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EP1220638A1 - Method and device for blood component concentration determination - Google Patents

Method and device for blood component concentration determination

Info

Publication number
EP1220638A1
EP1220638A1 EP00966351A EP00966351A EP1220638A1 EP 1220638 A1 EP1220638 A1 EP 1220638A1 EP 00966351 A EP00966351 A EP 00966351A EP 00966351 A EP00966351 A EP 00966351A EP 1220638 A1 EP1220638 A1 EP 1220638A1
Authority
EP
European Patent Office
Prior art keywords
coil
concentration
blood
measuring
repetition rate
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.)
Withdrawn
Application number
EP00966351A
Other languages
German (de)
French (fr)
Inventor
Heinz Süsstrunk
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Pendragon Medical AG
Original Assignee
Suesstrunk Anita
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by Suesstrunk Anita filed Critical Suesstrunk Anita
Priority to EP00966351A priority Critical patent/EP1220638A1/en
Publication of EP1220638A1 publication Critical patent/EP1220638A1/en
Withdrawn legal-status Critical Current

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Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/05—Detecting, measuring or recording for diagnosis by means of electric currents or magnetic fields; Measuring using microwaves or radio waves
    • 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 or pH-value ; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid or cerebral tissue
    • A61B5/14532—Measuring characteristics of blood in vivo, e.g. gas concentration or pH-value ; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid or cerebral tissue for measuring glucose, e.g. by tissue impedance measurement

