Biological information measuring device

Abstract

To provide a biological information measuring device capable of detecting an appropriate pressure as a pressure applied to a detection part of a dielectric sensor.SOLUTION: A blood glucose level measuring device 1 includes: a sensor unit 7 including a dielectric sensor 31 having a sensor substrate 31a, a detection unit 31b formed of a conductive material provided on one surface of the sensor substrate and a ground conductive material 311 having a surface area larger than a surface area of the detection unit 31b provided on the other surface of the sensor substrate, a pressure sensor 371 having a pressure detection unit 371a for detecting a pressure applied to the pressure detection unit 371a, a pressure transmission member 35 composed of a rigid body for transmitting the pressure applied to the dielectric sensor 31 to the pressure detection unit 371a, and a rigid first belt part 21a for supporting the pressure detection unit 371a in a state of being sandwiched between the pressure transmission member 35 and itself; a belt 2 on which the sensor unit 7 is provided; an air pump 63 and an air bag 52 for applying a pressing force to the dielectric sensor 31; and a control unit 62 configured to control the pressing force based on the pressure detected by the pressure sensor 371.SELECTED DRAWING: Figure 1

Description

[Technical Field]

[0001] The present invention relates to a biological information measuring device that measures biological information using a dielectric sensor. [Background technology]

[0002] Traditionally, technology that measures biometric information such as blood glucose levels non-invasively using wearable devices attached to the human body, such as wristbands and smartwatches, has been attracting attention.

[0003] Patent Document 1 discloses a technology that uses an infrared light source, a sensor, and a contact force sensor to detect the contact force with the arm to accurately measure the concentration of a biological component (blood glucose level) by wearing the device on the arm and using the reflection of infrared light, and then compares the contact force with a judgment value and calculates the blood glucose level using light intensity data when the contact force is within a predetermined range.

[0004] Patent Document 2 discloses a technology for improving the accuracy of measuring biological information (blood glucose level) using light, in which a pressure mechanism built into the main body case applies an optimal pressure to the skin surface of the subject, which is the measurement site. In this technology, the optimal pressure is defined as the point at which the amplitude of the volume pulse wave detected using a sensor module is maximized while changing the pressure. Furthermore, in an example, a technology is disclosed in which vein authentication technology is applied to detect blood vessels and blood glucose levels are measured only in areas where blood vessels are present.

[0005] Patent Document 3 discloses a technique in which a pulse wave measuring device is worn on the wrist, an air pump is driven, and air supplied by the air pump flows into an air bag, which is then inflated until the air pressure reaches a predetermined pressure value, thereby maintaining the device in an appropriate position where the pulse wave can be accurately measured. [Prior art documents] [Patent documents]

[0006] [Patent Document 1] Japanese Patent Application Laid-Open No. 2015-198689 [Patent Document 2] Japanese Patent Application Laid-Open No. 2016-112042 [Patent Document 3] Japanese Patent Application Laid-Open No. 2009-066179 Summary of the Invention [Problem to be solved by the invention]

[0007] However, the above-mentioned prior art only measures the optimal pressure to press against the skin surface in order to ensure and maintain an accurate measurement position and to accurately measure the pulse wave, but does not specifically mention the pressure applied to the sensor itself that measures the pulse wave, etc. Dielectric sensors that detect the dielectric constant experience fluctuations in the dielectric constant depending on the state of contact between the conductive detection unit and the skin. In particular, since the measurement results change depending on the pressure applied to the detection unit, the above-mentioned prior art pressure detection method was unable to detect the appropriate pressure applied to the detection unit. The present invention has been made in consideration of the above-mentioned problems, and aims to provide a biological information measuring device having a structure capable of detecting an appropriate pressure as the pressure applied to the detection portion of a dielectric sensor. [Means for solving the problem]

[0008] The present invention provides a biological information measuring device comprising: a sensor having a first substrate having a first surface and a second surface opposite to the first surface and including a dielectric; a first conductor provided on the first surface of the first substrate; and a second conductor provided at a position on the first substrate away from the first conductor and having a surface area larger than the surface area of ​​the first conductor when viewed in a plan view; a pressure sensor having a detection unit and detecting pressure applied to the detection unit; a sensor unit comprising: a rigid body having a third surface and a fourth surface opposite to the third surface, the third surface abutting the second surface of the sensor, the fourth surface abutting the detection unit of the pressure sensor; and a rigid support member having an abutment portion abutting a part of the detection unit opposite to the side abutting the pressure transmission member, the rigid support member supporting the detection unit; a belt on which the sensor unit is provided; a pressing unit provided on the belt and applying a pressing force to the sensor; and a control unit that controls the pressing force of the pressing unit based on the pressure detected by the pressure sensor. In the above configuration, the control unit may be configured to control the pressing force of the pressing unit so that the pressing force becomes a predetermined pressing force that allows the sensor to obtain appropriate biological information. In the above configuration, a buffer material may be provided between the second surface of the sensor and the third surface of the pressure transmitting member. In the above configuration, the pressure transmission member may be configured to have a blocking portion formed on the outer edge of the third surface so as to surround the end of the cushioning material on the third surface side, thereby preventing lateral movement of the cushioning material. In the above configuration, the sensor may be configured to include a crown-shaped lid portion provided between the second surface of the sensor and the cushioning material, which covers the surface of the cushioning material facing the second surface and the side of the end portion on the second surface side.

[0009] In the above configuration, the pressing unit may have an air bag provided on the belt in a position facing the first surface of the sensor when the belt is worn, and an electric pump that supplies air to the air bag, and the electric pump inflates the air bag to indirectly apply a pressing force to the first surface, and the control unit may be configured to control the amount of air supplied by the electric pump to the air bag based on the pressure detected by the pressure sensor. In the above configuration, at least a portion of the belt to which the sensor unit is attached may be rigid, and the support member may be formed from the rigid portion of the belt. In the above configuration, a rigid second substrate may be provided, and at least the detection portion of the pressure sensor may be provided on the second substrate, and the support member may be formed from the second substrate. In the above configuration, the pressure sensor may be a resistance change type pressure sensor or a capacitance type pressure sensor. In the above configuration, the buffer material may be made of sponge, spring, or rubber. In the aforementioned configuration, the sensor may be configured to detect the dielectric constant of the subject's skin based on a change in a signal flowing through the first conductor. In the aforementioned configuration, the control unit may be configured to calculate biological information of the subject based on the dielectric constant detected by the sensor. The above configuration may further include an output device that outputs the bioinformation calculated by the control unit. In the above configuration, a rigid second substrate may be provided, and components including one or more of a circuit for driving the sensor, a circuit for processing the output of the sensor, the pressure sensor, a circuit for driving the pressure sensor, and a circuit for processing the output of the pressure sensor may be provided on the second substrate, and the support member may be formed from the second substrate.

[0010] The present invention is a biological information measuring device comprising: a sensor having a substrate including a dielectric, a first conductor provided on one side of the substrate, and a second conductor provided at a position on the substrate away from the first conductor and having a surface area larger than the surface area of ​​the first conductor when viewed in a plan view; a pressure sensor having a detection unit and detecting pressure applied to the detection unit; a pressure transmission member made of a rigid body that transmits the pressure applied to the sensor to the detection unit; and a rigid support member that supports the detection unit while sandwiching it between the detection unit and the pressure transmission member; a belt on which the sensor unit is provided; a pressing unit provided on the belt that applies a pressing force to the sensor; and a control unit that controls the pressing force of the pressing unit based on the pressure detected by the pressure sensor.

