Wearable sensing device

Abstract

This wearable sensing device (1) comprises: a base material (10) composed of a flexible material to be worn on the body of a measurement subject; a plurality of electrodes (11) disposed on the surface of the base material in contact with the skin of the measurement subject; a sensor terminal (12) that detects, via the plurality of electrodes (11), a current flowing through the body of the measurement subject and measures the impedance in the measurement subject; and a plurality of wires (13) that connect the plurality of electrodes (11) and the sensor terminal (12).

Description

Wearable sensing device

[0001] The present invention relates to a wearable sensing device for collecting biological information.

[0002] Bioelectrical impedance analysis (BIA) is a method of measuring the absolute value or phase angle of bioelectrical impedance by applying a weak alternating current to a living body and non-invasively and simply estimating body composition (Non-Patent Document 1). Information such as body fat mass, muscle mass, body fluid volume, and cell health status can be obtained by BIA. BIA is used in various applications such as health management, goal setting in fitness, optimization of training programs in sports medicine, and monitoring of body fluid status and evaluation of nutritional status in the medical field.

[0003] In recent years, the absolute value or phase angle of bioelectrical impedance has been expected to play a role as a comprehensive index for capturing physical changes associated with aging, and its correlation with frailty and sarcopenia has been investigated. The absolute value or phase angle of bioelectrical impedance is considered useful for promoting health in old age and preventing care (Non-Patent Document 2).

[0004] As devices for BIA, stationary body composition analyzers equipped with multi-electrodes and devices that enable measurement in the supine position have been developed (Non-Patent Documents 2 and 3). These devices are used in fitness gyms, hospitals, etc.

[0005] However, the body composition analyzer disclosed in Non-Patent Document 2 requires a certain space and can only be measured at a predetermined position. In addition, the device disclosed in Non-Patent Document 3 requires electrode wiring for measurement in the supine position, so measurement is only possible within the range where the electrode wiring reaches. That is, conventional devices have a problem that it is difficult to measure while a person moves freely and continuously in real time.

[0006] Furthermore, while conventional devices can measure data by dividing the body into broad areas such as the upper body, lower body, and left and right arms, they are unable to provide detailed information on individual muscles or body parts. However, evaluating individual muscles is considered effective not only for athletes but also for injury prevention and treatment management, as well as for training tailored to individual needs (such as preventing sports injuries and maintaining the health of the elderly) in people of various age groups (Non-Patent Literature 4). Therefore, there is a need for measuring devices that can evaluate individual muscles.

[0007] Ken Yamauchi, "Principles of BIA and Body Composition Assessment," Surgery and Metabolism / Nutrition, Japanese Society for Surgical Metabolism and Nutrition, Vol. 53, No. 4, pp. 123-130, 2019, <https: / / www.jstage.jst.go.jp / article / jssmn / 53 / 4 / 53_123 / _article / -char / ja / > Kazuki Uemura, Minoru Yamada, Kenji Saho, Kei Okamoto, "Phage by Bioelectrical Impedance Method" Relationship between angle and physical activity level in the elderly, Physical Therapy, Japanese Physical Therapy Association, Vol. 46, No. 3, pp. 143-151, 2019, <https: / / www.jstage.jst.go.jp / article / rigaku / 46 / 3 / 46_11556 / _pdf / -char / ja> Masashi Taniguchi, Yoshihiro Fukumoto, Noriaki Ichihashi, "Establishment of a qualitative evaluation method for skeletal muscle in old age and its clinical application", Japanese Journal of Basic Physical Therapy, Japanese Society of Basic Physical Therapy, Vol. 22, No. 1, pp. 25-31, 2019, <https: / / www.jstage.jst.go.jp / article / jptf / 22 / 1 / 22_25 / _article / -char / ja / > M. Kadija, OMKnezevic, D. Milovanovic, A. Nedeljkovic, DMMirkov, "The effect of anterior cruciate ligament reconstruction on hamstring and quadriceps muscle function outcome ratios in male athletes”, Srpski Arhiv za Celokupno Lekarstvo, vol.144, iss.3-4, pp.151-157, 2016

[0008] The present invention was made to solve the above problems and aims to provide a wearable sensing device capable of evaluating individual body parts of a person being measured.

