectively plated sensor |
JP2001017404A (en) | 1999-07-09 | 2001-01-23 | Koike Medical:Kk | Medical measuring device |
EP1198196A4 (en) | 1999-07-14 | 2007-05-02 | Providence Health Sys Oregon | Adaptive calibration pulsed oximetry method and device |
US6760609B2 (en) | 1999-07-14 | 2004-07-06 | Providence Health System - Oregon | Adaptive calibration pulsed oximetry method and device |
US6512937B2 (en) * | 1999-07-22 | 2003-01-28 | Sensys Medical, Inc. | Multi-tier method of developing localized calibration models for non-invasive blood analyte prediction |
AU6894500A (en) | 1999-08-06 | 2001-03-05 | Board Of Regents, The University Of Texas System | Optoacoustic monitoring of blood oxygenation |
US6515273B2 (en) | 1999-08-26 | 2003-02-04 | Masimo Corporation | System for indicating the expiration of the useful operating life of a pulse oximetry sensor |
US6608562B1 (en) * | 1999-08-31 | 2003-08-19 | Denso Corporation | Vital signal detecting apparatus |
WO2001017426A1 (en) | 1999-09-10 | 2001-03-15 | Gorski Stephen H | Oximeter sensor with functional liner |
JP3627214B2 (en) | 1999-09-13 | 2005-03-09 | 日本光電工業株式会社 | Blood absorption substance measuring device |
US6708049B1 (en) | 1999-09-28 | 2004-03-16 | Nellcor Puritan Bennett Incorporated | Sensor with signature of data relating to sensor |
US6213952B1 (en) | 1999-09-28 | 2001-04-10 | Orsense Ltd. | Optical device for non-invasive measurement of blood related signals utilizing a finger holder |
US6339715B1 (en) * | 1999-09-30 | 2002-01-15 | Ob Scientific | Method and apparatus for processing a physiological signal |
US6537225B1 (en) | 1999-10-07 | 2003-03-25 | Alexander K. Mills | Device and method for noninvasive continuous determination of physiologic characteristics |
US6400971B1 (en) | 1999-10-12 | 2002-06-04 | Orsense Ltd. | Optical device for non-invasive measurement of blood-related signals and a finger holder therefor |
US7359741B2 (en) | 1999-11-15 | 2008-04-15 | Spo Medical Equipment Ltd. | Sensor and radiance based diagnostics |
US6665551B1 (en) | 1999-11-19 | 2003-12-16 | Nihon Kohden Corporation | Current driving system of light emitting diode |
CA2290083A1 (en) | 1999-11-19 | 2001-05-19 | Linde Medical Sensors Ag. | Device for the combined measurement of the arterial oxygen saturation and the transcutaneous co2 partial pressure of an ear lobe |
ES2235989T3 (en) | 1999-11-22 | 2005-07-16 | Mallinckrodt Inc. | OXIMETER TYPE SENSOR WITH EXTENDED METAL BAND. |
JP2001149349A (en) | 1999-11-26 | 2001-06-05 | Nippon Koden Corp | Sensor for living body |
US6542764B1 (en) | 1999-12-01 | 2003-04-01 | Masimo Corporation | Pulse oximeter monitor for expressing the urgency of the patient's condition |
US6377829B1 (en) | 1999-12-09 | 2002-04-23 | Masimo Corporation | Resposable pulse oximetry sensor |
US6671531B2 (en) | 1999-12-09 | 2003-12-30 | Masimo Corporation | Sensor wrap including foldable applicator |
US6950687B2 (en) | 1999-12-09 | 2005-09-27 | Masimo Corporation | Isolation and communication element for a resposable pulse oximetry sensor |
US6381479B1 (en) | 1999-12-17 | 2002-04-30 | Date-Ohmeda, Inc. | Pulse oximeter with improved DC and low frequency rejection |
US6408198B1 (en) | 1999-12-17 | 2002-06-18 | Datex-Ohmeda, Inc. | Method and system for improving photoplethysmographic analyte measurements by de-weighting motion-contaminated data |
US6397092B1 (en) * | 1999-12-17 | 2002-05-28 | Datex-Ohmeda, Inc. | Oversampling pulse oximeter |
US6360113B1 (en) | 1999-12-17 | 2002-03-19 | Datex-Ohmeda, Inc. | Photoplethysmographic instrument |
US6363269B1 (en) | 1999-12-17 | 2002-03-26 | Datex-Ohmeda, Inc. | Synchronized modulation/demodulation method and apparatus for frequency division multiplexed spectrophotometric system |
US6152754A (en) | 1999-12-21 | 2000-11-28 | Masimo Corporation | Circuit board based cable connector |
WO2001045553A1 (en) | 1999-12-22 | 2001-06-28 | Orsense Ltd. | A method of optical measurements for determining various parameters of the patient's blood |
US6594513B1 (en) | 2000-01-12 | 2003-07-15 | Paul D. Jobsis | Method and apparatus for determining oxygen saturation of blood in body organs |
