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WO2025206370A1 - Dispositif de mesure - Google Patents

Dispositif de mesure

Info

Publication number
WO2025206370A1
WO2025206370A1 PCT/JP2025/012963 JP2025012963W WO2025206370A1 WO 2025206370 A1 WO2025206370 A1 WO 2025206370A1 JP 2025012963 W JP2025012963 W JP 2025012963W WO 2025206370 A1 WO2025206370 A1 WO 2025206370A1
Authority
WO
WIPO (PCT)
Prior art keywords
substrate
signal
main surface
signal line
measuring device
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.)
Pending
Application number
PCT/JP2025/012963
Other languages
English (en)
Japanese (ja)
Inventor
貴之 関口
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.)
Taiyo Yuden Co Ltd
Original Assignee
Taiyo Yuden Co Ltd
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 Taiyo Yuden Co Ltd filed Critical Taiyo Yuden Co Ltd
Publication of WO2025206370A1 publication Critical patent/WO2025206370A1/fr
Pending legal-status Critical Current
Anticipated expiration legal-status Critical

Links

Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/145—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
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01R—MEASURING ELECTRIC VARIABLES; MEASURING MAGNETIC VARIABLES
    • G01R27/00—Arrangements for measuring resistance, reactance, impedance, or electric characteristics derived therefrom
    • G01R27/02—Measuring real or complex resistance, reactance, impedance, or other two-pole characteristics derived therefrom, e.g. time constant
    • G01R27/26—Measuring inductance or capacitance; Measuring quality factor, e.g. by using the resonance method; Measuring loss factor; Measuring dielectric constants ; Measuring impedance or related variables

