US20110004080A1 - Method for non-invasive analysis of a substance concentration within a body - Google Patents

Method for non-invasive analysis of a substance concentration within a body Download PDF

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Publication number
US20110004080A1
US20110004080A1 US12/883,063 US88306310A US2011004080A1 US 20110004080 A1 US20110004080 A1 US 20110004080A1 US 88306310 A US88306310 A US 88306310A US 2011004080 A1 US2011004080 A1 US 2011004080A1
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US
United States
Prior art keywords
temperature
substance
wavelength band
infrared radiation
wavelength
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Abandoned
Application number
US12/883,063
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English (en)
Inventor
Yonatan Gerlitz
Alexander Ostritsky
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GlucoVista Inc
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Glucovista LLC
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
Priority claimed from US12/101,859 external-priority patent/US8401604B2/en
Priority claimed from US12/607,903 external-priority patent/US8611975B2/en
Priority to US12/883,063 priority Critical patent/US20110004080A1/en
Assigned to GLUCOVISTA LLC reassignment GLUCOVISTA LLC ASSIGNMENT OF ASSIGNORS INTEREST (SEE DOCUMENT FOR DETAILS). Assignors: GERLITZ, YONATAN, OSTRITSKY, ALEXANDER
Application filed by Glucovista LLC filed Critical Glucovista LLC
Publication of US20110004080A1 publication Critical patent/US20110004080A1/en
Priority to AU2011302301A priority patent/AU2011302301C1/en
Priority to PCT/US2011/051218 priority patent/WO2012037029A1/en
Priority to CN2011800439846A priority patent/CN103118594A/zh
Priority to JP2013529225A priority patent/JP5752796B2/ja
Priority to RU2013117005/14A priority patent/RU2562173C2/ru
Priority to CA2810831A priority patent/CA2810831C/en
Priority to EP11825737.7A priority patent/EP2615975A4/en
Priority to EP19208977.9A priority patent/EP3628223A3/en
Priority to CN201710799742.9A priority patent/CN107647872A/zh
Priority to BR112013005648A priority patent/BR112013005648A2/pt
Assigned to GLUCOVISTA, INC. reassignment GLUCOVISTA, INC. CHANGE OF NAME (SEE DOCUMENT FOR DETAILS). Assignors: GLUCOVISTA LLC
Priority to US14/312,464 priority patent/US9681832B2/en
Priority to JP2015101712A priority patent/JP5963914B2/ja
Priority to US16/174,168 priority patent/US11141082B2/en
Abandoned legal-status Critical Current

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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/145—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue
    • A61B5/14532—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
    • 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
    • A61B5/14546—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 analytes not otherwise provided for, e.g. ions, cytochromes
    • 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
    • A61B5/1491—Heated applicators
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/01—Measuring temperature of body parts ; Diagnostic temperature sensing, e.g. for malignant or inflamed tissue

