Sensors for measuring biological signals

Abstract

To provide a biological signal measuring sensor being worn on a surface of a human body without a sense of discomfort and capable of stably measuring a biological signal.SOLUTION: A biological signal measuring sensor comprises an electrode body 1 knitted by inserting a plurality of insertion yarns into a ground weave formed of insulating knitting yarns, and a water content supply part 2 for supplying water content to the electrode body 1. The electrode body 1 includes an electrode part 10 exposed by continuously planarly disposing the conductive insertion yarns in a partial area in a side coming into contact with a human body surface, and a contact part 12 exposed by planarly disposing a plurality of conductive insertion yarns in an area enclosing the electrode part 10 in a side coming into contact with the human body surface. The water content supply part 2 includes a water content holding part 20 attached to a position facing the electrode part 10 in an opposite side of a skin side of a fabric C.SELECTED DRAWING: Figure 1

Description

[Technical field]

[0001] The present invention relates to a biosignal measuring sensor for measuring a biosignal by closely contacting an electrode with a body surface. [Background technology]

[0002] It has been proposed to attach a biosignal measuring sensor to the human body to detect biosignals, and store the detected signals in an information processing device such as a server via a communication network for analysis. By detecting and analyzing such biosignals, it is possible to constantly monitor a person's health condition, and for example, it is possible to grasp the health condition of the circulatory system and prevent diseases such as heart disease and dyspnea.

[0003] Sensors for measuring biological signals are commercially available, including wristwatch-type pulse measuring devices equipped with an LED element that is worn on the wrist to measure pulse rate, and blood oxygen measuring devices such as pulse oximeters that are worn on the fingers to measure blood oxygen levels.

[0004] On the other hand, various sensors have been proposed for measuring biosignals such as electromyograms for measuring electrocardiograms and muscle conditions, nerve signals for measuring nerve activity, and electroencephalograms, which are essential for monitoring the circulatory system. For example, Patent Document 1 describes a bioelectrode having a resin film on which a conductive pattern is provided and an elastic base provided on the conductive pattern so as to face the resin film, in which the conductive pattern is formed of a plurality of electrode parts for detecting biosignals and a plurality of wiring parts each having one end connected to the plurality of electrode parts. Patent Document 2 describes an electrode for measuring bioelectric signals using a multi-electrode woven fabric in which a conductive region and a non-conductive region are formed by tapestry weaving using non-conductive yarns for the warp and conductive and non-conductive yarns for the weft, and the electrode is provided with a plurality of electrodes made of conductive regions. Patent Document 3 describes a biosignal detection garment comprising an electrode made of a conductive fiber structure, a measuring device for detecting and processing a bioelectric signal acquired by the electrode in contact with a living body, a wiring part for electrically connecting the electrode and the measuring device, and a garment main body in which the electrode, the measuring device, and the wiring part are arranged at predetermined positions.

[0005] Such sensors for measuring biological signals are attached to clothing or the like and worn on the surface of the human body. However, when measuring electrical signals emitted from a living body, poor contact between the electrode surface of the sensor and the skin of the human body can generate noise, making it difficult to obtain a sufficient amount of analyzable biological signals.

[0006] For this reason, it has been proposed to place a conductive liquid or a conductive resin sheet between the electrode surface of the sensor and the skin. As the conductive liquid, a liquid or gel having conductivity, such as physiological saline, ethylene glycol, or hyaluronic acid, is used, but the conductive liquid evaporates or flows out due to a decrease in viscosity caused by body temperature, which limits the measurement time.

