Biological information measuring device

Abstract

A biological information measuring device to be worn on a human body, the biological information measuring device including at least a first electrode and a second electrode, and configured to be capable of measuring an electrocardiogram waveform based on a potential difference between the first electrode and the second electrode, the biological information measuring device including: a main body case including a side surface formed of an electrically conductive material and functioning as the first electrode, a bottom surface on which the second electrode is disposed and which comes into contact with the human body when worn, and a top surface opposite the bottom surface; an electrocardiogram signal sensing circuit configured to sense a signal related to the potential of the first electrode and the second electrode; a first circuit configured to connect the first electrode and the electrocardiogram signal sensing circuit; and a second circuit configured to have an electrostatic discharge protection element mounted thereto and to connect the first electrode and the second electrode via the electrostatic discharge protection element.

Description

Technical Field

[0001] This invention belongs to the technical field of healthcare, and specifically relates to a biological information measuring device. Background Technology

[0002] In recent years, it has become common for individuals to measure their own blood pressure, electrocardiogram (ECG) waveforms, and other information related to their physical health (hereinafter referred to as biometrics) using measuring devices, and to effectively utilize these results for health management. As a result, the demand for portable devices has increased, leading to the development of many portable measuring devices (such as Patent Document 1).

[0003] Patent Document 1 discloses a watch-type biometric information measuring device equipped with ECG electrodes and capable of measuring ECG waveforms. In such small devices as watch-type wearable devices, the capacity of the grounding point (GND) is insufficient. Therefore, in ESD (Electrostatic Discharge) tests, when the display unit (shower) is positioned downwards and the casing is metal, static electricity can penetrate from the metal casing, which is the target of ESD application, into the control board connected to the device's grounding point (GND). This may cause malfunctions of the control board or damage to components.

[0004] It should be noted that, although the technology for preventing malfunctions of the control board and damage to electronic circuit components mounted on the control board caused by static electricity intruding into the metal casing is a different technical field from that of electrocardiographs, there are known technologies that designate the metal casing as GND (connected to GND) (e.g., Patent Document 2). In the technology described in Patent Document 2, electrostatic discharge resistance is improved by making the conductive aluminum casing connected to the ground terminal of the control board.

[0005] Existing technical documents

[0006] Patent documents

[0007] Patent Document 1: Japanese Patent Application Publication No. 2024-14478

[0008] Patent Document 2: Japanese Patent Application Publication No. 2014-181562 Summary of the Invention

[0009] The problem that the invention aims to solve

[0010] However, if the casing or other parts that the human body can touch are used as the grounding terminal in a device such as an electrocardiograph, it will be impossible to pass the withstand voltage test and leakage current test from the point of view of safety standards (because if voltage is applied, current will flow between the grounding terminal, which is a metal casing, and the electrodes used for measuring the electrocardiogram).

[0011] In view of the problems described above, the present invention aims to provide a technique for achieving high electrostatic resistance in a biometric measuring device having a metal housing and electrodes.

[0012] Solution for solving the problem

[0013] To solve the above-mentioned problems, the biological information measuring device of the present invention adopts the following configuration. That is,

[0014] A bio-information measuring device, worn on the human body for use, the bio-information measuring device having at least a first electrode and a second electrode, and configured to perform measurement of electrocardiogram waveforms based on the potential difference between the first electrode and the second electrode, the bio-information measuring device having:

[0015] The main body shell has a side surface formed of conductive material that functions as the first electrode, a bottom surface on which the second electrode is disposed and which abuts against the human body when worn, and a top surface opposite the bottom surface;

[0016] An electrocardiogram signal sensing circuit senses signals related to the potentials of the first electrode and the second electrode;

[0017] A first circuit connects the first electrode to the electrocardiogram signal sensing circuit; and

[0018] The second circuit is equipped with an electrostatic discharge protection element, and the first electrode and the second electrode are connected via the electrostatic discharge protection element.

[0019] That is, the first and second electrodes mentioned above only become conductive via the electrostatic discharge protection element when a current exceeding a specific frequency / applied voltage is generated due to electrostatic discharge phenomena, etc. With such a configuration, even if static electricity enters the bio-information measuring device via the second electrode, the static electricity can be released to the main body housing, which serves as the first electrode, via the electrostatic discharge protection element provided on the signal line for electrocardiogram measurement where current can easily flow.

