CA2330553C - Implantable blood glucose sensor system - Google Patents
Implantable blood glucose sensor system Download PDFInfo
- Publication number
- CA2330553C CA2330553C CA002330553A CA2330553A CA2330553C CA 2330553 C CA2330553 C CA 2330553C CA 002330553 A CA002330553 A CA 002330553A CA 2330553 A CA2330553 A CA 2330553A CA 2330553 C CA2330553 C CA 2330553C
- Authority
- CA
- Canada
- Prior art keywords
- enclosure
- sensor
- response
- chemical analyte
- signal
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Expired - Fee Related
Links
Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/0002—Remote monitoring of patients using telemetry, e.g. transmission of vital signals via a communication network
- A61B5/0031—Implanted circuitry
-
- 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
- A61B5/14532—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 for measuring glucose, e.g. by tissue impedance measurement
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B2560/00—Constructional details of operational features of apparatus; Accessories for medical measuring apparatus
- A61B2560/02—Operational features
- A61B2560/0204—Operational features of power management
- A61B2560/0214—Operational features of power management of power generation or supply
- A61B2560/0219—Operational features of power management of power generation or supply of externally powered implanted units
Abstract
An implanted sensing device (1) for monitoring an analyte (e.g. blood-glucose) includes a non-toxic macromolecular material (2) encapsulated within an envelope (3) of bio-compatible semi-permeable membrane. A sensor (4) responds to change of a physical property (e.g. viscosity) of the material (2) when the analyte contacts the material (2), to signal the change to a measurement circuit (50) that together with the sensor (4) and a transponder (6) are included within the envelope (3). The transponder (6) is interrogated externally of the implanted sensor (1) by an interrogation unit (7) to transmit measurement data for processing and storage. The interrogation signal is utilised within the device (1) to power the circuit (5) and transponder (6) and conveys data to the device for re-calibration or re-setting of signal- datum values to compensate for ageing or drift.
Description
IMPLANTABLE BLOOD GLUCOSE SENSOR SYSTEM
This invention relates to sensing devices and systems, and is particularly concerned with sensing devices and systems for use in monitoring the presence or activity of specific chemical analytes.
According to one aspect of the present invention a sensing device for use in monitoring the presence or activity of a specific chemical analyte, comprises an enclosure having a membrane-wall that is semi-permeable to said chemical analyte, macromolecular material contained within the enclosure, said material exhibiting physical change in response to contact with said chemical analyte, a sensor contained within the enclosure to respond to said physical change, and means for transmitting a signal from said sensing device dependent on the response of said sensor.
The sensing device according to the invention is especially applicable for monitoring the presence or level of activity of a specific bio-chemical, drug or other analyte in vivo, within the body of a human or animal patient. In this context the sensing device may be provided for implant subcutaneously or otherwise within the patient so that the particular analyte can be sensed as it permeates the semi-permeable wall of the device.
The said material may be such as to exhibit change in a rheological parameter thereof in response to the analyte.
The parameter may be viscosity, and the material, which may be for example a mixture of concanavalin A and ficoll, may be responsive to the presence of glucose to exhibit a change of its viscosity or other parameter. In the context of response to glucose, the sensing device of the invention has particular application for in vivo monitoring of the blood-glucose of diabetic patients.
The means for transmitting a signal from the sensing device of the invention may be contained within said enclosure, and said enclosure may be in the form of a capsule wholly or substantially wholly of semi-permeable membrane. Moreover, the means for transmitting a signal from the sensing device may include means for deriving digital data in accordance with the response of the sensor and for transmitting this from said sensing device.
According to another aspect of the present invention a sensing system for use in monitoring the presence or activity of a specific chemical analyte, comprises a sensing device and interrogating means that is operable for interrogating said sensing device, said sensing device comprising an enclosure having a membrane-wall that is semi-permeable to said chemical analyte, macromolecular material contained within the enclosure, said material exhibiting physical change in response to contact with said chemical analyte, a sensor contained within the enclosure to respond to said physical change, and means operable in response to interrogation of said sensing means by said interrogating means for transmitting a signal dependent on the response of said sensor, to said interrogating means.
The signal dependent on the response of said sensor may be transmitted to said interrogating means by electromagnetic-wave transmission. Similarly, interrogation of said sensing means may be effected by electromagnetic-wave transmission from said interrogating means. In this latter case, electrical power for the means operable in response to interrogation of said sensing means, may be derived from the electromagnetic-wave interrogating transmission.
According to another aspect of the present invention, there is provided a subcutaneous-implant capsule for use in monitoring at least one of presence and activity of a specific chemical analyte, the subcutaneous-implant capsule comprising: an external wall defining an enclosure for subcutaneous implantation, said wall having at least a portion that is semi-permeable to said chemical analyte; a macromolecular material contained within the enclosure, said material exhibiting physical change in response to contact with said chemical analyte; a sensor also contained within the enclosure for providing a response to said physical change in the macromolecular material, and a transmitter for transmitting a signal from said sensor wherein the external wall of the enclosure totally encloses said sensor, said transmitter and the macromolecular material.
According to another aspect of the present invention, there is provided a sensing system for use in monitoring at least one of presence and activity of a specific chemical analyte, the sensing system comprising: a bio-compatible implant capsule and interrogating means that is operable for interrogating said capsule, said capsule defining a wall enclosure for bio-compatible implantation, said wall enclosure being at least partially semi-permeable to the specific chemical analyte, a macromolecular material contained within the enclosure, said macromolecular material exhibiting a physical change in response to contact with said specific chemical analyte, a sensor located within the enclosure to respond to said physical change, and a transmitter operable in response to interrogation of said capsule by said interrogating means, the transmitter transmitting to said interrogating means a signal dependent on the response of said sensor, and wherein said wall enclosure totally encloses said sensor, said transmitter and said material.
According to another aspect of the present invention, there is provided a sensing device for use in monitoring at least one of presence and activity of a specific chemical analyte, the sensing apparatus comprising:
an enclosure having a membrane-wall that is semi-permeable to said chemical analyte, a macromolecular material contained within the enclosure, said macromolecular material exhibiting physical change in response to contact with said chemical analyte, a sensor contained within the enclosure, said sensor being responsive to said physical change exhibited by said macromolecular material to provide an electrical response to said change, and further means contained within the enclosure, said further means being connected within the enclosure to said sensor, and said further means comprising means for deriving a signal dependent on said electrical response of said sensor, and signal-transmitting means for transmitting said signal from within said enclosure to radiate from the sensing device.
According to another aspect of the present invention, there is provided a sensing system for use in monitoring at least one of presence and activity of a specific chemical analyte, comprising a sensing device and interrogating means that is operable for interrogating said sensing device, said sensing device comprising an enclosure having a membrane-wall that is semi-permeable to said chemical analyte, macromolecular material contained within the enclosure, said material exhibiting physical change in response to contact with said chemical analyte, a sensor contained within the enclosure to respond to said physical change, and further means contained within the enclosure, 4a said further means being connected within said enclosure to said sensor, and said further means being operative in response to interrogation of said sensing means by said interrogating means to transmit to said interrogation means a signal dependent on the response of said sensor to said physical change, said signal being transmitted to said interrogation means by radiation from within the sensing device.
According to another aspect of the present invention, there is provided a sensing device for use in monitoring at least one of the presence and activity of a specific chemical analyte, the sensing device comprising: an enclosure having a membrane-wall that is semi-permeable to said chemical analyte; a macromolecular material contained within the enclosure, said macromolecular material exhibiting physical change in response to contact with said chemical analyte; a sensor contained within the enclosure to respond to said physical change of the macromolecular material in response to contact with said chemical analyte, and a transmitter dependent on the response of said sensor for transmitting a signal from said sensing device; and wherein said macromolecular material comprises a material having a rheological parameter exhibiting a change thereof in response to contact with said chemical analyte, and said response of the sensor is dependent upon said change in said rheological parameter.
A sensing system, and sensing devices for use therein, all according to embodiments of the present invention will now be described, by way of example, with reference to the accompanying drawings, in which: -4b Figure 1 is a block schematic diagram illustrating the sensing system according to an embodiment of the present invention;
Figure 2 is a sectional view of a sensing device according to an embodiment of the invention, that forms part of the system of Figure 1;
Figure 3 is a block-schematic representation of the electrical circuitry of the sensing device of Figure 2;
Figure 4 is a block-schematic representation of electrical circuitry that may be used as an alternative to the electrical circuitry of Figure 3 for the sensing device of Figure 2;
Figure 5 provides a block-schematic representation of the electrical circuitry of a transponder of the sensing device of Figure 2;
Figure 6 provides a block-schematic representation of the electrical circuitry of an interrogator unit that forms part of the sensing system of Figure 1; and Figure 7 is illustrative of a practical implementation of the sensing system of Figure 1.
The sensing system to be described is for use for in vivo monitoring of the presence or level of activity of a specific bio-chemical, drug or other analyte within a patient.