US7198778B2 (en) | 2000-01-18 | 2007-04-03 | Mallinckrodt Inc. | Tumor-targeted optical contrast agents |
US6564088B1 (en) | 2000-01-21 | 2003-05-13 | University Of Massachusetts | Probe for localized tissue spectroscopy |
AU2001234590A1 (en) | 2000-01-28 | 2001-08-07 | The General Hospital Corporation | Fetal pulse oximetry |
JP2003521984A (en) | 2000-02-10 | 2003-07-22 | シーメンス メディカル ソリューションズ ユーエスエー インコーポレイテッド | Method and apparatus for detecting biological parameters |
AU2001236874B8 (en) | 2000-02-11 | 2004-05-27 | Government Of The United States Of America As Represented By The Secretary Of The Army | Pacifier pulse oximeter sensor |
US6385821B1 (en) | 2000-02-17 | 2002-05-14 | Udt Sensors, Inc. | Apparatus for securing an oximeter probe to a patient |
JP2001245871A (en) | 2000-03-07 | 2001-09-11 | Kazumasa Onodera | Doze judging device using saturation percentage of oxygen in artery blood in judging doze |
IL135077A0 (en) * | 2000-03-15 | 2001-05-20 | Orsense Ltd | A probe for use in non-invasive measurements of blood related parameters |
US6538721B2 (en) * | 2000-03-24 | 2003-03-25 | Nikon Corporation | Scanning exposure apparatus |
WO2001073394A2 (en) | 2000-03-29 | 2001-10-04 | Kinderlife Instruments, Inc. | Method and apparatus for determining physiological characteristics |
US6453183B1 (en) | 2000-04-10 | 2002-09-17 | Stephen D. Walker | Cerebral oxygenation monitor |
US6801797B2 (en) | 2000-04-17 | 2004-10-05 | Nellcor Puritan Bennett Incorporated | Pulse oximeter sensor with piece-wise function |
US6699199B2 (en) | 2000-04-18 | 2004-03-02 | Massachusetts Institute Of Technology | Photoplethysmograph signal-to-noise line enhancement |
WO2001082790A2 (en) | 2000-04-28 | 2001-11-08 | Kinderlife Instruments, Inc. | Method for determining blood constituents |
US6456862B2 (en) | 2000-05-02 | 2002-09-24 | Cas Medical Systems, Inc. | Method for non-invasive spectrophotometric blood oxygenation monitoring |
US6449501B1 (en) | 2000-05-26 | 2002-09-10 | Ob Scientific, Inc. | Pulse oximeter with signal sonification |
US6554788B1 (en) | 2000-06-02 | 2003-04-29 | Cobe Cardiovascular, Inc. | Hematocrit sampling system |
US6430525B1 (en) | 2000-06-05 | 2002-08-06 | Masimo Corporation | Variable mode averager |
US6510331B1 (en) | 2000-06-05 | 2003-01-21 | Glenn Williams | Switching device for multi-sensor array |
GB0014854D0 (en) * | 2000-06-16 | 2000-08-09 | Isis Innovation | System and method for acquiring data |
GB0014855D0 (en) | 2000-06-16 | 2000-08-09 | Isis Innovation | Combining measurements from different sensors |
US6470199B1 (en) | 2000-06-21 | 2002-10-22 | Masimo Corporation | Elastic sock for positioning an optical probe |
DE10030862B4 (en) | 2000-06-23 | 2006-02-09 | Nicolay Verwaltungs-Gmbh | Device for fixing a medical measuring device, in particular a pulse oximetry sensor, and use of such a device |
US6697656B1 (en) | 2000-06-27 | 2004-02-24 | Masimo Corporation | Pulse oximetry sensor compatible with multiple pulse oximetry systems |
US6597931B1 (en) | 2000-09-18 | 2003-07-22 | Photonify Technologies, Inc. | System and method for absolute oxygen saturation |
US6587703B2 (en) | 2000-09-18 | 2003-07-01 | Photonify Technologies, Inc. | System and method for measuring absolute oxygen saturation |
US6640116B2 (en) | 2000-08-18 | 2003-10-28 | Masimo Corporation | Optical spectroscopy pathlength measurement system |
US6719686B2 (en) | 2000-08-30 | 2004-04-13 | Mallinckrodt, Inc. | Fetal probe having an optical imaging device |
US6606510B2 (en) | 2000-08-31 | 2003-08-12 | Mallinckrodt Inc. | Oximeter sensor with digital memory encoding patient data |
US6600940B1 (en) | 2000-08-31 | 2003-07-29 | Mallinckrodt Inc. | Oximeter sensor with digital memory |
US6553241B2 (en) | 2000-08-31 | 2003-04-22 | Mallinckrodt Inc. | Oximeter sensor with digital memory encoding sensor expiration data |
US6628975B1 (en) | 2000-08-31 | 2003-09-30 | Mallinckrodt Inc. | Oximeter sensor with digital memory storing data |
US6591123B2 (en) | 2000-08-31 | 2003-07-08 | Mallinckrodt Inc. | Oximeter sensor with digital memory recording sensor data |