[0009] The wearable sensing device of the present invention is characterized by comprising: a substrate made of a flexible material configured to be attached to the body of a person to be measured; a plurality of electrodes arranged on the surface of the substrate that is in contact with the skin of the person to be measured; a sensor terminal configured to detect an electric current flowing through the body of the person to be measured via the plurality of electrodes and measure the impedance of the person to be measured; and a plurality of wires connecting the plurality of electrodes and the sensor terminal.

[0010] According to the present invention, by integrating a substrate, multiple electrodes, sensor terminals, and wiring, the impedance of individual parts of a person being measured can be measured. With this invention, there is no need to measure at a fixed location, and measurements can be performed even when the person being measured is moving around freely.

[0011] Figure 1 is an external view of a wearable sensing device according to the first embodiment of the present invention. Figure 2 is an external view of a conventional device. Figure 3 is an external view of another conventional device. Figure 4 is an external view showing one example of a wearable sensing device according to the first embodiment of the present invention. Figure 5 is an external view showing another example of a wearable sensing device according to the first embodiment of the present invention. Figure 6 is an external view showing another example of a wearable sensing device according to the first embodiment of the present invention. Figure 7 is an external view showing another example of a wearable sensing device according to the first embodiment of the present invention. Figure 8 is a block diagram showing the electrical configuration of a sensor terminal according to the first embodiment of the present invention. Figure 9 is a functional block diagram of the MPU of a wearable sensing device according to the first embodiment of the present invention. Figure 10 is an external view showing one example of a wearable sensing device according to the second embodiment of the present invention. Figure 11 is an external view showing another example of a wearable sensing device according to the second embodiment of the present invention. Figure 12 is an external view showing another example of a wearable sensing device according to the second embodiment of the present invention. Figure 13 is an external view showing another example of a wearable sensing device according to the second embodiment of the present invention. Figure 14 is an external view showing one example of a wearable sensing device according to the third embodiment of the present invention. Figure 15 is an external view showing another example of a wearable sensing device according to the third embodiment of the present invention. Figure 16 is an external view showing another example of a wearable sensing device according to the third embodiment of the present invention. Figure 17 is an external view showing another example of a wearable sensing device according to the third embodiment of the present invention. Figure 18 is an external view showing one example of a wearable sensing device according to the fourth embodiment of the present invention. Figure 19 is an external view showing another example of a wearable sensing device according to the fourth embodiment of the present invention. Figure 20 is an external view showing another example of a wearable sensing device according to the fourth embodiment of the present invention. Figure 21 is an external view showing another example of a wearable sensing device according to the fourth embodiment of the present invention. Figure 22 is a functional block diagram of the MPU of a wearable sensing device according to the fifth embodiment of the present invention. Figures 23A and 23B show an example of electromyography measurement results.Figure 24 shows an example of how a wearable sensing device according to the fifth embodiment of the present invention is worn. Figure 25 is a functional block diagram of the MPU of a wearable sensing device according to the sixth embodiment of the present invention. Figure 26 is a functional block diagram of the MPU of a wearable sensing device according to the seventh embodiment of the present invention. Figure 27 is a functional block diagram of the MPU of a wearable sensing device according to the eighth embodiment of the present invention.