Definitions

  • This embodiment relates to a measurement device.
  • the dielectric constant of a liquid varies depending on the concentration of glucose contained in the liquid.
  • the imaginary part of the complex dielectric constant (hereinafter simply referred to as the imaginary part) has different frequency characteristics depending on the glucose concentration. As shown by the arrow on the right side of this graph, the glucose concentration increases downward and decreases upward. As shown in the figure, at frequencies higher than the inflection point 300 near 10 GHz, the imaginary part becomes smaller as the glucose concentration in the aqueous solution increases. In the frequency range 310, the intervals between the three curves are wide, indicating that the imaginary part changes significantly with changes in glucose concentration.
  • the dielectric constant of human skin has a dependency on the glucose concentration in the interstitial fluid of the dermis layer similar to the glucose concentration dependency shown in Figure 1.
  • the measuring device estimates the blood glucose level as information related to the dielectric constant of the skin.
  • a sensor having a transmission line structure is used.
  • An AC signal flows through the signal line, and when the subject touches the signal line, the wavelength of the AC signal flowing through the signal line changes depending on the dielectric constant of the skin that touches the signal line. This change in wavelength is related to the dielectric constant of the skin.
  • the measuring device measures the blood glucose level by measuring the change in wavelength of the AC signal flowing through the signal line.
  • the information regarding the dielectric constant of a living body obtained by the measuring device is not limited to blood glucose levels.
  • the dielectric constant of a living body can also be affected by the amount of cancer cells. Therefore, the amount of cancer cells may also be measured as information regarding the dielectric constant of a living body.
  • Figure 2 is a top view of the blood glucose level measuring device 1.
  • Figure 3 is a cross-sectional view of the blood glucose level measuring device 1 taken along the III-III plane shown in Figure 2.
  • Figure 4 is a cross-sectional view of the blood glucose level measuring device 1 taken along the IV-IV plane shown in Figure 2.
  • the insulating film 11 does not necessarily have to be provided. If the insulating film 11 is not provided, the subject will directly touch the signal line 12 when measuring the blood glucose level. By providing the insulating film 11, it is possible to prevent the signal line 12 from becoming dirty or rusting due to the subject directly touching the signal line 12.
  • the integrated circuit 21 When measuring blood glucose levels, the integrated circuit 21 sends an AC electrical signal to the signal line 12 via a pair of conductors 16. The integrated circuit 21 then obtains the blood glucose level based on a comparison between the electrical signal that has passed through the signal line 12 (a sensor-passing signal, described below) and the electrical signal that has not passed through the signal line 12 (a local signal, described below).
  • Equation (1) is a general transmission line equation for voltage.
  • a and B are constants, and x is the position on the transmission line.
  • ⁇ is the initial phase.
  • ⁇ is the phase constant, which represents the amount of phase lead per unit length.
  • the first term on the right side of equation (1) represents a traveling wave
  • the second term represents a reflected wave.
  • the impedance of signal line 12 and the impedance of a phase detector (phase detector 212, described below) electrically connected to signal line 12 are matched.
  • the transmission line equation for signal line 12 in this embodiment can be expressed by the following equation (2).
  • phase constant ⁇ can be transformed into the following equation (3): L is the inductor of a circuit model equivalent to a transmission line, C is the capacitance of a circuit model equivalent to a transmission line, ⁇ ⁇ _eff is the effective relative permittivity, ⁇ 0 is the permittivity of a vacuum, ⁇ 0 is the magnetic permeability of a vacuum, and c is the speed of light.
  • Figure 6 is a diagram illustrating the phase change of an AC signal passing through signal line 12.
  • the wavelength of the AC signal at the dielectric constant of skin 201 in this fasting state is equal to the length (here, the length in the Y direction) from the input end (left end) to the output end (right end) of signal line 12.
  • the subject touches signal line 12 while fasting an AC signal is transmitted with a wavelength equal to the length of signal line 12, as shown in Figure 6 (A). Therefore, when the phase of the AC signal at the input end of signal line 12 is 0 radians, the phase of the AC signal at the output end of signal line 12 is 0 radians.
  • phase advance Rd The amount of phase advance of the AC signal passing through signal line 12 relative to the fasting state is referred to as phase advance Rd.
  • the blood glucose measuring device 1 calculates the phase lead amount Rd and calculates the blood glucose level based on the phase lead amount Rd.
  • the thickness of the sensor substrate 14 affects measurement sensitivity.
  • support substrate 13 is an example of a second substrate.
  • Surface 13a is an example of a third main surface.
  • Surface 13b is an example of a fourth main surface.
  • An integrated circuit 21 and passive components 22 are provided on surface 13b, opposite surface 13a of support substrate 13.
  • Passive components 22 are a group of components that generate power to drive integrated circuit 21, and may include resistors, capacitors, coils, etc. Based on the power supplied from passive components 22, integrated circuit 21 performs various processes, including measuring blood glucose levels.
  • Oscillator circuit 211 oscillates an AC signal of a single frequency.
  • the frequency of the AC signal oscillated by oscillator circuit 211 is a frequency selected from a range in which the dielectric constant of the skin can change depending on the blood sugar level.
  • Oscillator circuit 211 oscillates an AC signal of a frequency selected from range 310 in Figure 1, for example. Note that the frequency of the AC signal oscillated by oscillator circuit 211 may be selected from a range other than range 310.
  • the AC signal oscillated by the oscillator circuit 211 is an example of a first signal.
  • the AC signal that passes through the signal line 12, i.e., the sensor passing signal, is an example of a second signal.
  • the AC signal that does not pass through the signal line 12, i.e., the local signal, is an example of a third signal.