US6490466B1 (en) | 2000-09-21 | 2002-12-03 | Mallinckrodt Inc. | Interconnect circuit between non-compatible oximeter and sensor |
US6571113B1 (en) | 2000-09-21 | 2003-05-27 | Mallinckrodt, Inc. | Oximeter sensor adapter with coding element |
JP3845776B2 (en) | 2000-09-22 | 2006-11-15 | 日本光電工業株式会社 | Absorbent concentration measuring device in blood |
US6505060B1 (en) * | 2000-09-29 | 2003-01-07 | Datex-Ohmeda, Inc. | Method and apparatus for determining pulse oximetry differential values |
US6434408B1 (en) * | 2000-09-29 | 2002-08-13 | Datex-Ohmeda, Inc. | Pulse oximetry method and system with improved motion correction |
IL138884A (en) | 2000-10-05 | 2006-07-05 | Conmed Corp | Pulse oximeter and a method of its operation |
US6819950B2 (en) | 2000-10-06 | 2004-11-16 | Alexander K. Mills | Method for noninvasive continuous determination of physiologic characteristics |
US6519484B1 (en) | 2000-11-01 | 2003-02-11 | Ge Medical Systems Information Technologies, Inc. | Pulse oximetry sensor |
US6466809B1 (en) * | 2000-11-02 | 2002-10-15 | Datex-Ohmeda, Inc. | Oximeter sensor having laminated housing with flat patient interface surface |
US6560470B1 (en) | 2000-11-15 | 2003-05-06 | Datex-Ohmeda, Inc. | Electrical lockout photoplethysmographic measurement system |
US6505133B1 (en) | 2000-11-15 | 2003-01-07 | Datex-Ohmeda, Inc. | Simultaneous signal attenuation measurements utilizing code division multiplexing |
US6594512B2 (en) | 2000-11-21 | 2003-07-15 | Siemens Medical Solutions Usa, Inc. | Method and apparatus for estimating a physiological parameter from a physiological signal |
US6760610B2 (en) | 2000-11-23 | 2004-07-06 | Sentec Ag | Sensor and method for measurement of physiological parameters |
US20020068859A1 (en) | 2000-12-01 | 2002-06-06 | Knopp Christina A. | Laser diode drive scheme for noise reduction in photoplethysmographic measurements |
US6760607B2 (en) | 2000-12-29 | 2004-07-06 | Masimo Corporation | Ribbon cable substrate pulse oximetry sensor |
US6985763B2 (en) * | 2001-01-19 | 2006-01-10 | Tufts University | Method for measuring venous oxygen saturation |
US6501974B2 (en) | 2001-01-22 | 2002-12-31 | Datex-Ohmeda, Inc. | Compensation of human variability in pulse oximetry |
US6510329B2 (en) * | 2001-01-24 | 2003-01-21 | Datex-Ohmeda, Inc. | Detection of sensor off conditions in a pulse oximeter |
JP2002224088A (en) | 2001-02-01 | 2002-08-13 | Unitec Denshi Kk | Measuring instrument of oxygen saturation in blood |
US6618602B2 (en) | 2001-03-08 | 2003-09-09 | Palco Labs, Inc. | Method and apparatus for simultaneously determining a patient's identification and blood oxygen saturation |
US20020133067A1 (en) | 2001-03-15 | 2002-09-19 | Jackson William H. | New born and premature infant SIDS warning device |
US6591122B2 (en) | 2001-03-16 | 2003-07-08 | Nellcor Puritan Bennett Incorporated | Device and method for monitoring body fluid and electrolyte disorders |
JP3530868B2 (en) | 2001-03-26 | 2004-05-24 | 建夫 斎藤 | Tissue blood flow measurement device |
US6556852B1 (en) | 2001-03-27 | 2003-04-29 | I-Medik, Inc. | Earpiece with sensors to measure/monitor multiple physiological variables |
JP2002303576A (en) | 2001-04-05 | 2002-10-18 | Nippon Colin Co Ltd | Oxygen saturation measuring device |
KR100612827B1 (en) | 2001-04-19 | 2006-08-14 | 삼성전자주식회사 | Method and apparatus for noninvasively measuring hemoglobin concentration and oxygen saturation |
AU2002252717A1 (en) | 2001-04-19 | 2002-11-05 | Sean T. O'mara | Pulse oximetry device and method |
US6505061B2 (en) * | 2001-04-20 | 2003-01-07 | Datex-Ohmeda, Inc. | Pulse oximetry sensor with improved appendage cushion |
US20020156354A1 (en) | 2001-04-20 | 2002-10-24 | Larson Eric Russell | Pulse oximetry sensor with improved spring |
DE60125326T2 (en) | 2001-05-03 | 2007-09-27 | Ge Healthcare Finland Oy | Pulse oximeter |
US6985764B2 (en) * | 2001-05-03 | 2006-01-10 | Masimo Corporation | Flex circuit shielded optical sensor |
ATE369787T1 (en) | 2001-06-20 | 2007-09-15 | Purdue Research Foundation | PRESSURE CUFF WITH BODY ILLUMINATION FOR USE IN OPTICAL NON-INVASIVE MEASUREMENT OF BLOOD PARAMETERS |