[0007] In order to address these issues, Patent Document 4 describes a bioelectrode that includes a biosignal receiving unit consisting of a conductive porous body or a non-conductive porous body having a good conductive material or a non-polarizable material fixed to at least a part of its surface and interior, a connector part electrically connected to the biosignal receiving unit, a cover for suppressing water evaporation that covers the surface of the biosignal receiving unit opposite the surface that comes into contact with the living body, and a moisture replenishment mechanism that supplies moisture to the biosignal receiving unit using an electrolyte solution or non-electrolyte liquid. [Prior art documents] [Patent documents]

[0008] [Patent Document 1] Patent No. 3923861 [Patent Document 2] Patent No. 5487469 [Patent Document 3] Patent No. 6301969 [Patent Document 4] Patent No. 6073745 Summary of the Invention [Problem to be solved by the invention]

[0009] As described in Patent Document 1, when a resin film with a conductive pattern is used in a sensor, the conductive pattern is easily broken due to expansion, contraction, twisting, etc. of the resin film attached to the human body, and the resin film has low washing durability. Furthermore, when the resin film is in close contact with the surface of the human body, the user feels an uncomfortable sensation that is different from that of clothing.

[0010] In Patent Documents 2 and 3, electrodes and wiring are formed on the fabric of clothing using conductive fiber materials, but in Patent Document 2, the electrodes are arranged in a checkerboard pattern, which is different from the small electrodes recommended by medical professionals, and therefore the measurement accuracy of the electrocardiogram is inevitably impaired and reduced. Also, in Patent Document 3, the electrode part is impregnated with a conductive polymer, which is prone to peeling off, posing an issue in terms of washing durability.

[0011] In Patent Document 4, when a conductive liquid is interposed between the electrode surface of the sensor and the human skin, the sensor and its surroundings are constantly wet with liquid containing salts or ionic substances or retain its vapor, which may cause skin rashes due to the salts or ionic substances or skin disorders due to bacterial growth in the wet state.

[0012] In addition, biosignal measurement sensors must be kept clean because they are attached directly to the surface of the human body, and are washed together with clothing. During washing, sweat stains caused by sweating and washing with detergent to remove them can reduce the electrical conductivity of the material surface used for the electrodes, which can increase the electrical resistance of the electrodes and cause an increase in noise or poor measurement.

[0013] SUMMARY OF THE PRESENT DISCLOSURE ... An object of the present invention is to provide a sensor for measuring biological signals that can be attached comfortably to the surface of the human body and can stably measure biological signals. [Means for solving the problem]

[0014] The biosignal measuring sensor according to the present invention is a biosignal measuring sensor that is attached to a fabric of a garment, and includes an electrode body knitted by inserting a plurality of insertion yarns into a ground weave made of insulating knitting yarns, and a moisture supplying section that supplies moisture to the electrode body. The electrode body includes an electrode section in which conductive insertion yarns are continuously arranged in a planar shape as the insertion yarns in a part of a region on the side that contacts the human body surface and exposed, and an abutting section in which a plurality of insulating insertion yarns are arranged in a planar shape as the insertion yarns in a region surrounding the electrode section on the side that contacts the human body surface and exposed, and the moisture supplying section includes a moisture retaining section attached to a position facing the electrode section on the side opposite to the skin side of the fabric. Furthermore, the moisture supplying section includes a moisture guiding section that is attached to a position facing the electrode section on the skin side of the fabric and guides moisture from the moisture retaining section to the electrode section. Furthermore, the conductive insertion yarn is a yarn made of carbon nanotubes. Furthermore, the conductive insertion yarn is a spun yarn formed of a fiber material made of carbon nanotubes with an average fiber length of 80 μm to 350 μm. Furthermore, the conductive insertion yarn has an electrical conductivity of 10 3 The insulating insertion yarn is a yarn made of microfiber. Effect of the Invention

[0015] By virtue of the above-mentioned configuration, the present invention knits the electrode portion with knitting yarn and insertion yarn, giving it the same feel as the fabric of clothing, and moisture is supplied by seeping through the fabric to the electrode portion from the moisture retention portion provided on the opposite side of the fabric from the skin side, allowing the garment to be worn comfortably on the surface of the human body and enabling stable measurement of biological signals.

