WO2019044649A1 - 生体接触型電極および生体情報計測用衣服 - Google Patents
生体接触型電極および生体情報計測用衣服 Download PDFInfo
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- WO2019044649A1 WO2019044649A1 PCT/JP2018/031121 JP2018031121W WO2019044649A1 WO 2019044649 A1 WO2019044649 A1 WO 2019044649A1 JP 2018031121 W JP2018031121 W JP 2018031121W WO 2019044649 A1 WO2019044649 A1 WO 2019044649A1
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- electrode
- biocontact
- conductive
- static friction
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/24—Detecting, measuring or recording bioelectric or biomagnetic signals of the body or parts thereof
- A61B5/25—Bioelectric electrodes therefor
- A61B5/251—Means for maintaining electrode contact with the body
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/24—Detecting, measuring or recording bioelectric or biomagnetic signals of the body or parts thereof
- A61B5/25—Bioelectric electrodes therefor
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- A—HUMAN NECESSITIES
- A41—WEARING APPAREL
- A41D—OUTERWEAR; PROTECTIVE GARMENTS; ACCESSORIES
- A41D1/00—Garments
- A41D1/002—Garments adapted to accommodate electronic equipment
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- A—HUMAN NECESSITIES
- A41—WEARING APPAREL
- A41D—OUTERWEAR; PROTECTIVE GARMENTS; ACCESSORIES
- A41D13/00—Professional, industrial or sporting protective garments, e.g. surgeons' gowns or garments protecting against blows or punches
- A41D13/12—Surgeons' or patients' gowns or dresses
- A41D13/1236—Patients' garments
- A41D13/1281—Patients' garments with incorporated means for medical monitoring
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/24—Detecting, measuring or recording bioelectric or biomagnetic signals of the body or parts thereof
- A61B5/25—Bioelectric electrodes therefor
- A61B5/251—Means for maintaining electrode contact with the body
- A61B5/256—Wearable electrodes, e.g. having straps or bands
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/24—Detecting, measuring or recording bioelectric or biomagnetic signals of the body or parts thereof
- A61B5/25—Bioelectric electrodes therefor
- A61B5/263—Bioelectric electrodes therefor characterised by the electrode materials
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/24—Detecting, measuring or recording bioelectric or biomagnetic signals of the body or parts thereof
- A61B5/25—Bioelectric electrodes therefor
- A61B5/263—Bioelectric electrodes therefor characterised by the electrode materials
- A61B5/265—Bioelectric electrodes therefor characterised by the electrode materials containing silver or silver chloride
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/24—Detecting, measuring or recording bioelectric or biomagnetic signals of the body or parts thereof
- A61B5/25—Bioelectric electrodes therefor
- A61B5/263—Bioelectric electrodes therefor characterised by the electrode materials
- A61B5/268—Bioelectric electrodes therefor characterised by the electrode materials containing conductive polymers, e.g. PEDOT:PSS polymers
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/24—Detecting, measuring or recording bioelectric or biomagnetic signals of the body or parts thereof
- A61B5/25—Bioelectric electrodes therefor
- A61B5/263—Bioelectric electrodes therefor characterised by the electrode materials
- A61B5/27—Conductive fabrics or textiles
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/24—Detecting, measuring or recording bioelectric or biomagnetic signals of the body or parts thereof
- A61B5/25—Bioelectric electrodes therefor
- A61B5/279—Bioelectric electrodes therefor specially adapted for particular uses
- A61B5/28—Bioelectric electrodes therefor specially adapted for particular uses for electrocardiography [ECG]
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/68—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient
- A61B5/6801—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient specially adapted to be attached to or worn on the body surface
- A61B5/6802—Sensor mounted on worn items
- A61B5/6804—Garments; Clothes
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- H—ELECTRICITY
- H01—ELECTRIC ELEMENTS
- H01B—CABLES; CONDUCTORS; INSULATORS; SELECTION OF MATERIALS FOR THEIR CONDUCTIVE, INSULATING OR DIELECTRIC PROPERTIES
- H01B1/00—Conductors or conductive bodies characterised by the conductive materials; Selection of materials as conductors
- H01B1/06—Conductors or conductive bodies characterised by the conductive materials; Selection of materials as conductors mainly consisting of other non-metallic substances
- H01B1/12—Conductors or conductive bodies characterised by the conductive materials; Selection of materials as conductors mainly consisting of other non-metallic substances organic substances
- H01B1/124—Intrinsically conductive polymers
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- H—ELECTRICITY
- H01—ELECTRIC ELEMENTS
- H01B—CABLES; CONDUCTORS; INSULATORS; SELECTION OF MATERIALS FOR THEIR CONDUCTIVE, INSULATING OR DIELECTRIC PROPERTIES
- H01B1/00—Conductors or conductive bodies characterised by the conductive materials; Selection of materials as conductors
- H01B1/20—Conductive material dispersed in non-conductive organic material
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B2562/00—Details of sensors; Constructional details of sensor housings or probes; Accessories for sensors
- A61B2562/02—Details of sensors specially adapted for in-vivo measurements
- A61B2562/0209—Special features of electrodes classified in A61B5/24, A61B5/25, A61B5/283, A61B5/291, A61B5/296, A61B5/053
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B2562/00—Details of sensors; Constructional details of sensor housings or probes; Accessories for sensors
- A61B2562/12—Manufacturing methods specially adapted for producing sensors for in-vivo measurements
- A61B2562/125—Manufacturing methods specially adapted for producing sensors for in-vivo measurements characterised by the manufacture of electrodes
Definitions
- the present invention is a stretchable electrode useful for clothes for measuring biological information which is capable of measuring a weak electrical signal inside the living body by contacting the skin surface of the living body, and a living body using the electrode It relates to clothes for measuring information.
- an adhesive pad electrode made of a conductive adhesive material such as soft conductive solid gel having conductivity in order to measure a weak electric signal inside the living body such as an electroencephalogram, an electrocardiogram, an electromyogram etc.
- Patent Document 1 an adhesive pad electrode made of a conductive adhesive material such as soft conductive solid gel having conductivity in order to measure a weak electric signal inside the living body such as an electroencephalogram, an electrocardiogram, an electromyogram etc.
- an adsorption electrode (patent document 2) etc. which consists of a rubber ball and an electrode is used.
- a new garment attachment electrode has been devised to replace certain adsorption electrodes.
- an electrode combining a fabric electrode in which a metal conductor fiber such as stainless steel is woven and an electrode in which a part of the fabric electrode is impervious to water, and by impermeable to water, the skin and the electrode are sweated.
- the impedance between the skin and the electrode depends on sweating, so that it is not possible to obtain stable signal when dry skin or sweat is difficult to sweat, or when the sweat is applied, the electrode may cling to the skin There is a concern that it may stick and damage the feeling of wearing.
- a member with a high coefficient of friction is formed on a part of the cloth electrode composed of the conductive fiber structure. Means to be provided are taken (Patent Document 4). As described above, although it is possible to secure stability of signal acquisition by making the electrodes hard to shift, by providing a member having a high coefficient of friction in a part of the electrodes, the skin may be damaged or scratched when the electrodes and the skin are rubbed. You have to be careful.
- Patent Document 5 an electrode provided with a nonconductive fabric layer on one side of a conductive fabric knitted with metal plated fibers.
- Patent Document 5 the adhesion of the living body to the skin is good, and at the same time, itching and discomfort do not occur at the time of wearing, and the feeling of wearing is not impaired.
- the nonconductive layer becomes insulating between the conductive fabric and the skin. There is a concern that the electrical signal may be attenuated and the electrical signal may not be obtained stably.
- the wearer can wear the clothes even when it is dry or wet with rain or sweat.
- the electrodes are required to be stretchable and flexible without being easily shifted while being able to follow the clothes.
- the present invention is preferably flexible, capable of maintaining comfort when worn without concern that the electrode and the skin are rubbed while acquiring a stable electrical signal even in a dry or wet state.
- An object of the present invention is to provide a biocontact electrode.
- the present invention has the following configuration.
- a biocontact electrode used to measure a biosignal wherein the area of the electrode surface is 1 square centimeter or more, and the static friction coefficient ( ⁇ d) between the surface of the biocontact electrode and the dried skin is 0 .
- a biocontact electrode used to measure a biosignal wherein the area of the electrode surface is 1 square centimeter or more, and the static friction coefficient ( ⁇ w) between the surface of the biocontact electrode and the wet skin is 0.
- a biological contact electrode characterized by having 3 or more and 3.0 or less.
- the biocontact electrode according to [5] wherein the elastic resin binder has an elastic modulus of 1 GPa or less and an elongation at break of 200% or more.
- a static friction coefficient ( ⁇ d) between the surface of the biological contact electrode and the dry skin, and a static friction coefficient ( ⁇ w) between the surface of the biological contact electrode and the wet skin satisfy the following relational expression
- a clothing for measuring biological information comprising a plurality of the biological contact electrodes according to any one of [1] to [8].
