Biological information measuring device

Abstract

Provided is a biometric information measurement device that can detect a change in the biometric information of a wearer (a movement of a finger, the bending and stretching of an arm or foot, a posture change during sitting, a change in length of the body surface due to respiration, and a change in surface moisture amount). The present invention relates to a biometric information measurement device that is made of a fiber base material including a sensing member, and that is disposed in contact with a prescribed position of a living body, wherein the sensing member has at least two core-sheath structure threads in which high-resistance fibers as a cladding material are disposed around a linear conductor as a core material, two among the at least two core-sheath structure threads are disposed adjacent to each other to make it possible to read a change in resistance and / or a change in capacitance between the linear conductors of the two core-sheath structure threads, and the biometric information or a fluctuation thereof is measured based on said change. The present invention also relates to a garment provided with said device.

Description

[Technical Field]

[0001] The present invention relates to a bioinformation measuring device. More specifically, the present invention relates to a bioinformation measuring device that is made of a fiber substrate including a sensing element having a sheath-core structure yarn in which a linear conductor as a core material is surrounded by a high-resistance fiber as a sheath material, and that is placed in contact with a predetermined position on the human body, wherein the sensing element has at least two sheath-core structure yarns in which a linear conductor as a core material is surrounded by a high-resistance fiber as a sheath material, two of which are placed close to each other, and that can read changes in resistance and / or capacitance between the linear conductors of the two sheath-core structure yarns, and that measures bioinformation by detecting changes in the predetermined position of the living body or changes in the moisture content on the surface of the living body from these changes. [Background technology]

[0002] Smart textile technology has been proposed in the past, in which electrical functional elements are mounted on flexible and stretchable textile substrates. These technologies mount functional elements such as sensors, batteries, heaters, and Peltier elements on flexible textile substrates, and because they enable the creation of extremely thin and flexible products, they are extremely important in the coming IoT (Internet of Things) society.

[0003] As one of the above sensors, piezoelectric textured yarns and piezoelectric sensors, as shown in FIG. 1, have been proposed as fiber components with touch-sensing capabilities. As described in the following Patent Documents 1 to 5, piezoelectric textured yarns (also referred to as piezoelectric yarns or piezoelectric fibers) generally have a structure in which conductive fibers are coated with a piezoelectric material such as polylactic acid or polyvinylidene fluoride, which is then further coated with a conductor such as metal plating. Polylactic acid is a crystalline helical chiral polymer, and its uniaxially stretched film exhibits piezoelectricity. Piezoelectricity is the property of generating electric charge when stress is applied. This generates a negative charge on the inner layer conductive fiber (1) and a positive charge on the outer layer conductive fiber (3), as shown in FIG. 1, for example. The reverse can also occur. In this case, the piezoelectric material must be oriented, which poses a problem of difficulty in increasing productivity in the plating process. Therefore, textured yarns are currently very expensive, costing approximately 1,000 to 5,000 yen per meter. Furthermore, with the structure shown in Figure 1, it is currently difficult to produce long processed yarns of over 10,000 meters, making it extremely difficult to use piezoelectric yarns as warp yarns for woven fabrics or warp knitting. Furthermore, the rigidity of the piezoelectric material, polylactic acid, can cause the texture of the piezoelectric yarn to deteriorate, resulting in a lack of flexibility as a fiber.

[0004] Furthermore, as described in Patent Documents 6 and 7 below, contact-sensing fiber materials are known that sense contact or load by detecting a change in capacitance between two adjacent electrodes when contact or a load is applied. Other known technologies include detecting a change in capacitance when a conductor (such as a human body) approaches a single electrode. However, conventional technologies primarily use insulators such as urethane or silicone between the two electrodes, making it difficult to significantly change the distance between the electrodes, resulting in low output (sensitivity), high costs, and poor texture. Furthermore, as described in Patent Document 8, when a single electrode is used, the change in capacitance is extremely small, requiring the use of an advanced signal processing circuit to detect this small signal. However, currently, only proximity sensors with low contact sensitivity and low sensitivity are available.

[0005] On the other hand, as described in the following Patent Documents 9 and 10, technologies relating to covering yarns with excellent bulkiness and high productivity and high quality covering yarns are known, but there is no description or suggestion of using these covering yarn technologies as sensing fiber members.

[0006] The following Patent Document 11 describes a device for monitoring respiration, which is a clothing-like device that can be worn by a user. The described device is a device for monitoring respiration of a user, and includes a fabric support including a tubular portion formed by knitting a base yarn that is predominantly electrically insulating, the tubular portion being capable of covering the chest of the user, and at least one respiration sensor formed by knitting a detection yarn, the detection yarn forming a plurality of stitches, the detection yarn including at least one inner core made of an electrically insulating material and an outer sheath surrounding the inner core, the outer sheath being made of an electrically conductive material so as to form electrical contacts between the stitches of the detection yarn. and a respiratory sensor, the respiratory sensor forming a conductive band having first and second ends spaced apart, the ends connectable to a device for measuring the electrical resistance of the conductive band, the conductive band being positioned relative to the tubular portion such that when the chest of the user is covered with the fabric support, the conductive band alternatively expands and contracts due to the user's breathing, the expansion and contraction of the conductive band having the effect of changing the electrical contacts between the stitches of the detection yarn in the conductive band and causing a change in the electrical resistance of the conductive band. Patent Document 11 describes that a conventional elastic conductive yarn is obtained by wrapping a non-stretchable conductive yarn around a core made of a non-conductive elastic yarn, i.e., the conductive yarn is wound spirally around the non-conductive elastic yarn, and that when the elastic conductive yarn is stretched, the yarn elongates and adjacent turns of the winding move away from each other, causing a measurable change in electrical resistance that depends on the elongation of the elastic conductive yarn, and that wrapping the conductive yarn with a non-conductive yarn increases the total diameter of the conductive yarn, which increases the manufacturing cost of the clothing and may cause discomfort to a user wearing the clothing.

[0007] The following Patent Document 12 describes a bioinformation measurement garment, a bioinformation measurement system, a bioinformation measurement device, and a device control method that are simple in configuration but enable accurate measurement of a subject's bioinformation. The described resistance sensor detects fluctuations in the resistance of a chest respiratory information sensor and / or an abdominal respiratory information sensor in the shirt portion of the bioinformation measurement shirt. An analysis device CPU calculates the resistance fluctuation period based on the resistance data and outputs a respiration value based on the result. The bioinformation measurement garment is made of a non-conductive material that is stretchable enough to fit closely to the subject's upper body. The bioinformation measurement garment includes a conductive member whose electrical resistance changes when energized by changing its shape in response to changes in the subject's physique due to breathing, and is equipped with a respiratory information measurement sensor unit that can transmit electrical information based on the change in electrical resistance to a respiratory information analysis device. The bioinformation measurement shirt has chest electrodes and four limb electrodes made of a conductive material knitted into the shirt portion. In the embodiments, the chest electrodes and limb electrodes are exemplified by conductive fibers knitted into the back of the shirt (the side that contacts the subject's skin). Patent Document 12 cites an embodiment in which conductive fibers are exemplified by fibers (e.g., Thunderon® by Nippon Sanmo Dyeing Co., Ltd.) to which metal particles (e.g., silver particles, copper particles, or copper sulfide particles) are attached (e.g., by chemical bonding) (e.g., Thunderon® by Nippon Sanmo Dyeing Co., Ltd.). The respiratory information measuring sensor described therein is further characterized in that it is disposed at least around the chest or abdomen of the bioinformation measuring garment, and that the electrical resistance value changes as the cross-sectional area or length of the conductive member changes due to expansion and contraction caused by changes in the subject's physique caused by breathing. These features enable the respiratory information measuring sensor to directly detect physical changes in, for example, the circumference of the thorax or the circumference of the abdomen (waist) caused by breathing, thereby stabilizing the detection sensitivity of respiratory information. The respiratory information measuring sensor unit described herein is characterized in that the surface of the conductive member facing the subject's body surface and the opposite surface thereof are covered with a non-conductive material, thereby reducing the electrical influence on the subject caused by the energized state.

[0008] Patent Document 13 (see below) describes a posture-detecting garment in which at least the front and back body sections are made of stretchable fabric covering the body surface. The garment includes a belt-shaped stretchable member that is integral with the back body section, intersecting the center of the back and symmetrically positioned, converting changes in the stretch state of the body fabric into changes in capacitance. The garment is configured to detect the wearer's hunched posture based on the changes in capacitance detected by the stretchable member. The stretchable member is composed of at least two horizontally spaced apart stretchable members on the back of the back body. The stretchable member is made of a posture-detecting knitted fabric that stretches and contracts in correlation with the stretch state of the body fabric, and is knitted integrally with or attached to the body fabric. The objective of the described invention is to provide a posture-detecting garment that can be worn daily and that can objectively detect and evaluate the degree of posture deviation of the wearer. "Conductive yarn" refers to a bare material with metal components exposed on the yarn surface. Furthermore, "elastic thread" refers to a material that maintains a contracted state when no tensile force is applied (unstretched = normal state), freely expands in response to the tensile force, and returns (contracts) from the expanded state to its original contracted state when the tensile force is released and the material returns to its unstretched state. A suitable conductive thread is a metal-coated wire (plated wire) made of a resin fiber, natural fiber, or metal wire core coated with a metal component by wet or dry coating, plating, vacuum deposition, or other suitable deposition method. Each loop of the conductive thread is deformed into a contracted shape in the course direction and maintains this deformed shape. Because the conductive thread is a bare conductive material, the greater the number of contact points made by the loops and the greater the contact area when compressed in the course direction, the greater the number of conductive contact points (i.e., the greater the conductive area), the shorter the current path, and the lower the electrical resistance between two points separated in the course direction.

[0009] Patent Document 14 listed below describes a wearing device for detecting human body motion, which is worn on a part of the human body to detect the motion of the wearing person, and is equipped with a motion detection sensor unit that includes conductive yarn and whose electrical properties change when stretched and when not stretched, and a warning information generation unit that generates information related to a warning based on detection information from the motion detection sensor unit, the motion detection sensor unit includes a conductive stretch knitted fabric whose electrical properties change when stretched and when not stretched, and a stretchable fabric to which the conductive stretch knitted fabric is attached, the stretch resistance of the fabric being greater than that of the conductive stretch knitted fabric, the fabric is formed in an elongated shape and is configured to be separable along its longitudinal direction into a first base region in which the warning information generation unit is located and a second base region to which the conductive stretch knitted fabric is attached, the first base region and the second base region being configured to be freely attached and detached by a connecting means. The described invention aims to provide a human body movement detection garment that can accurately detect human body movement in parts of the body that include bendable parts such as joints and the back, or body movement information including respiratory information such as the presence or absence of breathing and respiratory cycles, with a simple configuration. The above-mentioned conductive stretch knitted fabric is a knitted fabric that is highly stretchable and flexible and has recovery properties when repeatedly stretched, yet has the property of changing electrical resistance between stretched and non-stretched, and can also achieve breathability, moisture permeability, water absorbency, etc., making it suitable for use as a wearable material. Furthermore, the above-mentioned conductive stretch knitted fabric uses a conductive stretch yarn that has a simple structure but changes electrical resistance depending on the stretch rate.