Definitions

  • the invention relates to a method for the non- invasive determination of the concentration of at least one component in blood and to a device for carrying out this method according -to the preamble of the independent claims.
  • Such methods or devices, respectively, are in particular used for determining the glucose concentration in blood.
  • WO 95/04496 describes a method based on an impedance measurement of the human body. It involves the application of electrodes to the body, which makes the measurement dependent on skin humidity and pressure ap- plied to the electrodes. Furthermore, it requires complex electronics for processing the measured signal .
  • a coil is brought within range of the body surface. Then, a measuring value depending on the inductance or loss of the coil, preferably the inductance, is measured at least at one frequency, and from this value the desired concentration of the component is e.g. determined by means of a suited calibration function.
  • a de- vice comprising a coil, a holder for attaching the coil and a driver for generating a periodically changing current in the coil.
  • a detector is used for detecting at least one measured signal depending on the temporal evolution of a voltage over or a current through the coil . It is found that the desired concentration can be derived from such a measured signal using suited calibration data.
  • no permanent magnetic field source is required of a size and direction where nuclear resonant oscillations could occur at the excitation frequencies.
  • Fig. 1 is a sectional view of an embodiment of the device according to the invention
  • Fig. 2 is a circuit block diagram of the de ⁇
  • Fig. 3 is the driver for the measuring coil
  • Fig. 4 is the temporal evolution of the currents m Fig. 3
  • Fig. 5 is a comparative table of measured and reference results.
  • a preferred mechanical set-up of the device in the shape of a w ⁇ stwatch is shown m Fig. 1. It comprises a housing 1, which is held to a body surface 3 by means of a holder or wristband 2. A support 4 is arranged in the housing 1, which support carries an electronic circuit 5 and a liquid crystal display 6. An opening 7 is provided on the side of the housing 1 that faces the body. Optics 8 are arranged m the opening 7. A light source 9 and a light sensor 10 are arranged behind the optics, wherein the light sensor 10 is positioned such that it receives light of the light source 9 reflected from the body.
  • a cylindrical electrical coil L is ar- ranged around the light source 9 and the light sensor 10, the axis of the coil being perpendicular to the body surface.
  • a further small permanent magnet 12 can be arranged in or beside coil L, the field of which permanent magnet is substantially parallel to the one of the coil . Even though such a permanent magnet is not absolutely required, it is found that its field improves the quality of the measured signals.
  • Fig. 2 shows a block diagram of the circuit of the device of Fig. 1. It comprises a microprocessor 14 connected to an input and output section 15. The latter comprises the display 6 as well as conventional control elements that can be operated by the user.
  • the microprocessor 14 and the input and output section 15 possess all capabilities of a conventional wristwatch. Beyond that, the microprocessor is, however, capable to measure the glucose level or other components in the body tissue. For this purpose, it is connected via a driver circuit 16 to coil L.
  • a driver stage 17 is provided for driving the light source 9, which consists of three LEDs 9a, 9b, 9c of differing color (preferably red, yellow, and green or blue) .
  • the signals of the light sensor 10 are fed to an amplifier 18 with A/D-converter and then also to microprocessor 14.
  • the driver circuit 16 for coil L is shown in Fig. 3. It comprises two complementary transistors Tl, T2 , which are individually controlled by microprocessor 14 by means of signals Ul, U2.
  • the output of the complementary transistor pair Tl, T2 which are arranged between a supply voltage and ground, is connected to one terminal of coil L.
  • the second terminal of coil L is on ground.
  • a threshold value detector 20 measures the voltage U L over the coil and generates a signal as soon as the absolute value of the voltage U L is above a threshold value Up-
  • the operation of the driver circuit 16 is illustrated in Fig. 4.
  • Microprocessor 15 first switches on the upper transistor Tl during a first measuring phase, which causes the voltage U_, over the coil to rise to the value of the positive supply voltage. Then, transistor Tl is switched off while transistor T2 remains switched off during a second measuring phase. During this second meas- uring phase, the driver circuit 16 is therefore in high impedance state. Disconnecting the coil from the voltage UL generates a negative induction voltage over the coil. At the same time, the output "Out" of the threshold value detector 20 goes from 0 to 1. When the value of the volt- age U j _, drops, after a time T x , below the threshold value Uf, the output "Out" goes from 1 to 0. Then, after a predefined time, at the end of the second measuring phase, the lower transistor T2 can optionally be switched on for fully discharging the voltage over the coil. Thereafter, the measuring cycle starts anew with the first measuring phase .
  • the output "Out" is fed to microprocessor 15, which determines the time T x .
  • This determination can e.g. be carried out by a suitable fast counter or analogue in- tegration of the signal and analog-digital conversion thereof .
  • measurement frequencies can be used, such as 75.95 MHz for the determi- nation of the concentration of NaCl in solution or 86.4 MHz for insulin.
  • the measurement frequency for a component is determined by calibration measurements, wherein probes of differing concentration of the component are measured. For each probe, the inductance and/or loss or the value of T x is measured as a function of the frequency F. The spectra measured in this way are compared to each other, and the frequency showing the strongest dependence of the measured signal from the component's concentration is used as measurement frequency.
  • a pre- ferred range of frequencies F lies between 10 kHz and 1 GHz, preferably between 10 MHz and 1 GHz, in particular between 50 MHz and 200 MHz. It is, however, also possible to measure at other frequencies .
  • the device only de- termines the blood sugar level and is fixedly set to the frequency 75.87 MHz. It is, however, also possible to vary the measuring frequency for measuring the concentration of other components.
  • the value of the measuring signal not only depends on the concentration of the component to be measured, but also on the quantity of blood in the measuring range. Since the quantity of blood can vary e.g. depending on blood circulation in the vessels or because of variations in blood pressure, it is preferred to run a second measurement.
  • This second measurement can e.g. be based on the method described above and determine the concentration of a second blood component in the measuring area, whereby the amount of blood can be determined and the blood sugar value can be corrected.
  • a further improvement can be achieved by an additional optical measurement.
  • the magnitude of the signal received by light sensor 10, i.e. the reflected light is determined.
  • This signal i.e. the reflection coefficient of the body, also depends of the amount of blood in the analyzed tissue.
  • the measuring signal T x is converted into the desired blood sugar level by means of a calibration table or calibration coefficient.
  • a calibration step is performed where the measured signal is compared to a blood sugar level that was determined in conventional manner.
  • the number of calibration measurements depends on the desired accuracy. For most applications, one calibration measurement above 10 mmol/lt and one between 4 and 6 mmol/lt is sufficient.
  • the calibration step allows to calculate a calibration function (consisting e.g. of a calibration factor or a calibration table) .
  • this calibra- tion step is repeated for each new user.
  • Fig. 5 shows a table of measurements of a calibrated device in comparison with analytically found reference results. It is found that the present method has a high accuracy.
  • the inventor assumes that in the present method the magnetic pulses of coil L excite intermolecu- lar oscillations in the blood, and in particular also in frequency ranges below 1 GHz.
  • the inductance and/or loss of the coil and the value of the time T x depend on the amplitude of the excited oscillations.
  • a possible measurement range is between 10 kHz and 1 GHz, a preferred measurement range is 10 MHz to 1 GHz, wherein it a range between 50 MHz and 200 MHz has been found to be especially suited for measurements.
  • a periodic electromagnetic signal is applied and a coupling of the elec- tromagnetic field and the atoms and/or bonds of the molecule is used.
  • a piezoelectric emitter 22 for sound or ultrasound which generates mechanical oscillations and receives corresponding echoes. While there are shown and described presently preferred embodiments of the invention, it is to be distinctly understood that the invention is not limited thereto but may be otherwise variously embodied and practiced within the scope of the following claims.

