Patent
Method and multisensory device for non-invasive blood glucose level monitoring
| العنوان: | Method and multisensory device for non-invasive blood glucose level monitoring |
|---|---|
| Patent Number: | 11925,463 |
| تاريخ النشر: | March 12, 2024 |
| Appl. No: | 16/303371 |
| Application Filed: | August 19, 2016 |
| مستخلص: | The present invention allows for non-invasive monitoring of the blood sugar levels in diabetic patients. At least one heat and waterproof applicator is applied to the skin surface by a dosage pressure. Temporal dynamics of physiological parameters of the local tissue region are measured under the applicator. Temporal dynamics of climatic parameters of the environment are measured simultaneously or before the beginning of measurement of physiological parameters in the monitoring mode. Further, enthalpy of tissue is calculated with account for the influence of climatic parameters. Magnitude of thermal effect of metabolism of the local area of living tissue is calculated on the basic thermodynamics equation, connecting enthalpy of tissue with variables of thermodynamic state. Relative changes in the level of glucose are calculated in blood, proportional to the value of the thermal metabolism of the local area of living tissue. |
| Inventors: | “INTERCELLULAR SUBSTANCE TECHNOLOGIES LABORATORY R&D INTERCELL” LIMITED LIABILITY COMPANY (“R&D INTERCELL” LLC) (Moscow, RU) |
| Assignees: | LCM Biosensor Technologies, Inc. (East Setauket, NY, US) |
| Claim: | 1. A method for monitoring blood glucose levels, the method comprising: applying at least one heat and waterproof applicator to a skin surface with a dosed pressure, forming a closed system in a local area of living tissue under the applicator; exerting an external physical effect on the local area of the tissue under the applicator, including the dosed pressure; measuring temporal dynamics of physiological parameters in the local area of the living tissue under the applicator, including at least the temporal dynamics of: osmotic pressure of an intercellular substance and/or an amount of water in an intercellular space of the tissue under the applicator; temperature of a dermis under the applicator via radio thermometry or heat flow through a skin area under the applicator via a heat detector; and elastic pressure of the tissue under the applicator, measuring values of environmental climatic parameters before beginning the measurement of the temporal dynamics of the physiological parameters, including at least: room temperature and relative humidity in a measurement room; and atmosphere pressure, measuring an external environment temperature or external heat flow through an enclosing structure between the measurement room and an external environment; calculating a value of enthalpy, H, in a layer of the tissue under the applicator accounting for an influence of the climatic parameters, according to the formula: H=H 0 (T skin , P sensor) x θ(T room , T ext , RH room , P atm), where T skin is the temperature of the dermis, P sensor is the dosed pressure of the applicator on the skin surface, T room is the room temperature, T ext is an ambient air temperature behind the enclosing structure, RH room is the relative humidity in the measurement room, and P atm is the atmospheric pressure; and calculating changes in blood glucose level based on a thermodynamics equation that connects the enthalpy with thermodynamic variables or variables of a thermodynamic state. |
| Claim: | 2. The method according to claim 1 , wherein calibration parameters are determined in order to determine phenomenological constants used in the calculating of the changes in the blood glucose level. |
| Claim: | 3. The method according to claim 2 , wherein the calibration parameters are determined individually for each patient by invasive blood glucose measurements. |
| Claim: | 4. The method according to claim 3 , wherein the calibration parameters are determined by a calibration procedure comprising measuring a continuous glucose level in blood under conditions of a glucose tolerance test and determining tissue-to-insulin sensitivity. |
| Claim: | 5. The method according to claim 1 , wherein the temperature of the dermis under the applicator is determined by measuring temporal dynamics of a skin surface temperature under the applicator. |
| Claim: | 6. The method according to claim 1 , wherein the amount of water and its equilibrium content in the intercellular space of the tissue under the applicator includes temporal dynamics of the amount of water and its equilibrium content in the intercellular space of predetermined layers of the skin and subcutaneous tissues under the applicator, wherein the predetermined layers include the layer, and wherein the amount of water and its equilibrium content in the intercellular space of the predetermined layers of the skin and the subcutaneous tissues under the applicator is determined by measuring an amount of water in the stratum corneum under the applicator. |
| Claim: | 7. The method according to claim 6 , wherein a change in the amount of water in the local area of the tissue under the applicator is determined by measuring electrical characteristics of the stratum corneum. |