[0010] Patent Document 15 below describes a human body motion detection garment that employs a conductive harness using a knitted fabric. The described work glove, an example of such human body motion detection garment, is worn by a person to detect the movement of the human fingers. The garment includes a gyro sensor module attached to the back of the glove, corresponding to a first part of the human body, for detecting a first physical quantity (angular velocity, angular acceleration) of the first part; an acceleration sensor module attached to the thumb and index finger of the glove, corresponding to a second part connected to the first part via a joint, for detecting a second physical quantity (velocity, acceleration) of the second part; and a conductive harness through which signals output from these sensors flow electrically. The conductive harness is attached to the work glove, which is a garment. The described invention aims to provide a human body motion detection garment, as an example, that preferably employs a conductive harness using a conductive stretch knitted fabric that is highly stretchable and flexible, has good recovery properties after repeated stretching, and exhibits little or no change in electrical resistance even after repeated stretching.

[0011] The following Patent Document 16 describes a fabric with a strain sensor that is unlikely to interfere with the wearer's movements and is unlikely to break due to the wearer's movements. The described fabric with a strain sensor includes a stretchable fabric body and a strain sensor attached to the fabric body that can follow the stretching of the fabric body. The fabric also includes a wiring portion that is electrically connected to the strain sensor, is integrally formed with the fabric body, and deforms in response to the stretching of the fabric body. The wiring portion may be formed by sewing a conductive filament to the fabric body. Alternatively, the wiring portion may be formed by knitting or weaving a conductive filament together with a non-conductive filament when the fabric body is knitted or woven. The placement portion may be formed from a belt-shaped member attached to one surface of the fabric body. The object of the described invention is to provide a fabric with a strain sensor in which the wiring is less likely to interfere with movements such as stretching the fabric body and is less likely to break, and to provide clothing that is less likely to interfere with the wearer's movements and is less likely to break due to the wearer's movements. The fabric with the strain sensor can have a wiring portion formed by sewing a conductive filament to the fabric body, which allows the wiring portion to be easily and reliably formed by sewing the filament.

[0012] Patent Document 17 listed below describes a motion measuring device that is attached to a sheet material worn on the human body and measures the motion of the wearer, with the aim of accurately detecting the posture and motion of the wearer, such as hunched back, while eliminating the effects of breathing volume (depth) or periodic fluctuations. The device has a conductive elastic material made up of multiple linear bodies that are aligned with the deformation direction of the sheet material, the linear bodies are incorporated into the sheet material so that they are parallel to each other, and the electrical resistance of each linear body changes with deformation in the surface direction of the sheet material. The device has a calculation means that calculates the difference in electrical resistance values ​​from the linear bodies, and a measurement means that measures the motion of the wearer from the calculation results of this calculation means. In the case of clothing using the conductive stretchable material, when the wearer breathes, the resistance value fluctuates depending on the breathing volume (depth), and the period fluctuates significantly depending on the breathing rate. Therefore, even if the resistance value of the conductive stretchable material is averaged, a certain sampling time must be ensured for averaging, making it difficult to perform real-time measurements. Furthermore, when periodic fluctuations are added to the breathing volume, the clothing cannot detect the correct resistance value, making it difficult to detect the degree of posture at each stage. The described invention was made in consideration of the above-mentioned circumstances and provides a motion measurement device, method, and program that can accurately detect the wearer's posture, such as hunched back, by using a simple configuration and eliminating the effects of breathing volume (depth) or periodic fluctuations. This motion measurement device includes a conductive stretchable material having multiple linear members whose electrical resistance changes with deformation of the linear members, a calculation means for calculating the difference in electrical resistance values ​​from the linear members of the conductive stretchable material, and a measurement means for measuring the wearer's motion based on the calculation results of the calculation means. The linear members of the conductive stretchable material are incorporated into the garment so that they are parallel to each other and aligned along the deformation direction of the sheet material, and their electrical resistance changes with deformation in the planar direction of the sheet material. By varying the lengths of the linear members of the conductive stretchable material to vary the electrical resistance of each linear member in its initial state (i.e., a state in which it is not deformed by an external force), different levels of electrical resistance can be detected. By calculating the difference in electrical resistance values ​​from the pair of linear members of the conductive stretchable material, the motion measurement device can accurately detect the wearer's posture, such as hunched back, while eliminating the effects of breathing volume (depth) or periodic fluctuations.

[0013] The following Patent Document 18 describes a sensor system comprising: a plurality of sensors formed of a polymer material in which a conductive particle material is dispersed at a first dispersion density; a port configured to communicate with an electronic module; and a plurality of conductive lead wires formed of the polymer material in which the conductive particle material is dispersed at a second dispersion density, the lead wires being connected between the sensors and the port, wherein each of the sensors is configured to increase in resistance when deformed under pressure, and the second dispersion density is higher than the first dispersion density, such that each of the lead wires has sufficient conductivity to transmit electronic signals between each sensor and the port in any deformation state of the lead wire. The described invention generally relates to an article of clothing having a sensor system. Aspects of the described invention relate to a sensor system including one or more sensors formed from a polymeric material having a conductive particle material dispersed therein and a conductive lead wire connected to the sensor. The lead wire may also be formed from a polymeric material having a conductive particle material dispersed therein. The sensor and lead wire may have the same or different polymeric material and / or conductive particle material. According to another aspect, the data communicated to the external device can be used in one or more different applications. Such applications may include, among other uses, using the data as control input for a program executed by the external device, such as a game program, or for athletic performance monitoring. Athletic performance monitoring may include monitoring one or more performance metrics, such as speed, distance, lateral movement, acceleration, jump height, weight transfer, ground contact pattern, balance, foot pronation or supination, lift time measurement while running, lateral cutting force, ground contact time, center of pressure, throwing arm speed / force, kicking foot speed / force, weight distribution, and / or impact force, among others. The described sensors have conductivity (and resistivity) that changes based on deformation and applied force and can be thought of as force-sensitive resistive materials. The way this happens is that deformation of the matrix material increases or decreases the distance between particles of the conductive material, which changes the resistance or conductivity of the material.

[0014] Patent Document 19 describes an apparatus (e.g., garments including, but not limited to, shirts, pants, etc.) for detecting and monitoring physiological parameters such as respiratory, cardiac, etc. The described apparatus is a physiological parameter monitoring garment having sensors formed of printed conductive ink on a compression garment arranged and configured for robust sensing and comfortable wear. In particular, the described garment (e.g., shirt, pants, underwear) is configured to enable robust sensing of one or more physiological parameters using conductive ink sensors printed directly on the garment and connected to an interface region of the garment by conductive traces (which may or may not be reinforced on the garment), which may connect to an analysis unit, such as a microprocessor, configured to measure, store, process, and / or transmit one or more recorded parameters. The conductive inks described are not only conductive but also stretchable, and therefore can function properly on compression garments. Typically, these respiratory sensors include fabric and / or conductive ink-based strain gauges. For example, the strain gauges can be formed from the described stretchable conductive inks and / or conductive elastic strips.

[0015] The following Patent Document 20 describes sensing wear that can simultaneously and sequentially detect body displacements, i.e., limb movements, body shape, posture, breathing, chewing, swallowing, pulse, fetal movements, and body electrical potentials, i.e., electrocardiograms and electromyograms, in a substantially non-invasive manner. A bioinformation measuring device is obtained that has a capacitor-type element having a structure in which at least a first stretchable conductor layer 2, a stretchable dielectric layer 3, and a second stretchable conductor layer 4 are stacked in this order, and a skin-contact electrode in which at least the skin contact surface is the stretchable conductor layer, and by integrating the measuring units for biodisplacement and biopotential, it is possible to simultaneously measure biodisplacement and biopotential even in a limited area without any discomfort. By integrating an elastic capacitor that can be detected as a change in capacitance with a skin-contact type that comes into contact with the skin of a living body, we have invented a biometric information measuring device that reduces the area required to mount the sensor and makes it possible to measure multiple biometric information simultaneously or sequentially while alleviating discomfort to the wearer. The bio-information measuring device used in the described invention has a high elongation rate in the planar direction, and therefore can be suitably used to measure deformation strain in the planar direction. There is no need to use gel, paste, adhesive tape, etc. between the skin contact electrode and the skin surface, and it is possible to measure bio-displacement and bio-potential even during walking or exercise. The stretchable conductor layer of the stretchable capacitor used in the described invention can be obtained by kneading and mixing conductive particles and a flexible resin and molding the mixture into a film or sheet.

[0016] The following Patent Document 21 describes a vest equipped with a motion sensor, characterized in that it has an outside air side fabric and a skin side fabric, and the sensor is arranged between the outside air side fabric and the skin side fabric. A motion sensor disposed in the pocket is fixed in the pocket by a hook-and-loop fastener.

[0017] The following Patent Document 22 describes a respiratory sensor and sensing wear that uses a stretchable capacitor that has a 1:1 correspondence between stretchability and capacitance, is highly sensitive, and has no hysteresis. The described capacitor has a layer structure consisting of at least a stretchable conductor layer, a stretchable dielectric layer, and a stretchable conductor layer stacked in this order. The stretchable conductor layer is a composition containing metal particles, and has a resistivity of 3 x 10-3 Ωcm or less when unstretched and a resistivity at 100% stretch that is within 100 times that of the unstretched state. The stretchable capacitor is obtained using a stretchable conductor layer with a low inorganic content, preferably a stretchable dielectric layer with a Poisson's ratio of 0.28 or greater. The resulting stretchable capacitor can be attached to a belt, shirt, etc., and breathing can be sensed by changes in the vest. Furthermore, by placing it on a joint in clothing, it is possible to read the wearer's motion.

[0018] The following Patent Document 23 describes a device capable of evaluating joint mobility. The flexible transducer is a conductive elastomer that provides a change in electrical output signal when stretched. The conductive material is a homogeneous mixture of a non-conductive elastomer and conductive particles dispersed therein.

[0019] Patent Document 24 listed below describes an apparatus for monitoring physiological parameters of the human body. The monitoring device includes a smart garment, a processing unit, and a docketing station, which allows for quick and easy docking / undocking of the processor. The docketing station is connected to multiple knitting sensors.