[0016] In addition, since the electrode part is exposed by continuously arranging the conductive insertion thread in a planar shape, a good conductive state can be ensured and the electrode part can be made compact. In addition, moisture can penetrate the conductive insertion thread to maintain a good conductive state. Furthermore, by using the conductive insertion thread continuously, the wiring can be configured without seams and breaks due to expansion, contraction, twisting, etc. can be prevented.

[0017] In addition, since the contact portion with the exposed insertion thread is provided in the area surrounding the electrode portion, the contact portion adheres closely to the surface of the human body, so that the electrode portion can be maintained in contact with the surface of the human body.Moisture supplied to the electrode portion also permeates the contact portion, so that the entire area surrounding the electrode portion can be kept in a stable moist state. [Brief description of the drawings]

[0018] [Figure 1] 1 is a schematic cross-sectional view of a biosignal measuring sensor according to the present invention. [Diagram 2] 2 is a schematic plan view of an electrode body used in an electrode portion of a biosignal measuring sensor, viewed from the human body surface side. FIG. [Diagram 3] 1 is a diagram illustrating an example of a knitting structure for knitting an electrode body. [Figure 4] FIG. 13 is an explanatory diagram showing an example in which a biosignal measuring sensor is attached to underwear. [Diagram 5] FIG. 13 is an explanatory diagram showing an example in which a biosignal measuring sensor is attached as a band wrapped around a limb. DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS

[0019] Hereinafter, the embodiments of the present invention will be described with reference to the drawings. Note that the embodiments described below are preferred examples for carrying out the present invention, and therefore various technical limitations are imposed thereon, but the present invention is not limited to these embodiments unless otherwise specified in the following description to limit the present invention.

[0020] Fig. 1 is a schematic cross-sectional view of a biosignal measuring sensor according to the present invention, and Fig. 2 is a schematic plan view of an electrode body used in the electrode section of the biosignal measuring sensor, viewed from the human body surface side. The biosignal measuring sensor includes an electrode body 1 that is disposed on the skin side of a clothing fabric C and has an electrode section 10, a connection section 11 and a contact section 12, and a moisture supply section 2 that supplies moisture to the electrode section 10.

[0021] The electrode body 1 is knitted by inserting a plurality of insertion threads into a ground structure made of insulating knitting yarn, and the electrode section 10 is configured by continuously arranging and exposing the conductive insertion thread L1 in a planar manner in the ground structure G1 in a portion of the region on the side that contacts the human body surface. The connection section 11 is attached by extending the conductive insertion thread L1 to the ground structure G1 that is extended with a predetermined width, and a contact section 13 is formed at the end by exposing the extended conductive insertion thread L1 in a planar manner. The contact section 12 is configured by exposing a plurality of insulating insertion threads L2 in a planar manner in the ground structure G2 in a region surrounding the electrode section 10 on the side that contacts the human body surface.

[0022] The electrode body 1 is knitted from a ground fabric to which multiple insertion threads are attached, so it can be made of a material similar to the fabric of clothing, and even when attached to clothing and worn, it can be deformed in the same way as clothing and can be worn on the surface of the human body without feeling unnatural.

[0023] Since the ground fabric G1 to which the conductive insertion thread L1 is attached is knitted using insulating knitting yarn, the conductive insertion thread L1 is attached in an electrically insulated state, and the connection part 11 can ensure the insulation state by covering the skin side on which the conductive insertion thread L1 is exposed with an insulating sheet or the like and attaching it to the fabric C.

[0024] In addition, since the conductive insertion thread L1 is made of a single continuous thread and attached to the ground tissue G1, it deforms in accordance with the deformation of the ground tissue G1, such as expansion, contraction, and twisting, and does not break. In the electrode section 10 and the contact section 13, a single conductive insertion thread L1 is folded back at a predetermined width and exposed in a planar shape, so that a sufficient conductive area can be secured in a compact size.

[0025] The contact parts 12 are arranged on both sides of the electrode part 10 so as to surround the electrode part 10, and a plurality of insulating insertion yarns L2 are exposed in a pile shape and arranged in a planar shape in the ground structure G2 made of insulating knitted yarn. Therefore, the contact parts 12 can be in contact with the surface of the human body with a pleasant feel.

