Conductive cloth for bioelectrode and use therefor

Abstract

To provide conductive cloth for a bioelectrode capable of performing highly accurate sensing of biological information and simultaneously enhancing comfort in wearing due to soft texture belonging to fibers by suppressing motion artifact during body motion, and its use.SOLUTION: In a conductive cloth for a bioelectrode having fibers having a conductive metal coating layer whose thickness is 0.10 μm or more and 1.0 μm or less around it on at least one side, the conductive cloth is a woven fabric, and the flexural rigidity (B) of the woven fabric is 0.10×10-4 Nm2 / m or less, surface resistance of the one side is 1 kΩ / square or less, and the average deviation (SMD) of the surface roughness of the one side is 1.50 μm or less, and a biological information measurement device includes the conductive cloth for bioelectrode in which a conductive metal coating layer is used by being attached to a skin surface of a living body, a bioelectrode including the conductive cloth for a bioelectrode, and the bioelectrode.SELECTED DRAWING: Figure 1

Description

[Technical Field]

[0001] The present invention relates to a conductive cloth for a bioelectrode and its use. [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 clearly acquire bioelectrical potentials by reducing noise (motion artifacts) that occurs when the contact state between the device and the skin changes due to the user's body movements.

[0003] The sensing part that comes into contact with the skin is the most important part when acquiring bioelectric potentials, and conventionally, electrodes have been made using metal plates. Metal plate electrodes have low contact impedance with the skin, which reduces motion artifacts and provides high sensing performance. However, they can become stiff and sweaty when worn for long periods of time, making them less comfortable for the user. In response, research and development is underway to develop electrode surface materials that are more comfortable, using conductive fabric made from conductive fibers.

[0004] For example, Patent Document 1 below proposes "a fabric electrode that can be used as an electrode for a biological sensor, has excellent adhesion to the skin, and is difficult to peel off from the skin when worn, and a manufacturing method thereof." The fabric electrode described in Patent Document 1 is worn with the non-conductive fabric side facing the skin, so it is unlikely to cause itching or discomfort when worn, has good breathability, and is flexible enough to follow the movements of the living body and is difficult to peel off from the skin when worn. [Prior art documents] [Patent documents]

[0005] [Patent Document 1] Patent No. 6487746 Summary of the Invention [Problem to be solved by the invention]

[0006] However, although Patent Document 1 discloses a fabric electrode structure that is comfortable to wear and does not cause itching or discomfort, it does not achieve an electrode with a pleasant texture. Furthermore, because the non-conductive fabric is attached to the skin side, the sensing performance of biological information is insufficient. In other words, a conductive fabric for a bioelectrode that suppresses motion artifacts, has high sensing performance, and is comfortable for the user has not yet been realized.

[0007] The present invention has been made to solve the problems of the prior art described above, and its objective is to provide a conductive fabric for bioelectrodes that can suppress motion artifacts during body movement, enabling accurate sensing of biological information, while at the same time increasing comfort when worn due to the soft texture of the fibers, and uses thereof. [Means for solving the problem]

[0008] The present inventors have conducted extensive research and experiments to solve the above problems, and as a result have unexpectedly found that the above problems can be solved by the following configuration, which has led to the completion of the present invention.

[0009] That is, the present invention is as follows. [1] A conductive cloth for a bioelectrode having fibers with a conductive metal coating layer having a thickness of 0.10 μm or more and 1.0 μm or less on at least one side, the conductive cloth being a woven fabric, and the bending rigidity (B) of the woven fabric is 0.10 × 10 -4 Nm 2 / m or less, the surface resistance of one side is 1 kΩ / □ or less, the surface roughness mean deviation (SMD) of one side is 1.50 μm or less, and the conductive metal coating layer is used by being attached to the skin surface of a living body. [2] The fineness of the yarn constituting the woven fabric is 1 dtex or more and 100 dtex or less, and the woven fabric satisfies the following formula:

number

[0010] According to the present invention, it is possible to provide a conductive fabric for bioelectrodes that suppresses motion artifacts when acquiring bioinformation and combines high sensing performance with a comfortable texture. [Brief explanation of the drawings]

[0011] [Figure 1] This is an SEM image of the cross section of a fiber that appears on the surface of the fabric. It shows the presence of a conductive metal coating layer with a thickness of 0.10 μm to 1.0 μm around the fiber. DETAILED DESCRIPTION OF THE INVENTION

[0012] Hereinafter, an embodiment of the present invention (hereinafter referred to as "embodiment") will be described in detail.