[0012] [First Embodiment] Embodiments of the present invention will be described below with reference to the drawings. Figure 1 is an external view of a wearable sensing device according to the first embodiment of the present invention. The wearable sensing device 1 of this embodiment is a device capable of measuring the impedance of a person being measured. The wearable sensing device 1 consists of a base material 10 which is attached, for example, by wrapping it around the knee of a person being measured 100, a plurality of electrodes 11 arranged on the surface of the base material 10 that is in contact with the skin of the person being measured 100, a sensor terminal 12 which measures the impedance of the person being measured 100 at the site where the base material 10 is attached, and a plurality of wires 13 which connect the plurality of electrodes 11 and the sensor terminal 12.

[0013] The base material 10 can be a flexible material with elasticity, such as silicone rubber. Any electrode 11 can be used, such as an Ag / AgCl electrode used in medical applications. Multiple electrodes 11 and sensor terminals 12 are connected by wiring 13. Details of the sensor terminals 12 attached to the base material 10 will be described later.

[0014] Figure 2 is an external view of a conventional stationary device disclosed in Non-Patent Literature 2. In Figure 2, 1000 is a measuring platform on which the person being measured places their feet, 1001 is an electrode provided on the measuring platform 1000, 1002 is a grip held by the person being measured, 1003 is an electrode provided on the grip 1002, and 1004 is a display unit.

[0015] Figure 3 is an external view of the device disclosed in Non-Patent Document 3. In Figure 3, 2000 is an electrode attached to the hands and feet of the person being measured, 2001 is a measuring device that measures the impedance of the person being measured via the electrodes 2000, and 2002 is wiring that connects the multiple electrodes 2000 and the measuring device 2001. In the devices of Figures 2 and 3, impedance can only be measured at the location where the device is installed, and measurement is only possible when the person being measured is not moving.

[0016] On the other hand, in this embodiment, as shown in Figure 4, a band-type base material 10 is used, which can be wrapped around the knee of the person being measured, as shown in Figure 1, or around specific parts of the body such as the thigh, calf, upper arm, or abdomen. Hook and loop fasteners 14a and 14b are attached to both ends of the base material 10 in the longitudinal direction (left and right direction in Figure 4). The base material 10 is attached to the person being measured by connecting the hook and loop fasteners 14a and 14b while the base material 10 is wrapped around the person being measured.

[0017] Furthermore, a sock-type base material 10 may be used as shown in Figure 5, a leggings-type base material 10 may be used as shown in Figure 6, or a shirt-type base material 10 may be used as shown in Figure 7. In this embodiment, by mounting the electrodes 11, sensor terminals 12, and wiring 13 on the base material 10, the electrodes and the signal processing part can be integrated, and measurements can be performed even when the person being measured moves around freely.

[0018] Figure 8 is a block diagram showing the electrical configuration of the sensor terminal 12. The sensor terminal 12 includes a voltage application unit 120 that applies voltage between a plurality of electrodes 11 for impedance measurement, an amplification unit 121 that amplifies the signals detected by the electrodes 11, an A / D conversion unit 122 that converts the signals amplified by the amplification unit 121 into digital signals, a memory 123 that stores the output data of the A / D conversion unit 122, an MPU (Micro Processing Unit) 124 that calculates the impedance of the person being measured and estimates the body composition of the person being measured from the impedance calculation result, an acceleration sensor 125, a temperature sensor 126, a pulse wave sensor 127, a transmission unit 128, an amplification unit 129 that amplifies the electromyographic potential detected by the electrodes 11, an A / D conversion unit 130 that converts the signals amplified by the amplification unit 129 into digital signals, and a memory 131 that stores the output data of the A / D conversion unit 130.

[0019] The amplification unit 121, A / D conversion unit 122, and memory 123 are configured for impedance measurement, while the amplification unit 129, A / D conversion unit 130, and memory 131 are configured for electromyography measurement. Amplification units 121, 129 and A / D conversion units 122, 130 are provided for each electrode 11. Note that the frequency of electromyography is, for example, several hundred Hz, while the frequency of the voltage applied by the voltage application unit 120 is, for example, several tens of kHz, so the frequencies are significantly different.