Referring to Figure 1, the sensing system includes a sensing device 1 that is implanted subcutaneously in the patient. The sensing device 1 includes a non-toxic macromolecular mixture or compound 2 encapsulated within an envelope 3 of bio-compatible semi-permeable membrane. The 4c mixture or compound 2 has the characteristic that its physical properties change when it is in the presence of the relevant analyte, and the change in the physical condition of the mixture or compound 2 that in this respect takes place when the analyte permeates the wall of the envelope 3 is sensed by a sensor 4. The sensor 4 is encapsulated with the mixture or compound 2 within the envelope 3, and supplies an electric signal dependent on the sensed physical-change to a measurement circuit 5.
The circuit 5, like the device 4, is encapsulated with the mixture or compound 2 within the envelope 3, and from the signal supplied by the sensor 4 derives a digital-data signal that provides a measure of the physical condition of the mixture or compound 2 sensed. This signal is supplied to a radio-frequency transponder 6 which is also encapsulated with the mixture or compound 2 within the envelope 3.
The transponder 6 is interrogated externally of the implanted sensing device 1 by actuation of an interrogation unit 7. The measurement data derived by the circuit 5 is in consequence transmitted from the transponder 6 and this data as received by the unit 7 is either processed and stored within the unit 7 locally, or communicated to a data-acquisition system (not shown).
The activity of the chemical analyte within the patient can be determined from the measurement data received from 5 the sensing device 1 and can thus be continually or periodically monitored by the system of the invention.
Moreover, suitable alarm and/or other action (for example, administration of a drug) can be taken when the activity of the analyte makes this desirable or necessary in the context of the monitoring operation.
The sensing device of the invention has particular application in the monitoring of blood-glucose in diabetic patients. Attempts have been made to develop an in vivo glucose sensor for this purpose, focused on adapting known biosensor-technology. But these attempts have been largely frustrated by problems of bio-compatibility, drift, instability, fouling, infection and electrical interconnection with the implant. However, the principal problems arise from the inherent instability of any enzyme-based system which limits the potential life of the sensing device and the design of a reliable interface between the indwelling sensing device and its associated, external electronics. These problems can be to overcome to a major extent with the sensing system of the present invention in that the enclosure may be bio-compatible and contain a non-toxic macromolecular mixture or compound responsive by physical rather than bio-chemical change to the blood-glucose level of the patient. The physical response of the macromolecular mixture or compound is reversible so that the sensing device can have a very long operational life.
Although described above as utilised as an implant, the sensing device may be used in other contexts where it is desirable or necessary to provide for monitoring the presence or activity of a specific chemical, using self-... ...-~ . _ contained sensing without the necessity for external electrical or other connection with the sensing device.
The mixture or compound 2 has an important role in the sensing system and device of the invention in that it exhibits a physical change in response to the analyte that is being monitored. By way of example, the material 2 may be a mixture of concanavalin A and ficoll which exhibits a rheological change to glucose. Other suitable mixtures or compounds may be used, and for longevity and optimum performance may be custom synthesised using molecular-design or molecular-imprinting methods. The involvement of non-proteinaceous synthetic recognition molecules may be found preferable.
The physical change of the mixture or compound 2 sensed by the sensor 4 within the sensing device 1 may, as indicated above, be rheological, and may be specifically change of viscosity. By way of alternative, the physical change sensed may be related to electrical conductivity, density, volume, pressure or luminosity or fluorescence.
Luminosity or fluorescence may be sensed by the sensor 4 during stimulation of the mixture or compound 2 by visible or non-visible light incident on the device 1 from an externally-located laser. A similar stimulation of a sensed physical property may be achieved using acoustic radiation.
The semi-permeable envelope 3 may be fabricated of metallic, semi-synthetic or natural materials, examples of which are sintered titanium, polyvinyl chloride, silicone rubber, nylon and cellulose derivatives. For in vivo applications of the sensing device 1, the membrane is desirably treated with a chemical such as phosphoryl choline, or derivatives, to minimize cell or protein adhesion.
This invention relates to sensing devices and systems, and is particularly concerned with sensing devices and systems for use in monitoring the presence or activity of specific chemical analytes.
According to one aspect of the present invention a sensing device for use in monitoring the presence or activity of a specific chemical analyte, comprises an enclosure having a membrane-wall that is semi-permeable to said chemical analyte, macromolecular material contained within the enclosure, said material exhibiting physical change in response to contact with said chemical analyte, a sensor contained within the enclosure to respond to said physical change, and means for transmitting a signal from said sensing device dependent on the response of said sensor.
The sensing device according to the invention is especially applicable for monitoring the presence or level of activity of a specific bio-chemical, drug or other analyte in vivo, within the body of a human or animal patient. In this context the sensing device may be provided for implant subcutaneously or otherwise within the patient so that the particular analyte can be sensed as it permeates the semi-permeable wall of the device.
The said material may be such as to exhibit change in a rheological parameter thereof in response to the analyte.
The parameter may be viscosity, and the material, which may be for example a mixture of concanavalin A and ficoll, may be responsive to the presence of glucose to exhibit a change of its viscosity or other parameter. In the context of response to glucose, the sensing device of the invention has particular application for in vivo monitoring of the blood-glucose of diabetic patients.
The means for transmitting a signal from the sensing device of the invention may be contained within said enclosure, and said enclosure may be in the form of a capsule wholly or substantially wholly of semi-permeable membrane. Moreover, the means for transmitting a signal from the sensing device may include means for deriving digital data in accordance with the response of the sensor and for transmitting this from said sensing device.
According to another aspect of the present invention a sensing system for use in monitoring the presence or activity of a specific chemical analyte, comprises a sensing device and interrogating means that is operable for interrogating said sensing device, said sensing device comprising an enclosure having a membrane-wall that is semi-permeable to said chemical analyte, macromolecular material contained within the enclosure, said material exhibiting physical change in response to contact with said chemical analyte, a sensor contained within the enclosure to respond to said physical change, and means operable in response to interrogation of said sensing means by said interrogating means for transmitting a signal dependent on the response of said sensor, to said interrogating means.
The signal dependent on the response of said sensor may be transmitted to said interrogating means by electromagnetic-wave transmission. Similarly, interrogation of said sensing means may be effected by electromagnetic-wave transmission from said interrogating means. In this latter case, electrical power for the means operable in response to interrogation of said sensing means, may be derived from the electromagnetic-wave interrogating transmission.
According to another aspect of the present invention, there is provided a subcutaneous-implant capsule for use in monitoring at least one of presence and activity of a specific chemical analyte, the subcutaneous-implant capsule comprising: an external wall defining an enclosure for subcutaneous implantation, said wall having at least a portion that is semi-permeable to said chemical analyte; a macromolecular material contained within the enclosure, said material exhibiting physical change in response to contact with said chemical analyte; a sensor also contained within the enclosure for providing a response to said physical change in the macromolecular material, and a transmitter for transmitting a signal from said sensor wherein the external wall of the enclosure totally encloses said sensor, said transmitter and the macromolecular material.
According to another aspect of the present invention, there is provided a sensing system for use in monitoring at least one of presence and activity of a specific chemical analyte, the sensing system comprising: a bio-compatible implant capsule and interrogating means that is operable for interrogating said capsule, said capsule defining a wall enclosure for bio-compatible implantation, said wall enclosure being at least partially semi-permeable to the specific chemical analyte, a macromolecular material contained within the enclosure, said macromolecular material exhibiting a physical change in response to contact with said specific chemical analyte, a sensor located within the enclosure to respond to said physical change, and a transmitter operable in response to interrogation of said capsule by said interrogating means, the transmitter transmitting to said interrogating means a signal dependent on the response of said sensor, and wherein said wall enclosure totally encloses said sensor, said transmitter and said material.
According to another aspect of the present invention, there is provided a sensing device for use in monitoring at least one of presence and activity of a specific chemical analyte, the sensing apparatus comprising:
an enclosure having a membrane-wall that is semi-permeable to said chemical analyte, a macromolecular material contained within the enclosure, said macromolecular material exhibiting physical change in response to contact with said chemical analyte, a sensor contained within the enclosure, said sensor being responsive to said physical change exhibited by said macromolecular material to provide an electrical response to said change, and further means contained within the enclosure, said further means being connected within the enclosure to said sensor, and said further means comprising means for deriving a signal dependent on said electrical response of said sensor, and signal-transmitting means for transmitting said signal from within said enclosure to radiate from the sensing device.
According to another aspect of the present invention, there is provided a sensing system for use in monitoring at least one of presence and activity of a specific chemical analyte, comprising a sensing device and interrogating means that is operable for interrogating said sensing device, said sensing device comprising an enclosure having a membrane-wall that is semi-permeable to said chemical analyte, macromolecular material contained within the enclosure, said material exhibiting physical change in response to contact with said chemical analyte, a sensor contained within the enclosure to respond to said physical change, and further means contained within the enclosure, 4a said further means being connected within said enclosure to said sensor, and said further means being operative in response to interrogation of said sensing means by said interrogating means to transmit to said interrogation means a signal dependent on the response of said sensor to said physical change, said signal being transmitted to said interrogation means by radiation from within the sensing device.