- the coefficient of static friction ( ⁇ d) of the surface of the electric wiring portion with the dry skin excluding the electrode surface of the surface of the garment for measuring biological information except for the electrode surface is A garment for measuring biological information characterized by having a size of 0.5 or less.
- the coefficient of static friction ( ⁇ d) of the surface of the electrical wiring portion excluding the electrode surface of the surface of the clothing for measuring biological information excluding the electrode surface is Garment for biometric information measurement characterized by being 0.4 or less.
- a static friction coefficient ( ⁇ d) between the surface of the biological contact electrode and the dried skin, and a static friction coefficient ( ⁇ w) between the surface of the biological contact electrode and the wet skin satisfy the following relational expression
- a garment for measuring biological information comprising a plurality of the biological contact electrodes according to any one of the above [12] to [18].
- the coefficient of static friction ( ⁇ d) of the surface of the electrical wiring portion excluding the electrode surface on the surface of the garment for measuring biological information excluding the electrode surface is A garment for measuring biological information characterized by having a size of 0.5 or less.
- the clothes for measuring biological information according to the above [19], wherein the static friction coefficient ( ⁇ d) of the surface of the electric wiring portion excluding the electrode surface on the surface of the clothes for measuring biological information excluding the electrode surface is Garment for biometric information measurement characterized by being 0.4 or less.
- [22] The aforementioned [9], [10], [11], [19], [20], and the like, characterized by having a means for measuring the wearer's biological information and a mechanism for transmitting the measured information to the outside.
- the clothing for measuring biological information according to any one of [21].
- [23] The above-mentioned [9], [10], [11], [19], [20], [20], and [23] are characterized in that they have means for measuring biological information of the wearer and a mechanism for analyzing the measured information.
- the clothes for biometric information measurement as described in any one of 21].
- the present invention is a biocontact electrode using a stretchable conductor sheet or a conductive fabric comprising at least the conductive fine particles and the flexible resin binder as the conductive member of the surface of the biocontact electrode, wherein the biocontact electrode is a skin.
- biosignals can be obtained well, and in particular, the smaller the difference between the coefficient of friction when the skin is dry and when it is wet, the less discomfort the wearer has. It was made based on the findings.
- the area of the biocontact electrode attached to a part of the inside of the garment and brought into contact with the skin to measure the biosignal is 1 square centimeter or more, and the surface of the biocontact electrode is dry
- the coefficient of static friction ( ⁇ d) with the skin is 0.4 or more and 2.0 or less, preferably 0.5 or more and 2.0 or less.
- the coefficient of static friction of the garment fabric with the skin is generally at most about 0.5, so the biological contact electrode having a coefficient of static friction according to the present invention has a small difference in feel between the garment fabric and the electrode, and a comfortable feeling of wearing Can be maintained.
- the coefficient of static friction ( ⁇ w) between the surface of the biocontact electrode and the wet skin is 0.3 or more and 3.0 or less, sweat is applied during the summer or exercise, and between the biocontact electrode and the skin Even when sweat is accumulated, the feeling of wearing is not impaired because the difference in feel between the cloth and the electrode is small.
- the sheet resistance when unstretched biological contact electrode is not more than 300 [Omega ⁇ , and, since the sheet resistance increase ratio in elongation rate of 10% of the biological contact electrode is less than 10, an electrical signal required for the measurement As a result, a stable electrical signal is secured even if the electrode is stretched along with the fabric that deforms when the posture changes when worn. Also, because the tensile modulus of elasticity of the biocontact electrode is 1 GPa or less and the load at the time of elongation at an elongation rate of 10% of the biocontact electrode is 100N or less, the fabric deforms when it changes its posture when worn The electrodes follow, which reduces the discomfort.
- the stretchable conductor sheet comprising at least the conductive fine particles and the flexible resin binder as the component is used as the conductive layer on the surface of the biological contact electrode
- the coefficient of static friction ( ⁇ w) between ( ⁇ d) and the surface of the biocontact electrode and the moistened skin satisfy the following relational expression. 1.7 ⁇ ( ⁇ w) / ( ⁇ d) ⁇ 2.5
- the stretchable conductor sheet containing at least the conductive fine particles and the flexible resin binder as constituent components is used as the conductive layer on the surface of the biological contact electrode
- the water absorption of the stretchable conductor sheet is 0.5% by mass.
- the friction coefficient between dry skin and wet skin can be controlled by adjusting the amount to 25% by mass or less.
- the conductive particles and the insulating fine particles are used in combination to secure the electric signal by the conductive fine particles, and the insulating fine particles are used to adjust the coefficient of friction of the electrode surface.
- a void can be generated inside to secure water absorption, and fine particles can be fixed with a binder resin to maintain the shape as an electrode.
- the coefficient of static friction ( ⁇ d) between the surface of the biological contact electrode and the dried skin and the surface of the biological contact electrode wet It is preferable that the static friction coefficient ( ⁇ w) with the skin satisfy the following relational expression. 0.8 ⁇ ( ⁇ w) / ( ⁇ d) ⁇ 1.5 Thereby, the discomfort at the time of wear is reduced also at any time of normal time and sweating.
- the water retention rate of the conductive fabric is preferably at least 40% by mass, which means that the conductive fabric has both sufficient water supply capacity and retention capacity, and the difference in the coefficient of friction due to the degree of skin moisture is It becomes smaller and reduces the discomfort of the wearer.
- the upper limit of the water retention rate is about 350%.
- the biocontact electrode in the present invention is preferably an electrode that is flexible, foldable, and capable of reversibly elastically deforming by at least 2% by tension in the surface direction.
- the coefficient of static friction with respect to dry skin or wet skin in the present invention is a coefficient of static friction measured using a bioskin plate described later.
- the shape of the biocontact electrode is in the form of a sheet having an area of 1 square centimeter or more, and is attached to a part of the inside of the clothes. If the area is less than 1 square centimeter, a stable electrical signal can not be secured if the electrodes are displaced.
- the biocontact electrode has a layer structure having one or more conductive layers, and the coefficient of static friction ( ⁇ d) between the surface of the electrode in contact with the skin and the dried skin is 0.4 or more and 2.0 or less
- the electrode material and the electrode formation method are selected so as to be 0.5 or more and 2.0 or less.
- the biocontact electrode of the present invention may have a stretchable insulating layer on the side of the garment facing the fabric. The insulating layer may also serve as an adhesive layer for bonding the cloth and the biocontact electrode.
- the biological contact electrode of the present invention preferably has a coefficient of static friction between the surface of the biological contact electrode and the wet skin of 0.3 or more and 3.0 or less, preferably 0.4 or more and 3.0 or less.
- the coefficient of static friction with wet skin is preferably 1.5 or more and 2.5 or less.
- attaching using a liquid adhesive and a hot-melt adhesive sheet are mentioned.
- the conductive fine particles constituting the stretchable conductor sheet of the present invention, and preferably the insulating fine particles and the binder resin used in combination will be described.
- the conductive particles are metal-based particles and / or carbon-based particles, and as metal-based particles, metal particles such as silver, gold, platinum, palladium, copper, nickel, aluminum, zinc, lead, tin, brass, bronze, and copper Alloy particles such as solder, hybrid particles such as silver-coated copper, metal-plated polymer particles, metal-plated glass particles, metal-coated ceramic particles, and the like can be used.
- carbon-based fine particles graphite powder, activated carbon powder, scale-like graphite powder, acetylene black, ketjen black, fullerene, carbon nanotube and the like can be used.
- the conductive fine particles may be only one type or two or more types.
- the insulating fine particles are fine particles made of an organic or inorganic insulating material.
- resin fine particles such as acrylic resin fine particles, styrene resin fine particles, and melamine resin fine particles can be used.
- Inorganic fine particles include ceramic fine particles of silica, alumina, zirconia, talc, silicon carbide, magnesia, boron nitride and the like, and fine particles of salts poorly soluble in water, such as calcium phosphate, magnesium phosphate, barium sulfate and calcium sulfate It can be used.
- the insulating fine particles may be only one type or two or more types.
- the binder resin is preferably a resin having an elastic modulus of 1 GPa or less and an elongation at break of 200% or more, and examples thereof include thermoplastic resins, thermosetting and photocurable resins, and rubber elastomers.
- thermoplastic resin low density polyethylene, ethylene / vinyl acetate copolymer, polyvinylidene chloride, copolyester, etc. can be used.
- An acrylic resin, a silicone resin, a polyurethane resin etc. can be used as a heat
- Examples of the rubber / elastomer include urethane rubber, acrylic rubber, silicone rubber, butadiene rubber, nitrile rubber, isoprene rubber, styrene butadiene rubber, butyl rubber, chlorosulfonated polyethylene rubber, ethylene propylene rubber, vinylidene fluoride copolymer and the like.
- the binder resin may be only one type or two or more types.
- the biocontact type electrode of the present invention is further stirred after adding and stirring a solvent to the conductive fine particles, the insulating fine particles and the binder resin to liquefy it, and after coating or printing on a substrate, it is dried and the solvent is removed Obtained by a method obtained by the following method, a conductive fine particle, an insulating fine particle, and a liquid binder resin monomer are stirred, kneaded, liquefied, coated and printed on a substrate, and then cured by heating and light irradiation. be able to.