[0011] The present invention is a bioinformation measuring device comprising: a sensor having a substrate that is rigid and includes a dielectric, a first conductor provided on one side of the substrate, and a second conductor provided at a position on the substrate away from the first conductor and having a surface area larger than the surface area of ​​the first conductor when viewed in a plan view; a sensor unit including a pressure sensor having a detection unit and detecting pressure applied to the detection unit, and a rigid support member that supports the detection unit sandwiched between the detection unit and the substrate; a belt on which the sensor unit is provided; a pressing unit provided on the belt that applies a pressing force to the sensor; and a control unit that controls the pressing force of the pressing unit based on the pressure detected by the pressure sensor. [Effects of the Invention]

[0012] According to the present invention, it is possible to detect an appropriate pressure as the pressure applied to the detection portion of the dielectric sensor. [Brief explanation of the drawings]

[0013] [Figure 1] FIG. 1(a) is a side view showing a schematic configuration example of a blood glucose level measuring device 100 according to a first embodiment, and FIG. 1(b) is a side view of the blood glucose level measuring device 100 of FIG. 1(a) with the drive control unit 6 removed. [Figure 2](a) is a perspective view of the blood glucose measuring device 100 of Figure 1(b) rotated 180 degrees, and (b) is a view of the state in which the pressure transmission unit 30 of the sensor unit 7 has been removed from (a). [Figure 3] 2 is a partial cross-sectional view including a sensor unit 7 of the blood glucose level measuring device 100. FIG. [Figure 4] FIG. 2 is a perspective view of a dielectric sensor 31. [Figure 5] (A) and (B) are schematic diagrams illustrating the change in wavelength of the AC signal passing through the detection unit 31b of the dielectric sensor 31 when the skin 201 of the subject is pressed against the detection unit 31b when fasting and after a meal. [Figure 6] 10 is a schematic diagram illustrating an example of the transition over time of an AC signal flowing through the detection section 31b when the measurement subject touches the detection section 31b of the dielectric sensor 31 of the first embodiment. FIG. [Figure 7] 10(a) and 10(b) are diagrams showing the blood glucose measuring device 100 worn by a subject. [Figure 8] 10 is a diagram showing the order in which pressure generated by the inflation of air bag 52 is transmitted. FIG. [Figure 9] FIG. 2 is a functional block diagram showing the functional configuration of a control unit 62 according to the first embodiment. [Figure 10] 10 is a diagram showing an example of the relationship between pressure applied to the dielectric sensor 31 and a phase change relative to the magnitude of the pressure. FIG. [Figure 11] 10 is a flowchart showing a blood glucose level measurement process. [Figure 12] 10 is a flowchart showing a blood glucose level calculation process. [Figure 13] FIG. 10 is a diagram showing phase characteristics with respect to the number of measurements taken while at rest using a blood glucose measuring device of a conventional configuration in which measurements are taken by placing a dielectric sensor on the arm using its own weight. [Figure 14] FIG. 10 is a diagram showing phase characteristics with respect to elapsed time when the blood glucose measuring device of the conventional configuration is at rest. [Figure 15] FIG. 4 is a diagram showing phase characteristics with respect to the number of measurements taken at rest by the blood glucose level measuring device 100 of the first embodiment. [Figure 16]FIG. 4 is a diagram showing phase characteristics with respect to elapsed time at rest by the blood glucose measuring device 100 of the first embodiment. [Figure 17] FIG. 10 is a diagram showing contact pressure when the arm is swung in the blood glucose measuring device 100 of the first embodiment with and without close contact due to expansion of the air bag 52. [Figure 18] 10 is a partial cross-sectional view including a sensor unit 7A of a blood glucose level measuring device 100A according to a second embodiment. FIG. [Figure 19] 1(a) is a partial cross-sectional view of a blood glucose level measuring device 100B according to a modified example, and FIG. 1(b) is a partial cross-sectional view of a blood glucose level measuring device 100B according to a modified example. DETAILED DESCRIPTION OF THE INVENTION

[0014] DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS Hereinafter, embodiments of the present invention will be described in detail with reference to the accompanying drawings. The embodiment described below is an example of a means for realizing the present invention, and should be appropriately modified or changed depending on the configuration of the device to which the present invention is applied and various conditions, and the present invention is not limited to the embodiment described below.

[0015] In addition, in the following description of the drawings, the same or similar parts are designated by the same or similar reference numerals. However, it should be noted that the drawings are schematic, and the vertical and horizontal dimensions and scales of the components or parts may differ from those of the actual parts. Therefore, the specific dimensions and scales should be determined by taking into consideration the following explanation. Furthermore, it goes without saying that the drawings may include parts whose dimensional relationships and ratios differ from one another. [First embodiment] First, a first embodiment of the present invention will be described, with reference to Figures 1 to 11 showing the first embodiment. 〔composition〕 In the first embodiment, a case will be described in which a biological information measuring device according to the present invention is applied to a wearable blood glucose level measuring device that is worn on the arm.

[0016] 1(a) and (b) and 2(a) and (b), when the belt 2 of the blood glucose measuring device 1 is closed, the thickness direction is the Z direction, the width direction is the Y direction, and the direction perpendicular to the Z direction and the Y direction is the X direction. The same applies to Figures 3 and onwards. As shown in FIGS. 1(a) and 1(b), the blood glucose measuring device 100 includes a housing 1, a belt 2, a pressing unit 5, a drive control unit 6, and a sensor unit . The housing 1 has a flat shape and is provided with a drive control unit 6. The housing 1 is configured to include an upper surface, a lower surface, and a side surface connecting the periphery of the upper surface and the periphery of the lower surface. A belt 2 is attached to the housing 1, and is used by being worn on an arm 200 near the wrist of a person to be measured, which will be described later. As shown in FIGS. 1(a) and 1(b) and 2(a) and 2(b), the belt 2 includes a belt portion 21, a hinge 22, and a snap-fastening portion 23. The belt portion 21 includes a first belt portion 21a that is arc-shaped when viewed from the X direction, and a second belt portion 21b that has substantially the same shape as the first belt portion 21a.

[0017] In the first embodiment, the first belt portion 21a and the second belt portion 21b are rigid bodies made of, for example, rigid hollow members. The first belt portion 21a has a first end portion and a first other end portion. The second belt portion 21b has a second end portion and a second other end portion. The first belt portion 21a and the second belt portion 21b may be made of, for example, a rigid metal member or a resin member.

[0018] The hinge 22 connects a first end portion of the first belt portion 21a and a second end portion of the second belt portion 21b so that they can rotate around the hinge axis. This allows the arc-shaped first belt portion 21a and second belt portion 21b to rotate in directions that move the first other end portion and the second other end portion away from each other, thereby opening the belt 2. On the other hand, the belt 2 can be closed by rotating in directions that move the first other end portion and the second other end portion toward each other. When the belt 2 is closed, it has a substantially circular shape when viewed from the X direction.

[0019] 2(a) and 2(b), the snap fastening portion 23 is composed of a convex portion provided at the first other end portion of the first belt portion 21a and a concave portion provided at the second other end portion of the second belt portion 21b. The convex portion and the concave portion are configured so that the convex portion fits into the concave portion when the belt 2 is in a closed state. In other words, the first other end portion of the first belt portion 21a and the second other end portion of the second belt portion 21b can be connected. This allows the belt 2 to be maintained in a closed state. As shown in FIGS. 1(a) and 1(b), the pressing portion 5 includes a connecting portion 51 that connects to the second belt portion 21b, and an air bag 52 attached to the connecting portion 51. The drive control unit 6 includes a control unit 62, an air pump 63, an oscillator 64, a phase detector 65, and an output device 66. For example, electronic components such as ICs are mounted on a circuit board 61 such as a printed circuit board to realize the functions of the control unit 62, oscillator 64, and phase detector 65. This circuit board 61 is electrically connected to the dielectric sensor 31, the air pump 62, and the display device 66 via wiring. As shown in FIG. 1, this circuit board 61 is housed inside the housing 1. The control unit 62 executes calculations based on the detected values ​​from the sensors that make up the sensor unit 7, and controls the operations of the air pump 63, the output device 66, etc. based on the calculation results. The control unit 62 is composed of a microcomputer. Hereinafter, the microcomputer will be referred to as a "micon."

