Bioelectrode body and biological information measuring device

Abstract

To provide a bioelectrode body (electrode body) capable of acquiring vital information in a stable manner, which can be used comfortably even when worn for a long time.SOLUTION: A bioelectrode includes: a detection unit that comes in contact with the skin, in which the detection unit is composed of a woven fabric, a knitted fabric, or a nonwoven fabric composed of conductive fibers, and an elastic support layer, the elastic support layer is covered with and integrated with the woven fabric, the knitted fabric, or the nonwoven fabric on the skin side, and the woven fabric, the knitted fabric, or the nonwoven fabric has an elongation amount of 10 mm or less at a load of 500 g at least in one direction, and the flexural rigidity (B) is 0.015 gf cm2 / cm or more, 2.500 gf cm2 / cm or less; transmission means, one end of which is connected to the woven fabric, the knitted fabric, or the non-woven fabric, and the other end of which is connected to an outer element for transmitting an electric signal; and a base material part arranged on a surface opposite to the skin side of the elastic support layer, whose compression recovery property (RC) is 30% or more.SELECTED DRAWING: Figure 1

Description

[Technical Field]

[0001] The present invention relates to a bioelectrode (electrode body) and a bioinformation measuring device. [Background technology]

[0002] In recent years, wearable devices that can acquire vital signs by being worn on the human body have been attracting attention. In particular, for wearable devices designed to acquire bioelectrical potentials such as cardiac potentials and myoelectric potentials, active research and development has been conducted on electrodes that can reduce noise (motion artifacts) that occurs when the contact state between the device and the skin changes due to the user's body movements, thereby enabling clear acquisition of bioelectrical potentials.

[0003] For example, Patent Document 1 below proposes an "electrode body having a specific range of shear modulus or compressive shear modulus" in which the detection section is made up of a conductive cloth and a deformable section. According to Patent Document 1, the electrode body is capable of reducing motion artifacts and clearly acquiring bioelectric potentials even when large body movements occur. However, Patent Document 1 does not disclose the amount of stretch or bending rigidity of the conductive cloth, much less the compressive linearity (LC) of the detection section.

[0004] Furthermore, Patent Document 2 below proposes an "electrode member made of a textile structure and a conductive polymer." According to Patent Document 2, the electrode member can maintain high conductivity even after repeated washing, and is applicable to bioelectrodes. However, Patent Document 2 does not disclose the elongation or bending rigidity of the textile structure, much less the compressive linearity (LC) of the detection unit.

[0005] Furthermore, Patent Document 3 below proposes "a stretchable electrode capable of maintaining high conductivity even when stretched, a wiring sheet, and a non-permeable sheet-like interface for measuring biological information in which the stretchable electrode and wiring sheet are laminated together." The stretchable electrode described in Patent Document 3 is an electrode with excellent stretchability that has a specific range of stretch characteristics, and is said to result in a resistance change of less than five times at 20% stretch, thereby obtaining electrocardiogram data with little noise. However, Patent Document 3 does not disclose the stretch amount or bending rigidity of the non-permeable sheet-like material, much less the compression linearity (LC) of the detection unit. [Prior art documents] [Patent documents]

[0006] [Patent Document 1] Japanese Patent Application Publication No. 2023-143117 [Patent Document 2] Patent No. 6454649 [Patent Document 3] Patent No. 6888640 Summary of the Invention [Problem to be solved by the invention]

[0007] The proposals in Patent Documents 1 to 3 do not disclose an electrode structure that suppresses motion artifacts and provides sufficient comfort when worn for long periods of time, such as by patients with heart disease. Given this state of the art, the problem that the present invention aims to solve is to provide a bioelectrode (electrode assembly) that is comfortable to wear even for long periods of time and that can stably acquire vital information. [Means for solving the problem]

[0008] That is, the present invention is as follows. [1] The following: A detecting section that comes into contact with the skin, wherein the detecting section is composed of a woven, knitted or nonwoven fabric made of conductive fibers and an elastic support layer, the elastic support layer being covered by and integrated with the woven, knitted or nonwoven fabric on the skin side, the woven, knitted or nonwoven fabric having an elongation of 10 mm or less in at least one direction when subjected to a load of 500 g, and a bending rigidity (B) of 0.015 gf cm 2 / cm or more 2.500gf·cm 2 / cm or less; a transmission means, one end of which is connected to the woven, knitted or nonwoven fabric and the other end of which is connected to an external element and capable of transmitting an electrical signal; and a base material portion having a compression recovery (RC) of 30% or more, which is disposed on the surface opposite to the skin side of the elastic support layer; A bioelectrode comprising: [2] The bioelectrode according to [1], wherein the compressive linearity (LC) of the detecting section is 0.45 to 1.00. [3] A bioelectrode according to [1] or [2], wherein in the detection section, a binder is present on the surface of the constituent fibers of the woven, knitted or nonwoven fabric on the side that comes into contact with the skin, filling the spaces between the fibers, and the moisture content of the woven, knitted or nonwoven fabric under environmental conditions of 30°C and 70% is 4.5% or more. [4] The detection unit is made of a woven fabric, and the basis weight of the woven fabric is 10 g / m 2 More than 150g / m 2 The bioelectrode according to any one of the above [1] to [3], having a thickness of 0.01 mm or more and 1.00 mm or less, and a surface roughness Rq of 5 μm or more and 100 μm or less. [5] The detection unit is made of nonwoven fabric, and the basis weight of the nonwoven fabric is 10 g / m 2 More than 150g / m 2 The bioelectrode according to any one of [1] to [3] above, having a thickness of 0.01 mm or more and 1.00 mm or less, and a surface roughness Rq of 5 μm or more and 100 μm or less. [6] The detection unit is made of a knitted fabric, and the weight of the knitted fabric is 50 g / m 2 More than 200g / m 2The bioelectrode according to any one of [1] to [3] above, having a thickness of 0.10 mm or more and 1.50 mm or less, and a surface roughness Rq of 5 μm or more and 100 μm or less. [7] The area of ​​the detection part that comes into contact with the skin during use is 175 mm 2 Over 10,000mm 2 The bioelectrode according to any one of the above [1] to [6], which is: [8] A bioelectrode according to any one of [1] to [7], further comprising a high-friction portion arranged around the detection portion and having a static friction coefficient higher than the static friction coefficient of the detection portion that comes into contact with the skin during use. [9] A biological information measuring device comprising the bioelectrode according to any one of [1] to [8].