US6850787B2 (en) | 2001-06-29 | 2005-02-01 | Masimo Laboratories, Inc. | Signal component processor |
US6801802B2 (en) | 2001-06-29 | 2004-10-05 | Ge Medical Systems Information Technologies, Inc. | System and method for selecting physiological data from a plurality of physiological data sources |
US6697658B2 (en) | 2001-07-02 | 2004-02-24 | Masimo Corporation | Low power pulse oximeter |
US6731967B1 (en) | 2001-07-16 | 2004-05-04 | Pacesetter, Inc. | Methods and devices for vascular plethysmography via modulation of source intensity |
US6754516B2 (en) | 2001-07-19 | 2004-06-22 | Nellcor Puritan Bennett Incorporated | Nuisance alarm reductions in a physiological monitor |
DE10136355A1 (en) * | 2001-07-26 | 2003-02-13 | Niels Rahe-Meyer | Device for monitoring vital parameters of an animal or human body consists of a portable bag with sensors, analysis electronics and visual and audible output means as well as interfaces for connection to other devices |
US6802812B1 (en) | 2001-07-27 | 2004-10-12 | Nostix Llc | Noninvasive optical sensor for measuring near infrared light absorbing analytes |
USD455834S1 (en) | 2001-08-29 | 2002-04-16 | Bci, Inc. | Finger oximeter |
US6668183B2 (en) | 2001-09-11 | 2003-12-23 | Datex-Ohmeda, Inc. | Diode detection circuit |
IL145445A (en) | 2001-09-13 | 2006-12-31 | Conmed Corp | Signal processing method and device for signal-to-noise improvement |
US6671532B1 (en) | 2001-09-17 | 2003-12-30 | Respironics Novametrix, Inc. | Pulse oximetry sensor and dispensing method |
GB0123395D0 (en) * | 2001-09-28 | 2001-11-21 | Isis Innovation | Locating features ina photoplethysmograph signal |
US6697655B2 (en) | 2001-10-05 | 2004-02-24 | Mortara Instrument, Inc. | Low power pulse oximeter |
US6564077B2 (en) | 2001-10-10 | 2003-05-13 | Mortara Instrument, Inc. | Method and apparatus for pulse oximetry |
US20030073890A1 (en) | 2001-10-10 | 2003-04-17 | Hanna D. Alan | Plethysmographic signal processing method and system |
US6697653B2 (en) | 2001-10-10 | 2004-02-24 | Datex-Ohmeda, Inc. | Reduced wire count voltage drop sense |
US6840904B2 (en) * | 2001-10-11 | 2005-01-11 | Jason Goldberg | Medical monitoring device and system |
US6773397B2 (en) | 2001-10-11 | 2004-08-10 | Draeger Medical Systems, Inc. | System for processing signal data representing physiological parameters |
US20030073889A1 (en) | 2001-10-11 | 2003-04-17 | Keilbach Kevin A. | Monitoring led wavelength shift in photoplethysmography |
US6748254B2 (en) | 2001-10-12 | 2004-06-08 | Nellcor Puritan Bennett Incorporated | Stacked adhesive optical sensor |
WO2003034911A2 (en) | 2001-10-22 | 2003-05-01 | Vsm Medtech Ltd. | Physiological parameter monitoring system and sensor assembly for same |
US6701170B2 (en) | 2001-11-02 | 2004-03-02 | Nellcor Puritan Bennett Incorporated | Blind source separation of pulse oximetry signals |
US6839579B1 (en) | 2001-11-02 | 2005-01-04 | Nellcor Puritan Bennett Incorporated | Temperature indicating oximetry sensor |
JP4174648B2 (en) | 2001-11-12 | 2008-11-05 | ロート製薬株式会社 | Aqueous composition |
JP3858678B2 (en) | 2001-11-20 | 2006-12-20 | コニカミノルタセンシング株式会社 | Blood component measuring device |
JP3709836B2 (en) | 2001-11-20 | 2005-10-26 | コニカミノルタセンシング株式会社 | Blood component measuring device |
US20030100840A1 (en) | 2001-11-28 | 2003-05-29 | Nihon Kohden Corporation | Pulse photometry probe |
JP2003169791A (en) | 2001-12-04 | 2003-06-17 | Masaru Ide | Cardiopulmonary function control system by measuring arterial blood oxygen saturation degree |
US6839580B2 (en) * | 2001-12-06 | 2005-01-04 | Ric Investments, Inc. | Adaptive calibration for pulse oximetry |
US6780158B2 (en) | 2001-12-14 | 2004-08-24 | Nihon Kohden Corporation | Signal processing method and pulse wave signal processing method |
JP2003194714A (en) | 2001-12-28 | 2003-07-09 | Omega Wave Kk | Measuring apparatus for blood amount in living-body tissue |
US6934570B2 (en) | 2002-01-08 | 2005-08-23 | Masimo Corporation | Physiological sensor combination |
US6668182B2 (en) | 2002-01-10 | 2003-12-23 | Northeast Monitoring | Pulse oxymetry data processing |