[0020] A microcomputer is composed of a CPU (Central Processing Unit) that controls calculations and the entire device based on a control program, a ROM (Read Only Memory) that stores the CPU's control program and other information in a predetermined area, a RAM (Random Access Memory) that stores data read from the ROM and the calculation results required in the CPU's calculation process, and an I / F (Interface) that mediates the input and output of data to and from external devices.These components are connected to each other by a bus, which is a signal line for transferring data, so that data can be sent and received. Air pump 63 includes electric pump 63a and air transport pipe 63b. As shown in FIG. 1, electric pump 63a and a portion of air transport pipe 63b are housed inside housing 1. Air pump 63 drives electric pump 63a in response to a control signal from control unit 62, and supplies air into air bag 52 via air transport pipe 63b. This causes air bag 52 to expand, thereby pressing against arm 200 of the subject. Alternatively, driving electric pump 63a to suck up air from air bag 52 and contract air bag 52 reduces the pressing force acting on arm 200.

[0021] The air transport pipe 63b is disposed inside the first belt portion 21a and the second belt portion 21b, and one end thereof is connected to the electric pump 63a. The other end of the air transport pipe 63b is connected to the air bag 52 through a communication hole that is in communication with the hollow portion inside the second belt portion 21b and that is provided in the connecting portion 51 of the pressing portion 5. The air transport pipe 63b may be made of metal, resin material, or the like. The air transport pipe 63b may also be made of rigid piping or soft tubing. In the first embodiment, the first belt portion 21a and the second belt portion 21b are configured to rotate around the hinge axis, but may instead be made of flexible tubing.

[0022] The oscillator 64 and the phase detector 65 are electrically connected to the dielectric sensor 31, which will be described later, and output a detection signal. The output device 66 is a device that displays and outputs information such as the blood glucose level calculated by the control unit 62. That is, the output device 66 has an image display unit, a speaker, etc. As shown in FIG. 1, it is provided on the surface of the housing 1 opposite to the belt. As shown in FIGS. 1(a) and 1(b), the sensor section 7 includes a pressure transmitting section 30 and a pressure detecting device 37. As shown in FIGS. 2(a) and 3, the pressure transmitting section 30 includes a dielectric sensor 31, a buffer material 33, and a pressure transmitting member .

[0023] 3 and 4, the dielectric sensor 31 includes a sensor substrate 31a and a detection unit 31b made of a conductor. This conductor is also referred to as a first conductor. The sensor substrate 31a includes a substrate 310 made of a dielectric material and a ground conductor 311 provided on the other surface of the substrate 310 opposite to the first surface 312. This ground conductor is also referred to as a second conductor. The material that constitutes the substrate 310 may be made of a common substrate material such as polytetrafluoroethylene (PTFE) or polyimide. When the substrate 310 is viewed in plan, the detection section 31b is configured from a transmission line that has a certain thickness and width and extends in the X direction, passing through approximately the center of a part on one surface 312 of the substrate 310. The ground conductor 311 is formed over the entire surface of the substrate 310 opposite to the surface 312. Although it is not necessary to form the ground conductor 311 over the entire surface, the surface area of ​​the ground conductor 311 is formed to be larger than the surface area of ​​the detection unit 31b. The detection unit 31b and the ground conductor 311 are made of a material with high electrical conductivity, such as copper or gold. As shown in FIG. 4, the dielectric sensor 31 according to the first embodiment has a microstrip line configuration.

[0024] An oscillator 64 is connected to the detection section 31b of the dielectric sensor 31, and an AC signal from the oscillator 64 flows to the detection section 31b. The oscillator 64 generates an AC signal of a single frequency. The frequency of the AC signal generated by the oscillator 64 is selected from a range in which the dielectric constant of the skin can change depending on the blood sugar level. Furthermore, a phase detector 65 is connected to the detection unit 31b. The phase detector 65 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 control unit 62. The phase detector 65 may also be referred to as a phase comparator. The control unit 62 calculates the blood glucose level of the subject based on the phase difference Rx input from the phase detector 65, and displays the calculated blood glucose level information on the display unit of the output device 66 or outputs it as audio from the speaker. Although not shown in the figure, the wiring connected to the dielectric sensor 31 is connected to the control unit 62.

[0025] 5A and 5B are schematic diagrams illustrating changes in wavelength of an AC signal passing through detection unit 31b of dielectric sensor 31 when skin 201 of a subject is pressed against detection unit 31b in the fasting state and after a meal. Fig. 5A shows the phase change in the fasting state, and Fig. 5B shows the phase change after a meal. For ease of understanding, it is assumed here that when the subject is fasting, the wavelength of the AC signal at the dielectric constant of skin 201 in this fasting state is equal to the length from the input end to the output end of detection unit 31b (length in the X direction in FIG. 4).

[0026] That is, when the subject touches the detection unit 31b while fasting, an AC signal is transmitted with a wavelength equal to the length of the detection unit 31b, as shown in Fig. 5(A). Therefore, when the phase of the AC signal at the input end of the detection unit 31b is 0 radians, the phase of the AC signal at the output end of the detection unit 31b is 0 radians.

[0027] When the subject touches the detection unit 31b after eating and their blood glucose level rises, the wavelength shortens, as shown in Fig. 5(B). When the phase of the AC signal input to one end of the detection unit 31b is 0 radians, the phase of the AC signal output from the other end of the detection unit 31b advances in accordance with the amount the wavelength has shortened, compared to the phase shown in Fig. 5(A). The amount of phase advance of the AC signal passing through the detection unit 31b relative to the fasting state is denoted as phase advance Rd1.

[0028] Fig. 6 is a schematic diagram illustrating an example of the transition over time of an AC signal flowing through the detection unit 31b when the measurement subject touches the detection unit 31b of the dielectric sensor 31 of the first embodiment. In Fig. 6, the horizontal axis represents the time elapsed since a meal. The vertical axis on the left represents the blood glucose level, and the vertical axis on the right represents the phase. As shown in Figure 6, when blood glucose levels rise after a meal, the phase lead Rd increases in response to the rise in blood glucose levels. Then, when blood glucose levels begin to fall, the phase lead Rd decreases. In this way, the phase lead Rd changes in conjunction with the blood glucose levels.

[0029] The buffer material 33 is made of a flexible and elastic material to protect the sensor substrate 31a from damage due to the pressing force from the pressing portion 5. The buffer material 33 has, for example, a cubic shape, and the end face on the -Z direction side abuts against the surface 313 of the sensor substrate 31a of the dielectric sensor 31, and the end face on the + direction side abuts against the surface 35c of the pressure transmitting member 35 on the -Z direction side. The buffer material 33 may be made of, for example, sponge, rubber, or a spring.