[10] The bioinformation measuring device according to [9], which is wearable. [Effects of the Invention]

[0009] The bioelectrode according to the present invention is capable of suppressing motion artifacts and providing sufficient comfort when worn for long periods of time. [Brief explanation of the drawings]

[0010] [Figure 1] FIG. 1 is a cross-sectional view illustrating the configuration of a bioelectrode (electrode body) according to this embodiment. DETAILED DESCRIPTION OF THE INVENTION

[0011] Hereinafter, an embodiment of the present invention (hereinafter referred to as "embodiment") will be described. In this embodiment, a numerical range described using "to" includes the numerical values ​​described on both ends of "to". In this embodiment, an upper or lower limit value described in a numerical range described in stages can be replaced with an upper or lower limit value of a numerical range described in another stage. In this embodiment, an upper or lower limit value described in a numerical range can also be replaced with a value described in the Examples. In this embodiment, the scale, shape, length, and other configurations of each part shown in the drawings may be exaggerated for clarity.

[0012] One embodiment of the present invention is a method for producing a medicament for the treatment of a pulmonary arthritis. A detecting section that comes into contact with the skin, wherein the detecting section is composed of a woven, knitted or nonwoven fabric made of conductive fibers and an elastic support layer, the elastic support layer being covered by and integrated with the woven, knitted or nonwoven fabric on the skin side, the woven, knitted or nonwoven fabric having an elongation of 10 mm or less in at least one direction when subjected to a load of 500 g, and a bending rigidity (B) of 0.015 gf cm 2 / cm or more 2.500gf·cm 2 / cm or less; a transmission means, one end of which is connected to the woven, knitted or nonwoven fabric and the other end of which is connected to an external element and capable of transmitting an electrical signal; and a base material portion having a compression recovery (RC) of 30% or more, which is disposed on the surface opposite to the skin side of the elastic support layer; The bioelectrode (electrode body) comprises:

[0013] <Electrode body> FIG. 1 is a cross-sectional view showing the configuration of an electrode assembly according to one embodiment of the present invention. As illustrated in FIG. 1 , the bioelectrode 10 (electrode body 10) according to the present invention includes a woven, knitted, or nonwoven fabric 1 (conductive member 1 for the detection unit) made of conductive fibers, a transmission means 2 (wiring member 2) for transmitting a signal measured by the conductive member 1 for the detection unit, and a detection unit 6 made of an elastic support layer 3 (support layer 3) for supporting the conductive member 1 for the detection unit. The detection unit 6 is provided on one surface of a deformable substrate 4 having at least one surface. Furthermore, a high-friction portion 5 is preferably provided on the substrate 4 so as to surround the detection unit 6, preventing it from slipping when it comes into contact with the skin. When the conductive member 1 for the detection unit comes into contact with the user's skin, for example, bioelectrical potentials such as cardiac potentials and myoelectric potentials are measured and transmitted as measurement signals via the wiring member 2. The electrode body 10 may be attached to clothing or the like 7 for use.

[0014] The detection unit of this embodiment is composed of a woven, knitted or nonwoven fabric made of conductive fibers and an elastic support layer, and the elastic support layer is covered by the woven, knitted or nonwoven fabric on the skin side and is integrated therewith. The woven, knitted or nonwoven fabric made of conductive fibers has an elongation of 10 mm or less when subjected to a load of 500 g in at least one direction, and a bending rigidity (B) of 0.015 gf cm 2 / cm or more 2.500gf·cm 2 / cm or less, more preferably an elongation of 3 mm or less, and a bending stiffness (B) of 0.015 gf cm 2 / cm or more 2.200gf·cm 2 / cm or less. The elongation is 10 mm or less, and the bending stiffness (B) is 0.015 gf cm 2 / cm or more, even if the skin deforms during human movement, the conductive fibers in contact with the skin are less likely to move, and the electrical path in the fabric is stabilized, reducing motion artifacts. 2 / cm or less, the softness allows the material to come into contact with the skin without causing discomfort to the user. The elongation amount is measured using a Tensilon universal testing machine RTG1210 manufactured by A&D Corporation, and the bending stiffness (B) is measured using an automated pure bending tester KES-FB2-A manufactured by Kato Tech Co., Ltd., and the values ​​are calculated.