- the compounding amount of the conductive fine particles is determined in consideration of volume resistivity and stretchability, and when the volume percentage is large, the volume resistivity decreases and deterioration of the electric signal is suppressed, but the stretchability decreases, feeling of being drawn, feeling of fit Is worse. On the other hand, when the volume% is small, the elasticity is enhanced and the feeling of pulling and the feeling of fitting are improved, but the volume resistivity is increased and the electric signal is deteriorated.
- the blending amount of the conductive fine particles to the binder resin is preferably 20 to 60% by volume.
- the insulating fine particles can be blended in consideration of the volume resistivity and the static friction coefficient of the surface of the biocontact electrode.
- the addition of insulating fine particles can control the unevenness of the electrode surface and adjust the static friction coefficient.
- the compounding amount of the insulating fine particles to the binder resin is preferably 1 to 10% by volume.
- the water absorption rate of the elastic conductive sheet which comprises an elastic electrode is 0.5 mass% or more and 25 mass% or less.
- the conductive fabric in the present invention is a fiber structure having conductivity.
- a fiber structure composed of a fiber material containing at least conductive yarn or fiber can be used.
- Examples of the conductive fabric in the present invention include woven fabrics, knitted fabrics and non-woven fabrics composed of fibers containing conductive yarns (meaning including conductive yarns and conductive fibers; hereinafter the same).
- the conductive yarn means a yarn having a resistance of 100 ⁇ or less per 1 cm of fiber length.
- the conductive yarns include conductive fibers, fiber bundles of conductive fibers, twisted yarns obtained from fibers containing conductive fibers, braided yarns, spun yarns, blended yarns, ultrafine metal wires obtained by drawing metal wires in an extremely fine manner, films It is a generic term for ultra-fine films cut into ultra-fine fibers.
- the conductive fibers in the present invention include, for example, metal-coated chemical fibers or natural fibers, conductive metal oxide-coated chemical fibers or natural fibers, carbon-based conductive materials such as graphite, carbon, carbon nanotubes, graphene, etc. Chemical fibers or natural fibers coated with a conductive material, chemical fibers or natural fibers coated with a conductive polymer, and the like.
- a polymer material containing at least one conductive material selected from the group consisting of metals, conductive metal oxides, carbon conductive materials, and conductive polymers is spun. The fiber obtained can be used.
- a fiber bundle of the conductive fiber in the present invention for example, a fiber bundle made of microfibers or nanofibers of the conductive fiber is supported and impregnated with a conductive filler, a conductive polymer, etc. Can be used.
- a twisted yarn, a braided yarn, a spun yarn, a mixed yarn, etc. obtained using the fiber containing the conductive fiber may be used.
- the conductive yarns also include ultrafine metal wires obtained by drawing metal wires in an extremely thin manner.
- the conductive fibers, fiber bundles of the conductive fibers, twisted yarns obtained from fibers containing the conductive fibers, braided yarns, spun yarns, blended yarns, the average diameter of the ultrafine metal wires is preferably 250 ⁇ m or less, more preferably Is 120 ⁇ m or less, more preferably 80 ⁇ m or less, and particularly preferably 50 ⁇ m or less.
- the conductive yarn also includes an ultrafine film obtained by cutting a film into an ultrafine fibrous form, and the ultrafine film is a group consisting of metals, conductive metal oxides, carbon-based conductive materials, and conductive polymers. It means a fibrous film obtained by cutting a polymer film coated with at least one selected conductive material to a width of 800 ⁇ m or less.
- the conductive yarns at least one selected from the group consisting of chemical fibers coated with metal, a fiber bundle of conductive fibers carrying and impregnated with a conductive polymer, and ultrafine metal wires having an average diameter of 50 ⁇ m or less It is preferred to use a seed.
- a fiber structure in which a conductive yarn is embroidered on a nonconductive fabric and a fiber structure in which a solution containing a conductive polymer is impregnated in a nonconductive fabric and dried And a fiber structure impregnated with a solution containing a conductive filler and a binder resin and dried.
- a fiber structure in which a non-conductive cloth is impregnated with a conductive polymer-containing solution and dried it is preferable to use a fiber structure in which a non-conductive cloth is impregnated with a conductive polymer-containing solution and dried.
- the conductive polymer for example, a mixture containing poly (3,4-ethylenedioxythiophene) and polystyrene sulfonic acid can be preferably used.
- the fiber containing the conductive yarn is preferably a synthetic fiber multifilament, and at least a portion of the synthetic fiber multifilament is an ultrafine filament having a fineness of less than 30 dtex, or a fineness of more than 400 dtex and a single yarn fineness Is preferably a synthetic fiber multifilament of 0.2 dtex or less.
- the conductive fabric is a woven fabric made of fibers containing conductive yarns or is knitted, is the fabric weight less than 50 g / m 2 because priority is given to preventing the conductive polymer from falling off? It is preferable to exceed 300 g / m 2 for securing sufficient conductivity.
- the water retention rate of the conductive fabric in the present invention is 40% by mass or more and 350% by mass or less.
- the upper limit of the water retention rate is preferably 200% by mass, more preferably 150% by mass. If the water retention rate falls below this range, the difference in the coefficient of static friction of the biocontact electrode with dry and wet skin tends to be large, which is not preferable.
- the water retention rate in the present invention is the method described in JIS L 1913: 2010 General nonwoven fabric test method.
- the shape of the biocontact electrode is in the form of a sheet having an area of 1 square centimeter or more, and is attached to a part of the inside of the garment. If the area is less than 1 square centimeter, a stable electrical signal can not be secured if the electrodes are displaced.
- the biocontact electrode has one or more conductive layers, and the coefficient of static friction ( ⁇ d) between the surface of the conductive layer in contact with the skin and the dried skin is 0.4 or more and 2.0 or less, preferably 0.
- the electrode material and the electrode formation method are selected so as to be 45 or more and 2.0 or less, more preferably 0.5 or more and 0.8 or less.
- the biocontact electrode of the present invention may have a stretchable insulating layer on the side of the garment facing the fabric.
- the insulating layer may also serve as an adhesive layer for bonding the cloth and the biocontact electrode.
- the biocontact electrode according to the present invention is always used in contact with the skin to measure a biosignal, thereby securing a stable electrical signal even during activity associated with sweating.
- the coefficient of static friction between the surface of the biocontact electrode and the moistened skin is preferably 0.3 or more and 3.0 or less, in order to maintain the feeling of wearing without causing skin tears and inflammation. More preferably, it is 0.35 or more and 1.5 or less.
- the clothing for measuring biological information according to the present invention has a configuration in which the living body contact type electrode according to the present invention is attached to a part of the inside of the clothing.
- the base material of the clothing for measuring biological information according to the present invention is not particularly limited as long as it is a belt, a band-like article such as a bra, and / or a woven or non-woven fabric. In view of the fit to the body when worn and the followability of exercise and movement, etc., those having stretchability are preferable.
- Such clothing for measuring biological information serves as a means for measuring the biological information of the wearer, has a normal wearing method and feeling of wearing, and can simply measure various types of biological information simply by wearing.
- the clothing for measuring biological information provided with the biological contact electrode of the present invention is provided with an electrical wiring for connecting a signal obtained from the electrode to a measurement system.
- the electrical wiring may be made of the same material as the biocontact electrode, or any other conductor, preferably a conductor having extensibility.
- the conductor material preferably used in the present invention is a metal foil, a conductive yarn, a stretchable wire, a conductive fabric or the like.
- a conductive fine wire made of metal fine wires, metal plated fibers, a hybrid material of fibers and a conductive polymer, or the like can be used.
- the conductive yarn can be embroidered in a zigzag manner to realize stretchability in a pseudo manner.
- extensibility can also be exhibited by arranging with redundancy by braiding or the like.
- the electrical wiring portion needs insulation for safety, leakage prevention, and maintenance of signal quality. As such insulation, in the case of a telescopic wire, it is a wire coating.
- an insulating coat having flexibility and stretchability is preferably used.
- a method of attaching the biocontact electrode to clothes there is a method of forming the biocontact electrodes in advance and then sewing using threads, a method of bonding using a liquid adhesive or a hot melt adhesive sheet, and clothing It is possible to use a method of directly sewing a conductive yarn on a cloth, a method of partially knitting using a conductive yarn to construct clothes, and the like.
- the electrical properties of the biocontact electrode according to the present invention have a sheet resistance of 300 ⁇ ⁇ or less when unstretched and have a sheet resistance low enough to measure a weak biosignal, and the sheet resistance increase ratio at an elongation rate of 10% is 10 Obtain a stable electrical signal even if the electrode stretches with the fabric when worn. When the sheet resistance at unstretched time exceeds 300 ⁇ ⁇ and the sheet resistance increase ratio at an elongation rate of 10% is 10 or more, a stable electrical signal can not be obtained.