Definitions

  • the present application relates generally to the non-invasive measurement of various substances in a body, such as the measurement of the concentration of glucose in the human body and, more specifically, to a method employing an electro-optical system to non-invasively analyze the concentration of a substance in a body.
  • Spectroscopic techniques using infrared (“IR”) radiation are known in the prior art and have been widely used for non-invasive measurement of the concentration of substances of interest in a body.
  • IR infrared
  • One area of particular interest is the use of these techniques for the non-invasive measurement of the concentration of glucose and other constituents of the human bloodstream.
  • the infrared spectra includes the near infrared (approximately 1 to 3 microns), the middle infrared (approximately 3 to 6 microns), the far infrared (approximately 6 to 15 microns), and the extreme infrared (approximately 15 to 100 microns).
  • Typical prior art glucose and other non-invasive blood constituent measuring devices operate in the near infrared regions where the absorption of infrared energy by glucose and other blood constituents is relatively low.
  • glucose and other blood constituents have strong and distinguishable absorption spectra in both the middle and far infrared regions.
  • the present application discloses a method to analyze and determine, non-invasively, the concentration of a substance in a body.
  • the method comprises the steps of changing the temperature of the surface of a body from a first temperature to a second temperature, then changing the temperature of the surface of the body from the second temperature back to the first temperature. Measuring the infrared radiation absorbed or emitted from the body in a first wavelength band at predetermined time intervals during the change of the temperature of the surface of the body from the second temperature back to the first temperature. Measuring the infrared radiation absorbed or emitted from the body in a second wavelength band at predetermined time intervals during the change of the temperature of the surface of the body from the second temperature to the first temperature.
  • the method further comprises measuring the temperature at the surface of the body, and measuring the ambient temperature.
  • the method further comprises the steps of calculating a normalized ratio parameter based on the IR radiation measured for the first wavelength band, the IR radiation measured for the second wavelength band, the body surface temperature and the ambient temperature, and determining the concentration of the substance in the body by correlating the normalized ratio parameter with the body surface temperature and the ambient temperature.
  • An empirically deprived lookup table may be used to correlate the normalized ratio parameter with the concentration of the substance in the body.
  • FIG. 1 is a plot of infrared radiation emitted from and absorbed by a hypothetical body across a given spectrum
  • FIG. 2 is a plot of far infrared radiation emitted from and absorbed by a hypothetical body and a blackbody across a given spectrum
  • FIG. 3 is a block diagram illustrating one embodiment of a system for the non-invasive measurement of the concentration of a substance in a body
  • FIG. 4 is a perspective view of the optical and detector apparatus of FIG. 3 illustrating the path of travel for electromagnetic rays between the body and the detector;
  • FIG. 5 is a block diagram illustrating another embodiment of a system for the non-invasive measurement of the concentration of a substance in a body
  • FIG. 6 is a block diagram illustrating the control electronics for the systems illustrated in FIGS. 3 and 5 ;
  • FIG. 7 is a graph illustrating the temperature recovery function of the human skin as measured with the optical and detector system of FIGS. 3 , 4 and 5 ;
  • FIG. 8 is a process flow chart illustrating one embodiment of the present method for analyzing a concentration of a substance in a body.
  • Embodiments of the present disclosure provide methods to non-invasively analyze and measure the concentration of a substance in a body.
  • the analyzed substance may be glucose in the human bloodstream.
  • the present methods may be used to analyze and measure concentrations of other substances as well, such as cholesterol, for example.
  • FIG. 1 illustrates a sample plot of the IR radiation emission spectrum for a hypothetical body, where the ambient temperature T A is equal to x and the body temperature T B is equal to y. As shown, for a given ambient temperature and body temperature, a body more readily emits and absorbs IR radiation at certain wavelengths, represented by the peaks 10 in the spectrum shown by curve 12 .
  • the IR spectra includes the near infrared (approximately 1 to 3 microns), the middle infrared (approximately 3 to 6 microns), the far infrared (approximately 6 to 15 microns), and the extreme infrared (approximately 15 to 100 microns).
  • IR absorption/emission is particularly distinctive in the far infrared (“FIR”) spectrum.
  • FIR far infrared
  • Embodiments of the present methods measure the FIR radiation absorbed or emitted by a body at different wavelength bandwidths or bands.
  • the first wavelength band (or bands) is selected to be in a band (or bands) where the substance of interest is known to have significant absorption/emission characteristics.
  • the second wavelength band (or bands) is selected to be in a band (or bands) where the substance is known to have no or negligible absorption/emission.
  • the second wavelength band (or bands) is selected to be the entire FIR absorption/emission spectrum of the body.
  • the FIR measurements are normalized against a blackbody.
  • a blackbody as those of ordinary skill in the art will appreciate, is one that absorbs and emits radiation with a theoretical emissivity of one.
  • FIG. 2 illustrates a sample plot of the FIR absorption/emission spectrum for a hypothetical body (solid curve 20 ) and for a blackbody (dashed curve 22 ).
  • the ambient temperature T A is the same.
  • the body temperature T B is the same for each set of measurements.
  • the dashed vertical lines define a first wavelength band 24 in which the substance whose concentration is to be measured is known to have an FIR absorption/emission peak 26 .
  • the selected band 24 may be between about 9.3 microns and about 9.9 microns.
  • the temperature of an area of the surface of a body is changed from a first temperature to a second temperature for a period of time (i.e., as by heating or cooling), and then allowed to recover or revert from the second temperature to the first temperature over a period of time.
  • the IR radiation from the surface of the body is measured both in the wavelength bandwidth for the substance of interest and in the wavelength bandwidth not including the wavelength of the substance of interest at each of a plurality of predetermined time intervals.
  • the results of the measurements are plotted as a function of elapsed time versus temperature of the surface in two curves, one for the wavelength bandwidth of interest and one for the wavelength bandwidth not including the wavelength of interest.