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  • Health & Medical Sciences (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Physics & Mathematics (AREA)
  • Medical Informatics (AREA)
  • Surgery (AREA)
  • Biophysics (AREA)
  • Pathology (AREA)
  • Engineering & Computer Science (AREA)
  • Biomedical Technology (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Veterinary Medicine (AREA)
  • Molecular Biology (AREA)
  • Public Health (AREA)
  • Animal Behavior & Ethology (AREA)
  • General Health & Medical Sciences (AREA)
  • Optics & Photonics (AREA)
  • Emergency Medicine (AREA)
  • Nuclear Medicine, Radiotherapy & Molecular Imaging (AREA)
  • Radiology & Medical Imaging (AREA)
  • Measurement Of The Respiration, Hearing Ability, Form, And Blood Characteristics Of Living Organisms (AREA)

Abstract

For the non-invasive determination of a concentration of a component in blood, in particular for the determination of the concentration of blood sugar, an electric coil (L) arranged at the body is periodically operated with current pulses. After the current pulses, the voltage (UL) over the voltage is determined. It is found that the temporal evolution of this voltage (UL) depends on the concentration of the components to be measured if the frequency of the current pulse corresponds to an experimentally determined resonance frequency. The measuring method can e.g. be carried out by a device designed as wrist watch.