  • the phase detector 212 detects the phase difference Rx between the sensor passing signal and the local signal, and inputs the detected value of the phase difference to the calculation circuit 213.
  • the phase detector 212 may also be referred to as a phase comparator.
  • the arithmetic circuit 213 is a processor that executes predetermined arithmetic processing.
  • the arithmetic circuit 213 is, for example, a microcomputer unit equipped with a CPU (Central Processing Unit) and memory for storing programs, and the CPU executes arithmetic processing based on the programs.
  • the arithmetic circuit 213 may also be configured as a hardware circuit such as an FPGA (Field-Programmable Gate Array) or an ASIC (Application Specific Integrated Circuit).
  • the arithmetic circuit 213 may output the blood glucose measurement value in any manner. If the blood glucose measurement device 1 is connected to an output device such as a display device or speaker, the arithmetic circuit 213 may output the blood glucose measurement value to the output device such as a display device or speaker. If the blood glucose measurement device 1 is equipped with a memory, the blood glucose measurement value may be output to the memory. If the blood glucose measurement device 1 is connected to a communication device, the arithmetic circuit 213 may output the blood glucose measurement value to an external device via the communication device.
  • the arithmetic circuit 213 subtracts the fasting phase difference Ri, which is the phase difference Rx between the sensor passing signal and the local signal when the subject is fasting, from the phase difference Rx obtained in S101 to obtain the phase lead Rd (S102).
  • the fasting phase difference Ri is assumed to be measured in advance and stored in the arithmetic circuit 213 or in a memory accessible to the arithmetic circuit 213. For example, if the blood glucose measuring device 1 is implemented in a wearable device, the subject is asked to wear the blood glucose measuring device 1 all day, and the arithmetic circuit 213 stores the changes in the phase difference Rx during the wearing period. The arithmetic circuit 213 then stores the minimum value of the phase difference Rx as the fasting phase difference Ri. Note that the method of obtaining the fasting phase difference Ri is not limited to this.
  • the fasting blood glucose level Bi which is the blood glucose level when the subject is in a fasting state, is measured in advance and stored in association with the fasting phase difference Ri in the arithmetic circuit 213 or in a memory accessible to the arithmetic circuit 213.
  • the method for measuring the fasting blood glucose level Bi is not limited to a specific method.
  • the fasting blood glucose level Bi can be measured, for example, by drawing blood.
  • the arithmetic circuit 213 obtains the blood glucose fluctuation Bv from the fasting blood glucose Bi based on the phase lead Rd (S103).
  • a calibration curve (referred to as the first calibration curve) representing the relationship between the phase lead Rd and the fluctuation Bv is obtained in advance through simulation or an experiment using one or more subjects.
  • the first calibration curve may be a function or may be information in table format.
  • the first calibration curve is stored in advance in the arithmetic circuit 213 or in a memory accessible to the arithmetic circuit 213.
  • the arithmetic circuit 213 obtains the fluctuation Bv at the time of execution of S103 based on the phase lead Rd obtained in S102 and the first calibration curve.
  • the structure of the transmission line including the signal line 12 is not limited to the microstrip line structure.
  • a transmission line structure different from the microstrip line structure a blood glucose level measuring device 1a according to a first modified example will be described.
  • FIG 12 is a cross-sectional view of the blood glucose measuring device 1a cut along the ZX plane.
  • ground conductors 15a are provided on the surface 14a of the sensor substrate 14 so as to sandwich the signal line 12 from both sides.
  • the sensor substrate 14, ground conductor 15, signal line 12, and ground conductor 15a form a structure that includes a grounded coplanar line, which is a type of transmission line that differs from a microstrip line.
  • the arithmetic circuit 213 obtains the blood glucose level based on the phase difference between the sensor passing signal and the local signal.
  • the arithmetic circuit 213 may obtain the blood glucose level based on the frequency difference between the sensor passing signal and the local signal instead of the phase difference between the sensor passing signal and the local signal.
  • the oscillator circuit 211 oscillates a chirp signal.
  • the integrated circuit 21 includes a mixer circuit instead of the phase detector 212.
  • the mixer circuit generates a beat frequency signal indicating the frequency difference between the sensor passing signal and the local signal, and inputs this to the arithmetic circuit 213.
  • the arithmetic circuit 213 obtains a blood glucose measurement value based on the beat frequency signal.
  • the arithmetic circuit 213 may acquire the blood glucose level based on the phase difference between the sensor passing signal and the local signal, or may acquire the blood glucose level based on the frequency difference between the sensor passing signal and the local signal. In other words, the arithmetic circuit 213 is configured to acquire the blood glucose level based on a comparison between the sensor passing signal and the local signal.
  • the sensor substrate 14 has a relative dielectric constant of 4 or more and 20 or less.
  • the support substrate 13 may also be made of epoxy glass, LTCC, or aluminum oxide.
  • the support substrate 13 can be configured to be thicker than the sensor substrate 14.
  • the blood glucose level measuring devices 1, 1a, and 1b also include an oscillation circuit 211 that oscillates an AC signal, and an arithmetic circuit 213 that acquires the blood glucose level based on a comparison between a sensor passing signal, which is an AC signal that has passed through the signal line 12, and a local signal, which is an AC signal that has not passed through the signal line 12.
  • an integrated circuit 21 including an oscillator circuit 211 and an arithmetic circuit 213 may be provided on the surface 13b opposite the surface 13a of the support substrate 13.
  • the support substrate 13 does not necessarily have to be more rigid than the sensor substrate 14.
  • the sensor substrate 14 is made of one of the following materials: fluororesin, polyphenylene ether resin, ceramics, liquid crystal polymer resin, and polyimide resin, or a composite of two or more of these materials, and the support substrate 13 may be made of a different material from the sensor substrate 14.