[0013] One embodiment of the present invention is a conductive cloth for a bioelectrode having fibers on at least one side thereof with a conductive metal coating layer having a thickness of 0.10 μm or more and 1.0 μm or less around the periphery thereof, the conductive cloth being a woven fabric, and the bending rigidity (B) of the woven fabric is 0.10×10-4 Nm 2 / m or less, the surface resistance of one side is 1 kΩ / □ or less, the mean deviation of the surface roughness (SMD) of one side is 1.50 μm or less, and the conductive metal coating layer is used by being attached to the skin surface of a living body.

[0014] At least one fiber present on the surface of the conductive fabric of this embodiment is a fiber having a conductive metal coating layer with a thickness of 0.10 μm to 1.0 μm around it. This conductive metal coating layer is defined as a portion that covers the outermost layer of the fiber diameter and appears white in contrast to the interior of the fiber, as shown in FIG. 1, when the cross-section of the fiber is observed using backscattered electron images from a scanning electron microscope, and the difference in the composition of the elements that make up the cross-section is identified by contrast. The thickness of this layer (thickness) is calculated by measuring five arbitrary points on the surface of the fiber cross-section, as shown in FIG. 1, and averaging the measurements. Since this conductive metal coating layer is used by being attached to the skin of a living body, it is sufficient that the fiber having this conductive metal coating layer be present on at least one side of the conductive fabric (fabric). In other words, this fiber does not necessarily have to be present inside the fabric. The thickness of the conductive metal coating layer is 0.10 μm or more and 1.0 μm or less, preferably 0.3 μm or more and 1.0 μm or less. If the thickness of the conductive metal coating layer is less than 0.1 μm, sufficient surface conductivity cannot be obtained and the required sensing performance cannot be achieved. On the other hand, if the thickness is more than 1.0 μm, the thickness of the coating increases the rigidity of the fiber, and the texture and flexibility inherent to the material are lost.

[0015] The method for producing the woven fabric made of fibers having a conductive metal coating layer of this embodiment is not particularly limited, and any conventionally known method such as sputtering, vacuum deposition, electroplating, or electroless plating can be used. However, electroless plating is preferred because it provides high adhesion to the metal coating layer, making it easy to achieve low electrical resistance, and does not require plating of the base.

[0016] Regarding the order of fabrication of the conductive metal coating layer, either a method of weaving a fabric from fibers already bearing a conductive metal coating layer or a method of weaving a fabric using non-conductive fibers without a conductive metal coating layer and then forming a metal coating can be employed. However, the method of weaving a fabric from fibers already bearing a conductive metal coating layer is generally preferable because such fibers are relatively expensive and the productivity of weaving is low. The latter method is also preferable because it allows greater freedom in designing a fabric with the desired texture. The fibers having the metal coating layer in advance are not particularly limited, but examples thereof include nylon fibers whose surfaces are silver-plated, polyethylene terephthalate fibers whose surfaces are silver-plated, and nylon fibers whose surfaces are copper-plated.

[0017] The metal coating layer may be a single layer or multiple layers, but a single layer is preferred to achieve the above-mentioned thickness range. Examples of metals used in the outermost layer 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 their alloys. However, silver is preferred. This is due to its low potential for metal allergies, and its excellent electrode potential stability and low electrode impedance in the low-frequency band, making it ideal for capturing minute signals in the low-frequency band during biopotential measurement. In the case of multiple layers, the metal used in the lower layer of silver is not particularly limited, but copper is preferred for its high workability and for preventing metal allergies. The proportion of silver appearing in the outermost layer, as determined by weight fraction using quantitative EDX analysis, is preferably 50 mass% or more. If the silver occupancy rate is 50 mass % or more, a sufficient amount of silver appears, which increases the stability of the electrode potential and reduces the contact impedance.

[0018] The bending rigidity of the conductive cloth of this embodiment is 0.10 × 10 -4 Nm 2 / m or less. The bending stiffness is 0.10 × 10 -4 Nm 2 / m or less, the softness of the woven fabric is felt when it touches the skin, which is a factor in the feeling that the texture is good. -4 Nm 2 If the thickness exceeds 1 / m, the conductive fabric will lack flexibility when it comes into contact with the skin, and the feel will be perceived as poor.

[0019] The surface resistivity of the conductive fabric in this embodiment is 1 kΩ / □ or less. If the surface resistivity is greater than 1 kΩ / □, contact impedance with the skin increases during body movement, making it more likely to generate noise and making it difficult to accurately detect biological signals.