JP2003210438A (en) | 2002-01-22 | 2003-07-29 | Tyco Healthcare Japan Inc | Adapter for oximeter |
US6822564B2 (en) | 2002-01-24 | 2004-11-23 | Masimo Corporation | Parallel measurement alarm processor |
EP1332713A1 (en) | 2002-01-31 | 2003-08-06 | Btg International Limited | Venous pulse oximetry |
US7020507B2 (en) | 2002-01-31 | 2006-03-28 | Dolphin Medical, Inc. | Separating motion from cardiac signals using second order derivative of the photo-plethysmogram and fast fourier transforms |
DE60315596T2 (en) | 2002-01-31 | 2008-05-15 | Loughborough University Enterprises Ltd., Loughborough | VENOUS PULSE OXIMETRY |
US6882874B2 (en) | 2002-02-15 | 2005-04-19 | Datex-Ohmeda, Inc. | Compensation of human variability in pulse oximetry |
AU2003216348A1 (en) | 2002-02-22 | 2003-09-09 | Datex-Ohmeda, Inc. | Cepstral domain pulse oximetry |
US6709402B2 (en) | 2002-02-22 | 2004-03-23 | Datex-Ohmeda, Inc. | Apparatus and method for monitoring respiration with a pulse oximeter |
US20040039273A1 (en) | 2002-02-22 | 2004-02-26 | Terry Alvin Mark | Cepstral domain pulse oximetry |
US6805673B2 (en) | 2002-02-22 | 2004-10-19 | Datex-Ohmeda, Inc. | Monitoring mayer wave effects based on a photoplethysmographic signal |
US6702752B2 (en) | 2002-02-22 | 2004-03-09 | Datex-Ohmeda, Inc. | Monitoring respiration based on plethysmographic heart rate signal |
US20030171662A1 (en) | 2002-03-07 | 2003-09-11 | O'connor Michael William | Non-adhesive flexible electro-optical sensor for fingertip trans-illumination |
US6863652B2 (en) | 2002-03-13 | 2005-03-08 | Draeger Medical Systems, Inc. | Power conserving adaptive control system for generating signal in portable medical devices |
KR100455289B1 (en) * | 2002-03-16 | 2004-11-08 | 삼성전자주식회사 | Method of diagnosing using a ray and apparatus thereof |
CN100350870C (en) | 2002-03-21 | 2007-11-28 | 德特克斯-奥米达公司 | Neonatal bootie wrap |
US6647279B2 (en) | 2002-03-22 | 2003-11-11 | Jonas Alexander Pologe | Hybrid optical delivery system for photoplethysmography |
JP2003275192A (en) | 2002-03-25 | 2003-09-30 | Citizen Watch Co Ltd | Blood analyzer |
US6850788B2 (en) | 2002-03-25 | 2005-02-01 | Masimo Corporation | Physiological measurement communications adapter |
US7892183B2 (en) | 2002-04-19 | 2011-02-22 | Pelikan Technologies, Inc. | Method and apparatus for body fluid sampling and analyte sensing |
US20030212316A1 (en) | 2002-05-10 | 2003-11-13 | Leiden Jeffrey M. | Method and apparatus for determining blood parameters and vital signs of a patient |
US6711425B1 (en) | 2002-05-28 | 2004-03-23 | Ob Scientific, Inc. | Pulse oximeter with calibration stabilization |
JP2003339678A (en) | 2002-05-30 | 2003-12-02 | Minolta Co Ltd | Instrument for measuring blood state |
US8996090B2 (en) * | 2002-06-03 | 2015-03-31 | Exostat Medical, Inc. | Noninvasive detection of a physiologic parameter within a body tissue of a patient |
JP4040913B2 (en) | 2002-06-07 | 2008-01-30 | 株式会社パルメディカル | Noninvasive arteriovenous oxygen saturation measuring device |
EP2489306B1 (en) | 2002-06-20 | 2015-11-04 | The University of Florida | Perfusion monitor and system, including specifically configured oximeter probes and covers for oximeter probes |
US7024235B2 (en) | 2002-06-20 | 2006-04-04 | University Of Florida Research Foundation, Inc. | Specially configured nasal pulse oximeter/photoplethysmography probes, and combined nasal probe/cannula, selectively with sampler for capnography, and covering sleeves for same |
US6909912B2 (en) | 2002-06-20 | 2005-06-21 | University Of Florida | Non-invasive perfusion monitor and system, specially configured oximeter probes, methods of using same, and covers for probes |
US6865407B2 (en) | 2002-07-11 | 2005-03-08 | Optical Sensors, Inc. | Calibration technique for non-invasive medical devices |
EP1545298B1 (en) | 2002-07-26 | 2019-11-27 | Edwards Lifesciences Corporation | Method and apparatus for spectrophotometric blood oxygenation monitoring |
US6850789B2 (en) | 2002-07-29 | 2005-02-01 | Welch Allyn, Inc. | Combination SPO2/temperature measuring apparatus |