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

Abstract

L'invention concerne un dispositif de mesure comprenant : un premier substrat qui est formé d'un diélectrique et qui a une première surface principale sur laquelle une ligne de signal est disposée et une deuxième surface principale qui est sur le côté opposé à la première surface principale et sur laquelle est disposé un conducteur de masse ayant une aire supérieure à l'aire de la ligne de signal dans une vue en plan ; et un second substrat qui a une rigidité à la flexion supérieure à celle du premier substrat et qui présente une troisième surface principale reliée à la deuxième surface principale via le conducteur de masse. Ledit dispositif de mesure mesure des informations concernant la permittivité d'un corps vivant.
PCT/JP2025/012963 2024-03-29 2025-03-28 Dispositif de mesure Pending WO2025206370A1 (fr)

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
JP2024-057433 2024-03-29
JP2024057433 2024-03-29

Publications (1)

Publication Number Publication Date
WO2025206370A1 true WO2025206370A1 (fr) 2025-10-02

Family

ID=97219832

Family Applications (1)

Application Number Title Priority Date Filing Date
PCT/JP2025/012963 Pending WO2025206370A1 (fr) 2024-03-29 2025-03-28 Dispositif de mesure

Country Status (1)

Country Link
WO (1) WO2025206370A1 (fr)

Citations (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20110160554A1 (en) * 2008-06-18 2011-06-30 Alexander Megej Device and method for determining at least one characterizing parameter of multilayer body tissue
JP2013532508A (ja) * 2010-07-21 2013-08-19 キマ メディカル テクノロジーズ リミテッド 埋込み式誘電測定装置
JP2021502880A (ja) * 2017-11-15 2021-02-04 シンガポール・ユニバーシティ・オブ・テクノロジー・アンド・デザインＳｉｎｇａｐｏｒｅ Ｕｎｉｖｅｒｓｉｔｙ ｏｆ Ｔｅｃｈｎｏｌｏｇｙ ａｎｄ Ｄｅｓｉｇｎ 血糖を非侵襲的に監視するための装置および方法
US20220039682A1 (en) * 2019-02-28 2022-02-10 American University Of Beirut Biomarker monitoring sensor and methods of use
WO2023048681A1 (fr) * 2021-09-24 2023-03-30 Gazi Universitesi Rektorlugu Capteur de mesure de glycémie non invasive de haute précision et système avec technologie microruban
WO2023145233A1 (fr) * 2022-01-31 2023-08-03 太陽誘電株式会社 Dispositif de mesure et procédé de mesure

Patent Citations (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20110160554A1 (en) * 2008-06-18 2011-06-30 Alexander Megej Device and method for determining at least one characterizing parameter of multilayer body tissue
JP2013532508A (ja) * 2010-07-21 2013-08-19 キマ メディカル テクノロジーズ リミテッド 埋込み式誘電測定装置
JP2021502880A (ja) * 2017-11-15 2021-02-04 シンガポール・ユニバーシティ・オブ・テクノロジー・アンド・デザインＳｉｎｇａｐｏｒｅ Ｕｎｉｖｅｒｓｉｔｙ ｏｆ Ｔｅｃｈｎｏｌｏｇｙ ａｎｄ Ｄｅｓｉｇｎ 血糖を非侵襲的に監視するための装置および方法
US20220039682A1 (en) * 2019-02-28 2022-02-10 American University Of Beirut Biomarker monitoring sensor and methods of use
WO2023048681A1 (fr) * 2021-09-24 2023-03-30 Gazi Universitesi Rektorlugu Capteur de mesure de glycémie non invasive de haute précision et système avec technologie microruban
WO2023145233A1 (fr) * 2022-01-31 2023-08-03 太陽誘電株式会社 Dispositif de mesure et procédé de mesure

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