[0020] To measure the impedance of the person being measured, a voltage is applied between multiple electrodes 11 by the voltage application unit 120. The MPU 124 performs predetermined processing according to a program stored in an internal memory (not shown) and functions as an impedance calculation unit 1240 and a body composition estimation unit 1241, as shown in Figure 9.

[0021] The impedance calculation unit 1240 calculates the current flowing between the multiple electrodes 11 from the results stored in the memory 123, and calculates the impedance of the person being measured based on the voltage applied by the voltage application unit 120 and the calculated current.

[0022] The body composition estimation unit 1241 estimates the body composition of the subject based on the absolute value or phase angle of the impedance value calculated by the impedance calculation unit 1240. The method for estimating body composition is disclosed in Non-Patent Literature 1. The transmission unit 128 wirelessly transmits the impedance calculation results and body composition estimation results to an external terminal such as a smartphone.

[0023] When using a band-type wearable sensing device 1 as shown in Figure 4, the following examples of applications (I) to (VI) can be considered.

[0024] (I) Wrap the wearable sensing device 1 around the subject's face to evaluate the condition of facial muscles or the muscles used for chewing. (II) Wrap the wearable sensing device 1 around the subject's neck to evaluate the muscles used for swallowing. (III) Wrap the wearable sensing device 1 around the subject's upper arm to evaluate the condition of the biceps brachii muscle. (IV) Wrap the wearable sensing device 1 around the subject's abdomen to evaluate the condition of the abdominal muscles. (V) Wrap the wearable sensing device 1 around the subject's thigh to evaluate the condition of the quadriceps femoris, hamstrings, adductor muscles, and abductor muscles. (VI) Wrap the wearable sensing device 1 around the subject's calf to evaluate the condition of the gastrocnemius and tibialis muscles.

[0025] When using a sock-type, leggings-type, or shirt-type wearable sensing device 1 as shown in Figures 5 to 7, the following examples of applications (VII) to (X) can be considered.

[0026] (VII) A wearable sensing device 1 is attached to the neck of the subject to be measured, and the muscles used for swallowing are evaluated. (VIII) A shirt-type wearable sensing device 1 is attached to the subject to be measured, and the back muscles related to maintaining posture are evaluated. (IX) A leggings-type wearable sensing device 1 is attached to the subject to be measured, and the thigh muscles are evaluated. (X) A sock-type wearable sensing device 1 is attached to the subject to be measured, and the calf muscles (gastrocnemius) are evaluated.

[0027] [Second Embodiment] The second embodiment of the present invention solves the problems that arise when integrating the electrode 11, the sensor terminal 12, and the base material 10 in the first embodiment. In the first embodiment, the sensor terminal 12 must be provided in the wearable sensing device in order to enable measurement even when the person being measured moves around freely. Typically, the sensor terminal 12 is housed in a rigid material casing. If the sensor terminal 12 is placed in the center of the wearable sensing device, the elongation rate (Young's modulus) when subjected to the same force will differ between the base material 10 and the sensor terminal 12 as the base material 10 is pulled to attach the wearable sensing device to the person being measured. As a result, the stress on the joint between the base material 10 and the sensor terminal 12 increases, and the risk of damage to the sensor terminal 12 increases.

[0028] Therefore, in this embodiment, for example, in the case of a band-type wearable sensing device 1, the sensor terminal 12 is attached near the joint portion of the base material 10 (the portion to which the hook-and-loop fasteners 14a and 14b are attached), as shown in Figure 10. In the case of a sock-type wearable sensing device 1, the sensor terminal 12 is attached near the opening of the base material 10 through which the person being measured puts their foot (the calf portion of the person being measured), as shown in Figure 11.

[0029] In the case of the leggings-type wearable sensing device 1, as shown in Figure 12, the sensor terminal 12 is attached near the opening of the base material 10 through which the person being measured passes (the person's abdomen). In the case of the shirt-type wearable sensing device 1, as shown in Figure 13, the sensor terminal 12 is attached near the opening of the base material 10 through which the person being measured passes (the person's chest).