- the tensile property of the biological contact electrode of the present invention is 1 GPa or less, and the load at the time of elongation at a 10% elongation coefficient of the biological contact electrode is 100 N or less. Even when the fabric is stretched, the electrodes follow and stretch, and the wearing feeling is not impaired.
- the insulating layer can be formed by coating of a flexible resin or lamination of a flexible resin sheet.
- a flexible resin that can be used as the insulating layer of the present invention, it is preferable to use a resin having an elastic modulus of 1 GPa or less and a breaking elongation of 200% or more, and a thermoplastic resin, a heat / photocurable resin , Rubber, elastomer and the like.
- thermoplastic resin low density polyethylene, ethylene / vinyl acetate copolymer, polyvinylidene chloride, copolyester, etc. can be used.
- An acrylic resin, a silicone resin, a polyurethane resin etc. can be used as a heat
- the rubber / elastomer include urethane rubber, acrylic rubber, silicone rubber, butadiene rubber, nitrile rubber, isoprene rubber, styrene butadiene rubber, butyl rubber, chlorosulfonated polyethylene rubber, ethylene propylene rubber, vinylidene fluoride copolymer and the like.
- the binder resin may be only one type or two or more types.
- the dried skin of the surface of the electric wiring portion excluding the electrode surface of the surface contacting the living body of the clothing for measuring biological information regardless of the material of the contact surface.
- the coefficient of static friction ( ⁇ d) is preferably 0.50 or less, more preferably 0.40 or less, and still more preferably 0.25 or less.
- the surface of the electrical wiring means the surface of the insulating film when the electrical wiring is accompanied by insulation.
- the coefficient of static friction ( ⁇ d) with the wet skin of the surface of the electrical wiring portion excluding the electrode surface of the surface contacting the living body of the clothing for measuring biological information regardless of the material of the contact surface Is preferably 0.4 or less, more preferably 0.32 or less. It is more preferable that it is 0.24 or less. If the coefficient of friction of the electrical wiring portion with dry or wet skin exceeds this range, the subject may feel discomfort when worn. If the wearer feels uncomfortable, the biological information may be affected, which is not preferable.
- a stretchable conductor sheet containing conductive fine particles and a flexible resin binder at least as constituent components is used as a conductive member on the surface of a biological contact electrode.
- a conductive paste Using the materials shown in Table 1, the resin was dissolved in each solvent according to the weight blending ratio shown in Table 2, and the resulting solution was blended with silver particles and mixed in a three roll mill to obtain a conductive paste .
- the hot melt sheet shown in Table 1 and release paper shown in Table 1 are superimposed on the release contact processed biomedical electrode with PET film, and bonded with a roll laminator with the rubber roll temperature adjusted to 120 ° C, and an adhesive biological body A contact type electrode sheet was obtained.
- the living contact electrode sheet was cut out into a 5.0 cm square with a wiring width of 1.0 cm and a wiring length of 15.0 cm. Release the release paper from the cut out electrode with wire, place it at a predetermined position on the back side of the shirt (100% polyester), thermocompression-bond it with an iron, peel off the release-treated PET film, and put the electrode on the back Was produced.
- the stretchable conductive material sheet prepared above is held so as to have a distance of 5.0 cm between the chucks using a stretch tester (manual drawing machine) equipped with two 2.5 cm-wide chucks, and stretched in the longitudinal direction Elongation (displacement 0.5 cm) to a rate of 10%.
- the sheet resistance before and after the test uses a digital multimeter (“YOKOGAWA TY 530” made by Yokogawa Meter & Instruments) and measures the resistance ( ⁇ ) before and after extension on the outside (measurement distance 10 cm) of the two opposing chucks.
- the sheet resistance ( ⁇ ⁇ ) of the biocontact electrode was obtained.
- the measurement of the resistance value was performed immediately after the extension (within 3 seconds).
- the static friction coefficient of the biological contact electrode on the simulated skin was measured and determined as follows using a static friction coefficient measuring machine (manufactured by Shinto Scientific Co., Ltd., Tribogear TYPE: 10).
- the artificial skin used for evaluation is a bioskin plate that has the surface of a urethane elastomer film processed to reproduce the hydrophilicity and the surface wrinkles close to human skin (product number: P001-001, vertical 195 mm, manufactured by Viewrack Co., Ltd.) X 120 mm in width x 5 mm in thickness was used.
- test piece After immersion, the test piece is taken out of the immersion tank, sandwiched between two 200 mm ⁇ 200 mm square filter papers, and pressed with a 6.75 kg weight of 100 mm ⁇ 100 mm for 3 seconds, and the mass of the test piece immediately (Ww, mg ) Was measured, and the water absorption (c, mass%) was determined by the following formula (1).
- c (Ww-Wd) / Wd x 100 ...
- the signal-to-noise ratio at the time of electrocardiogram measurement uses the dispersion of the amplitude of R wave as a signal (S) from the waveform of the electrocardiogram excluding one minute at the beginning and one minute at the end of gymnastic time.
- the variance of the amplitude was noise (N), and the SN ratio was determined by the S / N equation.
- S signal
- N noise
- Example 2 A pair of component sheets in which the sheet of the biological contact electrode obtained in Example 1 was demolded integrated with the biological contact electrode part, the electrical wiring part and the connector part were produced. Next, it was placed on the left and right control so that the electrode placement portion was positioned about 10 cm below the teat equivalent position on the chest of a sports shirt made of knitted fabric using polyester-cotton-polyurethane blend spinning, and was laminated using an iron. Furthermore, using a brand name "Mobilon" (made by Nisshinbo Co., Ltd.), which is a urethane sheet with a hot melt layer, as an insulating layer, the electric wiring portion was pasted with an iron so as to cover the electric wiring portion.
- Mobilon made by Nisshinbo Co., Ltd.
- the coefficient of friction when dry between the surface of the electric wiring portion (the insulating layer covered with the electric wiring) and the bioskin plate was 0.36, and the coefficient of friction when wet was 0.24.
- a snap hook was sewn with a conductive thread on a connector portion corresponding to the opposite end of the biocontact electrode of the electrical wiring to make a connector, thereby obtaining a garment for measuring biological information.
- a heart rate sensor WHS-2 manufactured by Union Tool which has a wireless data transmission function to a smart phone as a detachable electronic unit, is connected to the obtained garment for measuring biological information, and an electrocardiogram signal from WHS-2 simultaneously with measurement.
- To the smart phone and set it to be able to display the screen data with the Apple smart phone made by Apple Inc. incorporating the application "myBeat” dedicated to the heart rate sensor WHS-2 and set RRI (ms (ms)) And HR (bpm (heart rate / minute)) could be measured.
- Example 2 The sheet-like biocontact electrode obtained in Example 2 was punched into a shape having a major axis of 40 mm and a minor axis of 20 mm to form an electrode portion.
- the electrodes are attached using an iron at substantially the same position as in the application example 1, and conduction is further directed from the left and right electrodes toward the center of the chest of the sports shirt.
- a thread (silver-coated thread) is embroidered in a zigzag to form an electrical wiring portion, and a snap hook for connection is sewn with a conductive thread at a predetermined position to provide a connector.
- the same fabric as the sports shirt is sewed to cover the inner side of the garment on which the silver coat yarn is embroidered, to form an insulating cover, and as a garment for measuring biological information.
- the coefficient of friction when dry between the surface of the electrical wiring portion (insulation cover placed on the electrical wiring) and the bioskin plate was 0.16, and the coefficient of friction when wet was 0.23.
- a system having a heart rate measurement function was configured in the same manner as in Application Example 1, and was worn by five subjects, and while performing electrocardiogram measurement, the first radio gymnastics and the second radio gymnastics were continuously performed. As a result, the electrocardiogram measurement during exercises of all five subjects could be implemented without any problem. Also, none of the five subjects complained of discomfort or discomfort.
- an insulating cover was formed using a caulking agent of silicone resin, not the same fabric as a sports shirt, as an insulating cover.
- the coefficient of friction with the bioskin plate of the electrical wiring portion having the insulating cover layer of the silicone resin caulking agent was 0.56 when dry, and the coefficient of friction when wet was 0.42.
- a system having a heart rate measurement function was configured in the same manner as in Application Example 1, and was worn by five subjects, and while performing electrocardiogram measurement, the first radio gymnastics and the second radio gymnastics were continuously performed.
- noise increased in two of the five subjects who had relatively large amounts of sweating, making it impossible to measure the electrocardiogram.
- the two also complained that they felt the sense that the sports shirts were gradually drawn with sweating.
- ⁇ Production example 1 of conductive yarn> A twisted yarn (250 denier) of nylon fiber was silver plated by electroless plating.
- the twisted yarn is immersed in a refining agent and washed with water, and then immersed in an aqueous solution containing 10 g / liter of stannous chloride and 20 ml / liter of 35% hydrochloric acid and then washed by water.
- a predetermined amount of electroless silver plating solution having the following composition was used to coat 10% by mass of silver.