[0026] FIG. 3 is a structural diagram illustrating a knitting structure for knitting an electrode body. In this example, the longitudinal direction of the ground structures G1 and G2 is the warp direction (the vertical direction in FIG. 3), and the width direction (the horizontal direction in FIG. 3) is the weft direction. The ground structures G1 and G2 have a warp knit structure consisting of a plurality of chain stitch rows arranged in the width direction at a predetermined interval using the knitting yarn L3, and in each chain stitch row, an elastic yarn L4 is passed through each stitch and woven so as to intertwine along the warp direction. Therefore, each chain stitch row is configured to be stretchable in the warp direction by the elastic yarn L4, and is in a state of contraction in the warp direction when no load is applied, but is in a state of elongation when a load is applied so as to pull in the warp direction.

[0027] In addition, the stitches of the same course when each chain stitch row is knitted form a stitch row that is linearly arranged in the weft direction. In the formed stitch row, the weft insertion yarn L5 passes through each stitch in the ground structure G1 and is inserted along the weft direction, and in the ground structure G2, the weft insertion yarn L6 passes through each stitch and is inserted along the weft direction. The weft insertion yarn L5 is inserted over the entire width of one stitch row of the ground structure G1, then turned back and inserted over the entire width of the stitch row of the next course, and is inserted into the stitch rows successively so as to swing over the entire width and knitted into the chain stitch row. The weft insertion yarn L6 is also knitted while being turned back over the entire width of the ground structure G2, similar to the weft insertion yarn L5. In the forming portion H of the abutting portion 12, the weft insertion yarns L5 and L6 are knitted so as to overlap at the turned back portion and be inserted into the chain stitch row to be connected and integrated.

[0028] The chain stitch row contracts in the longitudinal direction due to the elastic force of the elastic yarn 21, so that the whole can be stretched by pulling the ground structures G1 and G2 in the longitudinal direction, resulting in high stretchability in the longitudinal direction. Since the stitches of the chain stitch row are connected in the width direction by the weft insertion yarns L5 and L6 inserted in the weft direction, when the ground structures G1 and G2 stretch in the longitudinal direction, the chain stitch row stretches in the same manner in conjunction with each other. During the stretching operation, the stitch rows into which the weft insertion yarns L5 and L6 of the chain stitch row are inserted stretch the ground structures G1 and G2 so that the stitches move together in the longitudinal direction without shifting, so that a stable stretching operation is performed in the longitudinal direction.

[0029] In the contracted state, the ground structures G1 and G2 are arranged in a planar shape with the folded-back straight portions of the weft-insertion yarns L5 and L6 in close contact with each other. In addition, the ground structures G1 and G2 are hardly stretched or contracted in the weft direction because the weft-insertion yarns L5 and L6 are woven in the weft direction.

[0030] In the ground structure G1, a conductive insert yarn L1 is woven in the center, and weft insert yarns L7 and L8 are woven on both the left and right sides of the conductive insert yarn L1.

[0031] In the region corresponding to the electrode unit 10, the conductive insertion yarn L1 is folded back so as to overlap the weft insertion yarn L5 at a predetermined width and inserted into the stitch row. Therefore, like the weft insertion yarn L5, the ground structure G1 is arranged in a planar state in which the folded back linear parts of the conductive insertion yarn L1 are closely attached in a zigzag shape to form the electrode surface. The conductive insertion yarn L1 is arranged on the surface of the ground structure G1, and is fixed by the knitting yarn L3 that forms the inserted stitches, and is attached in an exposed state to the surface of the ground structure G1. The weft insertion yarns L7 and L8 are folded back so as to overlap the weft insertion yarn L5 on both sides of the folded back part of the conductive insertion yarn L1 and inserted into the stitch row, and the folded back parts are overlapped at the folded back part of the conductive insertion yarn L1 and inserted into the chain stitch row and connected. Therefore, in the electrode unit 10, the conductive insertion yarn L1 is held from both sides by the weft insertion yarns L7 and L8, and has shape stability against deformation such as expansion, contraction, and twisting.