| Claim: | 8. The method according to claim 6 , wherein a change in the amount of water in the local area of the tissue under the applicator is determined by measuring spectral characteristics of the stratum corneum. |
| Claim: | 9. The method according to claim 6 , wherein a change in the amount of water in the local area of the tissue under the applicator is determined by measuring thermophysical characteristics of the stratum corneum. |
| Claim: | 10. The method according to claim 6 , further comprising making an additional measurement of a dependence of a change in the amount of the water in the intercellular space under the applicator on the external physical effect, and calculating a quantity of water that ensures swelling of the intercellular substance in a predetermined state. |
| Claim: | 11. The method according to claim 10 , wherein the external physical effect further includes local decompression, heating, cooling, exposure to electric current, or magnetic field. |
| Claim: | 12. The method according to claim 11 , wherein additional parameters are measured to determine a state of the intercellular substance, and wherein the additional parameters are selected from a group consisting of: blood pressure and acidity. |
| Claim: | 13. The method according to claim 1 , wherein the local area of the living tissue is located on a hand. |
| Claim: | 14. The method according to claim 1 , further comprising calculating a heat generation rate in metabolism of the local area of the living tissue. |
| Claim: | 15. The method according to claim 1 , further comprising calculating an intensity of metabolism of the local area of the living tissue. |
| Claim: | 16. The method according to claim 15 , wherein the calculation of the intensity of the metabolism of the local area of the living tissue is a calculation of basal metabolism intensity of the local area of the living tissue. |
| Claim: | 17. The method according to claim 16 , further comprising measuring additional physiological and biochemical parameters to characterize the metabolism of the local area of living tissue. |
| Claim: | 18. The method according to claim 17 , wherein at least one of the additional physiological and biochemical parameters is selected from a group consisting of: at least one biochemical parameter of blood, partial pressure of oxygen in the blood, partial pressure of carbon dioxide in the blood, heart rate, and blood pressure. |
| Claim: | 19. The method according to claim 18 , wherein another of the additional physiological and biochemical parameters is selected from blood acidity, blood lactate concentration, and glucocorticoid hormone. |
| Claim: | 20. The method according to claim 19 , wherein a concentration of the another of the additional physiological and biochemical parameters is calculated by measuring dynamics thereof in the stratum corneum. |
| Claim: | 21. The method according to claim 19 , wherein a concentration of the another of the additional physiological and biochemical parameters is calculated by measuring dynamics thereof in a sweat solution of a sweat gland under the applicator. |
| Claim: | 22. The method according to claim 17 , wherein another of the additional physiological and biochemical parameters is an electrophysiological parameter. |
| Claim: | 23. The method according to claim 1 , wherein the layer of the tissue under the applicator for which the value of enthalpy is calculated is a deep layer of the skin. |
| Claim: | 24. The method according to claim 1 , wherein the thermodynamics equation that connects the enthalpy with the thermodynamic variables or the variables of the thermodynamic state is ΔH=ΔQ MET +ΔQ ΔT +K M ×ΔM+K P ×ΔP, where: ΔH is a change in the enthalpy resulting from tissue transition in the tissue under the applicator into a local thermodynamic equilibrium state; ΔQ MET is an amount of heat entering the tissue under the applicator during mass transfer; ΔQ ΔT is an amount of heat entering the tissue under the applicator during heat transition caused by a temperature gradient between the skin surface and a depth; K M and K P are constants; ΔM is a change in the amount of water in the tissue under the applicator during mass transfer caused by a chemical potential gradient between the skin surface and the depth; and ΔP is a change in the elastic pressure of the tissue under the applicator during the mass transfer. |
| Claim: | 25. The method according to claim 1 , wherein the amount of water and its equilibrium content in the intercellular space of predetermined layers of the skin and subcutaneous tissues under the applicator are determined by temporal dynamics of the amount of water in the local area of the tissue under the applicator, wherein the predetermined layers include the layer. |