According to another aspect of the present invention, there is provided a sensing device for use in monitoring at least one of the presence and activity of a specific chemical analyte, the sensing device comprising: an enclosure having a membrane-wall that is semi-permeable to said chemical analyte; a macromolecular material contained within the enclosure, said macromolecular material exhibiting physical change in response to contact with said chemical analyte; a sensor contained within the enclosure to respond to said physical change of the macromolecular material in response to contact with said chemical analyte, and a transmitter dependent on the response of said sensor for transmitting a signal from said sensing device; and wherein said macromolecular material comprises a material having a rheological parameter exhibiting a change thereof in response to contact with said chemical analyte, and said response of the sensor is dependent upon said change in said rheological parameter.
A sensing system, and sensing devices for use therein, all according to embodiments of the present invention will now be described, by way of example, with reference to the accompanying drawings, in which: -4b Figure 1 is a block schematic diagram illustrating the sensing system according to an embodiment of the present invention;
Figure 2 is a sectional view of a sensing device according to an embodiment of the invention, that forms part of the system of Figure 1;
Figure 3 is a block-schematic representation of the electrical circuitry of the sensing device of Figure 2;
Figure 4 is a block-schematic representation of electrical circuitry that may be used as an alternative to the electrical circuitry of Figure 3 for the sensing device of Figure 2;
Figure 5 provides a block-schematic representation of the electrical circuitry of a transponder of the sensing device of Figure 2;
Figure 6 provides a block-schematic representation of the electrical circuitry of an interrogator unit that forms part of the sensing system of Figure 1; and Figure 7 is illustrative of a practical implementation of the sensing system of Figure 1.
The sensing system to be described is for use for in vivo monitoring of the presence or level of activity of a specific bio-chemical, drug or other analyte within a patient.
Referring to Figure 1, the sensing system includes a sensing device 1 that is implanted subcutaneously in the patient. The sensing device 1 includes a non-toxic macromolecular mixture or compound 2 encapsulated within an envelope 3 of bio-compatible semi-permeable membrane. The 4c mixture or compound 2 has the characteristic that its physical properties change when it is in the presence of the relevant analyte, and the change in the physical condition of the mixture or compound 2 that in this respect takes place when the analyte permeates the wall of the envelope 3 is sensed by a sensor 4. The sensor 4 is encapsulated with the mixture or compound 2 within the envelope 3, and supplies an electric signal dependent on the sensed physical-change to a measurement circuit 5.
The circuit 5, like the device 4, is encapsulated with the mixture or compound 2 within the envelope 3, and from the signal supplied by the sensor 4 derives a digital-data signal that provides a measure of the physical condition of the mixture or compound 2 sensed. This signal is supplied to a radio-frequency transponder 6 which is also encapsulated with the mixture or compound 2 within the envelope 3.
The transponder 6 is interrogated externally of the implanted sensing device 1 by actuation of an interrogation unit 7. The measurement data derived by the circuit 5 is in consequence transmitted from the transponder 6 and this data as received by the unit 7 is either processed and stored within the unit 7 locally, or communicated to a data-acquisition system (not shown).
The activity of the chemical analyte within the patient can be determined from the measurement data received from 5 the sensing device 1 and can thus be continually or periodically monitored by the system of the invention.
Moreover, suitable alarm and/or other action (for example, administration of a drug) can be taken when the activity of the analyte makes this desirable or necessary in the context of the monitoring operation.
The sensing device of the invention has particular application in the monitoring of blood-glucose in diabetic patients. Attempts have been made to develop an in vivo glucose sensor for this purpose, focused on adapting known biosensor-technology. But these attempts have been largely frustrated by problems of bio-compatibility, drift, instability, fouling, infection and electrical interconnection with the implant. However, the principal problems arise from the inherent instability of any enzyme-based system which limits the potential life of the sensing device and the design of a reliable interface between the indwelling sensing device and its associated, external electronics. These problems can be to overcome to a major extent with the sensing system of the present invention in that the enclosure may be bio-compatible and contain a non-toxic macromolecular mixture or compound responsive by physical rather than bio-chemical change to the blood-glucose level of the patient. The physical response of the macromolecular mixture or compound is reversible so that the sensing device can have a very long operational life.
Although described above as utilised as an implant, the sensing device may be used in other contexts where it is desirable or necessary to provide for monitoring the presence or activity of a specific chemical, using self-... ...-~ . _ contained sensing without the necessity for external electrical or other connection with the sensing device.
The mixture or compound 2 has an important role in the sensing system and device of the invention in that it exhibits a physical change in response to the analyte that is being monitored. By way of example, the material 2 may be a mixture of concanavalin A and ficoll which exhibits a rheological change to glucose. Other suitable mixtures or compounds may be used, and for longevity and optimum performance may be custom synthesised using molecular-design or molecular-imprinting methods. The involvement of non-proteinaceous synthetic recognition molecules may be found preferable.
The physical change of the mixture or compound 2 sensed by the sensor 4 within the sensing device 1 may, as indicated above, be rheological, and may be specifically change of viscosity. By way of alternative, the physical change sensed may be related to electrical conductivity, density, volume, pressure or luminosity or fluorescence.
Luminosity or fluorescence may be sensed by the sensor 4 during stimulation of the mixture or compound 2 by visible or non-visible light incident on the device 1 from an externally-located laser. A similar stimulation of a sensed physical property may be achieved using acoustic radiation.
The semi-permeable envelope 3 may be fabricated of metallic, semi-synthetic or natural materials, examples of which are sintered titanium, polyvinyl chloride, silicone rubber, nylon and cellulose derivatives. For in vivo applications of the sensing device 1, the membrane is desirably treated with a chemical such as phosphoryl choline, or derivatives, to minimize cell or protein adhesion.
The sensing system of Figure 1 may be used specifically for monitoring blood-glucose levels in a patient suffering from diabetes, and the sensing device of the system may then take the form shown in Figure 2.
Referring to Figure 2, the sensing device in this case has the form of a thin capsule 11 containing for example a mixture of concanavalin A and ficoll, as the macromolecular material 12. The mixture or compound 12 is encapsulated within a continuous, seamless wall 13 formed wholly or substantially wholly of semi-permeable membrane. A sensor 14 immersed in the mixture or compound 12 within the capsule 11 is connected through the wall of an environmental housing 15 that contains the electronic circuitry of the sensing device 11. In particular, the housing 15 incorporates a substrate 16 to which the sensor 14 is coupled and which carries measurement and transponder circuitry 17 together with the transponder antenna 18 and a charge-storage capacitor 19.
The capsule 11 is implanted subcutaneously in a patient to respond to change in his/her blood-glucose level. The change of viscosity that occurs in the mixture or compound 12 in response to the change in glucose level permeating the semi-permeable wall 13, is sensed by the sensor 14 and communicated to the circuitry 17. In particular, for a concanavalin A - ficoll mixture a large change in viscosity (for example, 1 to 10 mM) is exhibited between the minimum and maximum levels of a patient's blood-glucose level. The output of the sensor 14 in response to the change is translated within the circuitry 17 into data representative of the viscosity and, correspondingly, of the blood-glucose level, for transmission to the appropriate interrogation unit via the antenna 18.
Referring to Figure 2, the sensing device in this case has the form of a thin capsule 11 containing for example a mixture of concanavalin A and ficoll, as the macromolecular material 12. The mixture or compound 12 is encapsulated within a continuous, seamless wall 13 formed wholly or substantially wholly of semi-permeable membrane. A sensor 14 immersed in the mixture or compound 12 within the capsule 11 is connected through the wall of an environmental housing 15 that contains the electronic circuitry of the sensing device 11. In particular, the housing 15 incorporates a substrate 16 to which the sensor 14 is coupled and which carries measurement and transponder circuitry 17 together with the transponder antenna 18 and a charge-storage capacitor 19.
The capsule 11 is implanted subcutaneously in a patient to respond to change in his/her blood-glucose level. The change of viscosity that occurs in the mixture or compound 12 in response to the change in glucose level permeating the semi-permeable wall 13, is sensed by the sensor 14 and communicated to the circuitry 17. In particular, for a concanavalin A - ficoll mixture a large change in viscosity (for example, 1 to 10 mM) is exhibited between the minimum and maximum levels of a patient's blood-glucose level. The output of the sensor 14 in response to the change is translated within the circuitry 17 into data representative of the viscosity and, correspondingly, of the blood-glucose level, for transmission to the appropriate interrogation unit via the antenna 18.
The sensor 14 in this example may be of a kind which in response to change of viscosity of the mixture or compound 12, exhibits a change of piezo-mechanical coupling efficiency. This change can be used to create a voltage or phase change in an applied signal. In the case in which phase-change is utilised, the circuitry 17 may take the form illustrated in Figure 3.