[0020] As described above, conventional sensing elements have been disclosed that are made of conductive materials such as conductive fibers or conductive inks and whose resistance changes when an external force is applied. However, these sensor resistances are low, ranging from a few ohms to a few hundred ohms, and therefore are susceptible to the effects of contact resistance, resulting in high power consumption in the readout circuit. Furthermore, there are issues with low reproducibility of output changes in response to external forces such as tension or load, making it difficult to obtain a stable output. When stretchable wiring is used as the conductive material constituting the sensing member to detect changes in electrical resistance in response to its expansion and contraction, the sensor response performance is determined by the physical properties of the rubber elastomer and the specifications of the conductive particles mixed in, and there are issues such as poor linearity and hysteresis, making it difficult to accurately detect external forces, and poor responsiveness and repeatability when returning to the original state. Furthermore, when a stretchable capacitor is used as the sensing member, there are issues such as poor linearity of the output relative to its expansion and contraction, poor response performance and repeatability, and insufficient weather resistance, making it unsuitable for long-term use. Furthermore, when using piezoelectric materials as contact sensing components, it is difficult to increase productivity due to the need to orient the piezoelectric material and the need for a plating process to form electrodes. This makes it difficult to currently produce long processed yarns of over 10,000 meters. The cost is also very high, at approximately 1,000 to 5,000 yen per meter of processed yarn. Furthermore, the rigidity of the piezoelectric materials, such as polylactic acid and fluororesin, can lead to poor texture, making it difficult to embed in knitted or woven fabrics, and lacking the flexibility of a fiber. [Prior art documents] [Patent documents]

[0021] [Patent Document 1] Patent No. 6025854 [Patent Document 2] Patent No. 6689943 [Patent Document 3] Japanese Patent Application Publication No. 2020-090768 [Patent Document 4] Japanese Patent Publication No. 2020-036027 [Patent Document 5] Patent No. 6107069 [Patent Document 6] Patent No. 5754946 [Patent Document 7] Japanese Patent Application Laid-Open No. 2006-234716 [Patent Document 8] Japanese Patent Application Laid-Open No. 2016-173685 [Patent Document 9] Japanese Patent Application Publication No. 10-25635 [Patent Document 10] Japanese Patent Application Laid-Open No. 2013-231246

[0022] [Patent Document 11] Special Publication No. 2018-507081 [Patent Document 12] Japanese Patent Application Laid-Open No. 2011-98214 [Patent Document 13] Patent No. 6960725 [Patent Document 14] Patent No. 698667 [Patent Document 15] Japanese Patent Application Publication No. 2018-21270 [Patent Document 16] Japanese Patent Application Laid-Open No. 2014-25180 [Patent Document 17] Japanese Patent Application Laid-Open No. 2017-123911 [Patent Document 18] Special Publication No. 2016-509635 [Patent Document 19] Special Publication No. 2017-512542 [Patent Document 20] Patent Publication No. 2019-72048 [Patent Document 21] Japanese Patent Publication No. 2022-55855 [Patent Document 22] International Publication No. 2018 / 056062 [Patent Document 23] U.S. Patent No. 4,444,205 [Patent Document 24] U.S. Patent Application Publication No. 2016 / 0113581 Summary of the Invention [Problem to be solved by the invention]

[0023] In view of the above-mentioned state of the art, the problem that the present invention aims to solve is to provide a device for measuring biological information, which is made of a fiber substrate including a sensing member that can be processed into long lengths, is easy to mass-produce, can be used as a warp thread for woven fabrics or warp knitting, is flexible and has an excellent texture, is significantly lower in cost than conventional contact-sensing fiber members (piezoelectric yarns) that use piezoelectric materials, and has a lower specific load elongation than conventional sensing members, and therefore has good linearity, almost no hysteresis, a fast response when returning to its original state, and good repeatability characteristics, and which is placed in contact with a predetermined position on a living body. [Means for solving the problem]

[0024] In order to solve the above problems, the present inventors have conducted extensive research and experiments, and as a result have unexpectedly found that the above problems can be solved by using the following structure, which has led to the completion of the present invention.

[0025] That is, the present invention is as follows. [1] A bioinformation measuring device made of a fiber substrate including a sensing member and placed in contact with a predetermined position on a living body, the sensing member having at least two sheath-core structure yarns in which a high-resistance fiber is arranged as a covering material around a linear conductor as a core material, two of which are arranged close to each other, and capable of reading changes in resistance and / or capacitance between the linear conductors of the two sheath-core structure yarns, and measuring the bioinformation and its fluctuations based on these changes. [2] The bioinformation measuring device described in [1], wherein the sensing member is a ply-twisted yarn in which two of the core-sheath yarns are further twisted together. [3] A bioinformation measuring device as described in [1] or [2], wherein the high-resistance fiber arranged in the sensing member is made of fiber having a carbon-based conductive material on at least a portion of its surface, and is capable of reading changes in resistance between the linear conductors. [4] The biological information measuring device according to any one of [1] to [3], wherein the sensing member has a specific load elongation of 5% or less. [5] The biological information measuring device according to any one of [1] to [4], wherein the biological information is a change in posture of the living body. [6] The biological information measuring device according to any one of [1] to [4], wherein the biological information is obtained by respiration. [7] The biological information measuring device according to any one of [1] to [4], wherein the biological information is a change in moisture content on the surface of the living body. [8] The sensor output change in response to a change in moisture content in the portion where the sensing member measures biological information is 1 / 20 or less of the sensor output change in biological information measurement, as described in [3]. The biological information measuring device described in [9] A bioinformation measuring device described in any one of [1] to [8], wherein at least one of the core-sheath structure yarns is a core-sheath structure yarn in which a high-resistance fiber as a covering material is wrapped in one direction around a linear conductor as a core material to form a covering.

[10] A bioinformation measuring device described in any one of [1] to [8], wherein at least one of the core-sheath structure yarns is a core-spun yarn in which a linear conductor as a core material is wrapped around a high-resistance short fiber as a covering material in a random direction to form a covering.

[11] The bioinformation measuring device described in [1], wherein two or more of the core-sheath structure yarns are arranged in partial contact within the fiber substrate.

[12] Clothing equipped with the biological information measuring device according to any one of [1] to

[11] .

[13] Clothing equipped with the biometric measuring device described in

[11] . [Effects of the Invention]

[0026] The sensing member used in the bioinformation measuring device according to the present invention can be processed in long lengths, is highly mass-producible, can be used as warp yarn for woven fabrics or warp knitting, is flexible and has a good texture, and is significantly less expensive than conventional contact-sensing fiber members (piezoelectric yarns) that use piezoelectric materials. That is, since the sensing member can sense load or tensile force using common fiber materials such as polyester or nylon, sensing fibers can be realized at very low cost. Furthermore, since covering technology, a fiber processing technology with established know-how, including core-spun yarns, is used, long lengths can be processed, is highly mass-producible, and, since textured yarns with a much better texture than piezoelectric yarns can be realized, processing into fiber members such as woven fabrics and knitting fabrics is easy. The sensing member used in the biological information measuring device according to the present invention changes in capacitance and / or resistance, and can detect the state in which a load or tensile force is continuously applied. Furthermore, in the sensing member used in the bioinformation measuring device according to the present invention, when the core-sheath structure yarn (generally also called a covering yarn) in which a linear conductor as the core material is wrapped around a high-resistance short fiber as a covering material in a random direction to form a covering is a core spun yarn, it is easy to use natural fibers or biodegradable yarns, and it is easy to impart functionality to the sheath yarn.

[0027] Furthermore, sensing members of the prior art mainly utilize sensor outputs such as electrical resistance and capacitance in response to the elongation of the stretchable wiring, which are determined by the physical properties of the rubber elastic body, and therefore have poor linearity, hysteresis, and a slow response when returning to their original state, and therefore cannot be said to have good repeatability.In contrast, the sensing member used in the bioinformation measuring device of the present invention has a lower specific load elongation than conventional sensing members, and therefore has good linearity, almost no hysteresis, and a fast response when returning to their original state, resulting in good repeatability.

[0028] Therefore, the bioinformation measuring device according to the present invention can detect slight body surface displacements and movements, such as slight stretching, body pressure such as foot pressure and finger pressure, or fluctuations in moisture content using clothing (e.g., T-shirts, underwear, vests, belts) containing a sensing fiber member (yarn) having a ply-twisted yarn in which two sheath-core yarns are further twisted together. This makes it possible to detect, for example, breathing, changes in posture, movements of the wrists, ankles, fingers, etc., muscle movements (pelvic floor muscles, brachioradialis muscles, calves, etc.), pressure from compression garments and socks, pressure on the soles of the feet and foot pressure distribution, swallowing, analysis of walking and running movements (for rehabilitation, disease prevention, etc.), and fluctuations in moisture content due to sweating, excretion, etc. In particular, the bioinformation measuring device according to the present invention can simultaneously detect the presence or absence of breathing and good or bad posture, and simultaneously detect the degree of hand opening (clenched fist or open hand) and wrist bending, among other signals. [Brief explanation of the drawings]

[0029] [Figure 1] FIG. 1 is a schematic diagram of a conventional piezoelectric textured yarn. [Figure 2] FIG. 2 is a schematic diagram of one embodiment of a sensing member. [Figure 3] 1 shows the appearance and enlarged photograph of a sensing element made of a plied yarn. [Figure 4] 1 is a photograph of a narrow woven fabric into which a sensing element made of ply-twisted yarn is woven. [Figure 5] This is a photograph of a sensing element in the form of a plain weave fabric, using core-sheath structure yarns as warp and weft threads, in which a linear conductor as a core material is wrapped in one direction as a covering material with high-resistance fiber. [Figure 6] This is a schematic diagram of an apparatus system for measuring the resistance change between two core-sheath structure yarns, which are made by wrapping a linear conductor as a core material around a high-resistance fiber as a covering material in one direction. [Figure 7] 10 is a graph showing an example of an output current value (sensor output) when a load or the like is applied to a sensing member of the present embodiment that is a plied yarn. [Figure 8]10 is a graph showing the relationship between the applied load and the rate of change in current value (sensor output) in the sensing member of the present embodiment, which is a plied yarn. [Figure 9] 1 is a graph showing an example of the output current value (sensor output) when a load or tensile force is applied to a sensing element in the form of a plain weave fabric (narrow fabric) using core-sheath structure yarns as warp and weft threads, in which a linear conductor as a core material is wrapped in one direction with a high-resistance fiber as a covering material to form a covering. [Figure 10] FIG. 1 is a schematic diagram of a manufacturing device for a core-sheath structure yarn. [Figure 11] FIG. 2 is a schematic diagram of a sheath-core structure yarn obtained by the above manufacturing apparatus. [Figure 12] FIG. 1 is an explanatory diagram of the principle of measuring the electrical properties between a pair of core-sheath structure yarns.

[0030] [Figure 13] FIG. 1 is a schematic diagram of a conventional piezoelectric textured yarn. [Figure 14] 1 shows the appearance and enlarged photograph of a sensing element made of a plied yarn using short fibers. [Figure 15] 10 is a graph showing an example of an output current value (sensor output) in a sensing member that is a plied yarn using short fibers.