[0020] Therefore, even small biometric devices like watch-type devices, which cannot easily obtain a ground terminal, can exhibit high electrostatic discharge resistance. Furthermore, since the main body housing serves as the electrode for electrocardiogram (ECG) measurement, high voltages are not required during voltage withstand and leakage current tests, and passing the voltage withstand test will not be hindered. It should be noted that while the main body housing, acting as the first electrode, could also release static electricity to an external ground wire, the purpose of this invention is solely to release static electricity to the metal housing of the biometric device.

[0021] Alternatively, the electrocardiogram signal sensing circuit may be disposed on a first substrate, which is arranged within the main housing in a direction parallel to the bottom surface.

[0022] A portion of the first circuit and the second circuit are disposed on a second substrate, which is arranged in the main body housing in a direction orthogonal to the bottom surface and is connected to the first electrode by a conductive guide strip.

[0023] With this configuration, signal lines connecting the first electrode and the second electrode (i.e., routes for static electricity to flow toward the casing) can be efficiently constructed within a small main body shell.

[0024] Alternatively, the first substrate and the second substrate can be integrally formed as a rigid-flexible substrate. With such a configuration, the ECG signal sensing circuit (first substrate portion) and the portion connected to the first electrode (second substrate portion) can be arranged in an L-shape within the housing, and the number of components constituting the device can be reduced.

[0025] Alternatively, a display can be provided on the top surface, and the first electrode and the display can be connected by a conductive strip. With such a configuration, even if ESD occurs when the display is facing down during an ESD test, static electricity can easily flow from the side of the main housing to the display, which is the top surface of the main housing, thus more effectively preventing static current from flowing into the electronic components inside the main housing.

[0026] Alternatively, the bio-information measuring device may include: a third substrate, disposed within the main housing in a direction parallel to the first substrate, and on which a control device for controlling the bio-information measuring device is mounted; and a fourth substrate, having an operation button configured to protrude from the side and a portion of an electrocardiogram (ECG) signal line connecting the ECG signal sensing circuit to the control device, and disposed at a position different from the second substrate in a direction orthogonal to the first substrate. Such a configuration allows for more efficient and effective use of the space within the main housing.

[0027] It should be noted that as long as the above-mentioned components and processes do not create technical contradictions, they can be combined with each other to constitute the present invention.

[0028] Invention Effects

[0029] According to the present invention, a technology can be provided that enables high electrostatic resistance in a biometric measuring device having a metal casing and electrodes. Attached Figure Description

[0030] Figure 1 This is a schematic perspective view of the biological information measuring device according to an embodiment of the present invention.

[0031] Figure 2 This is a schematic side view of the biological information measuring device according to the embodiment.

[0032] Figure 3 This is an external view of the main body of the biological information measuring device according to the embodiment, viewed from the bottom side.

[0033] Figure 4 This is a schematic cross-sectional view of the biological information measuring device as seen from the side.

[0034] Figure 5 This is a schematic cross-sectional view of the vicinity of the sensor substrate housing of the biological information measuring device according to the embodiment.

[0035] Figure 6 This is a schematic cross-sectional view illustrating the connection between the electrodes, sensor substrate, and frame conductive substrate of the biological information measuring device according to the embodiment.

[0036] Figure 7 This is a schematic circuit diagram of the signal lines of the electrodes and electrocardiogram signal sensing circuit of the biological information measuring device according to the embodiment.

[0037] Figure 8 This is a block diagram illustrating the functional configuration of the biological information measuring device according to the implementation method. Detailed Implementation

[0038] <Implementation Method>

[0039] Hereinafter, specific embodiments of the present invention will be described based on the accompanying drawings. However, unless otherwise specified, the dimensions, materials, shapes, relative configurations, etc. of the components described in the following embodiments are not intended to limit the scope of the present invention.

[0040] (Overall structure of the device)

[0041] Figure 1 This is a schematic perspective view showing the configuration of the biological information measuring device 1 according to this embodiment. Furthermore, Figure 2 This is a schematic side view showing the configuration of the biological information measuring device 1 according to this embodiment. Figure 1 , Figure 2 As shown, the bio-information measuring device 1 is a watch-type wearable device that generally has a main body 10 and a strap 20. It can measure bio-information such as electrocardiogram waveform, pulse wave (pulse), and blood pressure when worn on the wrist.