[0030] The pressure transmission member 35 includes a transmission portion 35a and a blocking portion 35b. The transmission portion 35a is rectangular in plan view and is made of a rigid plate-like member. The transmission portion 35a is configured to be larger than the end face of the buffer material 33 on the +Z direction side, and a surface 35c on the -Z direction side of the transmission portion 35a abuts against the entire end face of the buffer material 33 on the +Z direction side. The blocking portion 35b stands along the outer edge of the transmission portion 35a so as to surround the end portion of the buffer material 33 on the +Z direction side. With this configuration, the blocking portion 35b limits the movement of the buffer material 33 in the lateral direction. As shown in Figures 2(b) and 4, a groove portion 25 for placing a pressure transmission member 35 is formed in the first belt portion 21a, and the transmission portion 35a of the pressure transmission member 35 is housed in the groove portion 25. As shown in FIGS. 1(a) and 1(b) and 2(a) and 2(b), the pressure detection device 37 includes a pressure sensor 371 and a circuit board 372. The pressure sensor 371 is made up of a thin sensor and includes a pressure detection portion 371a and a wiring portion 371b.

[0031] Although not shown, the pressure detection unit 371a includes, for example, a sheet-like detection unit, a diaphragm disposed with a gap between it and the detection unit, and an output unit that outputs the amount of change in the diaphragm that deforms in response to pressure applied to the detection unit as a change in resistance value or capacitance. The output unit converts the resistance value or capacitance into a voltage value corresponding to these values ​​and outputs it. That is, the pressure sensor 371 may be configured as, for example, a resistance change type pressure sensor or a capacitance type pressure sensor.

[0032] Although not shown, the wiring section 371b has two wires, a first wire and a second wire. The first wire has a third end and a third other end, and the second wire has a fourth end and a fourth other end. The third end and the fourth end of the first wire and the second wire are connected to the positive electrode section and the negative electrode section of the output section, respectively. Furthermore, the third end and the fourth other end of the first wire and the second wire are connected to corresponding terminals of the sensor IC mounted on the circuit board 372, respectively. The sensor IC converts a voltage value corresponding to the resistance value or capacitance detected by the pressure sensor 371 into a pressure value. Although not shown, the circuit board 372 is a board on which a sensor IC is mounted that detects a pressure value corresponding to the resistance value or capacitance detected by the pressure sensor 371. Note that the circuit board 372 may be mounted with components including one or more of the control unit 62, the oscillator 64, and the phase detector 64. Although not shown, the circuit board 372 is connected to the control unit 62 by a wire passing through the inside of the belt 2. The wire is not limited to being provided inside the belt 2, but may be provided on the outside of the belt 2.

[0033] 3, pressure detection portion 371a of pressure sensor 371 is disposed in the center of surface 25b on the −Z direction side of groove portion 25, with one surface of the detection portion facing the −Z direction. In addition, a passage 25a is provided at the end of groove portion 25 on the −X direction side, penetrating from the inside to the outside of first belt portion 21a. The circuit board 372 is fixed near and outside the groove 25 of the first belt portion 21a, and the wiring portion 371b of the pressure sensor 371 is connected to the sensor IC of the circuit board 372 through the passage 25a. Therefore, the pressure transmitting member 35 is supported on the surface 25b of the groove portion 25 with the pressure detecting portion 371a of the pressure sensor 371 sandwiched therebetween.

[0034] Here, the pressure transmitting member 35 and the belt 2 are rigid bodies having the rigidity required to transmit substantially 100% of the pressure applied to the dielectric sensor 31 to the pressure detecting portion 371a. As for the belt 2, as long as only the first belt portion 21a or the groove portion 25 of the first belt portion 21a is made of a rigid body, the other portions do not have to be rigid. The blood glucose measuring device 1 according to the first embodiment is used by being attached to an arm 200 by a belt 2, as shown in FIGS. 7(a) and (b).

[0035] In the structural example of the belt 2 of the first embodiment, first, the snap fastening portion 23 is released from the connected state, and the first belt portion 21a and the second belt portion 21b are rotated around the hinge axis in a direction in which the first other end portion and the second other end portion move away from each other. This places the belt 2 in an open state, and the arm portion 200 is placed inside the belt 2. Next, the first belt portion 21a and the second belt portion 21b are rotated around the hinge axis in a direction in which they close each other, and the first other end portion and the second other end portion are connected to each other by the snap fastening portion 23, thereby attaching the blood glucose measuring device 1 to the arm portion 200. In this state, by inflating air bag 52 as shown in FIG. 7(b), a pressing force is applied from air bag 52 to the skin surface of dielectric sensor 31 on the side opposite to detection unit 31b. As shown in Figure 8, this pressure is transmitted in the following order: (1) the skin in contact with the air bag 52, (2) the dielectric sensor 31, (3) the cushioning material 33, (4) the pressure transmission member 35, (5) the pressure detection portion 371a of the pressure sensor 371, and (6) the groove portion 25 of the first belt portion 21a.

[0036] Since the pressure transmitting member 35 and the groove portion 25 are rigid bodies, the pressure detecting portion 371a sandwiched between these rigid bodies is in a state similar to that in which the pressure acting on the dielectric sensor 31 is applied almost directly. In other words, the pressure detecting device 37 detects a pressure that is approximately 100% of the pressure acting on the dielectric sensor 31. [Functional configuration] Next, the functional configuration of the control unit 62 will be described with reference to FIG. As shown in FIG. 9, the control unit 62 includes an air pressure control unit 621, a blood glucose level calculation unit 623, and an output device control unit 625 as functions realized by the CPU executing a control program. The air pressure control unit 621 has a function of controlling the operation of the air pump 63 based on the pressure value applied to the dielectric sensor 31 input from the pressure detection device 37 . Specifically, the amount of air supplied to the air bag 52 by the air pump 63 is controlled so that the pressure applied to the dielectric sensor 31 is kept constant at a pressure value suitable for detecting the dielectric constant. In FIG. 10, the horizontal axis represents pressure (N) and the vertical axis represents phase (deg.). In addition, the example shown in FIG. 10 shows the results of measurements taken during a time period when blood glucose levels change relatively little. 10, as the pressure on dielectric sensor 31 increases, the phase advances, and this phase advance causes an error in the blood glucose level. Therefore, the amount of air supplied to air bladder 52 is controlled so that the pressure remains constant at, for example, 0.5 N, which causes little phase change. Returning to FIG. 9, blood glucose level calculation section 623 has a function of calculating the measured blood glucose level of the subject based on phase difference Rx input from phase detector 65.

[0037] The blood glucose level calculation unit 623 calculates the dielectric constant by inputting the input phase difference Rx into a formula for calculating the dielectric constant from the phase difference Rx, which is stored in advance in ROM. Then, the blood glucose level is obtained by inputting the calculated dielectric constant into a formula for calculating the blood glucose level from the dielectric constant, which is stored in advance in ROM. Alternatively, the blood glucose level corresponding to the input phase difference Rx or dielectric constant is obtained from a table showing the correspondence between the phase difference Rx and the blood glucose level, or a table showing the correspondence between the dielectric constant and the blood glucose level, which is stored in advance in ROM. The output device control unit 625 has a function of controlling the output device based on the blood glucose level information acquired by the blood glucose level calculation unit 623.

[0038] Specifically, it controls the display of the blood glucose level numerical information on the display unit of the output device 66 and the output of the blood glucose level as audio from a speaker. Although not shown, for example, if the blood glucose measuring device 1 is connected to an external device by wire or wirelessly and the output device 66 has a communication function, the output device 66 may be controlled to transmit the blood glucose level information to the external device. [Blood Glucose Measurement Processing] Next, the blood glucose level measurement process executed by the control unit 62 of the blood glucose level measuring device 1 will be described. The CPU of the control unit 62 starts a control program stored in a predetermined area of ​​the ROM, and executes the blood glucose measurement process shown in the flowchart of FIG. 11 in accordance with the program. When the blood glucose measurement process is executed by the CPU, as shown in FIG. 11, the process first proceeds to step S100. In step S100, air pressure control section 621 controls air pump 63 to supply a predetermined amount of air to air bag 52 or to suck out a predetermined amount of air from air bag 52. Thereafter, the process proceeds to step S102.