[0031] [Figure 16] FIG. 1 is an explanatory diagram of a first embodiment. [Figure 17] 10 is a graph showing the sensing results of Example 1. [Figure 18] FIG. 10 is an explanatory diagram of a second embodiment. [Figure 19] 10 is a graph showing the sensing results of Example 2. [Figure 20] FIG. 10 is an explanatory diagram of a third embodiment. [Figure 21] 10 is a graph showing the sensing results of Example 3. [Figure 22] FIG. 10 is an explanatory diagram of a fourth embodiment. [Figure 23] 10 is a graph showing the sensing results of Example 4. [Figure 24]FIG. 10 is an explanatory diagram showing a state in which a sensing yarn is knitted into the center of the wristband of Example 4 using smooth knitting. DETAILED DESCRIPTION OF THE INVENTION

[0032] Hereinafter, embodiments of the present invention will be described in detail. One embodiment of the present invention is a bioinformation measuring device that consists of a fiber substrate including a sensing member and is placed in contact with a predetermined position on a living body. The sensing member has at least two sheath-core structure yarns in which a high-resistance fiber is arranged as a covering material around a linear conductor as a core material, and two of the yarns are arranged close to each other so that changes in resistance and / or changes in capacitance between the linear conductors of the two sheath-core structure yarns can be read, and the bioinformation measuring device measures the bioinformation and its fluctuations based on these changes. In this document, the term "biological information" refers to changes in position due to movement, posture, breathing, etc., of a living body such as a human or animal, body pressure, changes in water content on the surface of the living body, etc. The bioinformation measuring device according to the present invention makes it possible to measure such biological information with a simple method and high accuracy. The biological information measuring device of this embodiment can be appropriately configured depending on the type of biological information to be measured. For example, when measuring respiration, the body movement caused by breathing is due to the movement of the lungs, so the fiber substrate is attached to the living body so that the sensing member is located in at least one of the chest area near the diaphragm, which is the fourth or fifth rib from the bottom, the abdomen, the neck, and the chest area above the lungs. For example, when measuring the posture of a living body, it is preferable to detect the horizontal length of the back of the body, particularly between the shoulder blades, in order to detect a so-called hunched posture, so a fiber substrate with a sensing member mounted horizontally on the back is desirable. For example, when detecting the movement of the hand, such as clenching or unclenching, which involves a lot of movement of the forearm muscles, a fiber substrate with a sensing member located in the brachioradialis or wrist area is used. For measuring finger movement, a fiber substrate with a sensing member arranged parallel to the longitudinal direction of the finger is also suitable. The fiber substrate may be in the form of a woven or knitted fabric, and the structure of the fiber substrate is not limited. Alternatively, nonwoven fabric or paper may be used. Furthermore, the shape of the fiber substrate may be selected from various types of wear, such as underwear, T-shirts, work clothes, and vests, as well as wristbands, supporters, gloves, finger cots, and belts, depending on the object to be measured. In particular, when measuring whole-body movements such as breathing and posture, a comfortable fit, such as a shirt or tank top, is preferred because it allows for easy combination of comfortable wear and accurate measurement.

[0033] The number of sensing elements may be one at the location where the body movement to be measured is greatest, or one or more at multiple locations. For example, in the case of respiration measurement, measuring movement at multiple locations, such as the chest, abdomen, and neck, is preferable because it not only measures the respiratory rate but also provides information on the quality of breathing, such as whether breathing is abdominal or thoracic, whether breathing is shallow, and whether breathing is using the whole body. For example, when deep breathing with large diaphragm movement is taking place, large output fluctuations are obtained from both the diaphragm and the sensing elements located in the abdomen, while shallow breathing can be determined by the relatively small amount of change in the abdomen. It is also possible to mount two or more sensing elements at the target measurement location. For example, for the purpose of measuring respiration, inserting two or more sensing elements near the diaphragm and calculating the sum or difference of their outputs enables more accurate, reliable measurements without missing any measurements. Taking the sum of the outputs of multiple sensing elements attached to nearby locations has the advantage of easily obtaining a larger output and significantly reducing missed measurements. Taking the difference between these outputs also has the advantage of eliminating the effects of output fluctuations not caused by respiration, such as noise and the effects of vibrations generated around the living body, enabling more accurate measurements. The output of the sensing element is read using a readout circuit electrically connected to the sensing element. The readout circuit may include, for example, a current-voltage conversion circuit, an analog-to-digital conversion circuit, a filter circuit, an amplifier, and an interface unit. If necessary, a communication unit may be further provided, allowing the output of the sensing element to be read by an external device via wireless communication. In the case of wired communication, direct electrical connection to an external signal device via an interface unit is sufficient. While either wireless or wired communication may be used to output the sensing element, wireless communication, such as Bluetooth (registered trademark), BLE (Bluetooth (registered trademark) Low Energy), Zigbee, WiFi, NFC, or LPWA, is preferred because it allows measurement of biological information while the living body is free to move around. Wired communication is preferred because it facilitates accurate measurement with greater precision and fewer missed communications. The output from multiple sensing elements may be calculated on the readout circuit or in an external device after the output is communicated.

[0034] One embodiment of the sensing element used in the bioinformation measuring device of this embodiment is a sensing element having at least two sheath-core structure yarns in which a linear conductor as a core material is wrapped in one direction with a high-resistance fiber as a covering material to cover it, two of which are arranged close to each other, and characterized in that the sensing element reads changes in resistance and / or changes in capacitance (i.e., changes in impedance) between the linear conductors of the two sheath-core structure yarns arranged close to each other.

[0035] Another embodiment of the sensing element is a sensing element having at least two sheath-core yarns in which a high-resistance fiber is arranged as a covering material around a linear conductor as a core material, two of which are arranged close to each other, and at least one of the sheath-core yarns is a core spun yarn in which a high-resistance short fiber is wrapped around the linear conductor as a core material in a random direction to cover it, and the sensing element is characterized in that it reads changes in resistance and / or changes in capacitance between the linear conductors of the two sheath-core yarns arranged close to each other.

[0036] The linear conductor (core yarn) serving as the core material is not particularly limited as long as it is conductive. It may be a linear conductor made of conductive fibers, such as carbon fibers or metal fibers, which are themselves conductive, or a linear conductor made by imparting conductivity to non-conductive fibers. As the former, carbon fibers are preferred because of their high durability in moisture sensing, as described below. Stainless steel fibers are also preferred because they ensure rust resistance and allow for easy termination for connection to circuits, etc. As the latter, nylon fibers or other fibers plated with a metal such as silver or copper, metal foil processed into a tape and wound around the fibers, or fibers sprayed with an aerosol-like conductor are preferred from the perspective of improving texture and flexibility. In this case, multifilament conductive fibers are preferred because of their excellent conductivity and increased strength. Using high-strength fibers such as polyarylate or aramid instead of nylon can further increase tensile strength. Alternatively, a linear conductor may be used in which a stretchable metal ink is applied around an elastic body such as urethane or silicone to impart conductivity. In this case, a stretchable fiber member can be obtained. The linear conductor may also be a linear mixture of a conductive material and an insulating material. For example, if a material obtained by processing a material obtained by mixing a carbon-based conductive material or a metal with a resin such as nylon or polyester into a linear shape is used, a linear conductor can be obtained at significantly lower cost, although the conductivity will be inferior. Alternatively, the linear conductor may be one or more metal wires, from the perspective of cost reduction, although the texture will be worse. For example, using a metal wire with a diameter of approximately 30 μm to 1 mm can significantly increase strength.

[0037] The fineness of the linear conductor, for example, the conductive fiber, is preferably 10 dtex to 15,000 dtex, more preferably 20 dtex to 5,000 dtex, from the viewpoint of easily obtaining a good texture and easily obtaining high conductivity. Furthermore, in the case of a multifilament, the single yarn fineness is preferably 1 dtex to 30 dtex, more preferably 2 dtex to 10 dtex, from the viewpoint of easily obtaining a good texture and easily obtaining high conductivity. The number of filaments is more preferably 10 to 200. Having 10 or more filaments is preferable because it is easy to obtain a good texture and to ensure good conductivity. However, if the number of filaments is too high, costs will increase and rigidity will also increase, which may conversely result in a deterioration in texture. Taking all of these factors into consideration, it is preferable to keep the number of filaments within the above range.

[0038] The conductive material forming the linear conductors may be the same for the two core-sheath structured yarns in a pair, or different materials may be used, and any combination of materials can be used. For contact, load, or tension sensing applications, using the same conductive material is preferable because it allows for efficient production. When sensing liquids such as moisture, if different materials are used as the linear conductors of the two core-sheath structured yarns in a pair, a voltage or current is generated by an electrochemical reaction known as a galvanic action when a liquid adheres to the bridging material, making it possible to sense the liquid without a power source. Any combination of different materials can be used, such as iron and copper, iron and silver, aluminum and copper, or silver and copper.

[0039] In this specification, the term "high-resistance fiber" as a covering material (also referred to as a cover yarn or sheath yarn) is not particularly limited as long as it can form a high resistor or capacitance between the two fibers, in addition to fibers that can electrically insulate the two linear conductors serving as the core material. It encompasses insulating fibers that are substantially insulating, piezoelectric materials such as polylactic acid (PLA), and ferroelectric materials such as polyvinylidene fluoride (PVDF). However, in order to cover the linear conductors serving as the core material without gaps when left stationary and to make electrical short circuits less likely to occur, the covering material (cover yarn) preferably includes either a multifilament high-resistance fiber or a high-resistance spun yarn (short fiber) that can achieve a uniform covering thickness without unevenness, from the viewpoints of coverage, sensing performance, and texture, and is most preferably made of a multifilament high-resistance fiber or a high-resistance spun yarn. The material for the high-resistivity fiber is not particularly limited as long as it can maintain a certain level of insulation when not subjected to sensing actions such as contact, tension, or liquid contact (idling state). However, from the standpoints of cost and availability, synthetic fibers such as polyester (PE), nylon (Ny, polyamide), epoxy, and acrylic are preferred. Natural fibers such as cellulose fibers, semi-synthetic fibers, and recycled fibers such as cupra are also acceptable. Furthermore, piezoelectric materials such as polylactic acid (PLA) and polyvinylidene fluoride (PVDF), ferroelectric materials, and biodegradable resins can be used as high-resistivity fiber materials. Piezoelectric materials can maintain insulation when idle and also obtain an output signal corresponding to their piezoelectric properties when stress is applied, thereby increasing sensor sensitivity. However, from the standpoints of cost and the texture of woven and knitted fabrics, it is preferable to use fibers used for clothing, such as polyester, nylon, and acrylic.