[0015] The bioelectrode also includes a transmission means having one end connected to the woven, knitted or nonwoven fabric made of the conductive fiber and the other end connected to an external element to transmit an electrical signal. Furthermore, the bioelectrode has a substrate part with a compression recovery (RC) of 30% or more that is coated on the surface opposite the skin side of the elastic support layer. By making the compression recovery (RC) of the substrate part 30% or more, it is possible to reduce the feeling of pressure when worn while providing the optimal wearing pressure required for sensing.

[0016] <Detection section> The detection unit may be provided on at least one surface of the base material, or on multiple surfaces of the base material. However, it is preferable that the detection unit or wiring member is not provided at a position where the deformation of the base material switches between contact and non-contact with the skin. This is because the electrode body undergoes large shear deformation, which can suppress the generation of noise caused by new electrical contact points between the detection unit or wiring member and the skin, allowing for clearer measurement of biological signals. For example, if the base material is cylindrical and the detection unit is provided on one bottom surface, it is preferable that the detection unit is not provided on the side surface and that wiring members with uninsulated surfaces are not provided. Furthermore, two or more detection units may be provided on one surface of the base material, and in this case, the shapes of the detection units may be the same or different.

[0017] The compressive linearity LC[-] of the detection unit is preferably 0.45 to 1.00, more preferably 0.50 to 0.85. By setting the compressive linearity LC to 0.45 or more, deformation of the contact portion of the detection unit with the skin is suppressed, and motion artifacts can be reduced. The compressive linearity LC is measured using a compression tester KES-G5, and is a value calculated from the thickness and pressure when the detection unit is compressed.

[0018] The area of ​​the detector that comes into contact with the skin is preferably 175 mm 2 ~10,000mm 2 and more preferably 300 mm 2 ~8,000mm 2 This area is 175mm 2 This allows stable detection of biological signals, and 2 By keeping the thickness below 0.1 mm, the detection unit can be brought into contact with the skin without causing discomfort to the user. There are no particular limitations on the thickness of the detection unit, but it is, for example, 0.1 mm to 5.0 mm in the normal direction to the contact surface with the base material.

[0019] The surface of the detection unit preferably has a static friction coefficient of 0.3 to 0.7. A static friction coefficient of 0.3 or higher prevents the detection unit from sliding on the skin surface when shear deformation occurs in the electrode body, thereby maintaining contact and making it easier to suppress motion artifacts. Furthermore, a static friction coefficient of 0.7 or lower reduces discomfort caused by friction between the detection unit and the skin surface when wearing a device including the electrode body. The static friction coefficient can be calculated using a TL201 (manufactured by Trinity Labs Co., Ltd.) by contacting a finger model contactor with the surface of the detection unit with a contact pressure of 10 hPa and displacing the detection unit horizontally relative to the contactor at a rate of 30 mm / s.

[0020] <Conductive material for detection section> The conductive member for the detection unit is not particularly limited as long as it enables the detection unit to have conductivity. Note that conductivity here means that the specific resistance (volume resistance value) measured according to JIS C 2139 is 1000 Ω cm or less. Examples of raw materials that achieve this include conductive materials such as metal materials, carbon-based materials, and conductive polymers, as well as mixtures of these materials. The conductive member for the detection unit is not particularly limited, but from the viewpoint of improving the feel of the detection unit on the skin and reducing discomfort to the user, it is preferable that the conductive member for the detection unit includes, but is not limited to, at least one selected from the group consisting of woven fabrics, knitted fabrics, and nonwoven fabrics (short fiber or long fiber).Specific examples of the conductive member for the detection unit include woven fabrics, knitted fabrics, and nonwoven fabrics containing conductive fibers, as well as structures in which a conductive material is disposed on the surface of non-conductive woven fabrics, knitted fabrics, and nonwoven fabrics.In addition, the detection unit may be formed by attaching conductive short fibers as the conductive member for the detection unit to the support layer by electrostatic flocking or the like.

[0021] From the viewpoint of productivity, the conductive member for the detection unit is preferably a non-conductive fabric with a conductive material applied to its surface. Examples of conductive materials include metal materials, carbon-based materials, and conductive polymers. Examples of metal components include gold, platinum, silver, copper, nickel, chromium, iron, copper, zinc, aluminum, tungsten, stainless steel, titanium, magnesium, tin, vanadium, cobalt, molybdenum, and tantalum, as well as alloys thereof. Examples of carbon-based materials include carbon black, carbon nanotubes, and graphene. Examples of conductive polymers include PEDOT-PSS and PEDOT-PTS. Examples of conductive fabrics with a metal coating formed on the surface of a non-conductive fabric include, for example, the metal-plated fabric Sui-10-511M manufactured by Seiren Co., Ltd. Furthermore, to prevent changes in electrical resistance over time due to oxidation of the metal coating, a thin film made of metal oxide, resin, or the like may be formed in advance on the surface of the conductive member for the detection unit.