- ⁇ Production example 3 of conductive yarn> A polyester multifilament textured yarn of 50 denier 24 filaments is subjected to 10% weight reduction processing by alkaline hydrolysis, and after sufficient washing with water, subsequently, 0.3 g / L of palladium chloride, 30 g / L of stannous chloride, 36% After being immersed in a 40 ° C. aqueous solution containing 300 ml / L of hydrochloric acid, it was washed with water. Subsequently, the substrate was immersed in 0.1 N borofluoric acid and washed with water.
- ⁇ Production example 4 of conductive yarn> The spun yarn of the ultrafine fiber Berryma X manufactured by KB Salen Co., Ltd. is immersed in the conductive paint Denatron used as the conductive component using the thiophene-based conductive polymer PEDOT: PSS, and subjected to ultrasonic treatment for 3 minutes, and then squeezed. While pulling up and drying, a conductive yarn (F4) impregnated with a conductive polymer was obtained. The resistance value per 1 cm of yarn length of the obtained conductive yarn was 40 ⁇ .
- ⁇ Production example 5 of conductive yarn> Nineteen strands of copper silver alloy (diameter 80 ⁇ m) manufactured by Showa Electric Cable Co., Ltd. were twisted to obtain a conductive thread (F5). The resistance value per 1 cm of the obtained conductive yarn F5 was 0.026 m ⁇ .
- conductive yarn A conductive yarn Krakabo KC-792R-B22T4 manufactured by Kuraray Trading Co., Ltd., in which heat resistant nylon is used as core fiber and the surface is coated with carbon-containing nylon 6 resin, is used as the conductive yarn (F6).
- the resistance value per 1 cm of the conductive yarn F6 was 500 k ⁇ .
- the resistance value of this conductive yarn it measured using the normal tester.
- the characteristic values in Table 3 were measured by the following method.
- the stretchable conductive material sheet prepared above is held so as to have a distance of 5.0 cm between the chucks using a stretch tester (manual drawing machine) equipped with two 2.5 cm-wide chucks, and stretched in the longitudinal direction Elongation (displacement 0.5 cm) to a rate of 10%.
- the sheet resistance before and after the test uses a digital multimeter (“YOKOGAWA TY 530” made by Yokogawa Meter & Instruments) and measures the resistance ( ⁇ ) before and after extension on the outside (measurement distance 10 cm) of the two opposing chucks.
- the sheet resistance ( ⁇ ⁇ ) of the biocontact electrode was obtained.
- the measurement of the resistance value was performed immediately after the extension (within 3 seconds).
- the coefficient of static friction was measured and determined for each of the dry skin and the wet skin with respect to the simulated skin of the biocontact electrode using a friction coefficient measuring machine (manufactured by Shinto Scientific Co., Ltd., Trivogear TYPE: 10) as follows.
- the artificial skin used for evaluation is a bioskin plate that has the surface of a urethane elastomer film processed to reproduce the hydrophilicity and the surface wrinkles close to human skin (product number: P001-001, vertical 195 mm, manufactured by Viewrack Co., Ltd.) X 120 mm in width x 5 mm in thickness was used.
- biocontact electrode sheet The conductive fabric obtained on the release-treated PET film is temporarily bonded, and the hot melt sheet and release paper are further stacked, and bonded with a roll laminating machine in which the rubber roll temperature is adjusted to 120 ° C.
- One biocontact electrode sheet was obtained. This biocontact electrode sheet was cut out into a rectangle having a wiring width of 1.0 cm and a wiring length of 15.0 cm, and a circle having a diameter of 5.0 cm directly connected to the substantially rectangular shape. The circular part corresponds to the electrode, and the rectangular part corresponds to the wiring part.
- the cut out biological contact electrode sheet is peeled off from the release-treated PET film, placed at a predetermined position on the back side of the shirt (100% polyester), thermocompression-bonded with an iron, and the hot melt sheet overlaid on the wiring portion It pressure-bonded and produced the shirt provided with the electrode and wiring on the back side, without the insulating layer.
- a stainless steel hook is attached to the front side of the wiring end of the shirt provided with the obtained electrodes and wiring so as to be conductive with the wiring on the back side, and the heart rate sensor WHS-2 manufactured by Union Tool Co., Ltd. is made via the stainless steel hook. Were connected to make a shirt incorporating a heart rate measurement function.
- the signal-to-noise ratio at the time of electrocardiogram measurement uses the dispersion of the amplitude of R wave as a signal (S) from the waveform of the electrocardiogram excluding one minute at the beginning and one minute at the end of gymnastic time.