[0020] The surface roughness mean deviation (SMD) of the conductive fabric of this embodiment is 1.50 μm or less, preferably 1.00 μm or less, and more preferably 0.70 μm or less. If the SMD is greater than 1.50 μm, the unevenness of the fiber surface will be too great, resulting in poor adhesion of the metal coating layer, making it difficult to establish a conductive path and achieving low resistance. In addition, the fabric may be subjected to a press treatment or calendaring process to flatten the surface and reduce the SMD.

[0021] The conductive fabric of this embodiment is a woven fabric. The fiber material constituting the woven fabric is not particularly limited and may be any of natural fibers, recycled fibers, semi-synthetic fibers, and synthetic fibers, or a combination of several fibers. These fibers can be made into yarns, such as long fibers, short fibers, or composite fibers thereof, processed yarns, spun yarns, etc., and woven fabrics can be obtained using these yarns. From the standpoints of processability and durability, however, polyethylene terephthalate (PET) filament yarns are preferred. The cross-sectional shape of the fiber is also not particularly limited and may be a round cross-section, an irregular cross-section, etc., but a flat cross-section is preferred for the purpose of increasing surface smoothness and improving conductivity.

[0022] The conductive fabric of this embodiment is made of woven fabric. Compared to nonwoven fabrics and films, woven fabrics are more breathable and less likely to cause discomfort such as itching and rashes. Furthermore, compared to knitted fabrics, woven fabrics are superior in that they are less susceptible to slippage and deformation, thereby suppressing motion artifacts during sensing, and can be made into thin fabrics, thereby improving bending softness. Examples of weaves for woven fabrics include plain weave, twill weave, satin weave, and variations thereof. The fineness of the fibers constituting these fabrics is preferably in the range of 1 dtex to 100 dtex, more preferably 5 dtex to 50 dtex. A fineness within this range prevents excessive smoothness, allowing the woven fabric to be worn comfortably without sticking to the skin, and also prevents excessive bending stress, resulting in a woven fabric with a pleasant texture.

[0023] The fabric has the following formula:

number

[0024] The conductive fabric of this embodiment can be used as part of a bioelectrode. The electrode may be configured so that the surface of the conductive fabric bearing the metal coating layer is the surface and can be directly attached to the skin of a living body. Examples of shapes include a rectangular parallelepiped, cube, polyhedron, cylinder, and cone. A substrate is preferably included for improved durability and for ease of attachment to a device. The substrate material is not particularly limited, but examples include polyurethane, low-resilience or high-resilience urethane, rubber, and three-dimensional knitted fabric. The substrate material preferably has compressive and / or shear deformability. When the substrate has compressive and / or shear deformability, the force pulling the electrode caused by body movement first deforms the substrate. While the substrate is deformed, the contact state between the bioelectrode and the skin can be maintained, further reducing motion artifacts. The height of the electrode, when the surface in contact with the living body is the bottom, is preferably 1 mm or more, more preferably 2 mm or more, and even more preferably 5 mm or more, and is preferably 20 mm or less, more preferably 10 mm or less. If the height of the substrate is 20 mm or less, twisting is less likely to occur when the bioelectrode is attached to a living body, allowing for accurate measurement of biosignals. The surface that comes into contact with the living body may have a non-conductive region, and examples of the non-conductive region include the same material as the substrate. In addition, the non-conductive region may be made of a material that serves to prevent slippage from the living body, such as rubber, polyurethane, and high-friction knitted or woven fabrics.

[0025] The conductive fabric of this embodiment can be a bioinformation measuring device equipped with the bioelectrode (or including one or more of the electrodes). A bioinformation measuring device including one or more of the electrodes 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 (EEG), and is particularly suitable for measuring cardiac potential. The bioinformation measuring device can be in the form of a wearable device, a band, a watch, glasses, a hat, or the like, with a wearable device being preferred. When the bioinformation measuring device is wearable, it is sufficient that the electrodes are pressed against the area to be measured. Examples of the bioinformation measuring device include arm covers for the arm, tights for the lower body, and a shirt for the upper body. The fabric used in a wearable bioinformation measuring device is not particularly limited, but from the perspective of appropriately adjusting contact pressure, a compressive fabric containing elastic yarns such as polyurethane elastic yarns is preferred. The wearable bioinformation measuring device may also include other sensor devices, etc., as long as they do not impair the effects of the invention.