[0022] Furthermore, it is desirable for the conductive member for the detection unit to have a binder on the surface of the constituent yarns that come into contact with the skin. The binder is not particularly limited, but may be a thermosetting resin or a thermoplastic resin as long as it can restrict the movement of the conductive fibers. Examples include synthetic polymer compounds such as polyvinyl alcohol (PVA), polyurethane, polyester, acrylic resin, polyamide, polyimide, epoxy resin, and silicone, as well as synthetic rubbers such as butyl rubber. PVA, which is particularly hygroscopic, is preferred as a binder from the perspective of suppressing static electricity, a source of noise. The moisture content of the conductive member for the detection unit processed with a binder is preferably 4.5% or more, and more preferably 5.0% or more, under environmental conditions of 30°C and 70% humidity, which take into account the conditions near human skin. A moisture content of 4.5% or more reduces the generation of static electricity, a source of noise, between the skin and the electrodes.

[0023] When using woven or nonwoven fabric as the conductive material for the detection part, the basis weight should be 10 g / m 2 More than 150g / m 2 It is preferable that the thickness is 0.01 mm or more and 1.00 mm or less, and the surface roughness Rq is 5 μm or more and 100 μm or less. 2 With a thickness of 0.01 mm or more, the floating of the yarn is suppressed and the yarn is kept in a state of tension, making it difficult for the fibers to move, and therefore making it less likely for noise to occur. 2 By keeping the surface roughness Rq at 5 μm or more and the thickness at 1.00 mm or less, the fabric maintains the appropriate softness and does not impair comfort when worn. In addition, by keeping the surface roughness Rq at 5 μm or more, the appropriate unevenness reduces discomfort caused by adhesion to the skin. Furthermore, by keeping the surface roughness Rq at 100 μm or less, friction against the skin is less likely to be uncomfortable.

[0024] When using knitted fabric as the conductive material for the detection part, the weight per unit area should be 50 g / m 2 More than 200g / m 2 It is preferable that the thickness is 0.01 mm or more and 1.50 mm or less, and the surface roughness Rq is 5 μm or more and 100 μm or less.2 With a thickness of 0.01 mm or more, the yarn float is suppressed and tension is maintained, making it difficult for the fibers to move, which reduces the likelihood of noise. 2 By keeping the surface roughness Rq at 5 μm or more and the thickness at 1.50 mm or less, the fabric maintains the appropriate softness and does not impair comfort when worn. In addition, by keeping the surface roughness Rq at 5 μm or more, the appropriate unevenness reduces discomfort caused by adhesion to the skin. Furthermore, by keeping the surface roughness Rq at 100 μm or less, friction against the skin is less likely to be uncomfortable.

[0025] <Transmission means (wiring components)> The transmission means (wiring member) is not particularly limited as long as it has the same conductivity as the conductive member for the detection unit, but from the viewpoint of reducing the influence of radiation noise, it is preferable that the surface is electrically insulated except for the conductive member for the detection unit and the electrical contacts with the device to which the biological signal is sent.

[0026] <Elastic support layer> The material of the support layer is not particularly limited, but examples include synthetic resins such as nylon and polyester, thermosetting resin elastomers such as urethane, synthetic polymer compounds such as silicone, synthetic rubbers such as butyl rubber, and natural rubber. Thermosetting resin elastomers such as urethane are particularly preferred because they are inexpensive, easy to handle, and their softness when in contact with the skin can be adjusted. An example of a thermosetting resin elastomer such as urethane is the rubber sheet MX48HF3BK manufactured by Inoac Corporation.

[0027] <Base material part> The material of the substrate is not particularly limited, but examples include synthetic resins such as nylon and polyester, thermosetting resin elastomers such as urethane, synthetic polymer compounds such as silicone, synthetic rubbers such as butyl rubber, and natural rubber. Thermosetting resin elastomers such as urethane are particularly preferred because they are inexpensive, easy to handle, and allow for easy adjustment of compressive deformation. An example of a thermosetting resin elastomer such as urethane is low-resilience urethane foam PUF-03 manufactured by Wake Sangyo Co., Ltd. The shape of the substrate is not particularly limited as long as the substrate has at least one surface, and examples include a rectangular parallelepiped shape, a cube shape, a polyhedron shape, a cylindrical shape, a cone shape, etc. A cylindrical shape is preferred from the viewpoint that the anisotropy of shear deformation is small, and therefore the effect of reducing motion artifacts can be expected regardless of the direction of displacement applied to the electrode body. The dimensions of the base material are not particularly limited, but may be adjusted depending on the area of ​​the detection unit, for example, if the area of ​​the surface on which the detection unit is provided is 490 mm 2 ~12,000mm 2 and the thickness in the normal direction of the surface is 1 mm to 15 mm.

[0028] <High friction part> The material of the high-friction portion is not particularly limited, but examples include synthetic resins such as nylon and polyester, thermosetting resin elastomers such as urethane, synthetic polymer compounds such as silicone, synthetic rubbers such as butyl rubber, and natural rubber. Thermosetting resin elastomers such as urethane are particularly preferred because they are inexpensive, easy to handle, and have little adverse effect on the skin. An example of a thermosetting resin elastomer such as urethane is the rubber sheet MX48HF1BK manufactured by Inoac Corporation.