| Claim: | 26. A device for monitoring blood glucose levels, comprising: a heat and waterproof applicator having upper and inner surfaces and adapted to be applied on skin with a dosed pressure so as to form a closed system in a local area of living tissue under the applicator, sensors configured to measure physiological parameters, sensors configured to measure climatic parameters, a device configured to calibrate on a tissue site under the applicator, an installation platform for fixing the climatic parameters sensors, fixed over the applicator, at least one of an amplifier and an analog-digital converter installed on the upper surface of the applicator, and a processor, wherein the sensors configured to measure the climatic parameters are located on the installation platform, and the sensors configured to measure the physiological parameters are placed under the applicator, wherein the device is configured such that signals from the sensors configured to measure the physiological parameters and the sensors configured to measure the climatic parameters are sequentially applied to inputs of the at least one of the amplifier and the analog-digital converter; wherein the processor is configured to perform operations comprising: measuring temporal dynamics of the physiological parameters in the local area of the living tissue under the applicator, including at least the temporal dynamics of: osmotic pressure of an intercellular substance and/or an amount of water in an intercellular space of the tissue under the applicator; temperature of a dermis under the applicator via radio thermometry or heat flow through a skin area under the applicator via a heat detector; and elastic pressure of the tissue under the applicator, measuring values of environmental climatic parameters before beginning the measurement of the temporal dynamics of the physiological parameters, including at least: room temperature and relative humidity in a measurement room; and atmosphere pressure, measuring an external environment temperature or external heat flow through an enclosing structure between the measurement room and an external environment; calculating a value of enthalpy, H, in a layer of the tissue under the applicator accounting for an influence of the climatic parameters, according to the formula: H=H 0 (T skin , P sensor) x θ(T room , T ext , RH room , P atm), where T skin is the temperature of the dermis, P sensor is the dosed pressure of the applicator on a skin surface, T room is the room temperature, T ext is an ambient air temperature behind the enclosing structure, RH room is the relative humidity in the measurement room, and P atm is the atmospheric pressure; and calculating changes in blood glucose level based on a thermodynamics equation that connects the enthalpy with thermodynamic variables or variables of a thermodynamic state. |
| Claim: | 27. The device according to claim 26 , further comprising a resistor or Peltier element configured to provide thermal power, an electric current, voltage, or electromagnetic radiation source; and a device configured to create the dosed pressure for the applicator. |
| Claim: | 28. The device according to claim 26 , further comprising at least one sensor configured to measure the amount of water in the intercellular space of the tissue under the applicator by measuring water content in the stratum corneum. |
| Claim: | 29. The device according to claim 28 , wherein the at least one sensor configured to measure the amount of water in the intercellular space of the tissue under the applicator is configured to measure electrical characteristics of the stratum corneum. |
| Claim: | 30. The device according to claim 29 , wherein the at least one sensor configured to measure the electrical characteristics of the stratum corneum comprises at least one base electrode and at least one measuring electrode, a device for creating the dosed pressure, a power supply, and a measuring unit, wherein at least one of the base and measuring electrodes is made in a form of a dry waterproof design. |
| Claim: | 31. The device according to claim 30 , wherein an area of the at least one base electrode is larger than an area of the at least one measuring electrode. |
| Claim: | 32. The device according to claim 31 , wherein the area of the at least one measuring electrode satisfies the following condition: S (mm 2)>2P (mm)* 0.4 (mm). |
| Claim: | 33. The device according to claim 31 , wherein a working surface of the at least one base electrode is provided with means for increasing conductivity of the skin at a point of contact therewith. |
| Claim: | 34. The device according to claim 33 , wherein the means for increasing conductivity of the skin includes electrically conductive paste. |
| Claim: | 35. The device according to claim 30 , wherein the at least one base electrode and the at least one measuring electrode are aligned disks with a total area defined by a diameter larger than a predetermined size. |
| Claim: | 36. The device according to claim 35 , wherein the at least one base electrode and the at least one measuring electrode are formed as reciprocally coaxial discs. |
| Claim: | 37. The device according to claim 30 , wherein the measuring unit is configured to measure transverse electro-conductivity of the stratum corneum at a constant current or at a frequency current below a threshold. |
| Claim: | 38. The device according to claim 30 , wherein the measuring unit is configured to measure the dielectric constant of the stratum corneum at frequencies below a threshold. |
| Claim: | 39. The device according to claim 28 , wherein a the at least one sensor configured to measure the amount of water in the intercellular space of the tissue under the applicator is configured to measure spectral characteristics of the stratum corneum. |