[0042] like Figure 1 and Figure 2As shown, the main body 10 is configured to include a main housing 11 and a cuff cover 16, which will be described later. The main housing 11 includes a display 12 (e.g., an organic EL (Electro Luminescence) display), a bezel 131, operation buttons 13a and 13b, an earpiece 14, etc., and a sensor substrate receiving portion 15 for accommodating a sensor substrate. It should be noted that in this embodiment, the side where the display 12 is formed is designated as the surface of the main housing 11, and the side where the sensor substrate receiving portion 15 is formed is designated as the bottom of the main housing 11. Furthermore, hereinafter, the surface side of the main housing 11 will sometimes be referred to as the upper side, and the bottom side of the main housing 11 as the lower side.

[0043] The frame 131 forming the side of the main housing 11 is formed of a conductor (e.g., stainless steel) and functions as an electrode (right-hand electrode) for electrocardiogram waveform measurement. Therefore, in the following description of the frame 131 in relation to its function related to electrocardiogram waveform measurement, the frame 131 will also be referred to as the first electrode, etc.

[0044] Figure 3 The image shows the appearance of the main body 10 as viewed from the bottom side. Figure 3 As shown, at the bottom of the main housing 11, there is a central region covered by a resin cover 151 and an area corresponding to its outer periphery covered by a cuff cover 16. At least a portion of the resin cover 151 is formed of a light-transmitting resin, and the area covered by the resin cover 151 on the inner side of the main housing 11 corresponds to the sensor substrate receiving portion 15. The sensor substrate receiving portion 15, when viewed from above, is located in the central region of the main housing 11 covered by the resin cover 151, as shown... Figure 2 As shown, it is formed so that, when worn, the sleeve cover 16 protrudes towards the wrist. That is, the bottom surface of the resin cover 151 becomes the contact surface that comes into contact with the human body.

[0045] Furthermore, a second electrode 132 and a third electrode 133 are provided at the bottom of the main body housing 11, with their contact surfaces exposed to the human body. The second electrode 132 functions as a left-hand electrode, and the third electrode 133 functions as a GND electrode (the electrode that provides the reference potential for ECG waveform measurement). When measuring the ECG waveform, the bio-information measuring device 1 is worn, the contact surfaces of the second electrode 132 and the third electrode 133 are in contact with the skin surface of the wearing part, and the finger on the side without the bio-information measuring device 1 is used to touch the frame 131, thereby enabling ECG waveform measurement in lead I. It should be noted that the detailed structure of the second electrode 132 and the third electrode 133 will be described later.

[0046] Furthermore, although not shown, a charging terminal is also provided at the bottom of the main housing 11. Connecting the connection terminal of the power supply side device to the charging terminal allows for charging of the rechargeable battery (in... Figure 3 (Not shown in the image) is being charged.

[0047] In addition, such as Figure 3 As shown, the first LED (Light Emitting Diode) 111, the second LED 113, the first photodiode (PD) 112, and the second PD 121 mounted on the lower side (mounting surface) of the second sensor substrate 102 described later can be seen through the light-transmitting portion of the resin cover 151 from the bottom side of the main body housing 11.

[0048] The band 20 is configured to include, in addition to a band 21 for securing the biometric information measuring device 1 to the wrist and a hook-and-loop fastener 25, a first compression cuff 22 and a second compression cuff 23 for compressing the artery located in the wrist, and a sensing cuff 24 for detecting pressure pulse waves. It should be noted that the connection portions of each cuff 22, 23, and 24 to the main body housing 11 are covered by a cuff cover 16. The cuff cover 16 protects the connection portions of each cuff 22, 23, and 24 to the main body housing 11 and also functions to secure each cuff 22, 23, and 24 to the main body housing 11.

[0049] (Internal structure of the shell)

[0050] Next, based on Figures 4 to 6 The internal structure of the main shell 11 will be described. Figure 4 It is equivalent to Figure 3 A rough sectional view of section XX. Figure 5 It is Figure 4 An enlarged view of the area near the sensor substrate housing 15. Figure 6 It is equivalent to Figure 3 A simplified sectional view of the YY section. It should be noted that... Figures 4 to 6 This is not an accurate sectional view; the components have been appropriately omitted or distorted for ease of explanation.