US7096054B2 (en) | 2002-08-01 | 2006-08-22 | Masimo Corporation | Low noise optical housing |
KR100493157B1 (en) | 2002-08-02 | 2005-06-03 | 삼성전자주식회사 | Probe using in measuring organism signal and system for measuring organism signal comprising the same |
US7133711B2 (en) | 2002-08-07 | 2006-11-07 | Orsense, Ltd. | Method and system for decomposition of multiple channel signals |
US6707257B2 (en) | 2002-08-08 | 2004-03-16 | Datex-Ohmeda, Inc. | Ferrite stabilized LED drive |
US6720734B2 (en) | 2002-08-08 | 2004-04-13 | Datex-Ohmeda, Inc. | Oximeter with nulled op-amp current feedback |
US6825619B2 (en) | 2002-08-08 | 2004-11-30 | Datex-Ohmeda, Inc. | Feedback-controlled LED switching |
US6879850B2 (en) | 2002-08-16 | 2005-04-12 | Optical Sensors Incorporated | Pulse oximeter with motion detection |
US6763256B2 (en) | 2002-08-16 | 2004-07-13 | Optical Sensors, Inc. | Pulse oximeter |
US6745061B1 (en) | 2002-08-21 | 2004-06-01 | Datex-Ohmeda, Inc. | Disposable oximetry sensor |
US6643531B1 (en) | 2002-08-22 | 2003-11-04 | Bci, Inc. | Combination fingerprint and oximetry device |
JP2004089546A (en) | 2002-09-03 | 2004-03-25 | Citizen Watch Co Ltd | Blood analyzer |
US6912413B2 (en) | 2002-09-13 | 2005-06-28 | Ge Healthcare Finland Oy | Pulse oximeter |
US7341559B2 (en) | 2002-09-14 | 2008-03-11 | Masimo Corporation | Pulse oximetry ear sensor |
JP2004113353A (en) | 2002-09-25 | 2004-04-15 | Citizen Watch Co Ltd | Blood analyzer |
US20040186358A1 (en) | 2002-09-25 | 2004-09-23 | Bart Chernow | Monitoring system containing a hospital bed with integrated display |
US7142901B2 (en) | 2002-09-25 | 2006-11-28 | Masimo Corporation | Parameter compensated physiological monitor |
EP1549165B8 (en) | 2002-10-01 | 2010-10-06 | Nellcor Puritan Bennett LLC | Use of a headband to indicate tension and system comprising an oximetry sensor and a headband |
US7096052B2 (en) | 2002-10-04 | 2006-08-22 | Masimo Corporation | Optical probe including predetermined emission wavelength based on patient type |
JP2004135854A (en) | 2002-10-17 | 2004-05-13 | Nippon Colin Co Ltd | Reflection type photoelectric pulse wave detector and reflection type oxymeter |
JP2004148069A (en) | 2002-10-29 | 2004-05-27 | Tse:Kk | Reflection type detector for degree of blood oxygen saturation |
JP2004148070A (en) | 2002-10-29 | 2004-05-27 | Tse:Kk | Detector of a pluralty of components in blood |
JP4352315B2 (en) | 2002-10-31 | 2009-10-28 | 日本光電工業株式会社 | Signal processing method / apparatus and pulse photometer using the same |
US6731962B1 (en) | 2002-10-31 | 2004-05-04 | Smiths Medical Pm Inc | Finger oximeter with remote telecommunications capabilities and system therefor |
JP2004202190A (en) | 2002-11-08 | 2004-07-22 | Minolta Co Ltd | Biological information measuring device |
JP2004159810A (en) | 2002-11-12 | 2004-06-10 | Otax Co Ltd | Arterial oxygen saturation measuring instrument |
JP2004166775A (en) | 2002-11-18 | 2004-06-17 | Citizen Watch Co Ltd | Blood analyzer |
US7027849B2 (en) | 2002-11-22 | 2006-04-11 | Masimo Laboratories, Inc. | Blood parameter measurement system |
JP4489385B2 (en) | 2002-12-12 | 2010-06-23 | 株式会社日立メディコ | Measuring probe and biological light measuring device |
AU2003297060A1 (en) | 2002-12-13 | 2004-07-09 | Massachusetts Institute Of Technology | Vibratory venous and arterial oximetry sensor |
US6754515B1 (en) | 2002-12-17 | 2004-06-22 | Kestrel Labs, Inc. | Stabilization of noisy optical sources in photoplethysmography |
JP3944448B2 (en) | 2002-12-18 | 2007-07-11 | 浜松ホトニクス株式会社 | Blood measuring device |
KR100499139B1 (en) | 2003-01-07 | 2005-07-04 | 삼성전자주식회사 | Method of removing abnormal data and blood constituent analysing system using spectroscopy employing the same |
US7006856B2 (en) | 2003-01-10 | 2006-02-28 | Nellcor Puritan Bennett Incorporated | Signal quality metrics design for qualifying data for a physiological monitor |
US7016715B2 (en) | 2003-01-13 | 2006-03-21 | Nellcorpuritan Bennett Incorporated | Selection of preset filter parameters based on signal quality |
US7225006B2 (en) | 2003-01-23 | 2007-05-29 | Masimo Corporation | Attachment and optical probe |