| Claim: | 40. The device of claim 28 , wherein the at least one sensor configured to measure the amount of water in the intercellular space of the tissue under the applicator is configured to measure thermophysical characteristics of the stratum corneum. |
| Claim: | 41. The device according to claim 28 , wherein the at least one sensor configured to measure the amount of water in the intercellular space of the tissue under the applicator is configured to measure tissue pressure or the osmotic pressure of the intercellular substance. |
| Claim: | 42. The device according to claim 28 , wherein the at least one sensor configured to measure the amount of water in the intercellular space of the tissue under the applicator is configured to measure hydraulic pressure in a microcirculation system. |
| Claim: | 43. The device according to claim 28 , wherein the at least one sensor configured to measure the amount of water in the intercellular space of the tissue under the applicator is configured to measure the elastic pressure. |
| Claim: | 44. The device according to claim 28 , wherein the sensors configured to measure physiological parameters comprises an additional sensor for measuring metabolism, wherein the additional sensor is selected from a group consisting of blood biochemical parameters sensors and sensors for parameters of an acid-base state. |
| Claim: | 45. The device according to claim 44 , wherein the sensors for the parameters of the acid-base state include a blood lactate sensor. |
| Claim: | 46. The device according to claim 44 , wherein the sensors for the parameters of the acid-base state include a blood acidity sensor. |
| Claim: | 47. The device according to claim 44 , wherein the additional sensor is a blood cortisol sensor. |
| Claim: | 48. The device according to claim 44 , wherein the additional sensor is a heart rate sensor. |
| Claim: | 49. The device according to claim 44 , wherein the additional sensor is an electrophysiological parameter sensor. |
| Claim: | 50. The device according to claim 26 , wherein at least an air temperature sensor, a relative air humidity sensor in the measurement room, and a heat flow sensor configured to measure the heat flow through the enclosing structure between the measurement room and the external environment are used as the sensors configured to measure climatic parameters. |
| Claim: | 51. The device according to claim 26 , wherein the applicator is designed as a measuring capsule forming a closed cavity with diffusion and thermal contact with the skin surface. |
| Claim: | 52. The device according to claim 51 , wherein the closed cavity of the measuring capsule is hermetically sealed, and a working surface of the cavity for contacting the skin is made of a rigid membrane that is permeable or semi-permeable for water and heat. |
| Claim: | 53. The device according to claim 51 , wherein the closed cavity of the measuring capsule lacks a mechanical contact for contacting with the skin. |
| Claim: | 54. The device according to claim 51 , wherein the closed cavity of the measuring capsule serves as a water quantity sensor. |
| Claim: | 55. The device according to claim 54 , wherein the water quantity sensor is a water vapor pressure sensor. |
| Claim: | 56. The device according to claim 54 , wherein the water quantity sensor is a water vapor concentration sensor. |
| Claim: | 57. The device according to claim 56 , wherein the water vapor concentration sensor is based on spectroscopy. |
| Claim: | 58. The device according to claim 54 , wherein the water quantity sensor is configured to sense thermophysical characteristics of water vapor. |
| Claim: | 59. The device according to claim 54 , wherein the water quantity sensor is configured to sense heat capacity or thermal conductivity of water vapor. |
| Claim: | 60. The device according to claim 26 , further comprising pneumatic, mechanical, piezoelectric, electromagnetic, vacuum, or hydraulic means for creating the dosed pressure. |
| Patent References Cited: | 6918874 July 2005 Hatch 20090209828 August 2009 Musin 20120010477 January 2012 Amano 2 396 897 August 2010 201315991 April 2013 |
| Other References: | English translation of TW 201315991, patents.google.com, 10 pages, printed on Mar. 8, 2023 (Year: 2023). cited by examiner International Search Report for PCT/RU2016/000561, dated Feb. 9, 2017, 4 pages. cited by applicant Hamlin Shannan K. et al., “Monitoring Tissue Perfusion and Oxygenation”, 2014, p. 353, 354. cited by applicant Musin R.F., et al., “Natural Water Diffusion Through the Stratum Corneum of the Human Body Epidermis and its Electrical Properties”, Academy of Sciences of the USSR, the Institute of Radioengineering and Electronics, 1984, pp. 63-67. cited by applicant Musin R.F., et al., “Membrane Mechanisms of Water Transport in Epidermis”, Water and Ions in Biological Systems, 1988, pp. 167-172. cited by applicant Smith John L., The Pursuit of Noninvasive Glucose: “Hunting the Deceitful Turkey”, 2015, 192 pages. cited by applicant Stroitelnaia fizika (Transl: Structure Physics), Vlagosoderzhanie, 2011, p. 14.03. cited by applicant |
| Primary Examiner: | Kremer, Matthew |
| Attorney, Agent or Firm: | Nixon & Vanderhye PC |
| رقم الانضمام: | edspgr.11925463 |
| قاعدة البيانات: | USPTO Patent Grants |
| الوصف غير متاح. |