[0051] like Figure 4As shown, the main housing 11 houses a rechargeable battery 191, a control board 17, a piezoelectric pump 161, a valve 162, a pressure sensor 163, a flow path plate 164, and the like. Furthermore, a convex sensor board receiving portion 15 is provided near the bottom of the main housing 11, housing a sensor board assembly 100 composed of a first sensor board 101 and a second sensor board 102. Additionally, the side frame 131 constituting the side of the main housing 11 is connected to the display 12 constituting the top surface of the main housing 11 via a conductive strip TP.

[0052] Furthermore, at the bottom of the main body housing 11, in a portion of the area where the sensor substrate receiving portion 15 is not located when viewed from above, there is a first connecting portion 165 connecting the main body housing 11 (more specifically, the flow path plate 164 within the housing) to the first pressing cuff 22 and the sensing cuff 24, and similarly, a second connecting portion 166 connecting the main body housing 11 to the second pressing cuff 23. The first connecting portion 165 and the second connecting portion 166 are configured to be covered by a cuff cover 16, which is located in the area at the bottom of the main body corresponding to the outer periphery of the sensor substrate receiving portion 15. Furthermore, as described above, the portion located at the sensor substrate receiving portion 15 is configured to be covered by a resin cover 151.

[0053] The rechargeable battery 191 can be a common secondary battery such as a lithium-ion battery. The rechargeable battery 191 receives power supply via a charging terminal, thereby enabling repeated charging. In addition, the piezoelectric pump 161, valve 162, pressure sensor 163, flow path plate 164, first compression cuff 22, second compression cuff 23, and sensing cuff 24 are components related to blood pressure measurement.

[0054] The flow path plate 164 is a conductive component (metal) that internally forms a flow path for supplying gas from the piezoelectric pump 161 to each cuff. The flow path plate 164 is connected to the control board 17 via the spring connector 182 and functions as the overall GND (hereinafter also referred to as the device GND). Furthermore, for the first sensor board 101, the flow path plate 164 also functions as a shield against noise generated from internal devices such as the piezoelectric pump 161.

[0055] The control board 17 is equipped with a processor (CPU, not shown) and memory (RAM, not shown), and is responsible for the overall control of the biometric information measuring device 1. As described above, the control board 17 is connected to the flow path board 164 (device GND). However, in small devices such as watches, it is generally difficult to ensure sufficient GND area. In the event of ESD-induced static electricity entering the main housing 11, the static electricity will flow through the control board 17, potentially causing malfunctions or damage to electronic components in the circuit. In this regard, the biometric information measuring device 1 of this embodiment has a path that prevents static electricity from flowing to the device GND and instead releases it to the frame 131, thereby suppressing the flow of static electricity to the control board 17 and significantly improving static electricity resistance. Details will be described later.

[0056] (Sensor substrate assembly)

[0057] Next, the sensor substrate receiving portion 15 and the sensor substrate assembly 100 will be described. For example... Figure 5 As shown, the sensor substrate receiving portion 15 is a space protruding from the bottom of the main housing 11 toward the side that contacts the human body. Furthermore, this space houses a sensor substrate assembly 100 consisting of a first sensor substrate 101 and a second sensor substrate 102 stacked in two layers. It should be noted that the first sensor substrate 101 and the second sensor substrate 102 are connected via a conductive spring connector 183, functioning as a set of two.

[0058] For the second sensor substrate 102, the first LED 111 and the second LED 113, two light-emitting elements, and the first photodiode (PD) 112 and the second PD 121, two light-receiving elements, are disposed on the lower surface of the substrate. It should be noted that in this embodiment, the first LED 111 illuminates green light, and the second LED 113 illuminates red and / or infrared light in addition to green light. Furthermore, an isolation wall 152 is provided to isolate the first LED 111, the second LED 113, the first PD 112, and the second PD 121, respectively.

[0059] On the other hand, the first sensor substrate 101 is provided with amplifier circuits that amplify the biological signals acquired by each sensor, A / D (Analog-to-Digital) conversion circuits, etc. Of course, an electrocardiogram signal sensing circuit 50 for measuring electrocardiogram waveforms by sensing signals via the frame 131, the second electrode 132, and the third electrode 133 is also installed, and details related to this will be described later.

[0060] Thus, by forming the sensor substrate assembly 100 into a stacked structure consisting of a second sensor substrate 102 and a first sensor substrate 101, the area of ​​the substrate when viewed from above can be significantly reduced compared to mounting all components on a single substrate. It should be noted that the first sensor substrate 101 can also be a double-sided mounting substrate.