[0030] As in this embodiment, by positioning the sensor terminal 12 in a part of the wearable sensing device 1 where tensile stress is low, damage to the sensor terminal 12 can be minimized and the risk of the sensor terminal 12 breaking can be reduced.

[0031] [Third Embodiment] The third embodiment of the present invention solves the problems that arise in the first embodiment when integrating the electrode 11, the sensor terminal 12, and the base material 10, similar to the second embodiment. When the wearable sensing device envisioned in the present invention is removed from the body of the person being measured, bending inevitably occurs somewhere in the base material 10. This bending may damage and break the rigid sensor terminal 12. In addition, the direction in which the sensor terminal 12 is positioned may impair the elasticity of the base material 10. Furthermore, attaching and detaching the wearable sensing device may cause discomfort to the person being measured.

[0032] Therefore, in this embodiment, the outer shape of the sensor terminal 12 is a rectangular parallelepiped. In the case of a band-type wearable sensing device 1, as shown in Figure 14, the sensor terminal 12 is attached so that its longitudinal direction is approximately perpendicular to the longitudinal direction of the base material 10 (left-right direction in Figure 14). In the case of a sock-type wearable sensing device 1, as shown in Figure 15, the sensor terminal 12 is attached so that its longitudinal direction is approximately perpendicular to the longitudinal direction of the base material 10 (up-down direction in Figure 15).

[0033] In the case of a leggings-type wearable sensing device 1, the sensor terminal 12 is attached so that its longitudinal direction is approximately perpendicular to the longitudinal direction of the base material 10 (up and down direction in Figure 16), as shown in Figure 16. In the case of a shirt-type wearable sensing device 1, the sensor terminal 12 is attached so that its longitudinal direction is approximately perpendicular to the longitudinal direction of the base material 10 (up and down direction in Figure 17), as shown in Figure 17.

[0034] In this embodiment, the bending of the sensor terminal 12 can be minimized. Furthermore, the impact received by the sensor terminal 12 due to the bending of the base material 10 can be distributed across the entire sensor terminal 12, reducing the risk of damage to the sensor terminal 12. In addition, in this embodiment, the wearable sensing device 1 can be removed from the body of the person being measured without impairing the elasticity of the base material 10, improving the user experience for the person being measured.

[0035] [Fourth Embodiment] The fourth embodiment of the present invention solves the problems that arise when measuring the impedance of multiple subjects with different body sizes using a wearable sensing device of a fixed size. With conventional wearable sensing devices, the part of the muscle that the electrodes contact may change depending on the individual's body size. For example, when a wrap-around type wearable sensing device is attached to the calf of a subject, the part of the muscle that the electrodes contact may differ between a person with thick calves and a person with thin calves. Therefore, it may not be possible to measure the impedance accurately.

[0036] Therefore, in this embodiment, in the case of a band-type wearable sensing device 1, as shown in Figure 18, a plurality of electrodes 11a of the first group are attached to the surface of the substrate 10 that comes into contact with the skin of the person being measured, and a plurality of electrodes 11b of the second group are attached to a different location on the same surface from the first group. A sock-type wearable sensing device 1 is shown in Figure 19, a leggings-type wearable sensing device 1 is shown in Figure 20, and a shirt-type wearable sensing device 1 is shown in Figure 21.

[0037] This embodiment makes it possible to perform impedance measurements at an optimal location tailored to the individual. The arrangement of electrodes 11a and 11b is not limited to the examples shown in Figures 18 to 21. By arranging multiple electrode groups according to the muscle area to be measured, a wearable sensing device can be designed to suit the muscle to be measured.