[0026] The method for attaching a bioelectrode to a bioinformation measuring device is not particularly limited, but examples include sewing the electrode to the bioinformation measuring device, adhering the electrode to the device using a thermoplastic resin or adhesive, or crimping a portion of the electrode to the device using a crimp terminal. Adhering the electrode to the device using a thermoplastic resin is preferred because it is easier to attach. The electrode may be attached to the bioinformation measuring device in a removable or permanent manner. When the transmission section of the electrode 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 gluing the end of the wire to a measurement terminal of the bioinformation measuring device using solder or a conductive adhesive, or crimping using a crimp terminal. The wire may also be electrically connected to the bioinformation measuring device indirectly by connecting the wire to a detachable connector of the bioinformation measuring device. [Example]

[0027] The present invention will be described in detail below with reference to examples and comparative examples, but the present invention is not limited to these examples. The evaluation methods used in the examples are as follows.

[0028] (1) Metal coating thickness [μm] The sample was cut perpendicular to the fibers that make up the fabric with a cutter blade, and the cross section was observed using a JEOL JSM-IT500 scanning electron microscope with a signal of BED-C and an incident voltage of 10.0 kV. As shown in Figure 1, differences in the composition of the elements that make up the cross section were identified by contrast differences, and the film thickness of the outermost layer of the fiber diameter, which appears white in contrast to the interior of the fiber, was measured using the measurement function in the observation application. Three film thickness measurements were taken for each of five arbitrary fiber cross sections (n=5) that appeared on the surface of the fabric, and the average of a total of 15 data points was calculated.

[0029] (2) Weight [g / m 2 ] JIS-L-1096 8.4.2 Calculated using the mass per unit area of ​​the fabric in its standard state.

[0030] (3) Fabric thickness [mm] Peacock thickness gauge (dial thickness gauge, contact pressure: 7g / cm 2 ) and calculated as the average value of n=5.

[0031] (4) Bending rigidity B [×10 -4 Nm 2 / m] Using a 20x20cm sample taken at 20°C and 65%RH, the bending stiffness was measured in the longitudinal and transverse directions (n=3 each) using a Kato Tech KES-FB2 testing machine, and the bending stiffness was expressed as the average value of the bending stiffness B in the longitudinal and transverse directions. Standard conditions were used.

[0032] (5) Surface roughness SMD [μm] In an environment of 20°C and 65% RH, a 20 x 20 cm sample was placed on a Kato Tech KES-FB4 testing machine with a tension of 400 gf. Measurements were taken on three samples in each of the warp and weft directions, and the average value of the mean deviation (SMD) of the surface roughness in the warp and weft directions was expressed as the average value. Standard conditions were used. The larger the SMD value, the more uneven the fabric surface is judged to be.

[0033] (6) Surface resistance value [kΩ / □] In an environment of 20°C and 65% RH, samples were taken in 5x5cm size and measured at the centre of the sample using a Loresta GX-II main unit manufactured by Nitto Seiko Analytic Co., Ltd. and the attached LSP probe, with n=5 results expressed as an average value.

[0034] (7) Surface abundance of Ag [Mass%] Three randomly selected sample surfaces were quantitatively analyzed for elements present on the sample surface using a JEOL JSM-IT500 scanning electron microscope under conditions of signal SED and incident voltage of 15.0 kV using energy dispersive X-ray analysis. The weight percentage of Ag in the quantitative analysis results was averaged and shown.

[0035] (8) Electrode fabrication method To evaluate comfort during wear and electrocardiographic sensing performance, a pair of bioelectrodes was fabricated using the samples as follows. A cylindrical urethane foam substrate (10 mm thick, 40 mm diameter) was used. A 25 mm diameter sample fabric was attached to the center of one side of the substrate using adhesive to form a conductive area. The sample fabric was cut to a width of 5 mm and a length of 60 mm. One end of the wiring was attached to the conductive area, and the other end was connected to a metal snap button (11 mm diameter).

[0036] (9) Wearing test The following wearing test was conducted to evaluate the electrocardiographic sensing performance and comfort of the sample. Five adult male subjects wore a wearable biometric measurement device equipped with a pair of bioelectrodes fabricated using the sample fabric according to the electrode fabrication method described above (8). After 30 minutes of acclimation while wearing the device in a 20°C, 30% RH environment, electrocardiograms were measured for 10 minutes at a walking speed of 4 km / h on a treadmill. The Intercross-415 (Intercross Corporation) was used for the electrocardiogram measurement. The fabric under evaluation was worn in direct contact with the skin at two locations: the right lower rib and the left lower rib. The positive and negative cables of the Intercross-415 were connected to the metal snap buttons of the bioelectrodes. The body earth cable of the Intercross-415 was connected to a gel electrode (Cardinal Health Co., Ltd., Albo H124), which was attached to the subject's sternum between the clavicle and the second rib. After the electrocardiogram measurements, the subjects were asked to perform a sensory evaluation of the comfort of wearing the device and evaluate the samples attached to each electrode. The analysis methods and evaluation indices for sensing performance by electrocardiogram measurements and comfort of wearing the device are described below.