Description

METHOD AND DEVICE FOR BLOOD COMPONENT CONCENTRATION DETERMINATION
Cross References to Related Applications
This application claims the priority of European patent application 99810933.4, filed October 13, 1999, the disclosure of which is incorporated herein by reference in its entirety.
Technical Field
The invention relates to a method for the non- invasive determination of the concentration of at least one component in blood and to a device for carrying out this method according -to the preamble of the independent claims. Such methods or devices, respectively, are in particular used for determining the glucose concentration in blood.
Background Art
For measuring the concentration of glucose in blood, invasive blood collection is usually required. Since such blood collection is undesired for obvious reasons, alternative non- invasive procedures are searched for. It has e.g. been tried to determine glucose in blood by means of laser light, which, however, does not yield satisfactory results because the results strongly depend on temperature, physical exercise, sun tan, etc. This is a consequence of the fact that a measurement by means of laser light can only sample a comparatively small subcutaneous region of the tissue with a depth a approximately 3 mm. Further devices and methods are known where the glucose in blood is measured by means of nuclear resonance. This requires, however, the generation of very strong permanent magnetic fields, which makes correspond- ing apparatus heavy and expensive.
WO 95/04496 describes a method based on an impedance measurement of the human body. It involves the application of electrodes to the body, which makes the measurement dependent on skin humidity and pressure ap- plied to the electrodes. Furthermore, it requires complex electronics for processing the measured signal .
Disclosure of the Invention
Therefore, the problem to be solved lies in providing a method and apparatus of the type mentioned initially that yield accurate results in simple manner without requiring invasive blood collection. This problem is solved by the independent claims .
In a preferred embodiment of the method a coil is brought within range of the body surface. Then, a measuring value depending on the inductance or loss of the coil, preferably the inductance, is measured at least at one frequency, and from this value the desired concentration of the component is e.g. determined by means of a suited calibration function.
In a further aspect of the invention, a de- vice comprising a coil, a holder for attaching the coil and a driver for generating a periodically changing current in the coil is provided. A detector is used for detecting at least one measured signal depending on the temporal evolution of a voltage over or a current through the coil . It is found that the desired concentration can be derived from such a measured signal using suited calibration data. In contrast to measuring devices based on the determination of nuclear resonant oscillations, no permanent magnetic field source is required of a size and direction where nuclear resonant oscillations could occur at the excitation frequencies.
Brief Description of the Drawings
The invention will be better understood and objects other than those set forth above will become apparent when consideration is given to the following detailed description thereof . Such description makes reference to the annexed drawings, wherein: Fig. 1 is a sectional view of an embodiment of the device according to the invention,
Fig. 2 is a circuit block diagram of the de¬
Fig. 3 is the driver for the measuring coil, Fig. 4 is the temporal evolution of the currents m Fig. 3,
Fig. 5 is a comparative table of measured and reference results.
Modes for Carrying Out the Invention
A preferred mechanical set-up of the device in the shape of a wπstwatch is shown m Fig. 1. It comprises a housing 1, which is held to a body surface 3 by means of a holder or wristband 2. A support 4 is arranged in the housing 1, which support carries an electronic circuit 5 and a liquid crystal display 6. An opening 7 is provided on the side of the housing 1 that faces the body. Optics 8 are arranged m the opening 7. A light source 9 and a light sensor 10 are arranged behind the optics, wherein the light sensor 10 is positioned such that it receives light of the light source 9 reflected from the body. A cylindrical electrical coil L is ar- ranged around the light source 9 and the light sensor 10, the axis of the coil being perpendicular to the body surface. A further small permanent magnet 12 can be arranged in or beside coil L, the field of which permanent magnet is substantially parallel to the one of the coil . Even though such a permanent magnet is not absolutely required, it is found that its field improves the quality of the measured signals.
Fig. 2 shows a block diagram of the circuit of the device of Fig. 1. It comprises a microprocessor 14 connected to an input and output section 15. The latter comprises the display 6 as well as conventional control elements that can be operated by the user. The microprocessor 14 and the input and output section 15 possess all capabilities of a conventional wristwatch. Beyond that, the microprocessor is, however, capable to measure the glucose level or other components in the body tissue. For this purpose, it is connected via a driver circuit 16 to coil L. Furthermore, a driver stage 17 is provided for driving the light source 9, which consists of three LEDs 9a, 9b, 9c of differing color (preferably red, yellow, and green or blue) . The signals of the light sensor 10 are fed to an amplifier 18 with A/D-converter and then also to microprocessor 14.
The driver circuit 16 for coil L is shown in Fig. 3. It comprises two complementary transistors Tl, T2 , which are individually controlled by microprocessor 14 by means of signals Ul, U2. The output of the complementary transistor pair Tl, T2 , which are arranged between a supply voltage and ground, is connected to one terminal of coil L. The second terminal of coil L is on ground. A threshold value detector 20 measures the voltage UL over the coil and generates a signal as soon as the absolute value of the voltage UL is above a threshold value Up-