  • the difference between the two curves or functions due to the contribution of the IR wavelength emission/absorption of the substance of interest in the body can be analyzed by calculating the value of the functions for the two curves at each of the measurement times or by determining the difference between the constants for each of the two curves.
  • the average ratio of the two radiation measurements after normalization for a black body reading is correlated to the concentration of the desired substance in the body, such as the concentration of glucose in the bloodstream of a human body, for example.
  • the illustrated embodiment of the present system 30 comprises an infrared (“IR”) radiation detector 32 , an IR filter assembly 34 , heating and/or cooling apparatus 36 , and apparatus 38 for measuring the ambient temperature.
  • the IR detector 32 measures the body surface temperature.
  • the IR detector 32 may comprise a thermopile with collimating optics.
  • the IR detector 32 may comprise a different type of detector, such as a bolometer, for example.
  • the system 30 shown in FIG. 3 further comprises a display 42 for presenting information such as the substance concentration, the measured parameters and other information of interest.
  • the display 42 may comprise a liquid crystal display (“LCD”).
  • the IR filter assembly 34 is positioned between the body and the IR detector 32 .
  • the IR filter assembly 34 comprises two filters 44 , 46 , although those of ordinary skill in the art will appreciate that the IR filter assembly 34 may include any number of filters.
  • a first filter, filter 44 for example, will preferably be a narrow band filter passing the wavelengths of the spectral characteristic of the substance being measured.
  • a second filter, filter 46 for example, will preferably be a narrow band filter passing those wavelengths of a spectral characteristic not sensitive to the substance being measured.
  • filter 46 will limit the bandwidth to that region of the spectrum where there is no emission for the substance being measured (for glucose, for example, the bandwidth may be 10.5 ⁇ -15 ⁇ ), while filter 44 would have a bandwidth characteristic of the emission of the substance being measured (for glucose, for example, the bandwidth may be 8.5 ⁇ -10.5 ⁇ .
  • the second filter 46 may transmit, for example, all of the IR radiation between approximately 7 microns and approximately 15 microns.
  • the system 30 includes a drive motor 52 .
  • the drive motor 52 may comprise a solenoid.
  • the drive motor 52 is configured to provide a motive force for changing a position of the filter assembly 34 with respect to the IR detector 32 . Activation of the drive motor 52 enables the filters 44 , 46 to be sequentially positioned between the body and the IR detector 32 as each IR radiation measurement is taken.
  • FIG. 4 a schematic perspective view is shown of the configuration of an optical subsystem 13 and IR detector 32 components of the system 30 shown in FIG. 3 , illustrating the path of travel for IR radiation rays between a body 11 and the detector 32 .
  • the detector 32 includes a detector element 23 , detector base 25 and detector leads 27 .
  • the configuration of the optical and detector components is designed such that an image 12 of the sensitive or active area 47 of the detector 15 is created at the body 11 on the focal plane of mirror 31 .
  • the area of image 12 at the surface of body 11 preferably has a diameter of approximately 6 mm.
  • IR radiation emitted from or reflected by the body 11 at image 12 in beam 41 is collected and collimated by mirror 31 .
  • the IR radiation is reflected by mirror 31 and propagated to mirror 29 in a collimated beam 43 of parallel rays via filter 44 or filter 46 .
  • the focal plane of mirror 29 is located at the surface of a sensitive area of the IR detector 32 .
  • the beam 43 reaching mirror 29 is reflected and propagated as beam 45 and focused at the focal plane of mirror 29 incident on the IR detector 32 sensitive area.
  • the optical subsystem 13 is aligned such that the image 12 is positioned at the surface of body 11 and the beam 41 of IR radiation is incident on the sensitive area of IR detector 32 via mirror 31 , filter 33 or filter 35 and mirror 29 .
  • mirrors 29 and 31 are preferably ninety-degree)(90°) off-axis parabolic mirrors coated with gold or other suitable reflective material.
  • mirror 29 will have a focal length of about one (1) inch and mirror 31 will have a focal length of about three (3) inches.
  • Other suitably designed reflective mirrors may be used for the optical subsystem 13 such as ellipsoid mirrors or a combination of ellipsoid and hyperbolic mirrors, for example.
  • Filter 44 and filter 46 are mounted in frame 48 , frame 48 being positioned between mirror 29 and mirror 31 .
  • the filters 44 , 46 are switched between positions intercepting the beam 43 using a suitable driving mechanism, such as a motor or pneumatic pressure, for example, coupled to frame 48 .
  • motor 52 is coupled to the frame 48 and positions the frame 48 between the mirror 29 and mirror 31 such that the desired filter 44 , 46 intercepts the beam 43 .
  • FIG. 5 a block diagram of an alternative embodiment of the present system 60 is shown.
  • the drive motor 52 and the filter assembly 34 are replaced with a plurality of fixed position IR detectors.
  • two IR detectors 62 , 64 are shown.
  • each IR detector 62 , 64 includes its own IR filter 66 , 68 , respectively.
  • the filters 66 , 68 may, for example, be substantially similar to the two filters 44 , 46 provided in the embodiment of FIG. 3 with respect to the wavelengths of IR radiation each filter transmits.
  • the illustrated embodiments of the present system, 30 , 60 include apparatus 38 for measuring the ambient temperature.
  • the ambient temperature measuring apparatus 38 may comprise a thermistor, such as a negative temperature coefficient thermistor.
  • the ambient temperature measuring apparatus 38 will be referred to as thermistor 38 .
  • the ambient temperature measuring apparatus 38 may be any apparatus that is suitable for measuring the ambient temperature, such as a thermocouple, for example.
  • the thermistor 38 is shown attached to the IR detectors 32 and 62 , 64 , those of ordinary skill in the art will appreciate that it need not be.
  • the thermistor 38 measures the temperature of a housing (not shown) of the IR detectors 32 and 62 , 64 which is typically equal to the ambient temperature.
  • FIG. 6 a block diagram illustrating the control electronics for the systems illustrated in FIGS. 3 and 5 is shown.
  • Outputs 33 and 67 , 69 of the IR detector(s) 32 and 62 , 64 , the thermistor 38 output 39 , and control inputs 55 , 56 of the drive motor 52 and the heating/cooling apparatus 36 , respectively, are connected to control electronics 54 .
  • FIG. 6 illustrates further details of the control electronics 54 , which include a processing unit 71 and memory 72 .
  • the memory 72 may include one or more lookup tables for calculating and determining results of the measurements taken by the present system 30 , 60 .
  • the memory 72 may include an empirically derived lookup table that correlates a normalized ration parameter with the concentration of the substance of interest in the body.