[0039] As a result, a pressing force is applied to arm 200 of the subject, and skin 201 on the side opposite to the side to which the pressure is applied is pressed against detection unit 31b and surface 312 of dielectric sensor 31. The applied pressure deforms buffer material 33 and is transmitted to surface 35c of transmission unit 35a of pressure transmission member 35 via buffer material 33. The pressure transmitted to surface 35c of pressure transmission member 35 is transmitted to pressure detection unit 371a, which is in contact with surface 35d opposite surface 35c. Here, the air pressure control unit 621 controls the air pump 63 to supply air when the pressure on the dielectric sensor 31 does not reach a specified range, and to suck out air when the pressure exceeds the specified range.

[0040] Furthermore, in the first embodiment, air pump 63 is controlled to obtain a pressure value that brings the dielectric constant into a specified range. That is, even if the pressure is within the specified range, if the dielectric constant is not within the specified range, the amount of air supplied to air bag 52 is controlled so that the dielectric constant also falls within the range. In step S102, the air pressure control unit 621 acquires the detected value of the pressure applied to the dielectric sensor 31 from the pressure detection device 37, and the process proceeds to step S104.

[0041] In step S104, the air pressure control unit 621 determines whether the pressure value acquired in step S102 is within a specified value range. If it is determined that the pressure value is within the specified value range (Yes), the process proceeds to step S106, and if it is determined that the pressure value is not within the specified value range (No), the process proceeds to step S100.

[0042] If the process proceeds to step S106, air pressure control unit 621 stops air pump 63, and the process proceeds to step S108. Note that the configuration is such that the inflated state of air bladder 52 is maintained even when air pump 63 is stopped. That is, a stable state is maintained at a pressure appropriate for detecting the dielectric constant for measuring the blood glucose level. In step S108, the blood glucose level calculation unit 623 calculates the dielectric constant from the phase difference Rx detected by the dielectric sensor 31. Thereafter, the process proceeds to step S110.

[0043] In step S110, the air pressure control unit 621 determines whether the dielectric constant calculated in step S108 is within a specified value range. If it is determined that the dielectric constant is within the specified value range (Yes), the process proceeds to step S112, and if it is determined that the dielectric constant is not within the specified value range (No), the process proceeds to step S100. When the process proceeds to step S112, the blood glucose level is calculated by executing the blood glucose level calculation process in the blood glucose level calculation unit 623. After that, the process proceeds to step S114.

[0044] In step S114, the output device control unit 625 outputs blood glucose level information to the output device 66 based on the blood glucose level calculated in step S112. For example, the blood glucose level information is displayed on the display unit or output as audio from the speaker. After that, the series of processes ends. [Blood glucose calculation process] Next, the blood glucose level calculation process executed in step S112 will be described with reference to FIG. When the blood glucose level calculation process is started in step S112, the process first proceeds to step S200 as shown in FIG. In step S200, blood glucose level calculation section 623 acquires the phase difference Rx between the measurement signal and the reference signal from phase detector 65. Thereafter, the process proceeds to step S202.

[0045] In step S202, the blood glucose level calculation unit 623 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 in a fasting state, from the phase difference Rx obtained in step S200 to obtain the phase lead Rd. Then, the process proceeds to step S204.

[0046] Here, the fasting phase difference Ri is assumed to be measured in advance and stored in a memory such as a ROM. 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 control unit 62 stores the transition of the phase difference Rx during the wearing period. The control unit 62 then stores the minimum value of the phase difference Rx as the fasting phase difference Ri. Note that the method of acquiring the fasting phase difference Ri is not limited to this.

[0047] Similarly to the fasting phase difference Ri, the fasting blood glucose level Bi, which is the blood glucose level when the subject is fasting, is measured in advance and stored in a memory such as a ROM in association with the fasting phase difference Ri. 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. In step S204, the blood glucose level calculation section 623 acquires the blood glucose level fluctuation Bv from the fasting blood glucose level Bi based on the phase lead Rd acquired in step S202. Then, the process proceeds to step S206.

[0048] For example, a first calibration curve representing the relationship between the phase lead Rd and the fluctuation Bv is obtained in advance by simulation or an experiment using one or more subjects. The first calibration curve may be a function or may be information in a table format. The first calibration curve is stored in advance in a memory. In step S204, the fluctuation Bv at the time of execution of step S204 is obtained based on the phase lead Rd obtained in step S202 and the first calibration curve. In step S206, the blood glucose calculation unit 623 acquires the measured blood glucose value by adding the fluctuation Bv acquired in step S204 to the fasting blood glucose value Bi. After that, the series of processes ends and the process returns to the original process. The operation for acquiring the blood glucose measurement value shown in FIG. 11 is merely an example. The operation for obtaining a blood glucose measurement may be varied in many ways.

[0049] For example, a second calibration curve representing the relationship between the phase difference Rx and the blood glucose level is obtained in advance by simulation or an experiment using one or more subjects and stored in advance in a memory such as a ROM. Then, the blood glucose level calculation unit 623 may obtain the measured blood glucose level based on the phase difference Rx obtained in step S200 and the second calibration curve. [Effects of the first embodiment]

[0050] As described above, the blood glucose level measuring device 1 to which the biological information measuring device according to the first embodiment is applied comprises the belt 2, the sensor unit 7, the air pump 63, the air bag 52, and the control unit 62. The sensor unit 7 comprises a dielectric sensor 31 having a sensor substrate 31a having a surface 312 and a surface 313 opposite to the surface 312, and a detection unit 31b made of a conductor provided on the surface 312 of the sensor substrate 31a. The sensor unit 7 further comprises a pressure sensor 371 having a pressure detection unit 371a and detecting a pressure acting on the pressure detection unit 371a, and a pressure transmitting member 35 made of a rigid body having a surface 35c and a surface 35d opposite to the surface 35c, with the surface 35c abutting the surface 313 of the dielectric sensor 31 and the surface 35d abutting the pressure detection unit 371a of the pressure sensor 371. Furthermore, the pressure detecting unit 371a has a contact portion that contacts a portion of the pressure detecting unit 371a opposite to the side that contacts the pressure transmitting member 35, and includes a rigid groove portion 25 that supports the pressure detecting unit 371a. The belt 2 is a belt for attaching the sensor unit 7 to a part of the subject's body, and when the sensor unit 7 is worn by wrapping it around an arm 200, which is a part of the body, the sensor unit 7 is attached at a position where the detecting unit 31b of the dielectric sensor 31 contacts the skin 201 of the subject. The air pump 63 is provided in a housing 1 attached to the belt 2, and the air bladder 52 is provided at a position facing the dielectric sensor 31 on the second belt portion 21b that constitutes the belt 2. The air pump 63 inflates the air bladder 52, thereby indirectly applying a pressing force to the detecting unit 31b of the dielectric sensor 31. The control unit 62 controls the pressing force generated by the inflation of the air bladder 52 based on the pressure detected by the pressure sensor 371.