- the variance of the amplitude was noise (N), and the SN ratio was determined by the S / N equation.
- Evaluation of the clothing for biological information measurement provided with the electrode and wiring which consist of a conductive fabric using the conductive yarn obtained similarly below was performed. The results are shown in Table 3.
- the biocontact electrode according to the present invention suppresses stimulation on the skin and does not impair the comfort or the feeling of wearing, and suppresses the displacement of the electrode and reduces electrical noise. Few bioelectric signals can be obtained.
- the clothing for measuring biological information of the configuration of the present invention is useful as an input interface of a system for measuring biological information, as understood from the fact that electrocardiographic measurement is possible even during exercise. It can be used.
- the present invention provides a living body contact type electrode and a garment for measuring biological information, which enables good measurement without impairing the wearing comfort and wearing feeling even under dry conditions in winter and high humidity conditions in summer.
- the present invention can be applied to health management of daily life, grasping of biological information at the time of outdoor sports such as jogging and marathon, and labor management at outdoor work such as construction site.
- the description is assumed to be worn by a human, but the present invention is not limited to human use, and can be widely used for pets, livestock, and wild animals.
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Abstract
Description
[1] 生体信号を測定するため用いられる生体接触型電極であって、電極表面の面積が1平方センチメートル以上であり、前記生体接触型電極の表面と乾燥した皮膚との静摩擦係数(μd)が0.4以上、2.0以下であることを特徴とする生体接触型電極。
[2] 生体接触型電極の表面と乾燥した皮膚との静摩擦係数(μd)が0.5以上、2.0以下であることを特徴とする[1]に記載の生体接触型電極。
[3] 生体信号を測定するため用いられる生体接触型電極であって、電極表面の面積が1平方センチメートル以上であり、生体接触型電極の表面と湿潤した皮膚との静摩擦係数(μw)が0.3以上、3.0以下であることを特徴とする生体接触型電極。
[4] 生体接触型電極の表面と湿潤した皮膚との静摩擦係数(μw)が0.4以上、3.0以下であることを特徴とする[3]に記載の生体接触型電極。
[5] 導電性微粒子と柔軟性樹脂バインダーを少なくとも構成成分とする伸縮性導体シートを生体接触電極の表面の導電部材として用いたことを特徴とする[1]から[4]のいずれか一項に記載の生体接触型電極。
[6] 前記柔軟性樹脂バインダーの弾性率が1GPa以下で、かつ、破断伸度が200%以上であることを特徴とする[5]に記載の生体接触型電極。
[7] 生体接触型電極の表面と乾燥した皮膚との静摩擦係数(μd)と、生体接触型電極の表面と湿潤した皮膚との静摩擦係数(μw)が以下の関係式を満たすことを特徴とする[5]または[6]のいずれかに記載の生体接触型電極。
1.7≦(μw)/(μd)≦2.5
[8] 前記伸縮性導体シートの吸水率が0.5質量%以上 25質量%以下であることを特徴とする[5]から[7]のいずれか一項に記載の生体接触型電極。
[9] 前記[1]から[8]のいずれかに記載の生体接触型電極を複数備えることを特徴とする生体情報計測用衣服。
[10] 前記[9]に記載の生体情報計測用衣服において、前記生体情報計測用衣服の生体と接触する面の電極表面を除く電気配線部表面の乾燥した皮膚との静摩擦係数(μd)が0.5以下であることを特徴とする生体情報計測用衣服。
[11] 前記[9]に記載の生体情報計測用衣服において、前記生体情報計測用衣服の生体と接触する面の電極表面を除く電気配線部表面の湿潤した皮膚との静摩擦係数(μd)が0.4以下であることを特徴とする生体情報計測用衣服。
[13] 導電性ファブリックを生体接触電極の表面の導電部材として用いたことを特徴とする[3]または[4]に記載の生体接触型電極。
[14] 前記導電性ファブリックが、導電性繊維を少なくとも構成要素とする伸縮性の導電布帛からなることを特徴とする[12]または[13]に記載の生体接触型電極。
[15] 前記導電性ファブリックが、金属被覆合成繊維を10質量%以上含む織物、編み物、不織布から選択される少なくとも一つの導電性ファブリックであることを特徴とする[12]から[14]のいずれか一項に記載の生体接触型電極。
[16] 前記導電性ファブリックが、化学合成繊維と導電性高分子のハイブリッド材料を含むことを特徴とする[12]から[14]のいずれか一項に記載の生体接触型電極。
[17] 生体接触型電極の表面と乾燥した皮膚との静摩擦係数(μd)と、生体接触型電極の表面と湿潤した皮膚との静摩擦係数(μw)が以下の関係式を満たすことを特徴とする[12]から[16]のいずれか一項に記載の生体接触型電極。
0.8≦(μw)/(μd)≦1.5
[18] 前記導電性ファブリックの保水率が40質量%以上350%以下であることを特徴とする[12]から[17]のいずれか一項に記載の生体接触型電極。
[19] 前記[12]から[18]のいずれか一項に記載の生体接触型電極を複数備える事を特徴とする生体情報計測用衣服。
[20] 前記[19]に記載の生体情報計測用衣服において、前記生体情報計測用衣服の生体と接触する面の電極表面を除く電気配線部表面の乾燥した皮膚との静摩擦係数(μd)が0.5以下であることを特徴とする生体情報計測用衣服。
[21] 前記[19]に記載の生体情報計測用衣服において、前記生体情報計測用衣服の生体と接触する面の電極表面を除く電気配線部表面の湿潤した皮膚との静摩擦係数(μd)が0.4以下であることを特徴とする生体情報計測用衣服。
[22] 着用者の生体情報を計測する手段と計測した情報を外部に送信する機構を有する事を特徴とする前記[9]、[10]、[11]、[19]、[20]、[21]のいずれか一項に記載の生体情報計測用衣服。
[23] 着用者の生体情報を計測する手段と、計測した情報を解析する機構を有する事を特徴とする前記[9]、[10]、[11]、[19]、[20]、[21]のいずれか一項に記載の生体情報計測用衣服。
[24] 絶縁性微粒子がバインダー樹脂に対し、1~10体積%配合されていることを特徴とする[5]から[8]のいずれか一項に記載の生体接触型電極。
[25] 絶縁性微粒子がバインダー樹脂に対し、1~10体積%配合されていることを特徴とする[9]から[11]のいずれか一項に記載の生体情報計測用衣服。
1.7≦(μw)/(μd)≦2.5
これにより、平常時、発汗時のいずれにおいても着用時の違和感が低減される。
0.8≦(μw)/(μd)≦1.5
これにより、平常時、発汗時のいずれにおいても着用時の違和感が低減される。
生体接触型電極の形状は、面積が1平方センチメートル以上のシート状で、衣服内側の一部に取り付けられる。面積が1平方センチメートル未満の場合には、電極がずれた場合に安定な電気信号を確保できない。生体接触型電極は導電性を持つ層を一層または二層以上の層構造を持ち、皮膚に接触する電極の表面と乾燥した皮膚との静摩擦係数(μd)が0.4以上、2.0以下、好ましくは0.5以上、2.0以下となるように電極材料と電極作成方法が選定される。静摩擦係数(μd)が0.4以上、好ましくは0.5以上とすることにより、電極が容易にずれることを防止し、安定した電気信号を確保できる。また静摩擦係数(μd)を2.0以下に保つことにより、着用感を損なうことなく、また皮膚の破傷や炎症を未然に防止することができる。
本発明の生体接触型電極は、衣服の生地に面する側に伸縮性のある絶縁層を有してもよい。この絶縁層は衣服生地と生体接触型電極を接着する接着層を兼ねても良い。
本発明において伸縮性導体シートを生体接触型電極の接触面に用いる場合には、湿潤した皮膚との静摩擦係数は1.5以上、2.5以下であることが好ましい。
湿潤した皮膚との静摩擦係数をこの範囲に制御することにより、発汗に伴う活動時においても安定な電気信号を確保するとともに、皮膚の破傷や炎症を防ぎ、さらに電極が皮膚にまとわりつくことによる不快感を低減することができる。
導電性微粒子は金属系微粒子およびまたは炭素系微粒子であり、金属系微粒子としては、銀、金、白金、パラジウム、銅、ニッケル、アルミニウム、亜鉛、鉛、錫などの金属粒子、黄銅、青銅、白銅、半田などの合金粒子、銀被覆銅のようなハイブリッド粒子、さらには金属メッキした高分子粒子、金属メッキしたガラス粒子、金属被覆したセラミック粒子などを用いることができる。炭素系微粒子としては、グラファイト粉末、活性炭粉末、鱗片状黒鉛粉末、アセチレンブラック、ケッチェンブラック、フラーレン、カーボンナノチューブなどを用いることができる。導電性微粒子は1種のみであってもよいし2種以上であってもよい。