[0061] (The composition of the second and third electrodes)

[0062] In addition, such as Figure 6 As shown, the second electrode 132 and the third electrode 133 are fixed in contact with the lower surface of the first sensor substrate 101. Furthermore, the two electrodes are configured to generate a contact surface TS (located on the bottom side of the resin cover 151)... Figure 6 The dotted line in the image shows the part that protrudes towards the side of the body that is in contact with the wearer when it is worn.

[0063] Furthermore, an opening (not shown) is provided on the first sensor substrate 101, and electrode pads (not shown) are formed on the outer periphery of the first sensor substrate 101. Figure 6 As shown, the second electrode 132 and the third electrode 133 are screwed onto the first sensor substrate 101 via an opening in the first sensor substrate 101 and thus fixed to the first sensor substrate 101. This fixing is performed with the top surfaces of the second electrode 132 and the third electrode 133 in contact with the electrode pads formed on the outer periphery of the opening in the first sensor substrate 101, so the second electrode 132 and the third electrode 133 are fixed to the first sensor substrate 101 in a conductive state.

[0064] (The substrate adjacent to the inner wall of the frame)

[0065] Moreover, such as Figure 6 As shown, a frame conductive substrate 103 is disposed within the main body housing 11. This frame conductive substrate 103 is connected to the first sensor substrate 101 via a spring connector 184 and is joined to the inner wall of the frame 131, which serves as the first electrode, via a conductive strip TP. The frame conductive substrate 103 is bent into a generally L-shape and has a horizontal portion 103a disposed in a direction parallel to the first sensor substrate 101 (i.e., parallel to the bottom surface of the main body housing) and a vertical portion 103b disposed in a direction orthogonal to the first sensor substrate 101 (along the inner wall of the frame 131). It should be noted that the terms parallel, orthogonal, horizontal, and vertical are used here to facilitate the description of general directions, and the individual parts do not actually need to be horizontal or vertical. The frame conductive substrate 103 can be configured in a bent state by being wholly or partially composed of a flexible substrate.

[0066] Furthermore, an operation section board 104 for operating the button 13 is disposed inside the main housing 11 along the inner wall of the frame 131 opposite to the vertical portion 103b of the frame conductive board 103. The biological signals detected, amplified, and converted by the first sensor board 101 are transmitted to the control board 17 via the operation section board 104.

[0067] (ECG signal detection cable)

[0068] When measuring electrocardiogram (ECG) waveforms, if a user touches the frame 131 with their right hand while wearing the biometric information measuring device 1 on their left wrist, a signal is sent to the ECG signal sensing circuit 50 of the first sensor substrate 101 via the frame conductive substrate 103. Here, Figure 7 The diagram shows a schematic representation of the frame 131, the second electrode 132, the third electrode 133, and the signal lines of the ECG signal sensing circuit 50. (See diagram for reference.) Figure 7 As shown, the second electrode 132 and the third electrode 133 are connected to the frame 131 via TVS diodes D1 and D2, respectively. It should be noted that TVS diodes D1 and D2 can be disposed on the first sensor substrate 101 or on the frame conductive substrate 103. It should be noted that in... Figure 7 In the circuit, the circuit connecting the frame 131 to the electrocardiogram signal sensing circuit 50 is equivalent to the first circuit of the present invention, and the circuit configured with the TVS diode D1 is equivalent to the second circuit of the present invention.

[0069] In the event of ESD generated by the second electrode 132 and the third electrode 133, if the static electricity is not connected to the frame 131 via TVS diodes D1 and D2, it will flow into the control board 17 via the ECG signal sensing circuit 50 and then via the signal lines on the operation unit board 104. Regarding this, as... Figure 7 As shown, a line is provided connecting the second electrode 132 and the third electrode 133 to the frame 131 via TVS diodes D1 and D2. Thus, even if ESD is generated in the second electrode 132 and the third electrode 133, most of the static electricity will flow to the frame 131. The frame 131 is the first electrode used for ECG measurement and is not the device's GND.