[0029] The shape of the high-friction portion is not particularly limited, but for example, it is provided on the surface of the base member on which the detection unit is provided, so as to surround at least a portion of the detection unit, and the thickness of the surface in the normal direction is equal to or less than that of the detection unit. Furthermore, it is desirable that the static friction coefficient be greater than that of the surface of the detection unit that contacts the skin and be in the range of 0.5 to 1.5. A static friction coefficient of 0.5 or greater makes it less likely for the detection unit to slip on the skin surface when shear deformation occurs in the electrode body, thereby maintaining contact and making it easier to suppress motion artifacts. Furthermore, a static friction coefficient of 1.5 or less allows the detection unit to slide appropriately on the skin when wearing a device including the electrode body, making it easier to adjust the position of the device.

[0030] <Biological information measurement device> Another embodiment of the present invention is a biological information measuring device including the above-described bioelectrode (electrode body). A bioinformation measuring device including one or more of the electrode bodies can measure biopotentials while suppressing motion artifacts even when body movement is present. The bioinformation measuring device can be used to measure any biopotential, such as cardiac potential, myoelectric potential, and electroencephalogram, and is particularly suitable for measuring cardiac potential. In order to measure biopotentials more clearly, the contact pressure of the electrode body against the skin when worn is preferably 5 hPa to 40 hPa, and more preferably 10 hPa to 30 hPa. By setting the contact pressure to 5 hPa or more, the adhesion between the skin and the electrode portion is improved and sufficient initial compressive displacement of the electrode body occurs, allowing for clearer biopotential measurement. Furthermore, by setting the contact pressure to 40 hPa or less, the feeling of pressure on the user due to increased contact pressure is suppressed and excessive compressive deformation of the electrode body is prevented, thereby sufficiently suppressing motion artifacts.

[0031] The bioinformation measuring device can be in the form of a wearable device, a band device, a watch device, glasses, a hat, or the like, with a wearable device being preferred. When the bioinformation measuring device is a wearable device, any form is acceptable as long as the electrode body is pressed against the area to be measured, such as an arm cover type for the arm, a tights type for the lower body, or a shirt type for the upper body. The fabric used for a wearable bioinformation measuring device is not particularly limited, but from the viewpoint of appropriately adjusting the contact pressure, a compressive fabric containing elastic yarn such as polyurethane elastic yarn is preferred. Furthermore, the wearable bioinformation measuring device may be equipped with other sensor devices, etc., as long as the effects of the invention are not impaired.

[0032] The method for attaching the electrode body to the bioinformation measuring device is not particularly limited, but examples include sewing the electrode body to the bioinformation measuring device, adhering the electrode body to the device using a thermoplastic resin or adhesive, or crimping a part of the electrode body to the device using a crimp terminal. Adhering the electrode body to the device using a thermoplastic resin is preferred because it is easy to attach. The electrode body may be attached to the bioinformation measuring device in a removable or non-removable manner. When the transmission section of the electrode body attached to the bioinformation measuring device is a wire, the method for electrically connecting the wire to the bioinformation measuring device is not particularly limited, but examples include a method of bonding the end of the wire to the measurement terminal of the bioinformation measuring device with solder or a conductive adhesive, or a method of crimping using a crimp terminal. Furthermore, the wire may be connected to a detachable connector of the bioinformation measuring device to indirectly electrically connect the wire to the bioinformation measuring device. [Example]

[0033] The present invention will be specifically described below with reference to examples and comparative examples. First, the measurement methods used in the examples and comparative examples will be described. (1) Elongation of the conductive material for the detection unit [mm] Five samples of 1.5 cm wide and 7 cm long are cut from the conductive member for the detection section. Using an A&D Tensilon universal testing machine RTG1210, the measurement length of the sample is set to 5 cm, the measurement width to 1.5 cm, the tensile speed to 10 mm / min, and the upper load limit to 1 kg. The elongation (mm) at a load of 500 g is measured with N=5. The average value is used as the "elongation of the conductive member for the detection section."

[0034] (2) Bending rigidity B [gf cm 2 / cm] Five samples of 1.5 cm width and 7 cm length are cut out from the conductive fabric sample. Using an automated pure bending tester KES-FB2-A manufactured by Kato Tech, the measurement conditions are as follows: sample width 1.5 cm, bending curvature 2.5 cm -1 The bending characteristics are measured with N=5. The average value of bending stiffness B of N=5 in each measurement direction is used as the "bending stiffness B of the conductive member for the detection unit."

[0035] (3) Compression recovery of the base material RC [%] The material to be used for the base material is prepared as a φ2cm sample with N=5. Using a Kato Tech KES-G5 compression tester, the area of ​​the compression element is 2cm. 2 The substrate is compressed at a rate of 0.1 mm / sec until it reaches 10% of its original thickness, and then its recoverability is measured when it is released. The average value of the compression recoverability RC obtained for N=5 is used as the "compression recoverability RC of the substrate."