  • the processing unit 71 may comprise a central processing unit (“CPU”) running software and/or firmware.
  • the processing unit 71 may comprise one or more application-specific integrated circuits (“ASIC”).
  • the processing unit 71 also drives the display 42 to display results that may include the substance concentration, the measurements taken by the IR detectors 32 and 62 , 64 and/or the thermistor 38 , and other information of interest.
  • the processing unit 71 also controls a motor drive 74 , which in turn controls the drive motor 52 to change the position of the filter assembly 34 with respect to the IR detector 32 .
  • the illustrated control electronics 54 include one or more switches 75 for switching between measurement channels.
  • the switches 75 might change between a first channel that carries a signal from the IR detector 32 or IR detectors 62 , 64 and a second channel that carries a signal from the thermistor 38 .
  • the processing unit 71 controls the switches 75 .
  • the illustrated control electronics 54 further include an integrating amplifier 77 .
  • the integrating amplifier 77 amplifies a voltage generated by the IR detector 32 or IR detectors 62 , 64 to a measurable value.
  • the voltage generated by the IR detector 32 or IR detectors 62 , 64 is proportional to the detected body IR radiation, and may be very small.
  • the illustrated control electronics 54 further includes a comparator 79 .
  • the comparator 79 together with the integrating amplifier 77 , converts the voltage from the IR detector 32 or IR detectors 62 , 64 into a time interval that is inversely proportional to the input voltage and is measured by the processing unit 71 .
  • the heating/cooling apparatus 36 comprises a Peltier element 82 configured to provide a desired amount of heat or cold, a fan 84 to drive the heated or cooled air, and a funnel 86 to direct the heated or cooled air onto the body surface.
  • a Peltier element 82 configured to provide a desired amount of heat or cold
  • a fan 84 to drive the heated or cooled air
  • a funnel 86 to direct the heated or cooled air onto the body surface.
  • the heat/cooling apparatus 36 may be any apparatus that is suitable for this purpose.
  • Applying heat or cold to the body (skin) surface stimulates the absorption or emission of IR radiation by the substance whose concentration is to be measured.
  • IR radiation In the case of glucose, for example, cooling the skin stimulates the absorption of IR radiation while heating the skin stimulates the emission of IR radiation.
  • the heating/cooling apparatus 36 heats or cools the surface area of the body from a first temperature to a second temperature and maintains the surface area at the second temperature for a predetermined amount of time.
  • the heating/cooling apparatus 36 may also be utilized to heat or cool the surface area to change the temperature of the surface from the second temperature to the first temperature, or an intermediate temperature, at a controlled rate.
  • FIG. 7 a graph illustrating the temperature recovery function of the surface of a body as measured with the optical and detector system of FIGS. 3 , 4 and 5 is shown.
  • the graph 70 shown in FIG. 7 illustrates the temperature recovery function of the human skin as measured with an electro-optical system employing two IR filters.
  • the upper curve 73 describes the function of the recovery of the skin's temperature from a second temperature to a first temperature as measured with a filter for a first wavelength band where the substance of interest has a strong absorption/emission characteristic.
  • the lower curve 76 describes the function of the recovery of the skin's temperature from a second temperature to a first temperature as measured with a filter for a second wavelength band where the substance of interest has no or a negligible absorption/emission characteristic.
  • the lower curve 76 could describe the function of the recovery of the skin's temperature from a second temperature to a first temperature as measured with a filter for the entire FIR wavelength band including both a wavelength band where the substance of interest has a strong absorption/emission characteristic as well as the remaining wavelength band where the substance of interest has no or a negligible absorption/emission characteristic.
  • the IR radiation measurements taken by the IR detector 32 or the detectors 62 , 64 are plotted as a function of the temperature of the surface of the body versus the elapsed time when the temperature of the surface begins to change back to a first temperature from a second temperature.
  • the process flowchart 80 illustrates one embodiment of a method for measuring the concentration of a substance within a body.
  • the IR radiation detector(s) 32 or 62 , 64 and the heating/cooling apparatus 36 are positioned with respect to the body surface.
  • the heating/cooling apparatus 36 is activated to heat (or cool) the temperature of the body surface area, such as image area 12 (as shown in FIG. 4 ), for example, to change the surface area from a first temperature to a second temperature. The temperature of the body surface area is then held at the second temperature for a predetermined period of time.
  • the heating/cooling apparatus 36 is activated to cool (or heat) the body surface area to change the surface area from the second temperature back to the first temperature at a predetermined rate.
  • air at an ambient temperature may be used to cool (or heat) the body surface area to change the temperature of the body surface area from the second temperature back to the first temperature.
  • the absorption/emission of IR radiation over each of the first and second wavelength bands, the ambient temperature and the body surface temperature are measured at predetermined time intervals as the temperature of the body surface area changes back to the first temperature from the second temperature.
  • measurement of the IR radiation in both the first and second wavelengths is accomplished by switching between the two filters 44 , 46 at each of the predetermined time intervals.
  • all of the measured parameters including the IR radiation in both the first and second wavelength bands can be measured simultaneously.
  • the normalized ratio parameter is calculated from the IR radiation measurements.
  • the normalized ratio parameter is correlated with the ambient temperature and the body surface temperature using a lookup table.
  • the substance concentration is displayed.
  • an alternative method of measuring the absorption/emission of IR radiation, the ambient temperature and the body surface temperature is to first scan the body surface while taking multiple measurements at various points on the body surface to determine the most desirable location on the surface of the body to measure the concentration of the substance.
  • Software for example, may be used to identify the most desirable location on the surface of the body from the plurality of measurements taken during the body scan. Parameters for selecting the most desirable location may be, for example, repeatability, maximum signal strength, and the like.
US12/883,063 2008-04-11 2010-09-15 Method for non-invasive analysis of a substance concentration within a body Abandoned US20110004080A1 (en)