Referring to Figure 3, an oscillatory waveform is applied to the sensor 14 from an oscillator 20, and the output signal of the sensor 14 is supplied via a voltage-buffer stage 21 to a phase detector 22 for comparison with the output of a voltage-controlled oscillator 23 in a phase-locked loop that includes a loop-filter 24. The resultant output signal of the filter 24 is supplied with the output signal of the oscillator 20 to a signal processor 25 to derive the relevant data from the detected phase shift between the two signals, and to supply this to a transponder circuit 26.
Electrical energy to power the electronics of the capsule 11 is derived within the transponder circuit 26 without the need for the capsule 11 to include a battery. The required power is derived from the interrogation signal transmitted from the interrogation unit 7 (Figure 1).
This signal received via the antenna 18 charges the storage capacitor 19 and it is from this charge that the circuitry 17 is powered to gather the blood-glucose measurement data and transmit it via the antenna 18 for external use.
In an alternative construction of the capsule 11, the sensor 14 used is of a form that utilises the transmission of acoustic waves within the mixture or compound 12. The form of sensor 14 and circuitry 17 used in this case is shown in Figure 4 and will now be described.
,...~.._..._... _ ....,..., .~,.,._,..._..
Referring to Figure 3, an oscillatory waveform is applied to the sensor 14 from an oscillator 20, and the output signal of the sensor 14 is supplied via a voltage-buffer stage 21 to a phase detector 22 for comparison with the output of a voltage-controlled oscillator 23 in a phase-locked loop that includes a loop-filter 24. The resultant output signal of the filter 24 is supplied with the output signal of the oscillator 20 to a signal processor 25 to derive the relevant data from the detected phase shift between the two signals, and to supply this to a transponder circuit 26.
Electrical energy to power the electronics of the capsule 11 is derived within the transponder circuit 26 without the need for the capsule 11 to include a battery. The required power is derived from the interrogation signal transmitted from the interrogation unit 7 (Figure 1).
This signal received via the antenna 18 charges the storage capacitor 19 and it is from this charge that the circuitry 17 is powered to gather the blood-glucose measurement data and transmit it via the antenna 18 for external use.
In an alternative construction of the capsule 11, the sensor 14 used is of a form that utilises the transmission of acoustic waves within the mixture or compound 12. The form of sensor 14 and circuitry 17 used in this case is shown in Figure 4 and will now be described.
,...~.._..._... _ ....,..., .~,.,._,..._..
Referring to Figure 4, the sensor 14 in this case comprises spaced piezoelectric transducer elements 30 and 31 immersed in the mixture or compound 12. The element 30 is energised from an oscillator 32 and the consequent vibrations transmitted via the mixture or compound 12 are detected by the element 31. The resultant signal derived by the element 31, which can be readily correlated in amplitude and frequency with viscosity of the mixture or compound 12, is applied via a voltage buffer stage 33 for comparison with the output signal of the oscillator 32, in a comparator 34. The output signal of the comparator 34 is utilised within a processor 35 to derive in relation to the output signal of the oscillator 32, the desired measurement data for indicating blood-glucose level. Data stored in a non-volatile memory 36 sets the datum value against which the measurement data is derived for transmission by a transponder circuit 37.
The transponder 6 of Figure 1 (or specifically the transponder units 26 and 37 of Figures 3 and 4 respectively) may be constructed as illustrated in Figure 5.
Referring to Figure 5, the radio-frequency interrogation signal is received in the antenna 18 within a resonant circuit that is formed by an antenna coil 40 with shunt capacitor 41. The oscillatory output across the coil 40 is supplied via a rectifier 42 to charge the storage capacitor 19 in providing electrical power to the electronics of the capsule 11 via a regulator 43, and is also supplied via a comparator 44 to a demodulator 45.
The demodulator 45 derives data that is transmitted to the transponder 18 in the interrogation signal, and supplies this to a processor unit 46. This data is used within the processor unit 46 for protocol synchronisation and to set and/or re-set datum levels for the measurement data signalled by the measurement circuit 5 from the sensor 4 (Figure 1).
The data derived by the processor unit 46 is stored in a 5 memory 47. This stored data is read out and under control of the processor unit 46 is combined with other data in a MUX unit 48 for transmission via a modulator 49 and coil 50 of the antenna 18. Transmission is controlled by the processor unit 46 in dependence upon 10 power-supply operation as determined by a power on/reset unit 51.
The interrogation unit 7 of the system of Figure 1 may be as illustrated in Figure 6.
Referring to Figure 6, the transmission of the interrogation signal to the sensing device 1 is effected via an antenna 60 that is supplied with the signal from a modulator 61 via a power-amplifier 62. The modulator 61 modulates the transmitted radio-frequency signal with data that is derived from a control unit 63 that includes digital storage. This data is derived within the unit 63 or within a data-acquisition station (not shown) to which it may be connected, in dependence upon the data that is to be transmitted by the sensing device 1 and the datum levels to which measurement is to be carried out therein.
The data signals received by the antenna 60 from the sensing device 1 are amplified in an amplifier 64 and demodulated in a demodulator 65 for supply to the unit 63. A comparator 66 is active to derive control input signals for the unit 63 dependent upon the transmitted and received signals.
The interrogation unit 7 of Figure 1 may be implemented in the form of a unit that is worn on the wrist in the manner of a wristwatch. This is illustrated in Figure 7 where a capsule 70 of the same form as capsule 11 of Figure 2 is to be understood as having been implanted subcutaneously in the wrist of a patient, and the interrogation unit 71 in this case has straps 72 for holding it to the wrist immediately over the implanted capsule 70.
Referring to Figure 7, an antenna coil 73 is incorporated in the base of the unit 71 beneath the associated electronic circuitry 74. The unit 71 also incorporates an LCD display 75 and an audible-alarm facility 76 together with push-buttons 77 for setting data into the circuitry 74 and display 75.
The transponder 6 of Figure 1 (or specifically the transponder units 26 and 37 of Figures 3 and 4 respectively) may be constructed as illustrated in Figure 5.
Referring to Figure 5, the radio-frequency interrogation signal is received in the antenna 18 within a resonant circuit that is formed by an antenna coil 40 with shunt capacitor 41. The oscillatory output across the coil 40 is supplied via a rectifier 42 to charge the storage capacitor 19 in providing electrical power to the electronics of the capsule 11 via a regulator 43, and is also supplied via a comparator 44 to a demodulator 45.
The demodulator 45 derives data that is transmitted to the transponder 18 in the interrogation signal, and supplies this to a processor unit 46. This data is used within the processor unit 46 for protocol synchronisation and to set and/or re-set datum levels for the measurement data signalled by the measurement circuit 5 from the sensor 4 (Figure 1).
The data derived by the processor unit 46 is stored in a 5 memory 47. This stored data is read out and under control of the processor unit 46 is combined with other data in a MUX unit 48 for transmission via a modulator 49 and coil 50 of the antenna 18. Transmission is controlled by the processor unit 46 in dependence upon 10 power-supply operation as determined by a power on/reset unit 51.
The interrogation unit 7 of the system of Figure 1 may be as illustrated in Figure 6.
Referring to Figure 6, the transmission of the interrogation signal to the sensing device 1 is effected via an antenna 60 that is supplied with the signal from a modulator 61 via a power-amplifier 62. The modulator 61 modulates the transmitted radio-frequency signal with data that is derived from a control unit 63 that includes digital storage. This data is derived within the unit 63 or within a data-acquisition station (not shown) to which it may be connected, in dependence upon the data that is to be transmitted by the sensing device 1 and the datum levels to which measurement is to be carried out therein.
The data signals received by the antenna 60 from the sensing device 1 are amplified in an amplifier 64 and demodulated in a demodulator 65 for supply to the unit 63. A comparator 66 is active to derive control input signals for the unit 63 dependent upon the transmitted and received signals.
The interrogation unit 7 of Figure 1 may be implemented in the form of a unit that is worn on the wrist in the manner of a wristwatch. This is illustrated in Figure 7 where a capsule 70 of the same form as capsule 11 of Figure 2 is to be understood as having been implanted subcutaneously in the wrist of a patient, and the interrogation unit 71 in this case has straps 72 for holding it to the wrist immediately over the implanted capsule 70.
Referring to Figure 7, an antenna coil 73 is incorporated in the base of the unit 71 beneath the associated electronic circuitry 74. The unit 71 also incorporates an LCD display 75 and an audible-alarm facility 76 together with push-buttons 77 for setting data into the circuitry 74 and display 75.
Claims (19)
1. A subcutaneous-implant capsule for use in monitoring at least one of presence and activity of a specific chemical analyte, the subcutaneous-implant capsule comprising: an external wall defining an enclosure for subcutaneous implantation, said wall having at least a portion that is semi-permeable to said chemical analyte; a macromolecular material contained within the enclosure, said material exhibiting physical change in response to contact with said chemical analyte; a sensor also contained within the enclosure for providing a response to said physical change in the macromolecular material, and a transmitter for transmitting a signal from said sensor wherein the external wall of the enclosure totally encloses said sensor, said transmitter and the macromolecular material.