[0036] (4) Compressed linearity at the detection section LC[-] The material used for the detection part is φ1.6cm (area 2cm 2 A Kato Tech KES-G5 compression tester was used to prepare a sample with a compression element area of ​​2 cm. 2 The compressive properties in the thickness direction are measured under standard conditions. The average value of the compressive linearity LC obtained for N=5 is used as the "compressive linearity LC at the detection part."

[0037] (5) Moisture content in the conductive material for the detection unit [%] The conductive material for the detection unit is dried at 105°C for 2 hours, and the dry mass is measured. After that, the material is conditioned under 30°C and 70% humidity for 3 hours, and the conditioned weight is measured and calculated using the following formula: Moisture content (%) = {Conditioned mass (g) - Absolute dry mass (g)} / Absolute dry mass (g) × 100 The "moisture content in the conductive member for the detection section" is calculated by the above method.

[0038] (6) Weight of conductive material for detecting part [g / m 2 ] The mass of the sample of conductive material for the detection part was measured using an electronic balance and calculated using the following formula: Weight of conductive material for detection part (g / m 2 ) = Mass of conductive material for detection unit (g) / Area of ​​conductive material for detection unit (m 2 ) The weight of the conductive material for the detection section (g / m 2 )"

[0039] (7) Thickness of the conductive material for the detection unit [mm] The thickness of the conductive member for the detection section is measured at five locations using a Peacock No. 207 manufactured by Ozaki Seisakusho, and the average value is used as the "thickness of the conductive member for the detection section."

[0040] (8) Surface roughness Rq [μm] of the conductive material for the detection unit A 1.5cm x 7.0cm sample of the conductive material for the detection unit is prepared, and the surface shape of the surface that comes into contact with the skin is measured at 50x magnification using a Keyence VR3000. From the obtained data, the line roughness in the vertical and horizontal directions is measured at three locations in each direction to obtain the line roughness Rq. The average line roughness Rq in each measurement direction is compared, and the larger value is used as the "surface roughness Rq of the conductive material for the detection unit."

[0041] (9) Contact pressure of electrode part [hPa] The electrode garment was placed on a Tenken Souisha full-body waist-supporting realistic mannequin (gentleman) so that the first electrode was in contact with the lower right rib area and the second electrode was in contact with the lower left rib area. The contact pressure between the mannequin and the electrodes was then measured using an AMI3037-2 contact pressure measuring device manufactured by AMI Techno. The garment was then removed and re-put on, after which the pressure measurement was repeated five times in total, and the average value was used as the "contact pressure of the electrode part."

[0042] (10) Percentage of noise waveforms in electrocardiograms [%] Three subjects were asked to wear an electrode garment with the first electrode in contact with the right lower rib and the second electrode in contact with the left lower rib. The positive electrode of the Intercross-415 manufactured by Intercross was connected to the second electrode, and the negative electrode to the first electrode, with the electrode grounded to the manubrium with a gel electrode. In this state, subjects went about their daily lives for eight hours, during which time the electrocardiogram was continuously measured. The total time during which noise occurred in the obtained electrocardiogram waveforms was divided by the total time to be analyzed (8 hours), and this value multiplied by 100 was used as the noise waveform percentage. The average noise waveform percentage for the three subjects was used as the "noise waveform percentage in the electrocardiogram." Note that a noise percentage of 5% or higher was deemed to be insufficient performance as an electrode.

[0043] (11) Comfort when wearing Ten subjects were asked to wear the electrode garment for eight hours, with the first electrode in contact with the right lower rib area and the second electrode in contact with the left lower rib area. Subjective evaluations of comfort were then conducted using the following criteria for two items: (i) pressure sensation and (ii) stickiness. The average score of the ten subjects was used as the "wearing comfort" rating. A rating of 3 or higher (3, 4, or 5) was considered acceptable. (i) A feeling of pressure 5: There is no pressure at all and it is very comfortable. 4: There is almost no pressure and it is very comfortable. 3: There is some pressure, but it is comfortable. 2: There is a feeling of pressure and it is quite uncomfortable. 1: There is a strong feeling of pressure and it is very uncomfortable. (ii) Stickiness 5: No sticky feeling at all, very comfortable. 4: There is almost no sticking feeling and it is quite comfortable. 3: There is a slight sticking sensation, but it is comfortable. 2: Sticky feeling and quite uncomfortable. 1: There is a very sticky feeling and it is very uncomfortable.