[0032] In the region corresponding to the connection portion 11, the weft insertion yarns L7 and L8 are folded back so as to overlap with the weft insertion yarn L5 and inserted into the stitch row, and the folded back portions overlap each other in the central portion of the ground structure G1 and are inserted into the chain stitch row.

[0033] The conductive insertion yarn L1 is inserted into the overlapping chain stitches of the weft insertion yarns L7 and L8, leaving a space between each stitch (for example, three stitches), and is attached along the warp direction. Therefore, the conductive insertion yarn L1 is arranged on the surface of the ground structure G1, and is fixed by the knitting yarn L3 that forms the inserted stitches, and is attached in an exposed state on the surface of the ground structure G1.

[0034] In addition, the conductive insert yarn L1 is attached so as to be linear along the chain stitch row when the ground structure G1 is stretched, and when the ground structure G1 is contracted, it is in a slack state between the attached knitted yarn L3, and by using a twisted yarn capable of bending deformation as the conductive insert yarn L1, it is held in a meandering state in the weft direction. Therefore, even if the ground structure G1 expands or contracts, the conductive insert yarn L1 is hardly subjected to load in the yarn length direction.

[0035] The conductive insertion yarn L1 is held in the stitches together with the weft insertion yarn, and therefore moves together with the weft insertion yarn when the ground structure G1 expands and contracts in the longitudinal direction. Therefore, when the ground structure G1 is stretched by applying a tensile force in the longitudinal direction, the conductive insertion yarn L1 is stretched in the warp direction while maintaining its meandering shape with almost no deviation from the stitches. Even when the tensile force is released and the yarn returns to its original state, the conductive insertion yarn L1 maintains its original meandering shape with almost no deviation from the stitches, and almost no load is applied to the conductive insertion yarn L1 caused by deviation from the stitches when the ground structure G1 expands and contracts in the longitudinal direction.

[0036] In the contact portion 12, a plurality of insulating insert yarns L2 are arranged in the width direction and are attached by being inserted into the stitches along the chain stitch row. The insulating insert yarns L2 are inserted into the stitches sequentially with a plurality of stitches (for example, three stitches) spaced apart, and are attached to the ground tissue G2 by the knitting yarn L3, and are attached in an exposed state on the surface of the ground tissue G2. The insulating insert yarns L2 are attached so as to be linear along the chain stitch row when the ground tissue G2 is stretched, and are loosened between the knitting yarns L3 attached when the ground tissue G2 is contracted. Therefore, by using a non-twist yarn as the insulating insert yarn L2, the fibers spread out in a pile shape. The fibers spread out in a pile shape are arranged in a planar shape, and when the fibers are in close contact with the surface of the human body, a good feel similar to that of clothing can be obtained.

[0037] The knitting yarn used for the ground structure is preferably made of an insulating fiber material, but is not particularly limited and can be arbitrarily selected from known fiber materials. The yarn used for the chain knitting row can be, for example, synthetic fibers such as polyethylene terephthalate fiber, polytrimethylene terephthalate fiber, polybutylene terephthalate fiber, polyester-based elastomer fiber, polyamide-based fiber, polyacrylic fiber, polypropylene-based fiber, natural fibers such as cotton, hemp, wool, regenerated fibers such as cupra rayon, viscose rayon, lyocell, or any other fiber, and can be a mixture of multiple types of fiber materials. The yarn used for the elastic yarn can be a combination of polyurethane-based elastic fiber, polyolefin-based elastic fiber, natural rubber, synthetic rubber-based elastic fiber, etc. to provide elasticity.