2. The subcutaneous-implant capsule according to claim 1, wherein the entire wall of the enclosure is made wholly of semi-permeable membrane.
3. The subcutaneous-implant capsule according to claim 1 or 2, further comprising the macromolecular material having a rheological parameter exhibiting a reaction in contact with said chemical analyte wherein the response provided by the sensor is dependent upon the reaction of the rheological parameter.
4. The subcutaneous-implant capsule according to any one of claims 1 to 3, wherein the chemical analyte comprises glucose and the macromolecular material exhibits the physical change in contact with glucose.
5. The subcutaneous-implant capsule according to claim 3 or 4, wherein said macromolecular material is a mixture of concanavalin A and ficoll.
6. The subcutaneous-implant capsule according to any one of claims 1 to 5, wherein said transmitter comprises a device for deriving digital data in accordance with said response of the sensor and for transmitting said digital data from said capsule.
7. The subcutaneous-implant capsule according to any one of claims 1 to 6, wherein said transmitter comprises a receiving device for externally-applied adjustment of a datum and a deriving, device for deriving a signal relative to said datum.
8. A sensing system for use in monitoring at least one of presence and activity of a specific chemical analyte, the sensing system comprising: a bio-compatible implant capsule and interrogating means that is operable for interrogating said capsule, said capsule defining a wall enclosure for bio-compatible implantation, said wall enclosure being at least partially semi-permeable to the specific chemical analyte, a macromolecular material contained within the enclosure, said macromolecular material exhibiting a physical change in response to contact with said specific chemical analyte, a sensor located within the enclosure to respond to said physical change, and a transmitter operable in response to interrogation of said capsule by said interrogating means, the transmitter transmitting to said interrogating means a signal dependent on the response of said sensor, and wherein said wall enclosure totally encloses said sensor, said transmitter and said material.
9. A sensing system according to claim 8 wherein the signal dependent on the response of said sensor is transmitted to said interrogating means by electromagnetic-wave transmission.
10. A sensing system according to claim 8 or 9, wherein interrogation of said capsule is effected by electromagnetic-wave transmission from said interrogating means through said wall enclosure of said capsule.
11. A sensing system according to claim 10 wherein electrical power for said transmitter operable in response to interrogation of said capsule, is derived from the electromagnetic-wave interrogating transmission.
12. A sensing system according to any one of claims 8 to 11, wherein the chemical analyte comprises glucose and said material exhibits said physical change in response to contact therewith.
13. A sensing system according to any one of claims 8 to 12, wherein said material is a mixture of concanavalin A
and ficoll.
and ficoll.
14. A sensing system according to any one of claims 8 to 13, wherein said transmitter includes provision for adjustment of a datum in accordance with data transmitted by the interrogating means, and means for deriving said signal relative to said datum.
15. A sensing device for use in monitoring at least one of presence and activity of a specific chemical analyte, the sensing apparatus comprising: an enclosure having a membrane-wall that is semi-permeable to said chemical analyte, a macromolecular material contained within the enclosure, said macromolecular material exhibiting physical change in response to contact with said chemical analyte, a sensor contained within the enclosure, said sensor being responsive to said physical change exhibited by said macromolecular material to provide an electrical response to said change, and further means contained within the enclosure, said further means being connected within the enclosure to said sensor, and said further means comprising means for deriving a signal dependent on said electrical response of said sensor, and signal-transmitting means for transmitting said signal from within said enclosure to radiate from the sensing device.
16. A sensing device according to claim 15 wherein the signal-transmitting means is means for transmitting said signal by electromagnetic radiation.
17. A sensing system for use in monitoring at least one of presence and activity of a specific chemical analyte, comprising a sensing device and interrogating means that is operable for interrogating said sensing device, said sensing device comprising an enclosure having a membrane-wall that is semi-permeable to said chemical analyte, macromolecular material contained within the enclosure, said material exhibiting physical change in response to contact with said chemical analyte, a sensor contained within the enclosure to respond to said physical change, and further means contained within the enclosure, said further means being connected within said enclosure to said sensor, and said further means being operative in response to interrogation of said sensing means by said interrogating means to transmit to said interrogation means a signal dependent on the response of said sensor to said physical change, said signal being transmitted to said interrogation means by radiation from within the sensing device.
18. A sensing system according to claim 17 wherein the signal dependent on the response of said sensor is transmitted to said interrogating means by electromagnetic-wave transmission.
19. A sensing device for use in monitoring at least one of the presence and activity of a specific chemical analyte, the sensing device comprising: an enclosure having a membrane-wall that is semi-permeable to said chemical analyte; a macromolecular material contained within the enclosure, said macromolecular material exhibiting physical change in response to contact with said chemical analyte; a sensor contained within the enclosure to respond to said physical change of the macromolecular material in response to contact with said chemical analyte, and a transmitter dependent on the response of said sensor for transmitting a signal from said sensing device; and wherein said macromolecular material comprises a material having a rheological parameter exhibiting a change thereof in response to contact with said chemical analyte, and said response of the sensor is dependent upon said change in said rheological parameter.
Applications Claiming Priority (3)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
GBGB9805896.9A GB9805896D0 (en) | 1998-03-20 | 1998-03-20 | Remote analysis system |
GB9805896.9 | 1998-03-20 | ||
PCT/GB1999/000900 WO1999048419A1 (en) | 1998-03-20 | 1999-03-22 | Implantable blood glucose sensor system |
Publications (2)
Publication Number | Publication Date |
---|---|
CA2330553A1 CA2330553A1 (en) | 1999-09-30 |
CA2330553C true CA2330553C (en) | 2008-07-15 |
Family
ID=10828882
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
CA002330553A Expired - Fee Related CA2330553C (en) | 1998-03-20 | 1999-03-22 | Implantable blood glucose sensor system |
Country Status (13)
Country | Link |
---|---|
US (1) | US6579498B1 (en) |
EP (1) | EP1063916B1 (en) |
AT (1) | ATE341991T1 (en) |
AU (1) | AU752074B2 (en) |
CA (1) | CA2330553C (en) |
DE (1) | DE69933547T2 (en) |
DK (1) | DK1063916T3 (en) |
ES (1) | ES2277431T3 (en) |
GB (1) | GB9805896D0 (en) |
NZ (1) | NZ507666A (en) |
PT (1) | PT1063916E (en) |
WO (1) | WO1999048419A1 (en) |
ZA (1) | ZA200005714B (en) |
Families Citing this family (148)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US8527026B2 (en) | 1997-03-04 | 2013-09-03 | Dexcom, Inc. | Device and method for determining analyte levels |