[0044] [Example 1] <Method of manufacturing each part of the electrode body> "Conductive material for detection section" The conductive fabric was a metal-plated fabric Sui-10-511M manufactured by Seiren Co., Ltd., and this conductive fabric was punched out into a circle with a diameter of 5 cm to form the conductive member for the detection section. Wiring materials The conductive fabric used for the conductive member for the detection section was cut into a piece 5 mm wide and 6 cm long to be used as a wiring member. "Support layer" A rubber sheet MX48HF3BK manufactured by Inoac Corporation was punched out to a diameter of 3 cm to serve as the support layer. "Base material part" Low-resilience urethane foam "PUF-03" manufactured by Wake Sangyo Co., Ltd. was punched into a cylindrical shape with a diameter of 40 mm and a thickness of 10 mm, which was used as a base material member. "High friction material" A rubber sheet MX48HF1BK manufactured by Inoac Corporation was punched out to a diameter of 40 mm, and the inner side was further punched out to a circle with a diameter of 30 mm to obtain a ring-shaped rubber sheet with a width of 5 mm, which was used as the high-friction material. <How to make the detection unit> The wiring member was placed on top of the conductive member for the detection unit so that it overlapped by 2 cm from the edge, and a heat-sealed seal ("cloth adhesive tape" manufactured by Leonis Co., Ltd.) punched to a diameter of 5 cm was attached so that its edge was aligned with the conductive member for the detection unit and so that it sandwiched the wiring member. Next, the conductive fabric for the detection unit was placed on top of the support layer so that the center of the circular portion of the conductive fabric for the detection unit was aligned with the center of the circular surface of the support layer and so that the heat-sealed seal surface was in contact with the support layer. In this state, an iron heated to 130°C was pressed against the conductive member for the detection unit, which was covered with a cloth, to heat-seal the conductive member and the support layer, and the resulting product was used as the detection unit. <Method for manufacturing electrode body> An epoxy adhesive was applied to the circular surface of the detecting part where the wiring member protruded, and the detecting part was attached 5 mm from the edge of the circular surface of the base part. Next, epoxy adhesive was applied to the low-friction side so that the high-friction side of the high-friction material would be the side that came into contact with the skin, and the epoxy adhesive was attached to the base part so that it surrounded the periphery of the detecting part, resulting in an electrode body. <Wearing test> The resulting electrode was evaluated for contact pressure, the proportion of noise waveforms in electrocardiograms, and comfort.The results showed that the sample was excellent, with an extremely low proportion of noise waveforms, and little pressure or stickiness.

[0045] [Example 2] An electrode body was obtained in the same manner as in Example 1, except that the conductive fabric was made of a plain stitch knit using conductive fiber Silvern ZAG100d and the back side of the fabric was used as the side that came into contact with the skin. The proportion of noise waveforms in this electrode body was greater than in Example 1, but the feeling of pressure and stickiness was equivalent to that of Example 1, making it a good sample.

[0046] [Example 3] An electrode body was obtained in the same manner as in Example 1, except that urethane foam "#3" manufactured by Yawata Neji Co., Ltd. was used as the material for the substrate. The proportion of noise waveforms in this electrode body was slightly higher than in Example 1, but the pressure sensation and stickiness were equivalent to those of Example 1, making it a good sample.

[0047] [Example 4] An electrode body was obtained in the same manner as in Example 1, except that the conductive fabric used was a metal-plated fabric, Sui-10-30T, manufactured by Seiren Co., Ltd. The proportion of noise waveforms in this electrode body was slightly higher than in Example 1, but the pressure and stickiness were comparable to those of Example 1, making it a good sample.

[0048] [Example 5] An electrode body was obtained in the same manner as in Example 1, except that the support layer material was a low-resilience urethane foam "PUF-03" manufactured by Wake Sangyo Co., Ltd. The proportion of noise waveforms in this electrode body was greater than in Example 1, but the pressure sensation and stickiness were comparable to those of Example 1, making it a good sample.

[0049] [Example 6] As a binder, PVA5-88 manufactured by Kuraray Co., Ltd. was dissolved in soft water to a concentration of 30 wt%, and the PVA solution was applied with a brush only to the back surface of the conductive fabric obtained in the same procedure as in Example 2. The fabric was then dried at 50°C for 75 minutes, and the PVA processing amount was adjusted to approximately 70 g / m2. 2 An electrode body was obtained in the same manner as in Example 2, except that the PVA-treated back surface of the fabric was used so that it came into contact with the skin. The adhesion of this electrode body was slightly worse than in Example 1, but the proportion of noise waveforms and the feeling of pressure were as small as in Example 1, making it a good sample.

[0050] [Example 7] An electrode body was obtained in the same manner as in Example 1, except that the conductive fabric used was Asahi Kasei Eltas, with silver sputtered on both sides. The proportion of noise waveforms in this electrode body was greater than in Example 1, but the pressure and stickiness were comparable to those of Example 1, making it a good sample.