[0040] Furthermore, when sensing is performed based on changes in resistance, a material in which insulating fibers are slightly imparted with conductivity may be used as the cover yarn (sheath yarn) of the high-resistance fiber. In this case, the range of conductivity of the sheath yarn may be within a range in which changes in resistance between the linear conductors of two sheath-core structure yarns arranged close to each other can be read. Specifically, the resistance (sensor resistance) between the linear conductors of the sheath-core structure yarns arranged close to each other should be within the range of 0.5 kΩ to 5 GΩ, and the sensor resistance value should be 20 times to 1×10 times the resistance (wiring resistance) of the linear conductors alone. 9 It is preferable that the resistance value of the sensor is 0.5 kΩ to 100 MΩ, which simplifies the readout circuit. The electrical resistivity of the sheath yarn material should be within the range of 10 kΩ to 100 MΩ. As a result, when a voltage is applied between two linear conductors that constitute two adjacent core-sheath structure yarns, an electrical short circuit does not occur, and the sensor resistance value is sufficiently large compared to the wiring resistance value, so that the load, tensile force, etc. can be detected correctly without being affected by the wiring resistance. It is even more preferable that the sensor resistance value is within the range of 0.5 kΩ to 100 MΩ, which simplifies the readout circuit. The range of the electrical resistivity of the sheath yarn material is 10 4 Ω·m~5×10 9 Ω·m is preferable in that the above-mentioned range of sensor resistance can be easily satisfied. As a material for the sheath yarn to which slight conductivity has been imparted, a material obtained by adding a conductivity-imparting material, such as a carbon-based conductive material, metal particles, a metal sulfide such as copper sulfide, or a metal oxide such as tin oxide or zinc oxide, to an insulating material such as polyester, nylon, or acrylic can be used. Alternatively, the sheath yarn may be a mixture of both insulating and conductive fibers. For example, carbon-based fibers with carbon on at least a portion of their surface, such as CLACARBO (manufactured by Kuraray Co., Ltd., registered trademark) and BELLTRON (manufactured by KB SEIREN Co., Ltd., registered trademark), which are sold as antistatic fibers, or fibers plated with a metal compound, such as THUNDERON (manufactured by Nippon Sanmo Dyeing Co., Ltd., registered trademark), can be selected and used to achieve the desired sensor resistance value. Furthermore, by using core spun yarn (CSY) described below, natural fibers and biodegradable fibers that are difficult to use as long fibers can be easily used, and the characteristics of each fiber can be expressed.

[0041] The sensing member preferably uses a combination of fibers that dry quickly as the covering material (cover yarn). In particular, when sensing moisture, ethanol, etc., using a quick-drying fiber for the cover yarn allows the yarn to dry quickly after contact with moisture, etc., and return to its original state more quickly. While synthetic fibers with low moisture content can be used as quick-drying fibers, a combination of synthetic and cellulose fibers is particularly preferred to achieve both water absorption and quick-drying properties. In this case, synthetic fibers such as polyester, nylon, and acrylic are preferred, and cellulose fibers such as natural cellulose fibers like cotton and hemp, regenerated cellulose fibers like rayon, polynosic, lyocell, cupra, and modal, and semi-synthetic fibers like acetate are preferred, with multifilament long fibers being particularly preferred. The combination of these two fibers can also be used in the cover yarn, or in the double covering described below, where both synthetic and cellulose fibers are used separately.

[0042] The fineness of the multifilament high-resistance fiber used as the covering material (cover yarn) is preferably 15 dtex to 25,000 dtex, more preferably 30 dtex to 8,000 dtex, from the viewpoint of easily preventing an electrical short circuit between two linear conductors, and the single yarn fineness of the multifilament high-resistance fiber is preferably 1 dtex to 10 dtex, more preferably 2 dtex to 8 dtex, from the viewpoint of more easily obtaining a good texture.

[0043] The fineness of the high resistance spun yarn used as the covering material (cover yarn) is preferably 60 cotton count to 5 cotton count, more preferably 30 cotton count to 10 cotton count, from the viewpoint of easily ensuring insulation properties.

[0044] The method for manufacturing the core-sheath structure yarn arranged in the sensing member of this embodiment, in which a high-resistance fiber is arranged as a covering material around a linear conductor as a core material, is not particularly limited, but an example thereof is the following method described in Patent Document 9. Figure 10 is a schematic diagram of a covering device equipped with a two-legged flyer (12) and operated with a bobbin wound with cover yarn (covering material) (14). Figure 11 shows an enlarged view of part B in Figure 10. The core yarn (core material) 9 passes through the hollow portion of the hollow spindle 10, passes through an upper snail guide (not shown), and is taken up by a take-up roll (not shown). The cover yarn 14 is passed through one of the leg guides 15 and 16 of the two-legged flyer 12 and is unwound from the bobbin by the rotation of the hollow spindle (bobbin synchronization). The cover yarn 14 is wound around the core yarn 9 and passes through the snail guide before being taken up. The flyer 12 has two legs to balance the flyer 12 when it rotates. The above-mentioned covering devices may be arranged in two vertical rows, and two types of cover yarns (which may be the same or different) may be sequentially covered from two bobbins, thereby performing so-called double covering. In this case, if each cover yarn is covered in the same direction (both types of cover yarns are S-twisted or Z-twisted), the thickness can be made uniform, and gaps between the insulating fibers can be reliably filled, improving sensing performance, which is particularly preferable. The cover yarn may be a false twisted yarn (woolly yarn) from the viewpoint of easily improving the texture and covering property.

[0045] Figures 2 and 3 show an example of a sensing element according to one embodiment of the present invention, in which two sheath-core yarns (7) are further twisted together. In the present invention, yarns with this structure are referred to as plied yarns (8) or plied yarns. In plied yarns, the relationship between the winding direction of the covering material (cover yarn) of each sheath-core yarn and the twisting direction when the two sheath-core yarns are further twisted together is not particularly limited. However, it is preferable that the winding direction of the covering material (cover yarn) (6) around the linear conductor (5) serving as the core material of the two sheath-core yarns (7) arranged adjacent to each other is the same, and that the two sheath-core yarns are twisted together in the opposite direction to the winding direction of the covering yarn (cover yarn). By using a plied yarn in which the twist is applied in the opposite direction to the winding direction of the covering, the torque of the resulting yarn is reduced, making it easier to handle during the manufacturing process. In the case of the above-mentioned plied yarn, the two sheath-core yarns are naturally arranged close to each other, and the two sheath-core yarns have a point of contact where they intersect.

[0046] The sheath-core yarn has the following formula: Twist factor K=(SS+SC) 1 / 2 ×R The twist factor K, expressed by the formula {where SS is the fineness (dtex) of the linear conductor serving as the core material, SC is the total fineness (dtex) of the covering material, and R is the number of turns (twists) of the covering material (turns / m)}, is preferably 7000 or more and 30,000 or less. If the twist factor K is 7000 or more, electrical short circuits between two linear conductors are less likely to occur, while if it is 30,000 or less, it becomes easier to obtain a large sensor output. In the case of double covering, the twist factors for the first and second covering layers are calculated and the average value is used.

[0047] The sheath-core yarn in another embodiment of the sensing element has a structure in which a linear conductor as a core material is wrapped around a high-resistivity staple fiber as a covering material in a random direction to form a covering. Preferably, it is a core spun yarn (CSY) in which the core yarn is inserted and covered when the staple fiber that forms the sheath yarn is spun. The present inventors have investigated the use of core-spun yarns as sheath-core yarns and found that sensing performance can be achieved by ensuring the insulation of the core yarn. However, they found that under normal conditions, variations in the covering state cause partial deterioration in insulation and reduced sensing performance. They were able to create core-spun yarns that can continuously achieve excellent sensing performance by setting specific covering conditions. Specifically, it is important that the weight ratio of the core yarn to the sheath yarn is within a specific range. In a typical core spun yarn, the core yarn content is 15% by mass to 30% by weight, but in the present invention, the core yarn content is preferably 5% by mass to 12% by weight, and particularly preferably 10% by weight or less. In this embodiment, of the two or more sheath-core yarns, at least one must be a sheath-core yarn in which a linear conductor as a core material is wrapped around a high-resistance short fiber as a covering material in a random direction, and the sheath-core yarn is preferably a core spun yarn. The type and fineness of the core material may be the same as those of the core-sheath structure yarn described above, and the single yarn fineness of the high-resistance short fibers randomly wound as the covering material is preferably 30 cotton count to 5 cotton count, more preferably 20 cotton count to 5 cotton count, from the viewpoint of easily ensuring insulation. The winding amount may be adjusted so that the blend ratio of the core yarn described above falls within a preferred range.

[0048] As shown in FIG. 4, the sensing element can be in the form of a narrow woven fabric in which the above-described plied yarn is continuously distributed in one direction of the fabric. In the example shown in FIG. 4, the plied yarn is woven as a warp yarn in the center of the width direction of the narrow woven fabric. However, the plied yarn may be used as either the warp yarn or the weft yarn, or both, and any number of yarns may be arranged depending on the number of locations to be sensed. From the viewpoint of continuous production, it is preferable to arrange the plied yarn as part of the warp yarn. This makes it possible to sense contact of an object or load on the area woven with the plied yarn, and / or to sense contact of a liquid or changes in humidity. When the plied yarn is woven into part of a narrow woven fabric, the fiber member has a tape-like shape, which has the advantage of being easier to attach to textile products such as clothing and bags compared to a fabric in which only plied yarn is used. The width of the fabric in which the plied yarn is arranged is preferably 1 to 200 mm, more preferably 5 to 30 mm. The use of yarns other than the plied yarn is not particularly limited, and the weave is also not particularly limited. Furthermore, for the purpose of preventing static electricity from a fiber substrate or the like provided with the fiber sensing member of this embodiment, an antistatic yarn containing a conductive material may be wound around the above-mentioned plied yarn and embedded in a woven fabric. 6 ~10 10 Those having a resistivity of about Ω / cm are used, and examples thereof include "Belltron (registered trademark)" carbon Belltron type and white Belltron type manufactured by KB Seiren Co., Ltd., and "Clacarbo (registered trademark)" manufactured by Kuraray Co., Ltd. Alternatively, in the fiber substrate having the fiber sensing member of this embodiment disposed thereon, the same effect can be obtained by disposing the antistatic yarn in the vicinity of the member or between a plurality of such members disposed thereon.

[0049] Furthermore, it is also possible to create a woven fabric shape (see Figure 5) in which multiple plied yarns described above are arranged in a warp and weft direction. In Figure 5, five warp yarns are arranged in parallel and weft yarns are woven left and right, but the braid-like woven fabric shape is not limited to this structure. By using a sensing element in which multiple plied yarns are woven, it is possible to simultaneously measure the application of external forces such as loads and tensile forces at the positions of each plied yarn, thereby enabling mapping and measurement of the position of an applied external force. Alternatively, the above-mentioned sheath-core yarns can be used as warp and weft yarns to form a woven fabric. In this case, the two sheath-core yarns are arranged close to each other at the intersection of the warp and weft yarns, and the sensing function described above is realized at this intersection, making the fabric applicable as a sensing fiber member. Any shape can be used for such a woven fabric. These fabric-shaped sensing elements of the present invention differ from conventional stretch sensors using stretchable wiring in that they have low extensibility (are not easily stretched or contracted), resulting in good linearity, almost no hysteresis, and a fast response when returning to their original shape, resulting in good repeatability. Specifically, they are characterized by a low elongation rate (specific load elongation) when a 1 N repeated load is applied to a 1 cm wide sample (described below), preferably 5% or less, and more preferably 3% or less. There is no particular lower limit, but to ensure response to biological information, it is preferably 0.1% or more, and more preferably 0.5% or more. The above-mentioned plied yarn can be arranged in a knitted fabric. Alternatively, two or more of the above-mentioned core-sheath yarns can be arranged so that they are partially adjacent to each other or cross each other to exhibit sensing functions. The textile substrate on which the sensing member is disposed can be appropriately made extensible depending on the application. For example, in a case where a plied yarn is used as part of the knitting yarn constituting the knitted fabric and the sensing member is knitted into the textile substrate, the extensible amount of the textile substrate can be 20% or more or 50% or more. Furthermore, the above-mentioned sheath-core thread can also be used as the needle and bobbin threads on a sewing machine when sewing or embroidering textile substrates. In this way, one sheath-core thread is placed above and below the textile substrate, and the above-mentioned sensing function is exerted at the points close to the sheath-core threads, making it applicable as a sensing element. When constructing a fiber substrate such as the above-mentioned woven or knitted fabric, it is more preferable that the linear conductors of two pairs of sheath-core yarns are routed to the front side of the fiber substrate and the back side of the fiber substrate at their electrode lead-out portions (parts mounted on a circuit). In particular, it is preferable that all linear conductors for voltage application are routed to the same side of the fiber substrate, and linear conductors for signal output are routed to the opposite side. This preferred example has the advantages of enabling electrical short-circuiting and short-circuit prevention in a more space-saving manner when multiple linear conductors of sheath-core yarns are electrically connected to apply voltage and read out each signal independently, and of improving productivity due to simplified mounting.