The operation of the driver circuit 16 is illustrated in Fig. 4. Microprocessor 15 first switches on the upper transistor Tl during a first measuring phase, which causes the voltage U_, over the coil to rise to the value of the positive supply voltage. Then, transistor Tl is switched off while transistor T2 remains switched off during a second measuring phase. During this second meas- uring phase, the driver circuit 16 is therefore in high impedance state. Disconnecting the coil from the voltage UL generates a negative induction voltage over the coil. At the same time, the output "Out" of the threshold value detector 20 goes from 0 to 1. When the value of the volt- age Uj_, drops, after a time Tx, below the threshold value Uf, the output "Out" goes from 1 to 0. Then, after a predefined time, at the end of the second measuring phase, the lower transistor T2 can optionally be switched on for fully discharging the voltage over the coil. Thereafter, the measuring cycle starts anew with the first measuring phase .
The output "Out" is fed to microprocessor 15, which determines the time Tx. This determination can e.g. be carried out by a suitable fast counter or analogue in- tegration of the signal and analog-digital conversion thereof .
The time Tx depends on the inductance and loss (or quality factor Q) of the coil L, which, among other things, also depends on the magnetic and conductive properties of the tissue and blood of the user. In particular, it has been found that the coil inductance and/or loss and the value of Tx are a function of the blood composition. Depending on the length of the measuring period Tp or the excitation frequency F = l/Tp, dif- ferent components can be measured selectively. For example, the preferred frequency F for determining the blood sugar level is approximately 75.80 MHz, i.e. at this fre- quency the value of the coil inductance and loss or the time Tx depends strongly on the blood sugar level .
For other components, other measurement frequencies can be used, such as 75.95 MHz for the determi- nation of the concentration of NaCl in solution or 86.4 MHz for insulin. The measurement frequency for a component is determined by calibration measurements, wherein probes of differing concentration of the component are measured. For each probe, the inductance and/or loss or the value of Tx is measured as a function of the frequency F. The spectra measured in this way are compared to each other, and the frequency showing the strongest dependence of the measured signal from the component's concentration is used as measurement frequency. A pre- ferred range of frequencies F lies between 10 kHz and 1 GHz, preferably between 10 MHz and 1 GHz, in particular between 50 MHz and 200 MHz. It is, however, also possible to measure at other frequencies .
In the present embodiment the device only de- termines the blood sugar level and is fixedly set to the frequency 75.87 MHz. It is, however, also possible to vary the measuring frequency for measuring the concentration of other components.
The value of the measuring signal not only depends on the concentration of the component to be measured, but also on the quantity of blood in the measuring range. Since the quantity of blood can vary e.g. depending on blood circulation in the vessels or because of variations in blood pressure, it is preferred to run a second measurement. This second measurement can e.g. be based on the method described above and determine the concentration of a second blood component in the measuring area, whereby the amount of blood can be determined and the blood sugar value can be corrected. A further improvement can be achieved by an additional optical measurement. For this purpose, the magnitude of the signal received by light sensor 10, i.e. the reflected light, is determined. This signal, i.e. the reflection coefficient of the body, also depends of the amount of blood in the analyzed tissue.
It is found that the signal of light sensor 10, after suited scaling, can simply be added to the value Tx for producing more reliable results.
Preferably, the measuring signal Tx, possibly after an addition to the signal from the light sensor, is converted into the desired blood sugar level by means of a calibration table or calibration coefficient. For this purpose, a calibration step is performed where the measured signal is compared to a blood sugar level that was determined in conventional manner. The number of calibration measurements depends on the desired accuracy. For most applications, one calibration measurement above 10 mmol/lt and one between 4 and 6 mmol/lt is sufficient. The calibration step allows to calculate a calibration function (consisting e.g. of a calibration factor or a calibration table) . Preferably, this calibra- tion step is repeated for each new user.
In the embodiment shown here, light with a very broad spectrum is generated by means of three light emitting diodes of differing colors. It is also possible to use other light sources. Fig. 5 shows a table of measurements of a calibrated device in comparison with analytically found reference results. It is found that the present method has a high accuracy.
The inventor assumes that in the present method the magnetic pulses of coil L excite intermolecu- lar oscillations in the blood, and in particular also in frequency ranges below 1 GHz. The inductance and/or loss of the coil and the value of the time Tx depend on the amplitude of the excited oscillations. A possible measurement range is between 10 kHz and 1 GHz, a preferred measurement range is 10 MHz to 1 GHz, wherein it a range between 50 MHz and 200 MHz has been found to be especially suited for measurements.
In the present embodiment, a periodic electromagnetic signal is applied and a coupling of the elec- tromagnetic field and the atoms and/or bonds of the molecule is used. It is, however, also suggested to use in addition to the coil , a piezoelectric emitter 22 for sound or ultrasound, which generates mechanical oscillations and receives corresponding echoes. While there are shown and described presently preferred embodiments of the invention, it is to be distinctly understood that the invention is not limited thereto but may be otherwise variously embodied and practiced within the scope of the following claims.