[0038] Conventional wearable sensing devices have limitations on the number and position of electrodes depending on the electromyographic potential to be measured, requiring the user to fix the electrodes in place according to the desired electromyographic potential. In contrast, this embodiment eliminates the constraint of having to fix the electrodes in place according to the desired electromyographic potential by providing multiple electrode groups, which is expected to improve the user experience for the user.

[0039] Figures 18 to 21 show examples where two groups of electrodes are arranged, but it is also possible to arrange three or more groups of electrodes.

[0040] [Fifth Embodiment] The fifth embodiment of the present invention solves the problem in the fourth embodiment, which is that the optimal electrode to be used for measurement must be selected from among multiple electrodes. In the fourth embodiment, impedance measurement was made possible with an electrode position suited to the individual, but it was impossible to select the optimal electrode for measurement.

[0041] Figure 22 is a functional block diagram of the MPU 124 of the sensor terminal 12 in this embodiment. The MPU 124 performs predetermined processing according to a program stored in an internal memory (not shown) and functions as an impedance calculation unit 1240, a body composition estimation unit 1241, and an electrode selection unit 1242, as shown in Figure 22.

[0042] Figure 23A shows the measurement results of electromyography obtained with a combination of one electrode from the first group (hereinafter referred to as 11a-1) and eight electrodes from the second group (hereinafter referred to as 11b-1 to 11b-8). Figure 23B shows the measurement results of electromyography obtained with a combination of an electrode from the first group different from electrode 11a-1 (hereinafter referred to as 11a-2) and eight electrodes from the second group 11b-1 to 11b-8. Figures 23A and 23B show the measurement results when the wearable sensing device 1 is wrapped around the calf of a subject 100, for example, as shown in Figure 24.

[0043] In this embodiment, the electrode selection unit 1242 measures electromyography (EMG) for all electrode combinations included in the first group of electrodes 11a and the second group of electrodes 11b. As described above, the EMG data is stored in the memory 131. The electrode selection unit 1242 then selects the combination of two electrodes showing the largest EMG difference as the impedance measurement electrodes. The impedance calculation unit 1240 calculates the impedance of the subject from the current measurement results obtained from the electrode combination selected by the electrode selection unit 1242, similar to the first embodiment.

[0044] The myoelectric potential is an electrical signal generated when a muscle contracts and can be used to estimate muscle activity. In this embodiment, among each electrode, it is possible to estimate and select the electrode that best contacts the skin of the measurement subject, and it is expected that accurate impedance can be measured. Note that a myoelectric potential difference may be acquired in a single measurement, or an average value, maximum value, or minimum value of the myoelectric potential differences when multiple myoelectric potential measurements are performed within a certain period may be acquired.

[0045] [Sixth Embodiment] The sixth embodiment of the present invention improves the functions of the wearable sensing device in the first to fifth embodiments. The items that can be measured with conventional devices are only body weight, body fat percentage, and impedance value.

[0046] On the other hand, in the present invention, by wearing the wearable sensing device on the body of the measurement subject, real-time measurement during exercise and the like, which was impossible with conventional devices, becomes possible. FIG. 25 is a functional block diagram of the MPU 124 of the sensor terminal of this embodiment. The MPU 1 takes predetermined processes according to a program stored in an internal memory (not shown) and functions as an impedance calculation unit 1240, a body composition estimation unit 1241, an electrode selection unit 1242, and an exercise monitoring unit 1243 as shown in FIG. 25.

[0047] The exercise monitoring unit 1243 estimates the number of steps, walking distance, and posture of the measurement subject based on the acceleration measured by the acceleration sensor set on the sensor terminal 12. The transmission unit 128 wirelessly transmits the calculation result of the impedance, the estimation result of the body composition, and the estimation result of the exercise monitoring unit 1243 to an external terminal such as a smartphone. Thus, in this embodiment, it is possible to monitor the exercise of the measurement subject.