[0050] Figure 6 shows a schematic diagram of a device for measuring the resistance change between two sheath-core yarns, each consisting of a linear conductor core wrapped unidirectionally with a multifilament high-resistivity fiber sheath. However, there are no particular limitations to this device. The conductive fiber at the ends of the paired sheath-core yarns can be opened and connected to a source meter (SMU, source-measure unit) capable of supplying voltage and current while simultaneously measuring voltage, current, and resistance. Alternatively, resistance can be measured without using such a measuring device by creating a readout circuit consisting of an analog-to-digital converter, a current-to-voltage converter, an amplifier, etc.

[0051] The sensing principle is that the impedance between linear conductors changes as the shape of the core yarn and sheath yarn changes due to the application of load, tension, etc. There are several possible principles for the impedance change, and as these phenomena occur simultaneously, no specific mechanism is limited. One of the principles for the impedance change is that the application of an external force changes the distance between the core yarns or the width of the electrodes where the core yarns face each other, which changes the capacitance and resistance between the core yarns. Another possible principle is that the change in shape of the sheath yarn due to the application of an external force causes the yarns that make up the sheath yarn to come into closer contact with each other, forming many conductive paths and resulting in a decrease in resistance. For example, in one example of this embodiment, the area of ​​the sensing portion is 8.75 mm 2 A load of approximately 3N (pressure 3.43 x 10 5 When a pressure (equivalent to a pressure of 10 Pa) was applied, R changed from 3.5 GΩ to 1.5 GΩ, and ΔR / R was -57%, a very large change. Furthermore, the capacitance C at this time changed from 3.31 pF to 3.53 pF, and ΔC / C was 6.7%. When the change in resistance is large like this, it is thought that in addition to the change in impedance due to a simple change in shape between the core threads, the sheath threads come into closer contact with each other, increasing the number of contacts and increasing the minute current flowing through the sheath thread. If the insulating fiber that makes up the sheath thread were an ideal insulator, no current would flow between two linear conductors, but in reality, insulators have an electrical resistivity of 10 6 ~10 9 They are very slightly conductive, known as Ω·m. The electrical conduction mechanism within insulating polymers is known as hopping conduction, in which electrons and ions move between localized states. Ideally, insulating polymers are free of charged particles, but actual polymer materials contain impurities such as catalysts and moisture introduced during the manufacturing process. Dissociated ions resulting from these impurities move in response to an applied electric field, generating a weak current. In addition, in this embodiment of the present invention, kneading a conductive material such as a carbon material into the sheath yarn to create very slight conductivity is preferable because it allows for simpler circuit readout. When a load or tension is applied to a structure in which such very slightly conductive sheath yarn is placed between two adjacent linear conductors, the multiple fibers that make up the sheath yarn come into closer contact with each other, increasing the number of electrical contact points and increasing the value of the weak current. This reduces the sensor resistance, enabling the detection of load and tension. Another theory that explains the impedance change is that the space charge limited current changes as the distance between linear conductors changes. As will be explained later, when the contacting object is conductive, parasitic capacitance is added to the change in capacitance, so the contribution of the change in parasitic capacitance is superimposed on the change in capacitance due to the change in shape.

[0052] The principle of measuring the electrical properties between paired core-sheath structure yarns can be considered as an equivalent circuit consisting of a resistor (R) and a capacitor (C) as shown in Figures 2 and 12. When the sensing signal is read from a change in resistance value, a DC power supply can be used as the power supply shown in FIG. To measure changes in capacitance, an AC power source is used, an AC current of frequency f is applied between the linear conductors in the paired core-sheath structure yarns, and the change in impedance between them is detected. To measure capacitance, any common measuring instrument or circuit can be used, such as an LCR meter or an impedance analyzer. Alternatively, a lock-in amplifier circuit can be used, which performs frequency analysis by preparing an AC reference signal and multiplying the output signal by the reference signal. This method has the advantage of being able to measure minute changes in capacitance with greater accuracy. Alternatively, to read changes in capacitance, a DC power source can be used to apply a voltage between two linear conductors and measure the time change in impedance between them (monitor the change in current value). Using a DC power source has the advantage of being able to measure with a very inexpensive circuit. Here, the capacitance between two electrodes can be calculated using the following formula: C=ε(S / L) {where ε is the dielectric constant between the two electrodes, S is the electrode area, and L is the distance between the electrodes.}

[0053] From the above formula, C = ε(S / L), the capacitance C is inversely proportional to the distance L between the conductors and proportional to the electrode area. When the object to be detected for contact is an uncharged insulator, the distance between the pair of linear conductors becomes small and the electrode area remains almost unchanged, resulting in an increase in capacitance, allowing the detection of contact. Furthermore, when the contacting object is conductive, the parasitic capacitance due to the contact of the object is further added, resulting in a change in capacitance. For example, in the example of this embodiment described above (an example in which ΔR / R is -57%), when a load of approximately 3 N was applied using an insulator, C changed from 3.31 pF to 3.53 pF, and ΔC / C was 6.7%. However, when a load of approximately 3 N was applied using a grounded conductive material, C changed from 3.31 pF to 3.01 pF, and ΔC / C was -8.9%.

[0054] When a contacting object is conductive, the apparent capacitance decreases due to the addition of parasitic capacitance and increased charge leakage to ground. In this way, contact, load, or tensile force can be detected by reading the change in capacitance due to contact or load. In this embodiment, the cover yarn and the outside air (outside air: air in the atmosphere, vacuum in a vacuum, or the replacement gas in a replacement gas, etc.) exist as insulators between the two linear conductors. The principle of the current flowing between them varies depending on conditions such as the distance between the electrodes, the applied voltage, and the humidity of the outside air. For example, in addition to the space charge limited current described above, various principles such as leakage current and ionic conduction can be used, and either or both of the change in resistance and the change in capacitance may be read as an output signal.

[0055] The sensing member used in the bioinformation measuring device of this embodiment changes the impedance between two linear conductors due to an external action, and can detect this external action. For example, contact or application of a load changes the distance between the two linear conductors or the number of electrical contacts between the sheath threads, thereby changing the resistance and / or capacitance (i.e., impedance) between the two linear conductors, making it possible to detect contact or load. Furthermore, when the external action is a tensile force or bending stress, the distance between the linear conductors changes, causing a change in impedance, making it possible to detect this external action. Using this sensing member, it is possible to obtain sensor outputs corresponding to slight displacements and movements of the body surface, such as slight stretching, breathing, changes in posture, movements of the wrists, ankles, fingers, etc., muscle movements (pelvic floor muscles, brachioradialis muscles, calves, etc.), pressure from compression garments or socks, sole pressure and foot pressure distribution, swallowing, walking, running, etc. Alternatively, if a substance that can cause a change in impedance between two linear conductors is contained between them, the presence or absence of this substance can be detected. For example, if non-ultrapure water such as tap water, salt water, ionized drinks, or a mixture of water and ethanol is dropped between two linear conductors, the resistance between the linear conductors drops significantly and the current between them increases, allowing the presence or absence of these liquids to be detected. Furthermore, since a change in humidity also causes a change in impedance, the device can be used as a humidity sensor. When detecting slightly conductive liquids such as tap water or human sweat, the cover yarn is made of a material with lower conductivity than the liquid to be detected. This changes the impedance of the sensor before and after the liquid penetrates, allowing the liquid to be detected. For example, if carbon-based fiber is used for the cover yarn, the sensor resistance value will be slightly lower, and current will flow more easily through the carbon-based fiber than through water, making it impossible to detect water.

[0056] Alternatively, it is possible to simultaneously detect the application of an external force such as touch, load, or tensile force, and the contact of a liquid such as water. The change in resistance when an external force is applied is five times or more different from the change in resistance when water is dropped. Furthermore, the output changes moment by moment as the water dries. Therefore, it is possible to distinguish between these detections based on the behavior of the output value. In this embodiment, it is possible to simultaneously detect, for example, the amount of sweat on the human body, its change over time, water exposure, and urine leakage.

[0057] Alternatively, a sensor can be configured to detect the application of external force but have extremely low sensitivity (effectively no sensitivity) to contact with liquids such as moisture and sweat. For example, by using a material for the cover yarn that is more conductive than the liquid to be detected, the sensor can be highly sensitive to the application of external force and insensitive to contact with the liquid. For example, by using a high-resistivity fiber as the covering material (sheath yarn) with a carbon-based conductive material on at least a portion of its surface, it is possible to read changes in resistance between linear conductors, detect changes in breathing and posture of a living body, and movements of the wrist or fingers, and have the sensor output remain unchanged in response to sweating or water exposure. In this case, the change in sensor output in response to changes in moisture content in the area where biological information is measured is preferably 1 / 20 or less, more preferably 1 / 100 or less, of the change in sensor output in response to measurement of biological information such as external force to be detected.

[0058] FIG. 7 shows an example of a sensing element according to the present invention. A double-core / sheath yarn was fabricated using conductive multifilament fibers made of silver-plated nylon 66 fibers as the linear conductor and insulating polyester fibers as the sheath yarn. Two of the resulting double-core / sheath yarns were then twisted together to form a plied yarn. In this example, the linear conductor consisted of nylon fibers with a fineness of 220 dtex, a fineness of 300 dtex after silver plating, and 68 filaments. The sheath yarn was covered with two bobbins of 252 dtex / 108 filament woolly polyester yarn, each Z-twisted to a twist of 732 T / m. The two resulting double-core / sheath yarns were then twisted together in the S direction to form a plied yarn with a twist of 170 T / m. The fineness of this plied yarn was 2000 dtex. Twist coefficient of the ply-twisted yarn K = (300 + 252 × 2) 1 / 2 ×732=20756. The resistance between two adjacent linear conductors in two adjacent sheath-core yarns was measured by electrically disconnecting the two linear conductors at one end of the sheath-core yarn and connecting a source meter (SMU: Source Measure Unit, Keithley 2614B) between the two linear conductors at the other end, which can simultaneously supply voltage and current and measure voltage, current, and resistance. A voltage of 3 V was applied between the two linear conductors, and a homemade program constantly monitored the current output by the source meter, measuring the current before and after the application of load or tension. For the ply-twisted yarn, a sample with a 10 cm length (effective sensing length) of the paired linear conductors was prepared and the sensing characteristics were measured.