US6920345B2 (en) * | 2003-01-24 | 2005-07-19 | Masimo Corporation | Optical sensor including disposable and reusable elements |
US7272426B2 (en) | 2003-02-05 | 2007-09-18 | Koninklijke Philips Electronics N.V. | Finger medical sensor |
JP2004248820A (en) | 2003-02-19 | 2004-09-09 | Citizen Watch Co Ltd | Blood analyzer |
JP2004248819A (en) | 2003-02-19 | 2004-09-09 | Citizen Watch Co Ltd | Blood analyzer |
JP2004261364A (en) | 2003-02-28 | 2004-09-24 | Hamamatsu Photonics Kk | Concentration information measuring apparatus |
US6968221B2 (en) | 2003-03-14 | 2005-11-22 | Futrex, Inc. | Low-cost method and apparatus for non-invasively measuring blood glucose levels |
JP2004290412A (en) | 2003-03-27 | 2004-10-21 | Citizen Watch Co Ltd | Blood analyzer |
JP2004290545A (en) | 2003-03-28 | 2004-10-21 | Citizen Watch Co Ltd | Blood analyzer |
JP2004290544A (en) | 2003-03-28 | 2004-10-21 | Citizen Watch Co Ltd | Blood analyzer |
JP4551998B2 (en) | 2003-04-23 | 2010-09-29 | オータックス株式会社 | Optical probe and measurement system using the same |
JP2004329406A (en) | 2003-05-02 | 2004-11-25 | Iiguru Kk | Medical sensor, pulse type oxygen concentration sensor, and kit for attaching these sensors to body of patient |
JP4131434B2 (en) | 2003-05-08 | 2008-08-13 | 日本光電工業株式会社 | Pulse oximeter probe and mounting method thereof |
KR100571811B1 (en) | 2003-05-09 | 2006-04-17 | 삼성전자주식회사 | Ear type measurement apparatus for bio signal |
JP2004344367A (en) | 2003-05-22 | 2004-12-09 | Moririka:Kk | Medical purpose measuring instrument |
JP2004351107A (en) | 2003-05-30 | 2004-12-16 | Moririka:Kk | Portable medical measuring instrument |
US6993372B2 (en) * | 2003-06-03 | 2006-01-31 | Orsense Ltd. | Method and system for use in non-invasive optical measurements of blood parameters |
US6992772B2 (en) * | 2003-06-19 | 2006-01-31 | Optix Lp | Method and apparatus for optical sampling to reduce interfering variances |
US6954664B2 (en) | 2003-06-20 | 2005-10-11 | Smiths Medical Pm, Inc. | Oximetry simulator |
US7047056B2 (en) | 2003-06-25 | 2006-05-16 | Nellcor Puritan Bennett Incorporated | Hat-based oximeter sensor |
US7025728B2 (en) | 2003-06-30 | 2006-04-11 | Nihon Kohden Corporation | Method for reducing noise, and pulse photometer using the method |
US7003338B2 (en) * | 2003-07-08 | 2006-02-21 | Masimo Corporation | Method and apparatus for reducing coupling between signals |
JP4326866B2 (en) | 2003-07-17 | 2009-09-09 | 帝人株式会社 | How to predict the occurrence of acute exacerbations |
US7263396B2 (en) | 2003-08-08 | 2007-08-28 | Cardiodigital Limited | Ear sensor assembly |
US7107088B2 (en) | 2003-08-25 | 2006-09-12 | Sarnoff Corporation | Pulse oximetry methods and apparatus for use within an auditory canal |
WO2005020798A2 (en) | 2003-08-27 | 2005-03-10 | Datex-Ohmeda, Inc. | Multi-domain motion estimation and plethysmographic recognition using fuzzy neural-nets |
US20050049468A1 (en) | 2003-09-03 | 2005-03-03 | Sven-Erik Carlson | Increasing the performance of an optical pulsoximeter |
CA2481857A1 (en) | 2003-09-19 | 2005-03-19 | Nir Diagnostics Inc. | Near infrared risk assessment of diseases |
US20050075550A1 (en) | 2003-10-03 | 2005-04-07 | Lindekugel Eric W. | Quick-clip sensor holder |
US7254434B2 (en) | 2003-10-14 | 2007-08-07 | Masimo Corporation | Variable pressure reusable sensor |
TWI250867B (en) | 2003-10-22 | 2006-03-11 | Surewin Technology Corp | Pulse wave analysis device |
DE20318882U1 (en) | 2003-12-03 | 2004-03-11 | Drewes, Susanne | Pulse-oximetry sensor suitable for new-born includes flexible, conformed, hygienic material embedding circuitry for disinfection and reuse |
US7305262B2 (en) | 2003-12-11 | 2007-12-04 | Ge Medical Systems Information Technologies, Inc. | Apparatus and method for acquiring oximetry and electrocardiogram signals |
EP3066978A1 (en) | 2003-12-30 | 2016-09-14 | Beta Biomed Services, Inc. | Method and system of monitoring respiration in an individual |
US7280858B2 (en) | 2004-01-05 | 2007-10-09 | Masimo Corporation | Pulse oximetry sensor |
JP2005200031A (en) | 2004-01-13 | 2005-07-28 | Showa Kiki Kogyo Co Ltd | Pos communication failure preventive device |