[0051] [Example 8] <Method of manufacturing each part of the electrode body> "Conductive material for detection section" The conductive fabric was a metal-plated fabric Sui-10-511M manufactured by Seiren Co., Ltd., and this conductive fabric was cut into a rectangular shape of 9 cm x 14 cm to be used as the conductive member for the detection section. Wiring materials The conductive fabric used for the conductive member for the detection section was cut into a piece 5 mm wide and 6 cm long to be used as a wiring member. "Support layer" A rubber sheet MX48HF3BK manufactured by Inoac Corporation was cut into a size of 7 cm x 12 cm and used as a support layer. "Base material part" Low-resilience urethane foam "PUF-03" manufactured by Wake Sangyo Co., Ltd. was cut into a rectangular parallelepiped shape measuring 8 cm x 13 cm and 10 mm thick, and used as the base material. "High friction material" A rubber sheet MX48HF1BK manufactured by Inoac Corporation was cut into a size of 8 cm x 13 cm, and the inner side was further cut out into a rectangle of 7 cm x 12 cm to obtain a hollow rectangular rubber sheet with a width of 5 mm, which was used as the high-friction material. <How to make the detection unit> The wiring member was placed on top of the conductive member for the detection unit, overlapping by 2 cm from the edge, and a heat-seal seal ("Fabric Adhesive Tape" manufactured by Leonis Co., Ltd.) was attached to the entire surface of the wiring member, sandwiching the wiring member. The center of the rectangular portion of the conductive fabric for the detection unit was then aligned with the center of the surface with the larger area of ​​the support layer, and the conductive fabric for the detection unit was placed on top of the support layer so that it completely covered one of the two larger surfaces and the heat-seal seal surface was in contact with the support layer. In this state, an iron heated to 130°C was pressed against the conductive member for the detection unit, which was covered with a cloth, to heat-seal the conductive member and the support layer, resulting in the detection unit. <Method for manufacturing electrode body> An epoxy adhesive was applied to the rectangular surface of the sensing part from which the wiring member protruded, and the sensing part was attached 5 mm from the edge of the rectangular surface of the base material. Next, epoxy adhesive was applied to the low-friction side of the high-friction material, with the high-friction side facing the skin, and the sensing part was attached to the base material so that it surrounded the sensing part. This resulted in an electrode body. The proportion of noise waveforms in this electrode body was slightly higher than in Example 1, and the feeling of pressure was also slightly greater, but the adhesion was good, comparable to that of Example 1.

[0052] [Comparative Example 1] An electrode body was obtained in the same manner as in Example 1 of Patent Document 1. The pressure and stickiness of this electrode body were equivalent to those of Example 1, but the proportion of noise waveforms was much higher than in Example 1, making this a sample with insufficient performance.

[0053] The results of Examples 1 to 8 and Comparative Example 1 are summarized in Table 1 below. [Table 1] [Industrial Applicability]

[0054] The bioelectrode body of the present invention can provide an electrode body that suppresses motion artifacts and provides sufficient comfort when worn for long periods of time, and can therefore be suitably used as an electrode body that can acquire vital information. [Explanation of symbols]

[0055] 10 Bioelectrode (electrode body) 1. Woven, knitted or nonwoven fabrics made of conductive fibers (conductive material for detection part) 2 Transmission means (wiring components) 3 Elastic support layer (support layer) 4 Base material part 5 High friction area 6. Detection unit 7. Clothing, etc.

Claims

1. below: A detecting section that comes into contact with the skin, wherein the detecting section is composed of a woven, knitted or nonwoven fabric made of conductive fibers and an elastic support layer, the elastic support layer being covered by the woven, knitted or nonwoven fabric on the skin side and being integrated therewith, the woven, knitted or nonwoven fabric having an elongation of 10 mm or less in at least one direction when subjected to a load of 500 g, and a bending rigidity (B) of 0.015 gf cm ２ / cm or more 2.500gf・cm ２ / cm or less; a transmission means, one end of which is connected to the woven, knitted or nonwoven fabric and the other end of which is connected to an external element and capable of transmitting an electrical signal; and a base material portion having a compression recovery (RC) of 30% or more, which is disposed on the surface of the elastic support layer opposite to the skin side; A bioelectrode comprising:

2. The bioelectrode according to claim 1, wherein the compressive linearity (LC) of the detection portion is 0.45 to 1.

00.

3. 3. The bioelectrode according to claim 1 or 2, wherein in the detection section, a binder is present on the surface of the constituent fibers of the woven, knitted or nonwoven fabric on the side that comes into contact with the skin, filling the spaces between the fibers, and the moisture content of the woven, knitted or nonwoven fabric under environmental conditions of 30°C and 70% is 4.5% or more.

4. The detection unit is made of a woven fabric, and the basis weight of the woven fabric is 10 g / m ２ 150g / m or more ２ The bioelectrode according to claim 1 or 2, wherein the thickness is 0.01 mm or more and 1.00 mm or less, and the surface roughness Rq is 5 μm or more and 100 μm or less.

5. The detection unit is made of a nonwoven fabric, and the basis weight of the nonwoven fabric is 10 g / m ２ 150g / m or more ２ The bioelectrode according to claim 1 or 2, wherein the thickness is 0.01 mm or more and 1.00 mm or less, and the surface roughness Rq is 5 μm or more and 100 μm or less.

6. The detection unit is made of a knitted fabric, and the weight of the knitted fabric is 50 g / m ２ More than 200g / m ２ The bioelectrode according to claim 1 or 2, wherein the thickness is 0.10 mm or more and 1.50 mm or less, and the surface roughness Rq is 5 μm or more and 100 μm or less.

7. The area of ​​the detection part that comes into contact with the skin during use is 175 mm ２ Over 10,000 mm ２ The bioelectrode according to claim 1 or 2, wherein:

8. The bioelectrode according to claim 1 or 2, further comprising a high-friction portion disposed around the detection portion and having a static friction coefficient higher than a static friction coefficient of the detection portion that contacts the skin during use.

9. A biological information measuring device comprising the bioelectrode according to claim 1 or 2.

10. The biological information measuring device according to claim 9 , which is a wearable device.

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