[0059] Figure 8 shows the relationship between the applied load and the rate of change in current when a load is applied to the plied yarn obtained above. The conditions for measuring the current value were exactly the same as those in Figure 7. The load was applied by placing the sensing fiber element on a flat stage and applying a load from above using a force gauge (IMADA, full-range 20 N), while measuring the load value at this time. A circular indenter with a diameter of 12.5 mm was used. The results shown in Figure 8 demonstrate that this plied yarn is useful as a sensing fiber element that can also detect the magnitude relationship of loads.

[0060] As an example of a woven fabric using the sheath-core yarn obtained above, a narrow woven fabric was produced using five of the above-mentioned sheath-core yarns as warp yarns and one as weft yarn, measuring 1 cm wide x 10 cm long and 850 μm thick, with the structure shown in Figure 5. Figure 9 shows the change in current value (sensor output) over time when a load was applied with a finger near the intersection of the sheath-core yarns of this fabric, followed by a tensile force. This demonstrates that this fabric is useful as a sensing fiber component for loads and tensile forces.

[0061] Fig. 14 shows a conceptual diagram of an example of a sensing member according to the present invention, in which the sheath yarn is CSY. This sensing yarn can be produced at significantly lower cost than the conventional piezoelectric sensing yarn shown in Fig. 13, which has electrodes on the inside and outside in contact with a piezoelectric body. Figure 15 shows the sensing characteristics of a sensing element for a plied yarn. The linear conductor was a multifilament conductive fiber made of silver-plated nylon 66 fibers. The sheath yarn was treated with CSY processing using cuprass sliver (manufactured by Asahi Kasei Corporation, cotton count 10 / 1). Two core-spun yarns were then twisted together to form a plied yarn. Here, the linear conductor consisted of nylon fibers with a fineness of 33 dtex (40 dtex after silver plating) and seven filaments. The sheath yarn was micro-lyocell (Lyocell Micro, manufactured by Lenzing, cotton count 15 / 1). The yarn was then subjected to CSY processing (core-spun yarn) using a Murata Machinery VORTEX spinning machine at a spinning speed of 300 m / min. The weight ratio of the core yarn to the sheath yarn was 8 / 92 (core yarn blend ratio 8 wt%). The two core-spun yarns were then twisted together to form a plied yarn with a twist of 163 T / m. The fineness of this plied yarn was 1180 dtex. Figure 15 shows the change in current value (sensor output) when a load was applied to the plied yarn obtained above. The load application and removal were repeated five times twice at different locations, and changes in current value due to the application and removal of load were confirmed at each measurement point. Figure 15 shows that this sensing element is capable of detecting load.

[0062] In the following examples, examples of biometric information measuring devices of this embodiment will be described, including a human respiration measuring device, a simultaneous respiration and posture measuring device, a finger bending measuring device, and a palm opening / closing and wrist bending measuring device. [Example]

[0063] Examples of the present invention will be described below with reference to examples, but the present invention is not limited to these examples.

[0064] In the following examples, the specific load elongation of the sensing members, clothing, etc. was measured as follows. <Specific load elongation (%)> A cloth-shaped sample was cut to a width of 1 cm and a length of 25 cm, and attached to a tensile tester with 5 cm on each end chucked so that the test length was 15 cm under an initial load of 10 g (0.1 N). The sample was stretched at a tensile speed of 80 mm / min until the load reached 1 N and then returned to its original state, and this process was repeated 75 times. The amount of elongation at each stretch was measured, and the elongation at the 75th stretch (the elongation rate relative to the initial length) was defined as the specific load elongation of the present invention.

[0065] [Example 1: Respiration sensing using narrow-width fabric with embedded sensing yarn] As shown on the left side of Figure 16, sensing wear was prepared by sewing a narrow fabric with sensing thread (sensing member) woven into the back of a tank top, and a person wore this to sense breathing. The position of the sensing thread was adjusted so that when the sensing wear was worn, the sensing thread was near the diaphragm, that is, about the fourth or fifth rib from the bottom. The tank top was made of a material consisting of 60% cotton, 30% polyester, and 10% polyurethane, and was sized to fit comfortably to the body. In other words, the sensing wear was designed to be in close contact with the surface of the body. The linear conductor constituting the sensing yarn was a conductive fiber consisting of a multifilament made of silver-plated nylon-6,6 fiber. The nylon fiber had a fineness of 66 dtex, and after silver plating, the fineness was 80 dtex, with 14 filaments. This linear conductor was covered with KB Seiren's Belltron B31 (registered trademark) (fineness 240 dtex) as a high-resistance fiber for the sheath yarn, producing a core-sheath structure yarn. Two of these were then twisted together to produce a plied yarn, which was used as the sensing yarn. The fineness of the sensing yarn was 1284 dtex. The covering conditions were as follows: first, double covering was performed using two sheath yarns with a twist count of 653 T / m (twist factor = 15258) in the Z direction; then, when the two sheath-core structure yarns were further twisted together, a plied yarn was produced with a twist count of 250 T / m (twist factor = 8344) in the S direction. This sensing yarn was woven into the center of the warp of a narrow woven fabric (woven tape) to produce a narrow woven fabric. The weave structure was plain weave, and 167T polyester wooly yarn was used for both the warp and weft of the narrow woven fabric except for the sensing yarn. The resulting narrow woven fabric was 10 mm wide, 430 μm thick, and weighed 2.14 g per meter of fabric length. An enlarged photograph of the narrow woven fabric used is shown on the right side of Figure 16. The black area in the center of the photograph is the sensing yarn, which is woven into the narrow woven fabric in a plain weave structure. A 25 cm length of this narrow woven fabric was sewn into the back of a tank top to produce the sensing wear shown on the left side of Figure 16. The specific load elongation of the tank top fabric was 9%, and the specific load elongation of the narrow woven fabric was 1.8%.

[0066] The respiratory sensing characteristics were evaluated as follows. Two adjacent linear conductors were electrically disconnected at one end of the sheath-core yarn, and a voltage of 1.0 V was applied to the other end. The output current was monitored. The voltage application and current measurement were performed using a source meter (SMU: Source Measure Unit, Keithley 2614B). The output current was continuously monitored using a homemade program. The results are shown in Figure 17. The results in Figure 17 reveal fluctuations in the output value, which increased during inspiration and decreased during expiration, indicating changes linked to respiration. Furthermore, the output current remained constant when the subject held their breath. Thus, this sensing garment demonstrates changes in sensor output linked to respiration. At a 25-cm-long section on the back of the human body where the sensing yarn was attached, the change in body surface length in response to respiration was approximately 3.9%. Note that the above measurements were performed on a woman 152 cm tall.

[0067] [Example 2: Simultaneous sensing of respiration and posture using narrow-width fabric with embedded sensing yarn] A narrow woven fabric woven with the same sensing yarn as in Example 1 was prepared, and a T-shirt was made by sewing this fabric so that it was positioned near the shoulder blades, to serve as sensing wear (left side of Figure 18). The T-shirt fabric was made of 89% polyester and 11% polyurethane. The specific load elongation of the T-shirt fabric was 11%, and the specific load elongation of the narrow woven fabric was 1.8%. The current value was measured under the same conditions as in Example 1 when the subject wore this sensing wear and moved in a way that indicated a good posture with an upright back ("◯") and a bad posture with a hunched back ("X"), as shown on the right side of Figure 8. Figure 19 shows an example of the current monitor results. The subject in this study was a male with a height of 178 cm. The subject maintained good posture from 0 to 42 seconds, then hunched slightly from 42 to 55 seconds. After returning to good posture, he assumed a significantly poorer posture from 60 to 78 seconds, as shown in the photograph on the right side of Figure 18. The results in Figure 19 indicate that the baseline level of the current is linked to poor posture, and that current fluctuations were linked to respiration regardless of posture. Comparing the respiratory rate with the results measured separately from rib movement confirmed that the changes in the output current in Figure 19 were completely linked to inhalation and exhalation.

[0068] [Example 3: Sensing finger bending with finger supporter / glove] The linear conductor constituting the sensing yarn was a conductive fiber made of multifilament silver-plated nylon-6,6 fibers. The nylon fiber had a fineness of 66 dtex, and after silver plating, the fineness was 80 dtex, with 14 filaments. The linear conductor was covered with Asahi Kasei's Bemberg® (registered trademark) (fineness 220 dtex) as a high-resistance fiber covering material (sheath yarn) to produce a core-sheath structure yarn. Two of these were further twisted together to produce a plied structure yarn. The fineness of the sensing yarn was 1255 dtex. The covering conditions were as follows: first, double covering was performed using two sheath yarns with a twist number of 1042 T / m (twist factor = 23439) in the Z direction; then, when the two sheath-core structure yarns were further twisted together, a plied structure yarn was produced with a twist number of 204 T / m (twist factor = 6490) in the S direction. A finger supporter was produced using this sensing yarn, as shown in Figure 20, on a WHOLEGARMENT flat knitting machine (MACH2XS 15S). A 168 dtex / 36 f polyester woolly yarn was used for the yarn used to knit the front part of the supporter and the ground yarn (ground yarn) used to knit the back part, and the yarn for the front and back parts was flechage knitted to create a structure with holes for fingers at both horizontal ends of the knitted part (a tubular shape extending in the wale direction of the knitted fabric). 46 courses were knitted on each of the front and back parts, for a total of 92 courses, to make one circumference, and these were extended in the lengthwise direction by 60 wales to create the structure shown in Figure 20. The loop length in this case was 5.5 mm. During the main knitting, the sensing yarn was knitted into the backside of the center of the front using needle-open bag knitting in four courses across the width of the tube and 38 wales with a loop length of 5 mm across the length.

[0069] This finger supporter (see Figure 20) was attached to the middle finger as shown in the left photograph of Figure 21. The sensor output current was monitored while bending and straightening the finger using the same measurement method as in Example 1, except that the applied voltage was 3.0 V. The results are shown on the right side of Figure 21. During the hatched periods marked B and C, movements B and C were performed, respectively. At other times, the finger was returned to its straightened position. The graph on the right side of Figure 21 shows that the sensor output current increased when the finger was bent, and the greater the bending, the greater the change in current value. An overshoot in the current value was observed at the beginning of movements B and C. This is due to the fact that the knitting structure of this example is somewhat resilient to shape changes. A different knitting structure, described later in Example 4, achieved high responsiveness. (In other words, the sensing yarn itself exhibits high responsiveness.) Here, the length of the outer surface of the finger during bending and straightening movements was measured: 4.0 cm in position A, 4.8 cm in position B, and 5.0 cm in position C. That is, in states B and C, the elongation was 20% and 25%, respectively, compared to state A. This indicates that the sensing thread in the finger supporter is stretched in response to the elongation of the finger surface when the finger is bent, and the current value increases.