US20050197548A1 (en) | 2004-03-05 | 2005-09-08 | Elekon Industries Usa, Inc. | Disposable/reusable flexible sensor |
JP4191642B2 (en) | 2004-04-02 | 2008-12-03 | 三菱電機株式会社 | Transflective liquid crystal display device and manufacturing method thereof |
US20050228248A1 (en) | 2004-04-07 | 2005-10-13 | Thomas Dietiker | Clip-type sensor having integrated biasing and cushioning means |
US7683759B2 (en) | 2004-10-06 | 2010-03-23 | Martis Ip Holdings, Llc | Patient identification system |
US20060084878A1 (en) | 2004-10-18 | 2006-04-20 | Triage Wireless, Inc. | Personal computer-based vital signs monitor |
WO2006134421A2 (en) | 2004-11-05 | 2006-12-21 | Envitec-Wismar Gmbh | Apparatus for improved pulse oximetry measurement |
US7359742B2 (en) | 2004-11-12 | 2008-04-15 | Nonin Medical, Inc. | Sensor assembly |
US7658716B2 (en) | 2004-12-07 | 2010-02-09 | Triage Wireless, Inc. | Vital signs monitor using an optical ear-based module |
JP2006204742A (en) | 2005-01-31 | 2006-08-10 | Konica Minolta Sensing Inc | Method and system for evaluating sleep, its operation program, pulse oxymeter, and system for supporting sleep |
US7548771B2 (en) | 2005-03-31 | 2009-06-16 | Nellcor Puritan Bennett Llc | Pulse oximetry sensor and technique for using the same on a distal region of a patient's digit |
KR100716824B1 (en) | 2005-04-28 | 2007-05-09 | 삼성전기주식회사 | Printed circuit board with embedded capacitors using hybrid materials, and manufacturing process thereof |
US7657294B2 (en) | 2005-08-08 | 2010-02-02 | Nellcor Puritan Bennett Llc | Compliant diaphragm medical sensor and technique for using the same |
US7657295B2 (en) | 2005-08-08 | 2010-02-02 | Nellcor Puritan Bennett Llc | Medical sensor and technique for using the same |
US7590439B2 (en) | 2005-08-08 | 2009-09-15 | Nellcor Puritan Bennett Llc | Bi-stable medical sensor and technique for using the same |
JP3116255U (en) | 2005-08-30 | 2005-12-02 | モリト株式会社 | Eggplant ring and key holder using the same |
JP3116260U (en) | 2005-08-30 | 2005-12-02 | マーテック株式会社 | Swivel hanger |
US7904130B2 (en) | 2005-09-29 | 2011-03-08 | Nellcor Puritan Bennett Llc | Medical sensor and technique for using the same |
US7486979B2 (en) | 2005-09-30 | 2009-02-03 | Nellcor Puritan Bennett Llc | Optically aligned pulse oximetry sensor and technique for using the same |
JP5049624B2 (en) | 2007-03-26 | 2012-10-17 | 株式会社東芝 | Metal fine particle dispersed film and method for producing metal fine particle dispersed film |
JP5049625B2 (en) | 2007-03-27 | 2012-10-17 | キヤノン株式会社 | Structure manufacturing method and structure manufacturing apparatus using the same |
-
2005
- 2005-09-30 US US11/241,031 patent/US7486979B2/en active Active
-
2006
- 2006-09-29 AT AT06815831T patent/ATE542475T1/en active
- 2006-09-29 WO PCT/US2006/038129 patent/WO2007041338A1/en active Application Filing
- 2006-09-29 EP EP06815831A patent/EP1945099B8/en not_active Not-in-force
- 2006-09-29 TW TW095136336A patent/TW200724091A/en unknown
-
2009
- 2009-01-09 US US12/351,742 patent/US8386002B2/en active Active
Patent Citations (1)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US6654621B2 (en) * | 2001-08-29 | 2003-11-25 | Bci, Inc. | Finger oximeter with finger grip suspension system |
Cited By (3)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US8692992B2 (en) | 2011-09-22 | 2014-04-08 | Covidien Lp | Faraday shield integrated into sensor bandage |
US8726496B2 (en) | 2011-09-22 | 2014-05-20 | Covidien Lp | Technique for remanufacturing a medical sensor |
US9610040B2 (en) | 2011-09-22 | 2017-04-04 | Covidien Lp | Remanufactured medical sensor with flexible Faraday shield |
Also Published As
Publication number | Publication date |
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EP1945099B1 (en) | 2012-01-25 |
US20070078309A1 (en) | 2007-04-05 |
US8386002B2 (en) | 2013-02-26 |
US20090118603A1 (en) | 2009-05-07 |
EP1945099A1 (en) | 2008-07-23 |
ATE542475T1 (en) | 2012-02-15 |
EP1945099B8 (en) | 2012-08-08 |
US7486979B2 (en) | 2009-02-03 |
TW200724091A (en) | 2007-07-01 |
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