[0038] The weft-inserted yarns are not particularly limited and can be arbitrarily selected from known fiber materials, such as synthetic fibers, such as polyethylene terephthalate fibers, polytrimethylene terephthalate fibers, polybutylene terephthalate fibers, polyester-based elastomer fibers, polyamide-based fibers, polyacrylic fibers, and polypropylene-based fibers, natural fibers, such as cotton, hemp, and wool, regenerated fibers, such as cupra rayon, viscose rayon, and lyocell, and other arbitrary fibers, and may be a mixture of multiple types of fiber materials.

[0039] The thickness of the knitting yarn, elastic yarn and weft-insertion yarn used in the ground structure is not particularly limited as long as it can be used in clothing, and may be appropriately selected within the range of 10 decitex to 4000 decitex.

[0040] The conductive insertion yarn may be a yarn made of a non-metallic material from the viewpoint of corrosion resistance and rust prevention, and is preferably a yarn made of a carbon material such as carbon fiber or carbon nanotube, and more preferably a yarn made of carbon nanotube. The conductive insertion yarn is preferably one having high electrical conductivity, specifically, an electrical conductivity of 10 3 It is preferable that the refractive index is 10 S / m or more. More preferably, 3 S / m~10 8 S / m, and 10 3 S / m~10 7 S / m is more preferable. The thickness of the conductive insertion yarn is desirably set to provide flexibility for bending deformation and to prevent breakage, and may be appropriately selected within the range of 20 decitex to 1000 decitex.

[0041] The insulating insertion yarn is preferably a yarn made of microfiber made of polyester-based or nylon-based fibers with a fiber diameter of 8 μm or less. The yarn made of microfiber has water absorption, breathability, and heat retention, and can increase the water retention around the electrode part, achieving a good texture. In addition, by using a non-twisted yarn, the fibers can be spread out and the entire contact part can be covered with microfiber in a planar manner.

[0042] When the electrode body is attached to clothing, it is expected that it will be washed together with the clothing, so a conductive thread that is durable against washing is preferred. For example, thread made of carbon nanotubes is particularly preferred because it has properties such as high water resistance and extremely low chemical reactivity.

[0043] A yarn made of carbon nanotubes can be produced by drawing out and spinning a large number of carbon nanotubes (carbon nanotube array) that are vertically aligned on a substrate. The individual carbon nanotubes drawn out from the carbon nanotube array are continuously aligned in the direction they are drawn out to form multiple fibers. A spun yarn is obtained by twisting these multiple fibers. Each carbon nanotube is preferably mainly made of double-walled carbon nanotubes, and preferably has a diameter of about 2 nm to 10 nm.

[0044] In the carbon nanotube array formed by vertically aligning these carbon nanotubes on a substrate, the length of the carbon nanotubes is preferably about 80 to 350 μm, and more preferably 100 to 200 μm, from the viewpoint of spinnability.

[0045] The resulting carbon nanotube yarn has an electrical conductivity of 10 3 It is preferable that the electrical conductivity is 10 S / m or more. 3 Below S / m, it becomes difficult to accurately measure weak biological signals.

[0046] Regarding the washing durability of the yarn made of carbon nanotubes, it is preferable that the decrease in electrical conductivity after being placed in a laundry net and washed 50 times in a top-loading fully automatic washing machine in a washing test method conforming to JIS L1930 2014 is less than 5%.

[0047] The electrode body 1 described above can be knitted using a known warp knitting machine capable of crochet knitting. Therefore, it is possible to knit into a shape other than the narrow tape shape described above, and for example, it can be knitted integrally into a shape according to the arrangement location of the sensor, such as a mesh shape, a bifurcated shape, or a trifurcated shape. In addition, although the warp knitted structure has been described as an example of a structure in which multiple chain stitch rows are arranged, other warp knitted structures may be used as long as they are a warp knitted structure in which stitch rows into which a weft insertion yarn can be inserted are knitted, and are not particularly limited.

[0048] The moisture supply section 2 includes a moisture retention section 20 attached to a position opposite the electrode section 10 on the side opposite the skin side of the fabric C, and a moisture guide section 21 attached to a position opposite the electrode section 10 on the skin side of the fabric C, and guides moisture from the moisture retention section 20 to the electrode section 10.