[0048] [Seventh Embodiment] FIG. 26 is a functional block diagram of the MPU 124 of the sensor terminal 12 of the seventh embodiment of the present invention. The MPU 124 takes predetermined processes according to a program stored in an internal memory (not shown) and functions as an impedance calculation unit 1240, a body composition estimation unit 1241, an electrode selection unit 1242, an exercise monitoring unit 1243, and a heat load monitoring unit 1244 as shown in FIG. 26. <0x

[0049] A temperature sensor 126 installed on the sensor terminal 12 measures the body temperature of the person being measured. The heat load monitoring unit 1244 estimates the heat load and sweating amount of the person being measured based on the temperature measured by the temperature sensor 126.

[0050] The transmitting unit 128 wirelessly transmits the impedance calculation results, body composition estimation results, exercise monitoring unit 1243 estimation results, and heat load monitoring unit 1244 estimation results to an external terminal such as a smartphone. In this way, the effects and load of exercise of the subject can be evaluated in this embodiment.

[0051] [Eighth Embodiment] Figure 27 is a functional block diagram of the MPU 124 of the sensor terminal 12 in the eighth embodiment of the present invention. The MPU 124 performs predetermined processing according to a program stored in an internal memory (not shown) and functions as an impedance calculation unit 1240, a body composition estimation unit 1241, an electrode selection unit 1242, an exercise monitoring unit 1243, a heat load monitoring unit 1244, and an exercise load monitoring unit 1245, as shown in Figure 27.

[0052] The pulse wave sensor 127 installed on the sensor terminal 12 detects the pulse wave of the person being measured. The pulse wave sensor 127 is an optical pulse wave sensor. The exercise load monitoring unit 1245 calculates the heart rate of the person being measured based on the measurement results of the pulse wave sensor 127 and estimates the exercise load of the person being measured.

[0053] The transmitting unit 128 wirelessly transmits the impedance calculation results, body composition estimation results, exercise monitoring unit 1243 estimation results, heat load monitoring unit 1244 estimation results, and exercise load monitoring unit 1245 estimation results to an external terminal such as a smartphone. In this way, the exercise load and training effect of the subject can be evaluated in this embodiment.

[0054] According to the sixth to eighth embodiments, it is possible to evaluate the condition of the subject's muscles by measuring impedance while simultaneously evaluating the subject's state during exercise. Furthermore, by detecting the subject's movement, it becomes possible to track the causal relationship between exercise and changes in muscle quality.

[0055] In the first to eighth embodiments, an acceleration sensor 125, a temperature sensor 126, and a pulse wave sensor 127 may be provided for each electrode. In the first to eighth embodiments, sensors 125 to 127 are provided inside the sensor terminal 12, but sensors 125 to 127 are also provided outside the sensor terminal 12. This makes it possible to grasp detailed real-time changes for different parts of the same muscle, and to perform exercise evaluation for different parts.

[0056] Some or all of the above examples may also be described as follows, but are not limited to the following.

[0057] (Note 1) The wearable sensing device of the present invention comprises a substrate made of a flexible material configured to be attached to the body of a person to be measured; a plurality of electrodes arranged on the surface of the substrate that is in contact with the skin of the person to be measured; a sensor terminal configured to detect an electric current flowing through the body of the person to be measured via the plurality of electrodes and measure the impedance of the person to be measured; and a plurality of wires connecting the plurality of electrodes and the sensor terminal.

[0058] (Note 2) In the wearable sensing device described in Note 1, the base material is in the shape of a band that is attached to the body of the person being measured by wrapping it around the person's body and joining one end to the other end, and the sensor terminal is attached near the joining portion.

[0059] (Note 3) In the wearable sensing device described in Note 1, the substrate is in the shape of clothing, and the sensor terminal is attached near the opening of the substrate through which the person being measured passes.

[0060] (Note 4) In the wearable sensing device described in Note 1, the external shape of the sensor terminal is a rectangular parallelepiped, and the sensor terminal is attached such that the longitudinal direction of the sensor terminal is substantially perpendicular to the longitudinal direction of the substrate.