[0051] With this configuration, the pressure transmitting member 35 and the groove portion 25 are rigid bodies, so that the pressure acting on the dielectric sensor 31 can be applied almost directly to the pressure detecting portion 371a that is sandwiched between these rigid bodies. As a result, a pressure that is almost the same as the pressure acting on the dielectric sensor 31 can be detected, so that an appropriate pressure can be detected as the pressure acting on the dielectric sensor 31. Furthermore, since the pressure applied to the dielectric sensor 31 can be controlled based on an appropriate pressure, pressure control suitable for measuring biological information can be performed. Furthermore, in the blood glucose measuring device 1 according to the first embodiment, the control unit 62 controls the pressing force due to the expansion of the air bag 52 so that the pressing force becomes a predetermined pressing force that allows the dielectric sensor 31 to obtain an appropriate dielectric constant, and so that the predetermined pressing force is stably maintained. With this configuration, the dielectric constant can be measured stably, and stable measurements can also be performed repeatedly. Furthermore, the blood glucose measuring device 1 according to the first embodiment is configured such that the buffer material 33 is provided between the surface 313 of the dielectric sensor 31 and the surface c of the pressure transmitting member . With this configuration, when a pressing force is applied to the dielectric sensor 31, the sensor substrate 31a can be prevented from being damaged. In addition, the blood glucose measuring device 1 of the first embodiment is configured so that the pressure transmission member 35 has a blocking portion 35b formed on the outer edge of the surface 35c so as to surround the end of the cushioning material 33 on the surface 35c side, thereby preventing lateral movement of the cushioning material 33. With this configuration, it is possible to prevent the buffer material 33 from skidding when a pressing force is applied to the dielectric sensor 31, and therefore it is possible to more reliably detect an appropriate pressure.

[0052] In the blood glucose measuring device 1 according to the first embodiment, the detection unit 31b is configured to be a conductive transmission line, and the dielectric sensor 31 detects the dielectric constant of the subject's skin based on a change in the signal flowing through the detection unit 31b. Furthermore, the control unit 62 calculates the blood glucose level of the subject based on the dielectric constant detected by the dielectric sensor 31. With this configuration, the blood glucose level can be calculated based on the dielectric constant detected by the dielectric sensor 31 pressed with an appropriate pressure, thereby making it possible to measure the blood glucose level of the subject more accurately. The blood glucose level measuring device 1 according to the first embodiment also includes an output device 66 that outputs information on the blood glucose level calculated by the control unit 62. With this configuration, the measured blood glucose level information can be immediately confirmed by display output, audio output, etc. [Correspondence in the first embodiment] In the first embodiment, the sensor substrate 31a corresponds to the first substrate, the surface 312 of the sensor substrate 31a corresponds to the first surface, the surface 313 corresponds to the second surface, the detection unit 31b corresponds to the first conductor, the ground conductor 311 corresponds to the second conductor, and the pressure detection unit 371a corresponds to the detection unit.

[0053] In addition, in the first embodiment, surface 35c of pressure transmission member 35 corresponds to the third surface, surface 35d corresponds to the fourth surface, groove portion 25 of first belt portion 21a corresponds to the support member, surface 25b corresponds to the abutment portion, pressure detection device 37 corresponds to the pressure sensor, and pressing portion 5 and air pump 63 correspond to the pressing portion. [Example of the first embodiment] Next, an example of the first embodiment will be described. Figures 13 to 17 are diagrams showing an example of the first embodiment.

[0054] In Figures 13 and 15, the horizontal axis represents the number of measurements, and the vertical axis represents the phase (deg.). In Figures 14 and 16, the horizontal axis represents the elapsed time (minutes), and the vertical axis represents the phase (deg.). In Figure 17, the vertical axis represents the contact pressure (N). 14 and 15 show the results of measurements taken with the blood glucose level measuring device 1 of the first embodiment controlled to an appropriate pressure value of 0.5 N or less.

[0055] In the blood glucose measuring device of the conventional configuration, when the phase was measured in a resting state, the maximum error in the measured values ​​over 10 measurements was 15.8 degrees, as shown in Fig. 13. In contrast, in the blood glucose measuring device 1 of the first embodiment, the maximum error in the measured values ​​over 10 measurements was 8.5 degrees, as shown in Fig. 15, which is approximately half the error compared to the conventional configuration. Furthermore, with the blood glucose measuring device of the conventional configuration, there were occasional instances where the phase changed significantly over time, as shown in the area circled by dotted lines in Figure 14. This is thought to be because the dielectric sensor became separated from the arm and floated away from it due to arm movement.

[0056] In contrast, in the blood glucose level measuring device 1 of the first embodiment, the phase is measured stably without any significant change over time, as shown in Figure 16. This is thought to be because in the blood glucose level measuring device 1 of the first embodiment, the detection unit 31b of the dielectric sensor 31 is brought into close contact with the arm 200 with appropriate pressure due to the expansion of the belt 2 and the air bladder 52. Next, in the blood glucose measuring device 1 of the first embodiment, the contact pressure when the arm is swung will be described in the cases where the dielectric sensor 31 is brought into close contact with the arm 200 by inflation of the air bag 52 and where it is not brought into close contact.

[0057] As shown in Figure 17, when the arm is swung without the air bag 52 providing a tight fit, the contact pressure changes by 0.3 N. In contrast, when the arm is swung while the air bag 52 provides a tight fit, the change in contact pressure is kept to less than 0.1 N. When swinging the arm, the elbow was bent and the arm was flexed, simulating walking. Second Embodiment Next, a second embodiment of the present invention will be described. Fig. 18 is a diagram showing the second embodiment. Fig. 18 is a partial cross-sectional view including a sensor unit 7A of a blood glucose level measuring device 1A according to the second embodiment.

[0058] The second embodiment differs from the first embodiment in that a lid 39 is provided between the dielectric sensor 31 and the buffer material 33 to assist in the transmission of pressure from the buffer material 33. Furthermore, the second embodiment differs from the first embodiment in that the circuit board 372 of the pressure detection device 37 is configured as a rigid body, the pressure sensor 371 is provided on the circuit board 372, and the entire pressure detection device 37 is disposed within the groove portion 25A. Hereinafter, the same components as those described in the first embodiment will be denoted by the same reference numerals and the description thereof will be omitted as appropriate, and only the parts that differ from the first embodiment will be described in detail. 〔composition〕 As shown in Figure 18, the blood glucose level measuring device 1A of the second embodiment is configured such that, in the blood glucose level measuring device 1 of the first embodiment, a sensor unit 7A is provided instead of the sensor unit 7, and a groove unit 25A is provided instead of the groove unit 25. The sensor section 7A includes a pressure transmitting section 30A and a pressure detecting device 37A. The pressure transmitting section 30A has a configuration in which a lid section 39 is added between the dielectric sensor 31 and the buffer material 33 in the pressure transmitting section 30 of the first embodiment.

[0059] The lid portion 39 is generally crown-shaped and covers the entire end face and side surface of the end portion on the -Z direction side of the buffer material 33. The outer diameter of the lid portion 39 is configured to be smaller than the inner diameter of the pressure transmission member 35. Therefore, even if the buffer material 33 shrinks in the +Z direction when the lid portion 39 is pressed, the +Z direction side end of the lid portion 39 will not collide with the blocking portion 35b of the pressure transmission member 35, and can move in the +Z direction inside the blocking portion 35b. Although the lid portion 39 and the pressure transmission member 35 are configured to be separate, this configuration is not limited thereto, and as long as the lid portion 39 can move back and forth between itself and the pressure transmission member 35, the two may be fixed together with an elastic material such as rubber. The groove portion 25A is configured such that the depth of the groove portion 25 in the first embodiment is deeper, and furthermore, the passage 25a is not provided in the first belt portion 21a. The pressure detection device 37A includes a pressure sensor 371A and a circuit board 372A. The pressure sensor 371A includes a pressure detection portion 371Aa and a wiring portion 371Ab.