US6001067A (en) | 1997-03-04 | 1999-12-14 | Shults; Mark C. | Device and method for determining analyte levels |
US7657297B2 (en) * | 2004-05-03 | 2010-02-02 | Dexcom, Inc. | Implantable analyte sensor |
US7192450B2 (en) | 2003-05-21 | 2007-03-20 | Dexcom, Inc. | Porous membranes for use with implantable devices |
US20050033132A1 (en) | 1997-03-04 | 2005-02-10 | Shults Mark C. | Analyte measuring device |
US8688188B2 (en) | 1998-04-30 | 2014-04-01 | Abbott Diabetes Care Inc. | Analyte monitoring device and methods of use |
US8974386B2 (en) | 1998-04-30 | 2015-03-10 | Abbott Diabetes Care Inc. | Analyte monitoring device and methods of use |
US9066695B2 (en) | 1998-04-30 | 2015-06-30 | Abbott Diabetes Care Inc. | Analyte monitoring device and methods of use |
US8480580B2 (en) | 1998-04-30 | 2013-07-09 | Abbott Diabetes Care Inc. | Analyte monitoring device and methods of use |
US6175752B1 (en) | 1998-04-30 | 2001-01-16 | Therasense, Inc. | Analyte monitoring device and methods of use |
US6949816B2 (en) | 2003-04-21 | 2005-09-27 | Motorola, Inc. | Semiconductor component having first surface area for electrically coupling to a semiconductor chip and second surface area for electrically coupling to a substrate, and method of manufacturing same |
US8346337B2 (en) | 1998-04-30 | 2013-01-01 | Abbott Diabetes Care Inc. | Analyte monitoring device and methods of use |
US8465425B2 (en) | 1998-04-30 | 2013-06-18 | Abbott Diabetes Care Inc. | Analyte monitoring device and methods of use |
DE19942898B4 (en) * | 1999-09-08 | 2007-07-05 | Disetronic Licensing Ag | dialysis probe |
US6658300B2 (en) * | 2000-12-18 | 2003-12-02 | Biosense, Inc. | Telemetric reader/charger device for medical sensor |
US6746404B2 (en) | 2000-12-18 | 2004-06-08 | Biosense, Inc. | Method for anchoring a medical device between tissue |
US6783499B2 (en) | 2000-12-18 | 2004-08-31 | Biosense, Inc. | Anchoring mechanism for implantable telemetric medical sensor |
US6636769B2 (en) * | 2000-12-18 | 2003-10-21 | Biosense, Inc. | Telemetric medical system and method |
US6560471B1 (en) | 2001-01-02 | 2003-05-06 | Therasense, Inc. | Analyte monitoring device and methods of use |
EP1397068A2 (en) | 2001-04-02 | 2004-03-17 | Therasense, Inc. | Blood glucose tracking apparatus and methods |
GB0111722D0 (en) * | 2001-05-14 | 2001-07-04 | Innovision Res & Tech Plc | Component identification |
ATE368351T1 (en) | 2001-05-14 | 2007-08-15 | Innovision Res & Tech Plc | PORTABLE COMMUNICATIONS DEVICE FOR USE IN A SALES SYSTEM |
GB0116860D0 (en) | 2001-07-10 | 2001-09-05 | Univ Montfort | Gel compositions |
US7591792B2 (en) * | 2001-07-26 | 2009-09-22 | Medrad, Inc. | Electromagnetic sensors for biological tissue applications and methods for their use |
US6702857B2 (en) | 2001-07-27 | 2004-03-09 | Dexcom, Inc. | Membrane for use with implantable devices |
US20030032874A1 (en) | 2001-07-27 | 2003-02-13 | Dexcom, Inc. | Sensor head for use with implantable devices |
US7323142B2 (en) | 2001-09-07 | 2008-01-29 | Medtronic Minimed, Inc. | Sensor substrate and method of fabricating same |
AU2002343567A1 (en) * | 2001-10-23 | 2003-05-06 | Medtronic Minimed Inc. | Method and system for non-vascular sensor implantation |
US8364229B2 (en) | 2003-07-25 | 2013-01-29 | Dexcom, Inc. | Analyte sensors having a signal-to-noise ratio substantially unaffected by non-constant noise |
US7613491B2 (en) | 2002-05-22 | 2009-11-03 | Dexcom, Inc. | Silicone based membranes for use in implantable glucose sensors |
US9247901B2 (en) | 2003-08-22 | 2016-02-02 | Dexcom, Inc. | Systems and methods for replacing signal artifacts in a glucose sensor data stream |
US8010174B2 (en) | 2003-08-22 | 2011-08-30 | Dexcom, Inc. | Systems and methods for replacing signal artifacts in a glucose sensor data stream |
US8260393B2 (en) | 2003-07-25 | 2012-09-04 | Dexcom, Inc. | Systems and methods for replacing signal data artifacts in a glucose sensor data stream |
US9282925B2 (en) | 2002-02-12 | 2016-03-15 | Dexcom, Inc. | Systems and methods for replacing signal artifacts in a glucose sensor data stream |
US7226978B2 (en) | 2002-05-22 | 2007-06-05 | Dexcom, Inc. | Techniques to improve polyurethane membranes for implantable glucose sensors |
US7736309B2 (en) | 2002-09-27 | 2010-06-15 | Medtronic Minimed, Inc. | Implantable sensor method and system |
US7226414B2 (en) * | 2002-10-09 | 2007-06-05 | Biotex, Inc. | Method and apparatus for analyte sensing |
DE60336834D1 (en) | 2002-10-09 | 2011-06-01 | Abbott Diabetes Care Inc | FUEL FEEDING DEVICE, SYSTEM AND METHOD |
US7727181B2 (en) | 2002-10-09 | 2010-06-01 | Abbott Diabetes Care Inc. | Fluid delivery device with autocalibration |
US7993108B2 (en) | 2002-10-09 | 2011-08-09 | Abbott Diabetes Care Inc. | Variable volume, shape memory actuated insulin dispensing pump |
AU2003303597A1 (en) | 2002-12-31 | 2004-07-29 | Therasense, Inc. | Continuous glucose monitoring system and methods of use |
US7134999B2 (en) | 2003-04-04 | 2006-11-14 | Dexcom, Inc. | Optimized sensor geometry for an implantable glucose sensor |
US7679407B2 (en) | 2003-04-28 | 2010-03-16 | Abbott Diabetes Care Inc. | Method and apparatus for providing peak detection circuitry for data communication systems |
US7875293B2 (en) | 2003-05-21 | 2011-01-25 | Dexcom, Inc. | Biointerface membranes incorporating bioactive agents |
US8066639B2 (en) | 2003-06-10 | 2011-11-29 | Abbott Diabetes Care Inc. | Glucose measuring device for use in personal area network |
US20040256452A1 (en) * | 2003-06-19 | 2004-12-23 | Coughlin Michael E. | RFID tag and method of user verification |
JP2007500336A (en) | 2003-07-25 | 2007-01-11 | デックスコム・インコーポレーテッド | Electrode system for electrochemical sensors |
US8282549B2 (en) | 2003-12-09 | 2012-10-09 | Dexcom, Inc. | Signal processing for continuous analyte sensor |
EP1648298A4 (en) | 2003-07-25 | 2010-01-13 | Dexcom Inc | Oxygen enhancing membrane systems for implantable devices |
US9763609B2 (en) | 2003-07-25 | 2017-09-19 | Dexcom, Inc. | Analyte sensors having a signal-to-noise ratio substantially unaffected by non-constant noise |
US8423113B2 (en) | 2003-07-25 | 2013-04-16 | Dexcom, Inc. | Systems and methods for processing sensor data |
WO2007120442A2 (en) | 2003-07-25 | 2007-10-25 | Dexcom, Inc. | Dual electrode system for a continuous analyte sensor |
US8369919B2 (en) | 2003-08-01 | 2013-02-05 | Dexcom, Inc. | Systems and methods for processing sensor data |
US7494465B2 (en) | 2004-07-13 | 2009-02-24 | Dexcom, Inc. | Transcutaneous analyte sensor |
US8886273B2 (en) | 2003-08-01 | 2014-11-11 | Dexcom, Inc. | Analyte sensor |
US7933639B2 (en) | 2003-08-01 | 2011-04-26 | Dexcom, Inc. | System and methods for processing analyte sensor data |
US7591801B2 (en) | 2004-02-26 | 2009-09-22 | Dexcom, Inc. | Integrated delivery device for continuous glucose sensor |
US20190357827A1 (en) | 2003-08-01 | 2019-11-28 | Dexcom, Inc. | Analyte sensor |
US7774145B2 (en) | 2003-08-01 | 2010-08-10 | Dexcom, Inc. | Transcutaneous analyte sensor |
US8275437B2 (en) | 2003-08-01 | 2012-09-25 | Dexcom, Inc. | Transcutaneous analyte sensor |
US9135402B2 (en) | 2007-12-17 | 2015-09-15 | Dexcom, Inc. | Systems and methods for processing sensor data |
US20100168657A1 (en) | 2003-08-01 | 2010-07-01 | Dexcom, Inc. | System and methods for processing analyte sensor data |
US8761856B2 (en) | 2003-08-01 | 2014-06-24 | Dexcom, Inc. | System and methods for processing analyte sensor data |
US8160669B2 (en) | 2003-08-01 | 2012-04-17 | Dexcom, Inc. | Transcutaneous analyte sensor |
US7276029B2 (en) | 2003-08-01 | 2007-10-02 | Dexcom, Inc. | System and methods for processing analyte sensor data |
US7519408B2 (en) | 2003-11-19 | 2009-04-14 | Dexcom, Inc. | Integrated receiver for continuous analyte sensor |
US7920906B2 (en) | 2005-03-10 | 2011-04-05 | Dexcom, Inc. | System and methods for processing analyte sensor data for sensor calibration |