本発明の生体接触型電極は、導電性微粒子と絶縁性微粒子およびバインダー樹脂にさらに溶剤を加えて攪拌・混練りし液状化し、基材上にコーティング、ないし印刷した後に、乾燥し溶剤を除去することで得る方法や、導電性微粒子と絶縁性微粒子および液状バインダー樹脂モノマーを攪拌・混練りし液状化し、基材上にコーティング、ないし印刷した後に、加熱・光照射により硬化して得る方法によって得ることができる。
前記導電糸とは、繊維長1cmあたりの抵抗値が100Ω以下の糸を意味する。
前記導電糸とは、導電性繊維、導電性繊維の繊維束、導電性繊維を含む繊維から得られる撚糸、組み糸、紡績糸、混紡糸、金属線を極細に延伸した極細金属線、フィルムを極細の繊維状に切断した極細フィルムの総称である。
また、前記導電性繊維として、例えば、金属、導電性金属酸化物、カーボン系導電性材料、および導電性高分子よりなる群から選ばれる少なくとも1種の導電性材料を含む高分子材料を紡糸して得られた繊維を用いることができる。
本発明における導電性繊維の繊維束としては、例えば、前記導電性繊維のマイクロファイバーやナノファイバーなどからなる繊維束に、導電性フィラーや導電性高分子等を担持、含浸させて得られたものを用いることができる。
前記導電性繊維、前記導電性繊維の繊維束、前記導電性繊維を含む繊維から得られる撚糸、組み糸、紡績糸、混紡糸、前記極細金属線の平均直径は、250μm以下が好ましく、より好ましくは120μm以下、更に好ましくは80μm以下、特に好ましくは50μm以下である。
前記導電糸には、フィルムを極細の繊維状に切断した極細フィルムも包含され、前記極細フィルムとは、金属、導電性金属酸化物、カーボン系導電性材料、および導電性高分子よりなる群から選ばれる少なくとも1種の導電性材料を被覆した高分子フィルムを幅800μm以下に切断して得られた繊維状フィルムを意味する。
前記導電性高分子としては、例えば、ポリ(3,4-エチレンジオキシチオフェン)とポリスチレンスルホン酸とを含む混合物を好ましく用いることができる。 前記導電糸を含む繊維としては、合成繊維マルチフィラメントが好ましく、該合成繊維マルチフィラメントの少なくとも一部が、繊度が30dtex未満の極細フィラメントであるか、或いは、繊度が400dtexを超え、かつ単糸繊度が0.2dtex以下の合成繊維マルチフィラメントであることが好ましい。
前記導電性ファブリックが、導電糸を含む繊維で構成された織物であるか、編み物である場合は、目付けは、導電性高分子の脱落防止を優先するという理由で、50g/m2未満であるか、十分な導電性確保という理由で、300g/m2を超えることが好ましい。
乾燥した皮膚との静摩擦係数をこの範囲に制御することにより、電極が容易にずれることを防止し、安定した電気信号を確保できる。また静摩擦係数(μd)を2.0以下に保つことにより、着用感を損なうことなく、また皮膚の破傷や炎症を未然に防止することができる。
本発明の生体接触型電極は、衣服の生地に面する側に伸縮性のある絶縁層を有してもよい。この絶縁層は衣服生地と生体接触型電極を接着する接着層を兼ねても良い。
電気配線部の乾燥皮膚または湿潤皮膚に対する摩擦係数がこの範囲を越えると、被験者が着用時に感じる不快感が大きくなる。着用者が不快感を持つと、生体情報にその影響が出る場合があり好ましくない。
まず導電性微粒子と柔軟性樹脂バインダーを少なくとも構成成分とする伸縮性導体シートを生体接触電極の表面の導電部材として用いた場合についての実施例を示す。
[導電ペーストの作製]
表1に示す材料を用いて、表2に示す重量配合比により樹脂を各溶剤に溶解し、得られた溶液に銀粒子を配合し、3本ロールミルにて混合し、導電性ペーストを得た。
離型処理PETフィルム上に上記の導電ペーストを使い、アプリケータを用いて乾燥膜厚が約100μmになるように塗布し、120℃、30分間、熱風乾燥オーブンで乾燥した後、離型処理PETフィルムを剥離して、シート状の生体接触型電極を得た。このシートを用いて後述する方法で、厚さ、未伸長時シート抵抗、伸長時シート抵抗増加比、伸長時荷重を測定した。実施例の測定結果を表2に示す。
上記で作製した離型処理PETフィルム付き生体接触型電極に表1に示すホットメルトシートと離型紙を重ね合わせ、ゴムロール温度を120℃に調整したロールラミネート機にて接着し、接着性のある生体接触型電極シートを得た。この生体接触型電極シートを配線巾1.0cm配線長15.0cmに続く5.0cm角の正方形状に切り抜いた。切り抜いた配線付き電極から離型紙を剥がしシャツ(ポリエステル100%)の裏面側の所定の位置に配置してアイロンで熱圧着し、さらに離型処理PETフィルムを剥がして、裏側に電極を備えたシャツを作製した。
電極および配線を備えたシャツの配線末端の表側にステンレススチール製のホックを裏側の配線と導通するように取り付け、ステンレススチール製ホックを介して、ユニオンツール社製の心拍センサWHS-2を接続し、心拍計測機能を組み込んだシャツを作製した。
幅2.5cmのチャックを2個備えた伸長試験機(手回し延伸機)を用いて、チャック間距離5.0cmになるように上記で作製した伸縮性導電性材料シートを挟み、長手方向に伸長率10%まで伸長(変位量0.5cm)した。試験前後のシート抵抗はデジタルマルチメータ(横河メータ&インスツルメンツ社製「YOKOGAWA TY530」)を用い、対向する2個のチャックの外側(測定距離10cm)にて伸長前後の抵抗値(Ω)を測定し、生体接触型電極のシート抵抗(Ω□)を得た。抵抗値の測定は伸長直後(3秒以内)に実施した。
引張試験機(ORIENTEC CORPORATION社製「RTM-250」)を用い、幅30mm,試験長さ50mmの伸縮性導電性材料シートを伸長率10%にしたときにかかる荷重(N)を測定し、シート長1cm当りの単位荷重(N/cm)を得た。
静摩擦係数測定機(新東科学社製、トライボギア TYPE:10)を用いて生体接触型電極の擬似皮膚に対する、乾燥時、及び湿潤時のそれぞれの静摩擦係数を以下のように測定し求めた。評価に用いた擬似皮膚には、ウレタンエラストマー膜の表面を加工して人の皮膚に近い親疎水性と表面のしわを再現したバイオスキンプレート(株式会社ビューラック社製、品番 P001-001、縦195mm×横120mm×厚み5mm)を用いた。乾燥時の静摩擦係数(μd)として、水平状態にある上昇板にバイオスキンプレートを固定し、縦75mm×横35mmの平面圧子に生体接触型電極を取り付けて、荷重150gの条件下で30秒静置した後、上昇速度平均10度/6秒で傾斜し、平面圧子が滑り始めた時の摩擦角(θd、度)を読み取り、μd=tan(θd×π/180)を得た。湿潤時の静摩擦係数(μw)は生体接触型電極を取り付けた後に1mlの水分を付与し、乾燥時の測定と同様の操作により摩擦角(θw、度)を読み取り、μw=tan(θw×π/180)を得た。実施例及び比較例の測定結果を表2に示す。
[吸水率の測定]
JIS L1907の繊維製品の吸水性試験方法、7.2 吸水率法に準拠して測定した。生体接触型電極試料から75mm×75mmの試験片を3枚採取し、質量(Wd、mg)を測定した後、イオン交換水を入れた浸漬槽に試験片を水中沈降させ、20分間浸漬する。浸漬後、試験片を浸漬槽から取り出し、200mm×200mmの角型濾紙2枚に挟み、底辺が100mm×100mmの6.75kgの錘で3秒間押さえた後、直ちに試験片の質量(Ww、mg)を測定し、下記式(1)により吸水率(c、質量%)を求めた。
c = (Ww-Wd)/Wd × 100 ・・・・・・ (1)
成人男性5名を被験者とし、実施例で作成した心拍計測機能を組み込んだシャツを着用し、15℃、40%RHの環境下で心電計測を行いながら、ラジオ体操第1と、ラジオ体操第2を続けて実施した。その間の着用感について、「触感が良い」を5点、「触感が悪い」を1点として、五段階の官能評価を行い、5人の平均において、4以上を◎、3以上4未満を○、2以上3未満を△、2未満を×とした。
以上のようにして心拍計測機能を持つ生体情報計測用衣服を用いた心電情報計測システムを構成した。得られた生体情報計測用衣服を被験者5名に着用させ、心電測定を行いながらラジオ体操第1とラジオ体操第2を続けて実施した。結果、被験者5名全員の体操中の心電計測が問題無く実施できた。また被験者5名とも、特に違和感、不快感を訴えることは無かった。
実施例2にて得られたシート状の生体接触型電極を、長径40mm、短径20mmの形状に打ち抜いて、電極部とした。次いで応用実施例1と同じスポーツシャツを用い、応用実施例1と、ほぼ同等の位置に電極部をアイロンを用いて貼り付け、さらに左右各々の電極部からスポーツシャツの胸中央部に向けて導電糸(銀コート糸)をジグザグに刺繍して電気配線部とし、所定位置に接続用のスナップホックを導電糸にて縫い付けコネクタとした。さらに銀コート糸を刺繍した部分の衣服内側を覆うように、スポーツシャツと同じ生地を縫い付けて絶縁カバーとし、生体情報計測用衣服とした。なお、電気配線部(電気配線に被せた絶縁カバー)表面と、バイオスキンプレートとの乾燥時摩擦係数は0.16、湿潤時摩擦係数は0.23であった。
応用実施例2において、絶縁カバーとしてスポーツシャツと同じ生地では無く、シリコーン樹脂のコーキング剤を用いて絶縁層を形成した。シリコーン樹脂コーキング剤の絶縁カバー層を有する電気配線部のバイオスキンプレートとの乾燥時摩擦係数は0.56、湿潤時摩擦係数は0.42であった。
以下、応用実施例1と同様に心拍計測機能を有するシステムを構成し、被験者5名に着用させ、心電測定を行いながらラジオ体操第1とラジオ体操第2を続けて実施した。結果、被験者5名のうち、比較的発汗量が多かった2名において、ラジオ体操2の後半からノイズが多くなり心電測定ができなくなった。また当該2名が、発汗と共に次第にスポーツシャツが引き連るような感覚を覚えたと訴えた。
<導電糸の製造例1>
無電解めっき法により、ナイロン繊維の撚糸(250デニール)を銀メッキした。まず無電解銀めっきのための下地処理として撚糸を精錬剤に浸漬、水洗後、塩化第一スズ10g/リットル、35%塩酸20ミリリットル/リットルを含んだ水溶液に浸漬した後、水洗することにより触媒性を付与し後、下記組成の無電解銀メッキ液を所定量用いて銀を10質量%被覆した。
〔無電解銀めっき液浴比〕(銀5g/1リットル)
エチレンジアミン四酢酸四ナトリウム 100g/1リットル
水酸化ナトリウム 25g/1リットル
ホルマリン 50g/1リットル
硝酸銀(水1リットルに溶解して滴下) 15.8g
アンモニア水(水1リットルに溶解して滴下) 50ミリリットル
得られた銀メッキ糸を撚り合わせ、糸長1cmあたりの抵抗値が120mΩの導電糸(F1)を得た。
アラミド繊維を用いて、導電糸の製造例1と同様の手法にて、ただし、無電解銀メッキ浴に対する繊維の処理量を半分に減じ、銀を20重量%被覆したアラミド繊維を得た。得られた繊維を撚り合わせ、糸長1cmあたりの抵抗値が65mΩの導電糸(F2)を得た。