Priority Applications (14)

Application Number Priority Date Filing Date Title
US12/883,063 US20110004080A1 (en) 2008-04-11 2010-09-15 Method for non-invasive analysis of a substance concentration within a body
EP11825737.7A EP2615975A4 (en) 2010-09-15 2011-09-12 METHOD FOR NON-INVASIVE ANALYSIS OF THE CONCENTRATION OF A SUBSTANCE IN AN ORGANISM
EP19208977.9A EP3628223A3 (en) 2010-09-15 2011-09-12 Method for non-invasive analysis of a substance concentration within a body
PCT/US2011/051218 WO2012037029A1 (en) 2010-09-15 2011-09-12 Method for non-invasive analysis of a substance concentration within a body
AU2011302301A AU2011302301C1 (en) 2010-09-15 2011-09-12 Method for non-invasive analysis of a substance concentration within a body
BR112013005648A BR112013005648A2 (pt) 2010-09-15 2011-09-12 método para análise não invasiva de uma concentração de substância dentro de um corpo
CN201710799742.9A CN107647872A (zh) 2010-09-15 2011-09-12 用于非侵入性分析身体内物质浓度的方法
CN2011800439846A CN103118594A (zh) 2010-09-15 2011-09-12 用于非侵入性分析身体内物质浓度的方法
JP2013529225A JP5752796B2 (ja) 2010-09-15 2011-09-12 体内物質の濃度を非侵襲的に分析する方法
RU2013117005/14A RU2562173C2 (ru) 2010-09-15 2011-09-12 Способ для неинвазивного анализа концентрации вещества в теле
CA2810831A CA2810831C (en) 2010-09-15 2011-09-12 Method for non-invasive analysis of a substance concentration within a body
US14/312,464 US9681832B2 (en) 2008-04-11 2014-06-23 Measurement apparatuses and methods using a combined substance cooling device
JP2015101712A JP5963914B2 (ja) 2010-09-15 2015-05-19 体内物質の濃度を非侵襲的に分析する方法
US16/174,168 US11141082B2 (en) 2008-04-11 2018-10-29 Method for non-invasive analysis of a substance concentration within a body