Claims

Claims
1. A method for the non-invasive determination of the concentration of a substance in blood, in particular for the determination of the concentration of glucose in blood, comprising the steps of measuring a measuring signal depending on one of the inductance or the loss of a coil (L) located in the vicinity of a surface of a body while an alternating electromagnetic field generated by said coil extends into said body and using calibration data for converting said measuring signal to said concentration.
2. The method of claim 1 comprising the step of measuring a signal depending on the inductance the coil (L) .
3. A method for the non-invasive determination of the concentration of a substance in blood, in particular for the determination of the concentration of glucose in blood, comprising the steps of sending periodic current pulses having a given repetition rate through a coil (L) located in the vicinity of a surface of a body and generating an electromagnetic field in said body, said electromagnetic field having no magnetic components sufficient for generating NMR oscillations at the given repetition rate, determining, between said current pulses, a measured signal, said measured signal depending on the temporal evolution of at least one of the current through the coil or a voltage over the coil, using calibration data for converting said measured signal to said concentration.
4. The method of claim 3 wherein said measured signal (Tx) corresponds to a time required by said current to fall below a given threshold.
5. A device for the non-invasive determination of the concentration of a substance in blood, in particular for the determination of the concentration of glucose in blood, comprising an electric coil (L) , a holder (2) for attaching the coil close to the surface of a body, a driver (Tl, T2 ) generating a periodically changing current in the coil at a given repetition rate (F) , and a detector (20) detecting at least one meas- ured signal (Tx) from the temporal evolution of at least one of the current through the coil or a voltage over the coil and deriving the concentration from the measured signal , said device not comprising a source for a permanent magnetic field of a magnitude and direction suited for causing NMR oscillations under the operation of said coil .
6. The device of claim 5 further comprising a light source (9) generating light for irradiating said surface and a light detector (10) for measuring reflected light and means for additive combination of a reflection coefficient measured by the light detector and the measured signal.
7. The device of claim 6 wherein the coil is arranged around the light source (9) and the light detector (10) .
8. The device of one of the claims 5 - 7 further comprising a wrist watch housing (1) , a time display (15) and a wristband.
9. The device of one of the claims 5 - 8 wherein said repetition rate is between 10 kHz and 1 GHz.
10. The device of one of the claims 5 - 9 wherein said repetition rate is between 10 MHz and 1 GHz.
11. The device of one of the claims 5 - 10 wherein said repetition rate is between 50 MHz and 200
MHz.
12. The device of one of the claims 5 - 11 wherein said repetition rate is 75.8 MHz for the detection of glucose.
13. The device of one of the claims 5 - 12 wherein said driver (Tl, T2) is adapted to generate periodic, repetitive current pulses in the coil (L) .
14. The device of claim 13 wherein said driver (Tl, T2) is adapted to apply a voltage over said coil during a first measuring phase for generating one of said current pulses and to go to a high impedance state during a second measuring phase during measuring of the time evolution.
15. The device of one of the claims 5 - 14 wherein said measured signal (Tx) corresponds to a decay time of said current .
EP00966351A 1999-10-13 2000-10-13 Method and device for blood component concentration determination Withdrawn EP1220638A1 (en)

Priority Applications (1)

Application Number Priority Date Filing Date Title
EP00966351A EP1220638A1 (en) 1999-10-13 2000-10-13 Method and device for blood component concentration determination

Applications Claiming Priority (4)

Application Number Priority Date Filing Date Title
EP99810933 1999-10-13
EP99810933A EP1092386A1 (en) 1999-10-13 1999-10-13 Method and device for determining the concentration of a substance in blood
EP00966351A EP1220638A1 (en) 1999-10-13 2000-10-13 Method and device for blood component concentration determination
PCT/IB2000/001464 WO2001026538A1 (en) 1999-10-13 2000-10-13 Method and device for blood component concentration determination

Publications (1)

Publication Number Publication Date
EP1220638A1 true EP1220638A1 (en) 2002-07-10

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EP99810933A Withdrawn EP1092386A1 (en) 1999-10-13 1999-10-13 Method and device for determining the concentration of a substance in blood
EP00966351A Withdrawn EP1220638A1 (en) 1999-10-13 2000-10-13 Method and device for blood component concentration determination

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EP99810933A Withdrawn EP1092386A1 (en) 1999-10-13 1999-10-13 Method and device for determining the concentration of a substance in blood

Country Status (3)

Country Link
EP (2) EP1092386A1 (en)
AU (1) AU7678600A (en)
WO (1) WO2001026538A1 (en)

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EP1691672B1 (en) * 2002-09-24 2009-01-07 Solianis Holding AG Device for the measurement of glucose concentrations
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US8197406B2 (en) 2003-12-02 2012-06-12 Biovotion Ag Device and method for measuring a property of living tissue
PL1718200T3 (en) 2004-02-05 2017-01-31 Dermal Devices Inc. Apparatus for measuring blood glucose using sub-dermal body tissue impedance measurements
US9179856B2 (en) 2009-04-17 2015-11-10 Biovotion Ag Sensing device for body tissue properties
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AU7678600A (en) 2001-04-23
EP1092386A1 (en) 2001-04-18

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