50デニール24フィラメントのポリエステルマルチフィラメント加工糸に、アルカリ加水分解により10%の減量加工を行い、十分に水洗の後、引き続き、塩化パラジウム0.3g/L、塩化第一錫30g/L、36%塩酸300ml/Lを含む40℃の水溶液に浸漬後、水洗した。続いて、酸濃度0.1Nのホウ弗化水素酸に浸漬後、水洗した。次に硫酸銅7.5g/L、37%ホルマリン30ml/L、ロッシェル塩85g/Lから成る無電解銅メッキ液に浸漬後、水洗した。続いて、スルファミン酸ニッケル300g/L、ホウ酸30g/L、塩化ニッケル15g/L、pH3.7の電気ニッケルメッキ液に通電しながら浸漬し、銅/ニッケルの二層金属被覆層を有する導電糸(F3)を得た。得られた導電糸の金属分は質量換算にて、銅8質量%、ニッケル2質量%であった。また糸長1cmあたりの抵抗値は300mΩであった。
KBセーレン株式会社製の極細繊維ベリーマXの紡績糸を、チオフェン系導電性高分子PEDOT:PSSを用いた導電性成分に用いた導電塗料デナトロンに浸漬し、超音波処理を3分間行った後に絞りながら引き上げ、乾燥することにより、導電性高分子を含浸した導電糸(F4)を得た。得られた導電糸の糸長1cmあたりの抵抗値は40Ωであった。
昭和電線ケーブル株式会社製の銅銀合金(直径80μm)の素線19本を撚糸して導電糸(F5)を得た。得られた導電糸F5の1cmあたりの抵抗値は0.026mΩであった。
耐熱性ナイロンをコア繊維とし、表面にカーボン含有のナイロン6樹脂を被覆した、クラレトレーディング株式会社製の導電糸クラカーボKC-792R-B22T4を導電糸(F6)として用いた。導電糸F6の1cmあたりの抵抗値は500kΩであった。なお、本導電糸の抵抗値については通常のテスターを用いて測定した。
製造例1~6にて得られた導電糸と、ポリエステル繊維を混合し、ニット編みすることにより表3.に示す導電性ファブリックを得た。それぞれの導電性ファブリックを用いた生体接触型電極の評価結果を表3に示す。
[伸長試験およびシート抵抗の測定]
幅2.5cmのチャックを2個備えた伸長試験機(手回し延伸機)を用いて、チャック間距離5.0cmになるように上記で作製した伸縮性導電性材料シートを挟み、長手方向に伸長率10%まで伸長(変位量0.5cm)した。試験前後のシート抵抗はデジタルマルチメータ(横河メータ&インスツルメンツ社製「YOKOGAWA TY530」)を用い、対向する2個のチャックの外側(測定距離10cm)にて伸長前後の抵抗値(Ω)を測定し、生体接触型電極のシート抵抗(Ω□)を得た。抵抗値の測定は伸長直後(3秒以内)に実施した。
引張試験機(ORIENTEC CORPORATION社製「RTM-250」)を用い、幅30mm,試験長さ50mmの伸縮性導電性材料シートを伸長率10%にしたときにかかる荷重(N)を測定し、シート長1cm当りの単位荷重(N/cm)を得た。
摩擦係数測定機(新東科学社製、トライボギア TYPE:10)を用いて生体接触型電極の擬似皮膚に対する、乾燥時、及び湿潤時のそれぞれの静摩擦係数を以下のように測定し求めた。評価に用いた擬似皮膚には、ウレタンエラストマー膜の表面を加工して人の皮膚に近い親疎水性と表面のしわを再現したバイオスキンプレート(株式会社ビューラック社製、品番 P001-001、縦195mm×横120mm×厚み5mm)を用いた。乾燥時の静摩擦係数(μd)として、水平状態にある上昇板にバイオスキンプレートを固定し、縦75mm×横35mmの平面圧子に生体接触型電極を取り付けて、荷重150gの条件下で30秒静置した後、上昇速度平均10度/6秒で傾斜し、平面圧子が滑り始めた時の摩擦角(θd、度)を読み取り、μd=tan(θd×π/180)を得た。湿潤時の静摩擦係数(μw)は生体接触型電極を取り付けた後に1mlの水分を付与し、乾燥時の測定と同様の操作により摩擦角(θw、度)を読み取り、μw=tan(θw×π/180)を得た。
[保水率の測定]
保水率は、JIS L 1913:2010 一般不織布試験方法に準拠する方法にて測定した。
離型処理PETフィルム上に得られた導電性ファブリックを仮接着し、さらにホットメルトシートと離型紙を重ね合わせ、ゴムロール温度を120℃に調整したロールラミネート機にて接着し、ホットメルト接着性のある生体接触型電極シートを得た。この生体接触型電極シートを配線巾1.0cm、配線長15.0cmの長方形と、概長方形に直接接続する直径5.0cmの円形に切り抜いた。円形部が電極、長方形部が配線部に相当する。切り抜いた生体接触型電極シートを離型処理PETフィルムから剥がし、シャツ(ポリエステル100%)の裏面側の所定の位置に配置してアイロンで熱圧着し、、さらに配線部分にホットメルトシートを重ねて圧着して絶縁層となし、裏側に電極と配線を備えたシャツを作製した。
得られた電極および配線を備えたシャツの配線末端の表側にステンレススチール製のホックを裏側の配線と導通するように取り付け、ステンレススチール製ホックを介して、ユニオンツール社製の心拍センサWHS-2を接続し、心拍計測機能を組み込んだシャツを作製した。
成人男性5名を被験者とし、実施例で作成した心拍計測機能を組み込んだシャツを着用し、15℃、40%RHの環境下で心電計測を行いながら、ラジオ体操第1と、ラジオ体操第2を続けて実施した。 その間の着用感について、「触感が良い」を5点、「触感が悪い」を1点として、五段階の官能評価を行い、5人の平均において、4以上を◎、3以上4未満を○、2以上3未満を△、2未満を×とした。
Claims (21)
- 生体信号を測定するため用いられる生体接触型電極であって、電極表面の面積が1平方センチメートル以上であり、前記生体接触型電極の表面と乾燥した皮膚との静摩擦係数(μd)が0.4以上、2.0以下であることを特徴とする生体接触型電極。
- 生体接触型電極の表面と乾燥した皮膚との静摩擦係数(μd)が0.5以上、2.0以下であることを特徴とする請求項1に記載の生体接触型電極。
- 生体信号を測定するため用いられる生体接触型電極であって、電極表面の面積が1平方センチメートル以上であり、生体接触型電極の表面と湿潤した皮膚との静摩擦係数(μw)が0.3以上、3.0以下であることを特徴とする生体接触型電極。
- 生体接触型電極の表面と湿潤した皮膚との静摩擦係数(μw)が0.4以上、3.0以下であることを特徴とする請求項3に記載の生体接触型電極。
- 導電性微粒子と柔軟性樹脂バインダーを少なくとも構成成分とする伸縮性導体シートを生体接触電極の表面の導電部材として用いたことを特徴とする請求項1から請求項4のいずれか一項に記載の生体接触型電極。
- 前記柔軟性樹脂バインダーの弾性率が1GPa以下で、かつ、破断伸度が200%以上であることを特徴とする請求項5に記載の生体接触型電極。
- 生体接触型電極の表面と乾燥した皮膚との静摩擦係数(μd)と、生体接触型電極の表面と湿潤した皮膚との静摩擦係数(μw)が以下の関係式を満たすことを特徴とする請求項5または6のいずれかに記載の生体接触型電極。
1.7≦(μw)/(μd)≦2.5 - 前記伸縮性導体シートの吸水率が0.5質量%以上 25質量%以下であることを特徴とする請求項5から7のいずれか一項に記載の生体接触型電極。
- 請求項1から請求項8のいずれかに記載の生体接触型電極を複数備えることを特徴とする生体情報計測用衣服。
- 請求項9に記載の生体情報計測用衣服において、前記生体情報計測用衣服の生体と接触する面の電極表面を除く電気配線部表面の乾燥した皮膚との静摩擦係数(μd)が0.5以下であることを特徴とする生体情報計測用衣服。
- 請求項9に記載の生体情報計測用衣服において、前記生体情報計測用衣服の生体と接触する面の電極表面を除く電気配線部表面の湿潤した皮膚との静摩擦係数(μd)が0.4以下であることを特徴とする生体情報計測用衣服。
- 導電性ファブリックを生体接触電極の表面の導電部材として用いたことを特徴とする請求項1または2に記載の生体接触型電極。
- 導電性ファブリックを生体接触電極の表面の導電部材として用いたことを特徴とする請求項3または4に記載の生体接触型電極。
- 前記導電性ファブリックが、導電性繊維を少なくとも構成要素とする伸縮性の導電布帛からなることを特徴とする請求項12または13に記載の生体接触型電極。
- 前記導電性ファブリックが、金属被覆合成繊維を10質量%以上含む織物、編み物、不織布から選択される少なくとも一つの導電性ファブリックであることを特徴とする請求項12から請求項14のいずれか一項に記載の生体接触型電極。
- 前記導電性ファブリックが、化学合成繊維と導電性高分子のハイブリッド材料を含むことを特徴とする請求項12から14のいずれか一項に記載の生体接触型電極。
- 生体接触型電極の表面と乾燥した皮膚との静摩擦係数(μd)と、生体接触型電極の表面と湿潤した皮膚との静摩擦係数(μw)が以下の関係式を満たすことを特徴とする請求項12から16のいずれか一項に記載の生体接触型電極。
0.8≦(μw)/(μd)≦1.5 - 前記導電性ファブリックの保水率が40質量%以上350%以下であることを特徴とする請求項12から17のいずれか一項に記載の生体接触型電極。
- 請求項12から18のいずれか一項に記載の生体接触型電極を複数備える事を特徴とする生体情報計測用衣服。
- 請求項19に記載の生体情報計測用衣服において、前記生体情報計測用衣服の生体と接触する面の電極表面を除く電気配線部表面の乾燥した皮膚との静摩擦係数(μd)が0.5以下であることを特徴とする生体情報計測用衣服。
- 請求項19に記載の生体情報計測用衣服において、前記生体情報計測用衣服の生体と接触する面の電極表面を除く電気配線部表面の湿潤した皮膚との静摩擦係数(μd)が0.4以下であることを特徴とする生体情報計測用衣服。
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JP2021094280A (ja) * | 2019-12-18 | 2021-06-24 | ミツフジ株式会社 | 配線構造、及び、電極構造 |
WO2022107710A1 (ja) | 2020-11-19 | 2022-05-27 | 日東電工株式会社 | 生体センサ |
JP2022081415A (ja) * | 2020-11-19 | 2022-05-31 | 日東電工株式会社 | 生体センサ |
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LT3960260T (lt) * | 2019-11-04 | 2023-08-10 | Boreal Technology & Investment S.L | Nešiojamas įrenginys ir jo būdas |
CN112603270A (zh) * | 2021-01-06 | 2021-04-06 | 嘉兴脉腾科技有限公司 | 全织物摩擦力传感器及睡眠监测***和睡眠监测方法 |
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