Applications Claiming Priority (3)

Application Number Priority Date Filing Date Title
US12/101,859 US8401604B2 (en) 2008-04-11 2008-04-11 Apparatus and methods for non-invasive measurement of a substance within a body
US12/607,903 US8611975B2 (en) 2009-10-28 2009-10-28 Apparatus and method for non-invasive measurement of a substance within a body
US12/883,063 US20110004080A1 (en) 2008-04-11 2010-09-15 Method for non-invasive analysis of a substance concentration within a body

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US12/607,903 Continuation-In-Part US8611975B2 (en) 2008-04-11 2009-10-28 Apparatus and method for non-invasive measurement of a substance within a body

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US14/312,464 Continuation-In-Part US9681832B2 (en) 2008-04-11 2014-06-23 Measurement apparatuses and methods using a combined substance cooling device
US16/174,168 Continuation US11141082B2 (en) 2008-04-11 2018-10-29 Method for non-invasive analysis of a substance concentration within a body

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US12/883,063 Abandoned US20110004080A1 (en) 2008-04-11 2010-09-15 Method for non-invasive analysis of a substance concentration within a body
US16/174,168 Active 2029-05-24 US11141082B2 (en) 2008-04-11 2018-10-29 Method for non-invasive analysis of a substance concentration within a body

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EP (2) EP3628223A3 (pt)
JP (2) JP5752796B2 (pt)
CN (2) CN107647872A (pt)
AU (1) AU2011302301C1 (pt)
BR (1) BR112013005648A2 (pt)
CA (1) CA2810831C (pt)
RU (1) RU2562173C2 (pt)
WO (1) WO2012037029A1 (pt)

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WO2014209908A3 (en) * 2013-06-23 2015-02-26 Glucovista Inc. Substance concentration measurement using a cooling device with endothermic reaction
WO2015196138A1 (en) * 2014-06-19 2015-12-23 Glucovista, Inc. Substance concentration monitoring apparatuses and methods
WO2016149410A1 (en) * 2015-03-16 2016-09-22 Glucovista, Inc. Correcting non-invasive substance concentration signal measurements
JP2017006554A (ja) * 2015-06-25 2017-01-12 花王株式会社 経表皮水分蒸散量の変化量の推定方法
CN106506302A (zh) * 2015-09-03 2017-03-15 Ls 产电株式会社 支持动态modbus协议映射的通信装置
US9681832B2 (en) 2008-04-11 2017-06-20 Glucovista Inc. Measurement apparatuses and methods using a combined substance cooling device
US10588552B2 (en) 2014-06-19 2020-03-17 Glucovista Inc. Substance concentration analysis methods and apparatuses
US10987055B2 (en) 2017-05-19 2021-04-27 Glucovista Inc. Substance concentration NIR monitoring apparatuses and methods

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US9795329B2 (en) * 2014-01-10 2017-10-24 Glucovista Inc. Non-invasive device and method for measuring a substance concentration
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RU2644501C2 (ru) * 2016-02-09 2018-02-12 Федеральное государственное бюджетное образовательное учреждение высшего образования "Тамбовский государственный технический университет" (ФГБОУ ВО ТГТУ) Способ неинвазивного определения концентрации глюкозы в крови по глюкограмме
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