[0060] The pressure sensor 371A is configured as a thin sensor similar to that of the first embodiment, and is mounted directly on a circuit board 372A. The pressure detection unit 371Aa has the same configuration as the pressure detection unit 371a of the first embodiment, but the wiring unit 371Ab is configured to be shorter than the wiring unit 371b of the first embodiment. The circuit board 372A is made of a dielectric material with a relatively high rigidity, which is sufficient to allow the pressure detection device 37A to detect approximately 100% of the pressure applied to the dielectric sensor 31, as in the first embodiment. The configuration is not limited to using a dielectric material with a relatively high rigidity, and the rigidity may be increased by, for example, covering the circuit board 372A with a metal. The pressure detection device 37A is placed in the groove 25A with the surface on which the pressure sensor 371A is mounted facing the surface 35d of the pressure transmitting member 35 and the pressure detection portion 371Aa in contact with the surface 35d.

[0061] With this configuration, when pressure is applied to the dielectric sensor 31 in the +Z direction, this pressure is transmitted to the crown-shaped lid portion 39, and the lid portion 39 uniformly presses the entire end face of the buffer material 33 on the -Z direction side. Furthermore, the pressure transmitted from the buffer material 33 is transmitted to the pressure transmitting member 35 and then to the pressure sensor 371A. The pressure transmitted to the pressure sensor 371A is then transmitted to the circuit board 372A and finally to the groove portion 25A of the first belt portion 21a.

[0062] Because the pressure transmitting member 35 and the circuit board 372A are rigid bodies, the pressure detecting section 371Aa sandwiched between these rigid bodies is in a state similar to that in which the pressure acting on the dielectric sensor 31 is applied substantially directly. In other words, the pressure detecting device 37A detects a pressure that is substantially 100% of the pressure acting on the dielectric sensor 31. Furthermore, because the lid section 39 can press the buffer material 33 straight, the pressure acting on the dielectric sensor 31 can be stably and reliably transmitted to the pressure sensor 371A. [Effects of the second embodiment]

[0063] As described above, the blood glucose level measuring device 1A to which the biological information measuring device of the second embodiment is applied is configured such that, in the blood glucose level measuring device 1 of the first embodiment, a crown-shaped lid portion 39 is provided between the surface 313 of the dielectric sensor 31 and the buffer material 33, covering the surface of the buffer material 33 facing the surface 313 and the side of the end portion on the surface 313 side. With this configuration, the cover 39 can press the buffer material 33 straight and evenly, so that the pressure applied to the dielectric sensor 31 can be transmitted to the pressure sensor 371A stably and reliably.

[0064] In the blood glucose measuring device 1A according to the second embodiment, the pressure detecting device 37A is configured to include a pressure sensor 371A and a rigid circuit board 372A, and the pressure sensor 371A is provided on the circuit board 372A. Furthermore, the pressure detecting device 37A is configured to be disposed in the groove 25A of the first belt part 23a.

[0065] With this configuration, the circuit board 372A can support the pressure detection portion 371Aa of the pressure sensor 371 in place of the groove portion 25 of the first embodiment, and the belt 2 can be made of a soft material other than a rigid body. This allows most of the portion that comes into contact with the arm 200 to be made of a soft material, thereby reducing discomfort caused by stiffness on the arm 200 of the subject. [Corresponding relationship in the second embodiment] In the second embodiment, the circuit board 372A corresponds to the second board and the support member. [Modification]

[0066] In the above embodiment, the entire belt 2 is configured as a rigid body, but this is not limiting. For example, only the portion where the sensor unit 7 is located may be configured as a rigid body, with the other portions not being rigid. In other words, the portions other than the rigid portion may be configured from a relatively soft material such as leather or cloth. In this case, the hinge 22 and the snap fixing portion 23 are not required. Furthermore, in the above embodiment and its modified examples, the buffer material 33 is provided between the sensor substrate 31a and the pressure transmitting member 35 to protect the sensor substrate 31a of the dielectric sensor 31, but this configuration is not limiting. For example, the buffer material 33 may be omitted by making the sensor substrate 31a of the dielectric sensor 31 sturdy. For example, the thickness of the substrate 210 of the sensor substrate 31a may be increased to make it sturdy, or the sensor substrate 31a may be shielded with a metal plate, a resin plate, or the like to make it sturdy.

[0067] Furthermore, in the above embodiment and its modified examples, the buffer material 33 is provided between the sensor substrate 31a and the pressure transmission member 35 in order to protect the sensor substrate 31a of the dielectric sensor 31, but the present invention is not limited to this configuration. For example, the sensor substrate 31a may be made of a rigid body, and the buffer material 33 and the pressure transmission member 35 may be removed. A specific example will be described below. FIG. 19(a) is a partial cross-sectional view of a blood glucose level measuring device 1B according to a modified example, and FIG. 19(b) is a partial cross-sectional view of a blood glucose level measuring device 1B according to a modified example. As shown in Figure 19(a), the blood glucose measuring device 1B of this modified example has a configuration in which the dielectric sensor 31 in the blood glucose measuring device 1 of the first embodiment is replaced with a dielectric sensor 31A, and the buffer material 33 and pressure transmission member 35 are removed. The dielectric sensor 31A includes a sensor substrate 31Aa and a detection section 31b.

[0068] The sensor substrate 31Aa is thicker than the sensor substrate 31a of the first embodiment, and has resistance to breakage and rigidity. As in the first embodiment, this rigidity allows the pressure detection device 37 to detect approximately 100% of the pressure applied to the dielectric sensor 31A. The surface 313 on the +Z direction side of the sensor substrate 31Aa contacts the surface on the −Z direction side of the pressure detection portion 371a of the pressure sensor 371, and the surface opposite to this surface of the pressure detection portion 371a contacts the groove portion 25.

[0069] That is, the sensor substrate 31Aa and the groove portion 25 of the first belt portion 21a are rigid bodies, and furthermore, the buffer material 33 and the pressure transmission member 35 are not interposed between the dielectric sensor 31A and the pressure sensor 371. Therefore, the pressure applied to the dielectric sensor 31A is applied almost directly to the pressure detection portion 371a of the pressure sensor 371. That is, the pressure detection device 37 detects a pressure that is almost 100% of the pressure applied to the dielectric sensor 31A. Furthermore, since the buffer material 33 and the pressure transmitting member 35 are not required, the device can be made smaller. On the other hand, as shown in Figure 19(b), the blood glucose level measuring device 1C of the modified example has a configuration in which the dielectric sensor 31 in the blood glucose level measuring device 1A of the second embodiment is replaced with a dielectric sensor 31A, and the buffer material 33, pressure transmission member 35 and lid portion 39 are removed. The dielectric sensor 31A is similar to the dielectric sensor 31A of the blood glucose level measuring device 1B. The +Z direction surface 313 of the sensor substrate 31Aa contacts the −Z direction surface of the pressure detection portion 371Aa of the pressure sensor 371A, and the opposite surface of the pressure detection portion 371a contacts the circuit board 372A.

[0070] That is, the sensor substrate 31Aa and the circuit board 372A are rigid bodies, and furthermore, the cover portion 39, the buffer material 33, and the pressure transmission member 35 are not interposed between the dielectric sensor 31A and the pressure sensor 371. Therefore, the pressure applied to the dielectric sensor 31A is applied almost directly to the pressure detection portion 371Aa of the pressure sensor 371A. That is, the pressure detection device 37A detects a pressure that is almost 100% of the pressure applied to the dielectric sensor 31A. Furthermore, the lid 39, the buffer material 33 and the pressure transmitting member 35 are no longer necessary, which allows the device to be made smaller.

[0071] In the above embodiment and its modified examples, the blood glucose measuring device is configured to be worn on the arm near the wrist, but this is not a limitation. For example, it may be worn on the wrist and used like a smart watch. Furthermore, it is not limited to being worn on the wrist or arm, but may be worn on other parts of the body where blood glucose levels can be measured, such as the leg or ankle.