[0049] The moisture retention portion 20 is made of a material capable of retaining moisture such as sponge, and is attached in a state of intimate contact with the fabric C by a frame-shaped support portion 22 attached to the side of the fabric C opposite the skin side, and a cover portion 23 removably attached to the support portion 22. The support portion 22 can be formed, for example, by cutting a loop member of a hook-and-loop fastener into a frame shape and fixing it to the fabric C by sewing or the like, and the cover portion 23 can be formed, for example, by cutting a hook-and-loop fastener so as to cover the entire support portion 22 and removably attaching it to the support portion 22. Then, by pressing the cover portion 23 covering the moisture retention portion 20 with a finger or the like, the moisture impregnated in the moisture retention portion 20 can be pushed out toward the fabric C and transferred to the fabric C.

[0050] The moisture transferred to the fabric C seeps out into the moisture guide section 21 disposed opposite the moisture retention section 20. The moisture guide section 21 is, for example, a flexible sheet member such as silicone having a large number of through holes formed in the thickness direction, and the seeped moisture passes through the through holes and seeps into the electrode section 10. The moisture guide section 21 is attached to the surface of the fabric C facing the skin, and the back surface of the electrode body 1 that faces the electrode section 10 is attached to the surface of the moisture guide section 21 so that it abuts against the surface of the moisture guide section 21. The moisture guide section 21 and the electrode section 10 can be attached to the fabric C by sewing, gluing, or the like.

[0051] The electrode portion 10 attached to the fabric C via the moisture guide portion 21 protrudes toward the skin, so that when the garment is worn, the electrode portion 10 can be set in a state of being pressed against the surface of the human body, enabling it to be stably positioned at the measurement position.

[0052] In this way, moisture is efficiently supplied from the moisture supply unit 2 to the electrode unit 10. By pressing the moisture retention unit during measurement, it becomes possible to perform measurement in a state where the electrode unit 10 is sufficiently saturated with moisture, and stable measurement can be performed under the same conditions. In the moisture guide unit 21, the supplied moisture passes through and seeps into the electrode unit 10 without being retained, so that the propagation of bacteria in the retained moisture can be suppressed.

[0053] The moisture supplied to the electrode portion 10 spreads and permeates the contact portion 11 surrounding the electrode portion 10, thereby maintaining the electrode portion 10 in a moist state, making it possible to perform measurements without difficulty even when only a small amount of moisture is supplied.

[0054] In addition, since the moisture retention unit 20 is attached to clothing, it is warmed by the body temperature, and there is almost no cold sensation when moisture is supplied, so that the measurement can be performed without any discomfort. In addition, the supplied water does not contain any substances that leave a sticky feeling after use, such as physiological saline or organic conductive substances, so that a good feeling of use can be obtained. When sweating, the electrode unit 10 is impregnated with sweat, so there is no need to supply moisture, and there is an advantage that even a compact-sized moisture retention unit can be used without any problems.

[0055] 4 is an explanatory diagram of an example in which biosignal measuring sensors are attached to underwear. In this example, four sensors S1 to S4 are attached to the chest area of ​​the underwear fabric (not shown in the drawing), and the electrode parts of each sensor are arranged on the left and right shoulders and armpits. The connection parts of the electrode bodies of each sensor are arranged radially so as to connect to a signal processing unit P arranged in the center of the chest. The connection parts of the electrode bodies of each sensor are covered with an insulating sheet or the like, and are electrically insulated from the outside.

[0056] By attaching it in this manner, it becomes possible to measure biosignals such as electrocardiograms, and even when worn, the connection parts of the electrode bodies of each sensor expand and contract to follow bodily movements, allowing for stable measurements.

[0057] 5 is an explanatory diagram of an example where biosignal measuring sensors are attached as bands wrapped around the hands and feet. In this example, the sensors S5 to S9 are configured in a band shape by fixing the ends of the connection parts of the electrode bodies to the electrodes, forming them into ring shapes, and attaching elastic fabric to the surfaces. The band-shaped sensors S5 and S6 are worn by wrapping them around both ankles, sensors S7 and S8 around both wrists, and sensor S9 around the chest.