[0070] (Functional composition of the device)

[0071] Next, the functional structure of the biological information measuring device 1 will be explained. Figure 8 This is a block diagram illustrating the functional structure of the biological information measuring device 1. For example... Figure 8As shown, the biological information measuring device 1 of this embodiment includes functional units such as a pulse wave measuring unit 110, a blood oxygen saturation (SpO2) measuring unit 120, a blood pressure measuring unit 130, an electrocardiogram waveform measuring unit 140, a display unit 150, an operation unit 160, a communication unit 170, a storage unit 180, and a power supply unit 190. The processor of the control board 17 controls each component of the biological information measuring device 1 by reading a program from the memory and executing the program, thereby realizing these functional units.

[0072] The pulse wave measuring unit 110 is configured to include a first LED 111, a second LED 113, and a first PD 112. It measures the pulse wave using a so-called photoelectric pulse wave method and calculates the pulse. Specifically, green light is irradiated from the first LED 111 and the second LED 113, and the reflected light reflected within the biological body is received by the first PD 112, thereby detecting the changes in blood flow (changes in blood vessel capacity) that accompany the heartbeat and measuring the pulse wave.

[0073] The SpO2 measuring unit 120 is configured to include a second LED 113 and a second PD 121. The second PD 121 receives reflected light from red light or infrared light irradiated by the second LED 113, thereby measuring blood oxygen saturation based on the intensity of the reflected light.

[0074] The blood pressure measuring unit 130 is configured to include a piezoelectric pump 161, a valve 162, a pressure sensor 163, a flow path plate 164, a first compression cuff 22, a second compression cuff 23, and a sensing cuff 24, and measures blood pressure using the so-called oscillometric method. Blood pressure measurement using the oscillometric method is a well-known technique, therefore detailed description is omitted.

[0075] The electrocardiogram (ECG) waveform measurement unit 140 is configured to include a frame 131, a second electrode 132 and a third electrode 133 located at the bottom of the main housing 11, and an ECG signal sensing circuit 50, measuring the ECG waveform in a so-called I-lead manner. Specifically, the ECG waveform is measured based on the potential difference between the second electrode 132 and the third electrode 133, which are in contact with the wrist of one arm when worn, and the fingers of the other hand, which are in contact with the frame 131, which functions as the first electrode.

[0076] The display unit 150 is configured to include a display 12, which displays various information such as measurement results of biological information and menu screens. The operation unit 160 is configured to include operation buttons 13a and 13b, through which user input operations are received. The communication unit 170 includes an antenna (not shown) for wireless communication, for example, for communication with other electronic devices such as information processing terminals via BLE communication. It should be noted that a terminal for wired communication may also be included.

[0077] The storage unit 180 is configured to include a main storage device (not shown) such as RAM, storing various information such as application programs and measured biological information. In addition to RAM, it may also include an auxiliary storage device such as flash memory. The power supply unit 190 is configured to include a rechargeable battery 191 and a charging terminal, functioning as a power supply source for all components constituting the biological information measuring device 1.

[0078] (Effects of this implementation method)

[0079] As described above, in the biometric information measuring device of this embodiment, the frame 131 of the main housing 11 functions as the first electrode and is connected to the second electrode 132 and the third electrode 133 via a signal line for electrocardiogram (ECG) measurement provided on the frame conductive substrate 103 and the first sensor substrate 101. Furthermore, TVS diodes D1 and D2, serving as electrostatic discharge (ESD) protection elements, are installed on this ECG measurement signal line. Therefore, even if ESD is generated in the biometric information measuring device 1 via the second electrode 132, the third electrode 133, etc., static electricity can be discharged to the frame 131 via the TVS diodes D1 and D2 on the ECG measurement signal line. Current flows more easily to the ECG measurement signal line than to the device ground. Moreover, static electricity can also be discharged to the ground wire outside the device via the display 12, which is connected to the frame 131 via a conductive strip TP.

[0080] Therefore, even small biometric devices, such as watch-type devices, which cannot obtain a large device ground (GND), can exhibit high electrostatic resistance. Furthermore, since the destination for static electricity release, namely the frame 131, is the electrode used for electrocardiogram measurement, high voltage does not need to be applied during the device's withstand voltage test, and no obstacles are encountered when passing the withstand voltage test and leakage current test.

[0081] <Other>

[0082] The foregoing examples are merely illustrative of the invention, and the invention is not limited to the specific embodiments described above. Various modifications and combinations can be made within the scope of the invention's technical concept. For example, a biological information measuring device only needs to include electrodes and circuits for measuring electrocardiogram waveforms; other functions and configurations for acquiring biological information are not necessarily required.