US20140121989A1 (en) | 2003-08-22 | 2014-05-01 | Dexcom, Inc. | Systems and methods for processing analyte sensor data |
US20050083194A1 (en) * | 2003-10-20 | 2005-04-21 | Yuan-Yao Shen | Wireless vital signs transmission device in a physiological detector |
US9247900B2 (en) | 2004-07-13 | 2016-02-02 | Dexcom, Inc. | Analyte sensor |
US8774886B2 (en) | 2006-10-04 | 2014-07-08 | Dexcom, Inc. | Analyte sensor |
US11633133B2 (en) | 2003-12-05 | 2023-04-25 | Dexcom, Inc. | Dual electrode system for a continuous analyte sensor |
EP2239567B1 (en) | 2003-12-05 | 2015-09-02 | DexCom, Inc. | Calibration techniques for a continuous analyte sensor |
US8287453B2 (en) | 2003-12-05 | 2012-10-16 | Dexcom, Inc. | Analyte sensor |
US8423114B2 (en) | 2006-10-04 | 2013-04-16 | Dexcom, Inc. | Dual electrode system for a continuous analyte sensor |
US8364231B2 (en) | 2006-10-04 | 2013-01-29 | Dexcom, Inc. | Analyte sensor |
US8306592B2 (en) | 2003-12-19 | 2012-11-06 | Olympus Corporation | Capsule medical device |
JP4574993B2 (en) | 2004-01-16 | 2010-11-04 | オリンパス株式会社 | Lesion detection system |
EP1718198A4 (en) | 2004-02-17 | 2008-06-04 | Therasense Inc | Method and system for providing data communication in continuous glucose monitoring and management system |
US8808228B2 (en) | 2004-02-26 | 2014-08-19 | Dexcom, Inc. | Integrated medicament delivery device for use with continuous analyte sensor |
US8277713B2 (en) | 2004-05-03 | 2012-10-02 | Dexcom, Inc. | Implantable analyte sensor |
US8792955B2 (en) | 2004-05-03 | 2014-07-29 | Dexcom, Inc. | Transcutaneous analyte sensor |
US7125382B2 (en) * | 2004-05-20 | 2006-10-24 | Digital Angel Corporation | Embedded bio-sensor system |
US7783333B2 (en) | 2004-07-13 | 2010-08-24 | Dexcom, Inc. | Transcutaneous medical device with variable stiffness |
US20060020192A1 (en) | 2004-07-13 | 2006-01-26 | Dexcom, Inc. | Transcutaneous analyte sensor |
US7640048B2 (en) | 2004-07-13 | 2009-12-29 | Dexcom, Inc. | Analyte sensor |
US8073548B2 (en) * | 2004-08-24 | 2011-12-06 | Sensors For Medicine And Science, Inc. | Wristband or other type of band having an adjustable antenna for use with a sensor reader |
US7205701B2 (en) * | 2004-09-03 | 2007-04-17 | Honeywell International Inc. | Passive wireless acoustic wave chemical sensor |
DE102004048864A1 (en) * | 2004-10-07 | 2006-04-13 | Roche Diagnostics Gmbh | Analytical test element with wireless data transmission |
US8133178B2 (en) | 2006-02-22 | 2012-03-13 | Dexcom, Inc. | Analyte sensor |
CA2601441A1 (en) | 2005-03-21 | 2006-09-28 | Abbott Diabetes Care Inc. | Method and system for providing integrated medication infusion and analyte monitoring system |
US8744546B2 (en) | 2005-05-05 | 2014-06-03 | Dexcom, Inc. | Cellulosic-based resistance domain for an analyte sensor |
US8112240B2 (en) | 2005-04-29 | 2012-02-07 | Abbott Diabetes Care Inc. | Method and apparatus for providing leak detection in data monitoring and management systems |
US7768408B2 (en) | 2005-05-17 | 2010-08-03 | Abbott Diabetes Care Inc. | Method and system for providing data management in data monitoring system |
US7620437B2 (en) | 2005-06-03 | 2009-11-17 | Abbott Diabetes Care Inc. | Method and apparatus for providing rechargeable power in data monitoring and management systems |
FR2890438B1 (en) * | 2005-09-08 | 2007-11-30 | Peugeot Citroen Automobiles Sa | SENSOR STRUCTURE, IN PARTICULAR FOR A SEVERE ENVIRONMENT IN A MOTOR VEHICLE AND PREHEATING PLUG COMPRISING SUCH A SENSOR |
US7756561B2 (en) | 2005-09-30 | 2010-07-13 | Abbott Diabetes Care Inc. | Method and apparatus for providing rechargeable power in data monitoring and management systems |
US7583190B2 (en) | 2005-10-31 | 2009-09-01 | Abbott Diabetes Care Inc. | Method and apparatus for providing data communication in data monitoring and management systems |
US7766829B2 (en) | 2005-11-04 | 2010-08-03 | Abbott Diabetes Care Inc. | Method and system for providing basal profile modification in analyte monitoring and management systems |
US8344966B2 (en) | 2006-01-31 | 2013-01-01 | Abbott Diabetes Care Inc. | Method and system for providing a fault tolerant display unit in an electronic device |
EP1991110B1 (en) | 2006-03-09 | 2018-11-07 | DexCom, Inc. | Systems and methods for processing analyte sensor data |
US7620438B2 (en) | 2006-03-31 | 2009-11-17 | Abbott Diabetes Care Inc. | Method and system for powering an electronic device |
US8226891B2 (en) | 2006-03-31 | 2012-07-24 | Abbott Diabetes Care Inc. | Analyte monitoring devices and methods therefor |
WO2007120381A2 (en) | 2006-04-14 | 2007-10-25 | Dexcom, Inc. | Analyte sensor |
WO2007121763A1 (en) | 2006-04-20 | 2007-11-01 | Lifescan Scotland Limited | Method for transmitting data in a blood glucose system and corresponding blood glucose system |
WO2007134622A1 (en) * | 2006-05-22 | 2007-11-29 | Lifescan Scotland Limited | Blood glucose level measurement and wireless transmission unit |
US7920907B2 (en) | 2006-06-07 | 2011-04-05 | Abbott Diabetes Care Inc. | Analyte monitoring system and method |
US8579853B2 (en) | 2006-10-31 | 2013-11-12 | Abbott Diabetes Care Inc. | Infusion devices and methods |
WO2008061552A1 (en) * | 2006-11-23 | 2008-05-29 | Lifescan Scotland Limited | Blood glucose meter capable of wireless communication |
US20080189163A1 (en) * | 2007-02-05 | 2008-08-07 | Inquira, Inc. | Information management system |
US8732188B2 (en) | 2007-02-18 | 2014-05-20 | Abbott Diabetes Care Inc. | Method and system for providing contextual based medication dosage determination |
US8930203B2 (en) | 2007-02-18 | 2015-01-06 | Abbott Diabetes Care Inc. | Multi-function analyte test device and methods therefor |
US8123686B2 (en) | 2007-03-01 | 2012-02-28 | Abbott Diabetes Care Inc. | Method and apparatus for providing rolling data in communication systems |
US7928850B2 (en) * | 2007-05-08 | 2011-04-19 | Abbott Diabetes Care Inc. | Analyte monitoring system and methods |
US8456301B2 (en) | 2007-05-08 | 2013-06-04 | Abbott Diabetes Care Inc. | Analyte monitoring system and methods |
US8461985B2 (en) | 2007-05-08 | 2013-06-11 | Abbott Diabetes Care Inc. | Analyte monitoring system and methods |
US8665091B2 (en) | 2007-05-08 | 2014-03-04 | Abbott Diabetes Care Inc. | Method and device for determining elapsed sensor life |
US20200037875A1 (en) | 2007-05-18 | 2020-02-06 | Dexcom, Inc. | Analyte sensors having a signal-to-noise ratio substantially unaffected by non-constant noise |
EP2152350A4 (en) | 2007-06-08 | 2013-03-27 | Dexcom Inc | Integrated medicament delivery device for use with continuous analyte sensor |
EP4098177A1 (en) | 2007-10-09 | 2022-12-07 | DexCom, Inc. | Integrated insulin delivery system with continuous glucose sensor |
US8417312B2 (en) | 2007-10-25 | 2013-04-09 | Dexcom, Inc. | Systems and methods for processing sensor data |
US9839395B2 (en) | 2007-12-17 | 2017-12-12 | Dexcom, Inc. | Systems and methods for processing sensor data |
CA2715628A1 (en) | 2008-02-21 | 2009-08-27 | Dexcom, Inc. | Systems and methods for processing, transmitting and displaying sensor data |
US8682408B2 (en) | 2008-03-28 | 2014-03-25 | Dexcom, Inc. | Polymer membranes for continuous analyte sensors |
US8583204B2 (en) | 2008-03-28 | 2013-11-12 | Dexcom, Inc. | Polymer membranes for continuous analyte sensors |
US11730407B2 (en) | 2008-03-28 | 2023-08-22 | Dexcom, Inc. | Polymer membranes for continuous analyte sensors |
EP2326944B1 (en) | 2008-09-19 | 2020-08-19 | Dexcom, Inc. | Particle-containing membrane and particulate electrode for analyte sensors |
US8103456B2 (en) | 2009-01-29 | 2012-01-24 | Abbott Diabetes Care Inc. | Method and device for early signal attenuation detection using blood glucose measurements |
US8560082B2 (en) | 2009-01-30 | 2013-10-15 | Abbott Diabetes Care Inc. | Computerized determination of insulin pump therapy parameters using real time and retrospective data processing |
US8480581B2 (en) | 2009-03-24 | 2013-07-09 | Cardiac Pacemakers, Inc. | Systems and methods for anemia detection, monitoring, and treatment |