[0058] Since the connection part of each sensor is elastic, it can be attached in a state of being in close contact with the attachment part, and it is prevented from slipping from the attachment part. A signal processing part P is attached to the sensor S9 attached around the chest, and each sensor is connected to the signal processing part P by wiring to transmit a biosignal. In this example, since the electrode body is attached by wrapping it around the human body, it does not need to be attached to the fabric side by sewing or the like, and it is sufficient to set it in a state of contact with the moisture supply part attached to the fabric side.

[0059] By attaching the sensor in this manner, it becomes possible to measure biosignals such as electrocardiograms, and normal physical movements can be carried out without any hindrance even while the sensor is attached.

[0060] As described above, an electrode body is used that has the same elasticity and feel as the fabric of clothing, so the biosignal measurement sensor can be worn comfortably and stable biosignal measurement can be performed. [Explanation of symbols]

[0061] C...Fabric, G1, G2...Ground structure, L1...Conductive insertion thread, L2...Insulating insertion thread, 1...Electrode body, 10...Electrode section, 11...Connection section, 12...Abutment section, 13...Contact section, 2...Moisture supply section, 20...Moisture retention section, 21...Moisture guide section, 22...Support section, 23...Cover section

Claims

1. A sensor for measuring biosignals which is attached to the fabric of a garment, the sensor comprising: an electrode body knitted by inserting a plurality of insertion threads into a ground weave made of insulating knitted yarn; and a moisture supply unit which supplies moisture to the electrode body, the electrode body comprising: an electrode unit in which conductive insertion threads are continuously arranged in a planar shape as the insertion threads in a part of an area on the side which contacts the surface of the human body and exposed; and a contact unit in which a plurality of insulating insertion threads are arranged in a planar shape as the insertion threads in an area surrounding the electrode unit on the side which contacts the surface of the human body and exposed; the moisture supply unit comprising a moisture retention unit attached to a position facing the electrode unit on the side opposite the skin side of the fabric.

2. The sensor for measuring biological signals according to claim 1 , wherein the moisture supply section includes a moisture guide section attached to a position facing the electrode section on the skin side of the fabric and configured to guide moisture from the moisture retention section to the electrode section.

3. 3. The biosignal measuring sensor according to claim 1, wherein the conductive insertion yarn is a yarn made of carbon nanotubes.

4. 4. The biosignal measuring sensor according to claim 3, wherein the conductive insertion yarn is a spun yarn made of a fiber material made of carbon nanotubes having an average fiber length of 80 μm to 350 μm.

5. The conductive insertion yarn has an electrical conductivity of 10 3 5. The sensor for measuring a biological signal according to claim 3, wherein the resistance is S / m or more.

6. 6. The biosignal measuring sensor according to claim 1, wherein the insulating insertion thread is a microfiber thread.

7. 7. Clothing having the biosignal measuring sensor according to claim 1 attached thereto.

8. 7. An electrode body for use in a sensor for measuring biological signals as described in any one of claims 1 to 6, wherein the base fabric is knitted by inserting a weft insertion yarn into each of stitch rows arranged along the weft direction of a warp knitted fabric having elasticity in the warp direction, and the electrode portion is formed by folding back the continuous conductive insertion yarn in the weft direction and inserting it into the stitch rows in a portion of the area of ​​the base fabric that comes into contact with the body surface, thereby exposing it.

9. 9. The electrode body according to claim 8, further comprising a connection portion in which the warp knitted structure of the ground structure is extended in the warp direction by a predetermined width and the conductive insertion yarn is inserted into the stitch row and extended in the warp direction.

10. The electrode body according to claim 9 , wherein the connection portion has a contact portion formed by inserting the conductive insertion yarn into the stitch row while folding it back in the weft direction and exposing it.

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