[0083] Furthermore, while a TVS diode was shown as an example of an electrostatic discharge protection element in the above embodiment, other electrostatic discharge protection elements may also be used. Moreover, the shape, holding method, and placement of the second electrode 132 and the third electrode 133 are not limited to the examples in the above embodiments, and any desired shape, holding method, and placement can be used.

[0084] Furthermore, in the above embodiment, the upper surface of the device is generally formed as the display 12, and the frame 131 part functions as the first electrode. However, the upper surface of the device may not have a display, and the upper surface of the main body housing 11 may also be formed of metal (in which case the upper surface also functions as the first electrode).

[0085] Furthermore, in the above embodiment, the frame conductive substrate 103 and the first sensor substrate 101 are connected via a spring connector, but the two substrates can also be integrated. That is, the horizontal portion 103a of the frame conductive substrate 103 can also serve as the first sensor substrate 101.

[0086] Explanation of reference numerals in the attached figures

[0087] 1: Organism information measurement device;

[0088] 10: Main body;

[0089] 11: Main body shell;

[0090] 12: Monitor;

[0091] 13a, 13b: Operation buttons;

[0092] 14: ear;

[0093] 15: Sensor substrate housing;

[0094] 16: Sleeve cover;

[0095] 17: Control board;

[0096] 20: Belt section;

[0097] 21: with;

[0098] 22: First press the cuff;

[0099] 23: Second pressing cuff;

[0100] 24: Sensing cuff;

[0101] 25: Hook and loop fasteners;

[0102] 50: Electrocardiogram signal sensing circuit;

[0103] 100: Sensor substrate assembly;

[0104] 101: First sensor substrate;

[0105] 102: Second sensor substrate;

[0106] 103: Frame conductive substrate;

[0107] 106: Threaded components;

[0108] 111: First LED;

[0109] 112: First PD;

[0110] 113: Second LED;

[0111] 121: Second PD;

[0112] 131: Frame (first electrode);

[0113] 132: Second electrode;

[0114] 133: Third electrode;

[0115] 151: Resin cover;

[0116] 152: Isolation wall;

[0117] 161: Piezoelectric pump;

[0118] 162: Valve;

[0119] 163: Pressure sensor;

[0120] 164: Flow plate;

[0121] 165: First connecting part;

[0122] 166: Second connecting part;

[0123] 182, 183, 184: Spring connectors;

[0124] 191: Rechargeable battery;

[0125] D1, D2: TVS diodes;

[0126] TP: Conductive strip;

[0127] TS: Contact surface.

Claims

1. A bio-information measuring device, worn on the human body for use, the bio-information measuring device having at least a first electrode and a second electrode, and configured to perform measurement of an electrocardiogram waveform based on the potential difference between the first electrode and the second electrode, the bio-information measuring device having: The main body shell has a side surface formed of conductive material that functions as the first electrode, a bottom surface on which the second electrode is disposed and which abuts against the human body when worn, and a top surface opposite the bottom surface; An electrocardiogram signal sensing circuit senses signals related to the potentials of the first electrode and the second electrode; The first circuit connects the first electrode to the electrocardiogram signal sensing circuit. as well as The second circuit is equipped with an electrostatic discharge protection element, and the first electrode and the second electrode are connected via the electrostatic discharge protection element.

2. The biological information measuring device according to claim 1, wherein, The electrocardiogram signal sensing circuit is disposed on a first substrate, which is arranged within the main housing in a direction parallel to the bottom surface. A portion of the first circuit and the second circuit are disposed on a second substrate, which is arranged in the main body housing in a direction orthogonal to the bottom surface and is connected to the first electrode by a conductive guide strip.

3. The biological information measuring device according to claim 2, wherein, The first substrate and the second substrate are integrally formed into a rigid-flexible substrate.

4. The biological information measuring device according to claim 1, wherein, A display is provided on the top surface. The first electrode and the display are configured to be conductive.

5. The biological information measuring device according to claim 2, wherein, The biological information measuring device has the following features: The third substrate is arranged inside the main housing in a direction parallel to the first substrate, and a control device for controlling the biological information measuring device is installed thereon. as well as The fourth substrate has an operation button configured to protrude from the side and a portion of an electrocardiogram signal line connecting the electrocardiogram signal sensing circuit to the control device, and is arranged at a position different from the second substrate along a direction orthogonal to the first substrate.

Images