[0070] [Example 4: Simultaneous sensing of palm opening and closing (open / closed palm) and wrist bending using a wristband] The linear conductor constituting the sensing yarn was a conductive fiber consisting of a multifilament made of silver-plated nylon-6,6 fibers. The nylon fiber had a fineness of 66 dtex, and after silver plating, the fineness was 80 dtex, with 14 filaments. The linear conductor was covered with Asahi Kasei's Bemberg® (registered trademark) (fineness 220 dtex) as a high-resistance fiber covering material (sheath yarn) to produce a core-sheath structure yarn. Two of these were then twisted together to produce a plied structure yarn. The fineness of the sensing yarn was 1255 dtex. The covering conditions were as follows: first, double covering was performed using two sheath yarns with a twist count of 1042 T / m (twist factor = 23439) in the Z direction; then, when the two sheath-core structure yarns were further twisted together, a plied structure yarn was produced with a twist count of 204 T / m (twist factor = 6490) in the S direction. A wristband was produced using this sensing yarn as shown in Figure 22 using a WHOLEGARMENT flat knitting machine (MACH2XS 15S). 168T72 polyester wooly yarn was used for the ground yarn (ground yarn) of the wristband body, and the structure has holes for passing the arms through at both vertical ends of the knitting section (a tubular shape extending in the direction of the knitting course). The front and back are 96 courses long, and 52 wales on each side, for a total of 104 wales, knitted around the circumference, resulting in the structure shown in Figure 22. The loop length at this time was 6 mm. During the main knitting, two rows of the sensing yarn were knitted in parallel to the longitudinal direction of the main tube using smooth knitting, in which four courses are knitted to form one course, as shown in Figure 24.

[0071] This wristband (see FIG. 22) was worn on the wrist as shown in the photograph on the left side of FIG. 23. The sensor output current value was monitored while bending and straightening five fingers using the same measurement method as in Example 1, except that the applied voltage was 3.0 V. The results are shown on the right side of FIG. 23. As shown in the photograph on the left side of FIG. 23, A represents the open hand, B represents the clenched hand, and C represents the clenched hand with the wrist bent. In the graph on the right side of FIG. 23, the hatched portions marked B and C indicate the movements B and C, respectively, while the hand returned to the open hand position A at other times. The graph on the right side of FIG. 23 shows that the sensor output current increases when the fingers are bent, and the greater the bending, the greater the change in current value. An overshoot is observed in the current value at the beginning of movements B and C. This is due to the fact that the knitting structure of this example is somewhat resilient to shape changes. A high responsiveness is achieved with a different knitting structure, as described below in Example 4. (In other words, the sensing thread itself has high responsiveness.) When the arm circumference was measured during movement, it was 18.0 cm in state A with the hand outstretched, 17.7 cm in state B, and 17.0 cm in state C. In other words, in states B and C, the circumference was reduced by 1.7% and 5.6%, respectively, compared to state A. The output current value during operations B and C decreased, and the hand-clenching movement was detected as the sensing thread, which was initially pulled, contracted.

[0072] [Example 5] The linear conductor constituting the sensing yarn was a conductive fiber made of multifilament silver-plated nylon-6,6 fiber. The nylon fiber had a fineness of 99 dtex, and after silver plating, the fineness was 120 dtex, with 21 filaments. A sheath-core structure yarn was produced using a high-resistance fiber for the covering material (sheath yarn)—Clacarbo (KC-782R B20T4, manufactured by Kuraray Co., Ltd.) with a fineness of 500 dtex. Two of these yarns were further twisted together to form a plied yarn, which was then directly sewn to the tank top in three pieces. The respiratory sensing garment was fabricated under the same conditions as in Example 1, except for the twist number during covering of the sheath yarn. The twist number during the sheath yarn covering was 838 T / m (twist coefficient = 28045), and the twist number during the further twisting of the two sheath-core structure yarns was 280 T / m (twist coefficient = 13252). The fineness of the completed plied structure yarn was 2865 dtex. The stitching was done in three places using a serger: the upper chest (at armpit height), the lower chest (under the bust), and the abdomen (the area with the greatest movement during abdominal breathing). The sensor resistance of a 30cm long sensing thread was 9.0kΩ, and the overall wiring resistance of one core thread of the linear conductor was 23Ω. Furthermore, when the sensing thread was thoroughly soaked in tap water and artificial sweat, the sensor resistance was measured and was 9.0kΩ, exactly the same as when dry. In this case too, the sensor output was read while wearing this sensing wear, and changes in sensor output linked to breathing were observed. Furthermore, when chest breathing and abdominal breathing were performed, the changes in the upper chest, lower chest, and abdomen were greater, respectively, making it possible to distinguish between chest and abdominal breathing. Furthermore, even when measuring by soaking the sensing element in tap water, the same sensor output was obtained as when dry. The above measurements were taken on a man with a height of 175 cm. [Industrial Applicability]

[0073] The sensing member used in the bioinformation measuring device according to the present invention can be processed in long lengths, is highly mass-producible, can be used as warp yarn for woven fabrics or warp knitting, is flexible and has a good texture, and is significantly less expensive than conventional contact-sensing fiber members (piezoelectric yarns) that use piezoelectric materials. That is, since the sensing member can sense load or tensile force using common fiber materials such as polyester or nylon, sensing fibers can be realized at very low cost. Furthermore, since covering technology, a fiber processing technology with established know-how, including core-spun yarns, is used, long lengths can be processed, is highly mass-producible, and, since textured yarns with a much better texture than piezoelectric yarns can be realized, processing into fiber members such as woven fabrics and knitting fabrics is easy. The sensing member used in the bioinformation measuring device according to the present invention can detect changes in capacitance and / or resistance, indicating that a load or tensile force is being continuously applied, and can also detect changes in moisture content. Furthermore, in the sensing member used in the bioinformation measuring device according to the present invention, when the core-sheath structure yarn in which high-resistivity short fibers as a covering material are wrapped around the linear conductor as the core material in a random direction to form a covering is a core spun yarn, it is easy to use natural fibers or biodegradable yarns, and it is easy to impart functionality to the sheath yarn. Therefore, the bioinformation measuring device according to the present invention can be widely used in smart textile applications in which an electrical functional element is provided on a flexible and stretchable fiber substrate. Furthermore, sensing members of the prior art mainly utilize sensor outputs such as electrical resistance and capacitance in response to the elongation of the stretchable wiring, which are determined by the physical properties of the rubber elastic body, and therefore have poor linearity, hysteresis, and a slow response when returning to their original state, and therefore cannot be said to have good repeatability.In contrast, the sensing member used in the bioinformation measuring device of the present invention has a lower specific load elongation than conventional sensing members, and therefore has good linearity, almost no hysteresis, and a fast response when returning to their original state, resulting in good repeatability. Therefore, the bioinformation measuring device according to the present invention can detect slight stretching and other displacements and movements of the body surface or fluctuations in moisture content using, for example, clothing (T-shirts, underwear, vests, belts, etc.) including a sensing fiber member (yarn) having a ply-twisted yarn formed by further twisting two sheath-core yarns together, thereby making it possible to detect, for example, breathing, changes in posture, movements of the wrists, ankles, fingers, etc., muscle movements (pelvic floor muscles, brachioradialis muscles, calves, etc.), swallowing movements, analysis of walking and running movements (for rehabilitation, preventive measures, etc.), and fluctuations in moisture content due to sweating, excretion, etc. In particular, the bioinformation measuring device according to the present invention can simultaneously detect the presence or absence of breathing and whether posture is good or bad, and simultaneously detect the degree of hand opening (clenched fist or open hand) and bending of the wrist, etc. Furthermore, the bio-information measuring device of the present invention can be applied to smart textiles, such as posture-improving innerwear that communicates with external devices such as smartphones using wireless communication such as Bluetooth (registered trademark), and displays the number of times per day that a person maintains good posture along with a target value using a sensor on the back. [Explanation of symbols]

[0074] 1. Conductive fiber 2. Piezoelectric materials 3 Conductors 4. Conventional piezoelectric yarn 5. Linear conductor as core material 6 High-resistance fibers (long fibers or spun yarns) as covering materials (cover yarns) 7. Core-sheath structure yarn 8 Ply-twisted yarn made by twisting two core-sheath yarns together 9 Core thread (core material) 10 spindles 11 Bobbin 12 Flyer 13 Flyer Cap 14 Cover thread 15 Flyer Foot Guide 16 Flyer Foot Guide 17 Flyer Foot Guide 18 Flyer Foot Guide

Claims

1. A bioinformation measuring device that consists of a fiber substrate including a sensing member and is placed in contact with a predetermined position on a living body, wherein the sensing member has at least two core-sheath structure yarns in which a high-resistance fiber is arranged as a covering material around a linear conductor as a core material, two of which are arranged close to each other so that changes in resistance and / or changes in capacitance between the linear conductors of the two core-sheath structure yarns can be read, and the bioinformation measuring device measures the bioinformation and its fluctuations from these changes, wherein the high-resistance fiber arranged in the sensing member consists of fiber having a carbon-based conductive material on at least a portion of its surface, and is capable of reading changes in resistance between the linear conductors.

2. 2. The biological information measuring device according to claim 1, wherein the sensing member is a ply-twisted yarn in which two strands of the sheath-core yarn are further twisted together.

3. The biological information measuring device according to claim 1 or 2, wherein the specific load elongation of the sensing member is 5% or less.

4. The biological information measuring device according to claim 1 or 2, wherein the biological information is a change in posture of the living body.

5. The biological information measuring device according to claim 1 or 2, wherein the biological information is obtained by respiration.

6. 3. The biological information measuring device according to claim 1, wherein the biological information is a change in moisture content of the surface of the living body.

7. 2. The biological information measuring device according to claim 1, wherein a change in sensor output in response to a change in moisture content in the portion of said sensing member where said biological information is measured is 1 / 20 or less of a change in sensor output in biological information measurement.

8. The bioinformation measuring device of claim 1 or 2, wherein at least one of the core-sheath structure yarns is a core-sheath structure yarn in which a high-resistance fiber as a covering material is wrapped in one direction around a linear conductor as a core material to form a covering.

9. The bioinformation measuring device of claim 1 or 2, wherein at least one of the core-sheath structure yarns is a core-spun yarn in which a linear conductor as a core material is wrapped around a high-resistance short fiber as a covering material in a random direction to form a covering.

10. The bioinformation measuring device according to claim 1 , wherein two or more of the core-sheath structure yarns are arranged so as to be partially in contact with each other at a fiber substrate.

11. Clothing equipped with the biological information measuring device according to claim 1 or 2.

12. Clothing equipped with the biological information measuring device according to claim 11.

Images