EP2410910A4 (en) | 2009-03-27 | 2014-10-15 | Dexcom Inc | Methods and systems for promoting glucose management |
WO2010129375A1 (en) | 2009-04-28 | 2010-11-11 | Abbott Diabetes Care Inc. | Closed loop blood glucose control algorithm analysis |
US9226701B2 (en) | 2009-04-28 | 2016-01-05 | Abbott Diabetes Care Inc. | Error detection in critical repeating data in a wireless sensor system |
WO2010138856A1 (en) | 2009-05-29 | 2010-12-02 | Abbott Diabetes Care Inc. | Medical device antenna systems having external antenna configurations |
EP2456351B1 (en) | 2009-07-23 | 2016-10-12 | Abbott Diabetes Care, Inc. | Real time management of data relating to physiological control of glucose levels |
WO2011026148A1 (en) | 2009-08-31 | 2011-03-03 | Abbott Diabetes Care Inc. | Analyte monitoring system and methods for managing power and noise |
WO2011026147A1 (en) | 2009-08-31 | 2011-03-03 | Abbott Diabetes Care Inc. | Analyte signal processing device and methods |
US9320461B2 (en) | 2009-09-29 | 2016-04-26 | Abbott Diabetes Care Inc. | Method and apparatus for providing notification function in analyte monitoring systems |
WO2012142502A2 (en) | 2011-04-15 | 2012-10-18 | Dexcom Inc. | Advanced analyte sensor calibration and error detection |
JP6443802B2 (en) | 2011-11-07 | 2018-12-26 | アボット ダイアベティス ケア インコーポレイテッドAbbott Diabetes Care Inc. | Analyte monitoring apparatus and method |
US9968306B2 (en) | 2012-09-17 | 2018-05-15 | Abbott Diabetes Care Inc. | Methods and apparatuses for providing adverse condition notification with enhanced wireless communication range in analyte monitoring systems |
US20140350370A1 (en) * | 2013-04-08 | 2014-11-27 | The Texas A&M University System | Glucose sensing assay |
CN103519828B (en) * | 2013-11-04 | 2015-04-29 | 理康互联科技(北京)有限公司 | Analyte detection system and sensing label thereof |
BR112018016211A8 (en) | 2016-02-09 | 2023-02-23 | Estab Labs Sa | TRANSPONDERS, INTEGRATED GATE SET, METHODS AND SYSTEM FOR TRANSMITTING A TRANSPONDER SPECIFIC SIGNAL |
JP7079245B2 (en) * | 2016-12-27 | 2022-06-01 | デックスコム・インコーポレーテッド | Systems and methods for patient monitoring using HCP-specific devices |
EP3396356A1 (en) * | 2017-04-28 | 2018-10-31 | Indigo Diabetes N.V. | Photonic embedded reference sensor |
US11331022B2 (en) | 2017-10-24 | 2022-05-17 | Dexcom, Inc. | Pre-connected analyte sensors |
US11382540B2 (en) | 2017-10-24 | 2022-07-12 | Dexcom, Inc. | Pre-connected analyte sensors |
Family Cites Families (20)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US4172459A (en) | 1977-10-17 | 1979-10-30 | Medtronic, Inc. | Cardiac monitoring apparatus and monitor |
US4436094A (en) | 1981-03-09 | 1984-03-13 | Evreka, Inc. | Monitor for continuous in vivo measurement of glucose concentration |
US4538616A (en) | 1983-07-25 | 1985-09-03 | Robert Rogoff | Blood sugar level sensing and monitoring transducer |
US4822336A (en) * | 1988-03-04 | 1989-04-18 | Ditraglia John | Blood glucose level sensing |
US5101814A (en) | 1989-08-11 | 1992-04-07 | Palti Yoram Prof | System for monitoring and controlling blood glucose |
FR2652736A1 (en) | 1989-10-06 | 1991-04-12 | Neftel Frederic | IMPLANTABLE DEVICE FOR EVALUATING THE RATE OF GLUCOSE. |
DE4034225C2 (en) | 1990-10-26 | 1994-01-27 | Reinhard Jurisch | Data carriers for identification systems |
GB9200638D0 (en) | 1992-01-10 | 1992-03-11 | Leicester Polytechnic | Drug system |
DE4203466A1 (en) | 1992-02-04 | 1993-08-05 | Rudolf Prof Dr Ehwald | Affinity sensor for concn. measurements of low molecular wt. analytes - consists of a hollow fibre or microcapsule contg. 2 macromolecular affinity ligands one of which can be displaced by the analyte |
NL9200207A (en) * | 1992-02-05 | 1993-09-01 | Nedap Nv | IMPLANTABLE BIOMEDICAL SENSOR DEVICE, IN PARTICULAR FOR MEASUREMENT OF THE GLUCOSE CONCENTRATION. |
WO1993020531A1 (en) | 1992-03-31 | 1993-10-14 | Micro-Sensys Gmbh | Process and system for transmitting serial data structures for information carrier identification systems, and information carriers |
US5383912A (en) | 1993-05-05 | 1995-01-24 | Intermedics, Inc. | Apparatus for high speed data communication between an external medical device and an implantable medical device |
DE69425817D1 (en) * | 1994-06-04 | 2000-10-12 | Orbisphere Lab | Device and method for luminance analysis |
US5597534A (en) | 1994-07-05 | 1997-01-28 | Texas Instruments Deutschland Gmbh | Apparatus for wireless chemical sensing |
US5628310A (en) * | 1995-05-19 | 1997-05-13 | Joseph R. Lakowicz | Method and apparatus to perform trans-cutaneous analyte monitoring |
US5704352A (en) | 1995-11-22 | 1998-01-06 | Tremblay; Gerald F. | Implantable passive bio-sensor |
US5833603A (en) | 1996-03-13 | 1998-11-10 | Lipomatrix, Inc. | Implantable biosensing transponder |
US5871698A (en) | 1996-05-02 | 1999-02-16 | Sandia Corporation | Chemical sensing flow probe |
AU9599498A (en) | 1997-09-30 | 1999-04-23 | M-Biotech, Inc. | Biosensor |
GB2335743A (en) | 1998-03-24 | 1999-09-29 | David Eglise | Remote monitoring of biological sensing implant |
-
1998
- 1998-03-20 GB GBGB9805896.9A patent/GB9805896D0/en not_active Ceased
-
1999
- 1999-03-22 DE DE69933547T patent/DE69933547T2/en not_active Expired - Lifetime
- 1999-03-22 ES ES99911921T patent/ES2277431T3/en not_active Expired - Lifetime
- 1999-03-22 AU AU30436/99A patent/AU752074B2/en not_active Ceased
- 1999-03-22 WO PCT/GB1999/000900 patent/WO1999048419A1/en active IP Right Grant
- 1999-03-22 AT AT99911921T patent/ATE341991T1/en active
- 1999-03-22 DK DK99911921T patent/DK1063916T3/en active
- 1999-03-22 PT PT99911921T patent/PT1063916E/en unknown
- 1999-03-22 CA CA002330553A patent/CA2330553C/en not_active Expired - Fee Related
- 1999-03-22 EP EP99911921A patent/EP1063916B1/en not_active Expired - Lifetime
- 1999-03-22 NZ NZ507666A patent/NZ507666A/en unknown
-
2000
- 2000-03-22 US US09/673,094 patent/US6579498B1/en not_active Expired - Lifetime
-
2002
- 2002-10-16 ZA ZA200005714A patent/ZA200005714B/en unknown
Also Published As
Publication number | Publication date |
---|---|
US6579498B1 (en) | 2003-06-17 |
WO1999048419A1 (en) | 1999-09-30 |
EP1063916B1 (en) | 2006-10-11 |
PT1063916E (en) | 2007-02-28 |
GB9805896D0 (en) | 1998-05-13 |
AU752074B2 (en) | 2002-09-05 |
DE69933547T2 (en) | 2007-06-06 |
ZA200005714B (en) | 2002-10-16 |
EP1063916A1 (en) | 2001-01-03 |
NZ507666A (en) | 2003-08-29 |
ATE341991T1 (en) | 2006-11-15 |
DE69933547D1 (en) | 2006-11-23 |
AU3043699A (en) | 1999-10-18 |
ES2277431T3 (en) | 2007-07-01 |
CA2330553A1 (en) | 1999-09-30 |
DK1063916T3 (en) | 2007-02-19 |
Similar Documents
Publication | Publication Date | Title |
---|---|---|
CA2330553C (en) | Implantable blood glucose sensor system | |
US8721544B2 (en) | System for in-vivo measurement of an analyte concentration | |
EP1130996B1 (en) | Generic integrated implantable potentiostat telemetry unit for electrochemical sensors | |
US20210330221A1 (en) | Analyte sensor | |
McKean et al. | A telemetry-instrumentation system for chronically implanted glucose and oxygen sensors | |
JP5795584B2 (en) | Medical device | |
WO2014096973A2 (en) | Systems and methods for internal analyte sensing | |
EP0954238B1 (en) | Sensor utilizing living muscle cells | |
US11020019B2 (en) | Dynamic amplifier change | |
GB2335496A (en) | Implanted blood glucose sensing and transmitting devices | |
US10709361B2 (en) | Methods and systems for correcting blood analyte measurements | |
JP2024509675A (en) | Network physical layer configuration for portable physiological parameter monitoring and therapeutic intervention systems | |
EP3638114B1 (en) | Method and system for providing calibration point acceptance criteria for calibrating an analyte sensor | |
EP3590422B1 (en) | Analyte sensor and method of using the same |
Legal Events
Date | Code | Title | Description |
---|---|---|---|
EEER | Examination request | ||
MKLA | Lapsed |
Effective date: 20150323 |