[0061] (Note 5) In the wearable sensing device described in Note 1, the first group of electrodes is attached to the surface of the substrate that comes into contact with the skin of the person being measured, and the second group of electrodes is attached to the surface of the substrate at a location different from the first group.

[0062] (Note 6) In the wearable sensing device described in Note 5, the sensor terminal includes an electrode selection unit configured to measure the electromyographic potential of the subject for all combinations of the plurality of electrodes of the first group and the plurality of electrodes of the second group, and to select the combination of two electrodes that show the largest electromyographic potential difference as the impedance measurement electrodes, and an impedance calculation unit configured to calculate the impedance of the subject from the measurement results of the current obtained by the combination of electrodes selected by the electrode selection unit.

[0063] (Note 7) The wearable sensing device described in Note 5 further comprises a sensor attached to the substrate and configured to acquire biological information other than the impedance of the person being measured, and a monitoring unit configured to estimate the state of the person being measured based on the measurement results of the sensor.

[0064] (Note 8) In the wearable sensing device described in Note 7, the sensor is provided for each electrode.

[0065] 1... Wearable sensing device, 10... Substrate, 11, 11a, 11b... Electrodes, 12... Sensor terminal, 13... Wiring, 14a, 14b... Velcro fasteners, 120... Voltage application unit, 121, 129... Amplification unit, 122, 130... A / D conversion unit, 123, 131... Memory, 124... MPU, 125... Acceleration sensor, 126... Temperature sensor, 127... Pulse wave sensor, 128... Transmitter, 1240... Impedance calculation unit, 1241... Body composition estimation unit, 1242... Electrode selection unit, 1243... Exercise monitoring unit, 1244... Heat load monitoring unit, 1245... Exercise load monitoring unit.

Claims

1. A wearable sensing device comprising: a base material made of a flexible material configured to be attached to the body of a person being measured; a plurality of electrodes arranged on the surface of the base material that is in contact with the skin of the person being measured; a sensor terminal configured to detect an electric current flowing through the body of the person being measured via the plurality of electrodes and measure the impedance of the person being measured; and a plurality of wires connecting the plurality of electrodes and the sensor terminal.

2. A wearable sensing device according to claim 1, wherein the base material is in the shape of a band that is attached to the body of the person to be measured by wrapping it around the person's body and joining one end to the other end, and the sensor terminal is attached near the joining portion.

3. A wearable sensing device according to claim 1, characterized in that the base material is in the shape of clothing, and the sensor terminal is attached near an opening in the base material through which the person being measured passes.

4. A wearable sensing device according to claim 1, characterized in that the external shape of the sensor terminal is a rectangular parallelepiped, and the sensor terminal is attached such that the longitudinal direction of the sensor terminal is substantially perpendicular to the longitudinal direction of the substrate.

5. A wearable sensing device according to claim 1, characterized in that a first group of the plurality of electrodes is attached to the surface of the substrate that comes into contact with the skin of the person being measured, and a second group of the plurality of electrodes is attached to a location on the surface of the substrate different from the first group.

6. A wearable sensing device according to claim 5, wherein the sensor terminal comprises an electrode selection unit configured to measure the electromyographic potential of the subject for all combinations of the plurality of electrodes of the first group and the plurality of electrodes of the second group, and select a combination of two electrodes that show the maximum electromyographic potential difference as impedance measuring electrodes, and an impedance calculation unit configured to calculate the impedance of the subject from the measurement results of the current obtained by the combination of electrodes selected by the electrode selection unit.

7. A wearable sensing device according to claim 5, further comprising: a sensor attached to the substrate and configured to acquire biological information other than the impedance of the person being measured; and a monitoring unit configured to estimate the state of the person being measured based on the measurement results of the sensor.

8. A wearable sensing device according to claim 7, characterized in that the sensor is provided for each electrode.

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