[0072] Furthermore, in the above embodiment and its modified examples, a dielectric sensor having a microstrip line structure has been described as an example, but the present invention is not limited to this configuration. For example, other structures such as a coplanar line, a coplanar strip line, or a grounded coplanar line may also be used.

[0073] Furthermore, in the above embodiment and its modified examples, a pressing force that indirectly presses the dielectric sensor 31 is generated by a combination of the air pump 63 and the air bag 52, but this configuration is not limited to this. For example, any other configuration may be used as long as it is capable of generating a pressing force that presses the dielectric sensor 31. For example, the entire sensor unit 7 may be configured to be able to advance and retreat relative to the arm 200, and a pressing force may be applied by pushing the entire sensor unit 7 toward the arm 200 using power such as an electric motor (see, for example, Patent Document 2).

[0074] Furthermore, in the above embodiment and its modified examples, the configuration in which the components related to the dielectric sensor 31, such as the oscillator 64 and the phase detector 65, are provided inside the housing 1 has been described as an example, but the present invention is not limited to this configuration. For example, the components related to the dielectric sensor 31 may be provided on the circuit board 372.

[0075] In the above embodiment and its modified examples, the circuit board 372 is configured to include a sensor IC for detecting pressure values, but this is not a limitation. In addition to the sensor IC, a power supply for oscillation, an amplifier, a wireless module for communicating with the outside, and the like may also be provided. Furthermore, instead of being limited to a configuration in which an IC is mounted, a circuit having the same functions as the sensor IC may be configured on the circuit board 372 using passive and active elements.

[0076] In the above embodiment and its modified examples, the biological information measuring device of the present invention has been described as being applied to a wearable device, but the present invention is not limited to this configuration. For example, the control unit 62 may not be provided inside the housing 1, and the sensors of the sensor unit 7 may be connected by wire or wirelessly to an external device such as a PC, and the external device may perform calculations of the dielectric constant and blood glucose level. Furthermore, in the above embodiment and variant examples, a configuration has been described in which the bioinformation measuring device of the present invention is applied to a device that measures blood glucose levels, but the configuration is not limited to this and the device may also be applied to a device that measures bioinformation other than blood glucose levels. [Explanation of symbols]

[0077] 100, 100A to 100C...blood glucose measuring device, 1...housing, 2...belt, 5...pressure section, 6...drive control section, 7, 7A...sensor section, 21...belt section, 21a...first belt section, 21b...second belt section, 22...hinge, 23...snap fixing section, 25, 25A...groove section, 25a...passage, 25b, 25Ab, 35c, 35d, 312, 313...surface, 30...pressure transmission section, 31...dielectric sensor, 31a...sensor substrate, 31b...detection section, 33...buffer material, 35...pressure transmission member, 35a...transmission section, 35b...blocking section, 37...pressure detection device, 39...lid section, 51...connecting section, 52...air bag, 61, 372, 372A...circuit board, 62...control section, 63...air pump, 63a...electric pump, 63b...air transport pipe, 64...oscillator, 65...phase detector, 66...output device, 200...arm section, 201...skin, 371, 371A...pressure sensor, 371a, 371Aa...pressure detection section, 371b, 371Ab...wiring section

Claims

1. a sensor including: a first substrate having a first surface and a second surface opposite to the first surface and including a dielectric; a first conductor provided on the first surface of the first substrate; and a second conductor provided at a position on the first substrate away from the first conductor and having a surface area larger than a surface area of ​​the first conductor when viewed in a plan view; a pressure sensor having a detection portion and detecting a pressure applied to the detection portion; a pressure transmission member made of a rigid body having a third surface and a fourth surface opposite to the third surface, the third surface abutting against the second surface of the sensor and the fourth surface abutting against the detection unit; a sensor unit including a rigid support member that supports the detection unit and has an abutment portion that abuts against a portion of the detection unit opposite to the side that abuts against the pressure transmission member; a belt on which the sensor unit is provided; a pressing portion provided on the belt and applying a pressing force to the sensor; a control unit that controls the pressing force of the pressing unit based on the pressure detected by the pressure sensor; A biological information measuring device comprising:

2. In claim 1, The control unit controls the pressing force of the pressing unit so that the pressing force becomes a predetermined pressing force that allows the sensor to obtain appropriate biological information.

3. In claim 1, A biological information measuring device comprising a buffer material between the second surface of the sensor and the third surface of the pressure transmitting member.

4. In claim 3, A bioinformation measuring device in which the pressure transmission member has a preventing portion formed on the outer edge of the third surface to surround the end of the cushioning material on the third surface side, preventing lateral movement of the cushioning material.

5. In claim 4, A biometric information measuring device comprising a crown-shaped lid portion disposed between the second surface of the sensor and the cushioning material, the crown-shaped lid portion covering the surface of the cushioning material facing the second surface and the side of the end portion on the second surface side.

6. In claim 1, the pressing unit has an air bag provided on the belt at a position facing the first surface of the sensor when the belt is worn, and an electric pump that supplies air to the air bag, and is configured to indirectly apply a pressing force to the first surface by inflating the air bag with the electric pump, The control unit controls the pressing force by controlling the amount of air supplied to the air bag by the electric pump based on the pressure detected by the pressure sensor.

7. In claim 1, At least a portion of the belt to which the sensor unit is attached is made rigid, The support member is a rigid portion of the belt.

8. In claim 1, a rigid second substrate; the pressure sensor has at least the detection unit provided on the second substrate; The support member is a biological information measuring device that is configured from the second substrate.

9. In claim 1, The pressure sensor is a resistance change type pressure sensor or a capacitance type pressure sensor.

10. In claim 1, The buffer material is made of sponge, spring, or rubber.

11. In claim 1, The sensor is a bioinformation measuring device that detects the dielectric constant of the subject's skin based on changes in the signal flowing through the first conductor.

12. In claim 11, The control unit is a biological information measuring device that calculates biological information of the subject based on the dielectric constant detected by the sensor.

13. In claim 12, A biological information measuring device including an output device that outputs the biological information calculated by the control unit.

14. In claim 1, a rigid second substrate; Components including one or more of a circuit for driving the sensor, a circuit for processing an output of the sensor, the pressure sensor, a circuit for driving the pressure sensor, and a circuit for processing an output of the pressure sensor are provided on the second substrate; The support member is a biological information measuring device that is configured from the second substrate.

15. a sensor including a substrate including a dielectric, a first conductor provided on one surface of the substrate, and a second conductor provided at a position on the substrate away from the first conductor, the second conductor having a surface area larger than a surface area of ​​the first conductor when viewed in a plan view; a pressure sensor having a detection portion and detecting a pressure applied to the detection portion; a pressure transmission member made of a rigid body that transmits the pressure applied to the sensor to the detection unit; a sensor unit including a rigid support member that supports the detection unit in a sandwiched state between the detection unit and the pressure transmission member; a belt on which the sensor unit is provided; a pressing portion provided on the belt and applying a pressing force to the sensor; a control unit that controls the pressing force of the pressing unit based on the pressure detected by the pressure sensor; A biological information measuring device comprising:

16. a sensor including a substrate that is rigid and includes a dielectric, a first conductor provided on one surface of the substrate, and a second conductor that is provided at a position on the substrate away from the first conductor and has a surface area larger than a surface area of ​​the first conductor when viewed in a plan view; a pressure sensor having a detection portion and detecting a pressure applied to the detection portion; a sensor unit including a rigid support member that supports the detection unit in a sandwiched state between the sensor unit and the substrate; a belt on which the sensor unit is provided; a pressing portion provided on the belt and applying a pressing force to the sensor; a control unit that controls the pressing force of the pressing unit based on the pressure detected by the pressure sensor; A biological information measuring device comprising:

Images