[0037] (9-A) Sensing performance by electrocardiogram measurement The electrocardiogram measurement results were analyzed as follows. The DTW (Dynamic Time Warping) method was used for analysis. DTW is a method for measuring the similarity between time-series data, and in this case it was applied to the time-series data of electrocardiogram waveforms. The similarity between the electrocardiogram waveforms obtained with the developed electrode and those of a benchmark product obtained with a metal plate electrode made of tantalum oxide was analyzed, and the calculated value of similarity obtained was defined as the DTW value, and the evaluation criteria are shown below. The lower the DTW value, i.e., the higher the similarity, the better the electrode's sensing performance can be determined. Sensing performance was determined to be good when the average DTW value obtained from the electrocardiogram waveforms of the five subjects while walking was less than 40, and poor when it was 40 or higher. (Evaluation criteria) DTW value 0-20: Very high similarity with almost no noise DTW value 20-40: Somewhat high similarity with some noise DTW value 40-60: ECG waveforms are partially obtained with a slightly low similarity. DTW value 60 or more: The similarity is very low and the ECG waveform cannot be obtained overall.

[0038] (9-B) Comfort when wearing Comfort when wearing the product was evaluated on a 5-point scale from 1 to 5 according to the following evaluation criteria. Here, 5 indicates the highest rating, i.e., the highest comfort when wearing the product. The average rating of the five subjects was used as the "comfort when wearing the product." Comfort greater than 3.5 was evaluated as good, and comfort less than 3.5 was judged as poor. (Evaluation criteria) 5: Very comfortable 4: Comfortable 3: Neither 2: Uncomfortable 1: Very uncomfortable.

[0039] [Example 1] PET fibers with a warp thread of 56 dtex 24f and a weft thread of 84 dtex 36f were woven into a plain weave, refined, preset, and then calendered to obtain a woven fabric. The woven fabric was then subjected to a metal coating process using an Ag electroless plating method to obtain a conductive cloth with an Ag film on the fiber surface. The physical properties of the obtained conductive cloth are shown in Table 1 below. Electrodes were prepared using the obtained conductive cloth according to the electrode preparation method described above, and a wearing test was conducted. The results are also shown in Table 1 below.

[0040] [Example 2] Instead of the electroless plating method used in Example 1, a sputtering method was used to form a metal coating using Ag on both sides of the fabric, resulting in a conductive cloth with an Ag film on the fiber surface. The physical properties of the resulting conductive cloth are shown in Table 1 below. Electrodes were produced using the resulting conductive cloth according to the electrode production method described above, and a wearing test was conducted, with the results also shown in Table 1 below.

[0041] [Example 3] Both the warp and weft were made of 25 dtex 12f flat PET fibers, which were woven into a plain weave and then refined and pre-set to obtain a woven fabric. The woven fabric was then electrolessly plated with a Cu and Ni alloy to form a base metal coating layer, and then subjected to Ag electroplating to form a metal coating, yielding a conductive cloth with a metal coating on the fiber surface. The physical properties of the resulting conductive cloth are shown in Table 1 below. Electrodes were fabricated using the resulting conductive cloth according to the electrode fabrication method described above, and a wear test was conducted. The results are also shown in Table 1 below.

[0042] [Example 4] A plain weave fabric was obtained by scouring and presetting PET warp and weft fibers of 8 dtex 8f, followed by calendering to obtain a woven fabric. A metal coating using Ag was formed on both sides of the fabric by sputtering, yielding a conductive cloth with an Ag film on the fiber surface. The physical properties of the obtained conductive cloth are shown in Table 1 below. Electrodes were made using the obtained conductive cloth according to the electrode manufacturing method described above, and a wearing test was conducted. The results are also shown in Table 1 below.

[0043] [Example 5] Both the warp and weft were made of 44 dtex 10 f nylon fibers that had been Ag-plated, and the resulting fabric was plain woven and then refined and pre-set to obtain a conductive fabric. The physical properties of the resulting conductive fabric are shown in Table 1 below. Electrodes were made using the resulting conductive fabric according to the electrode manufacturing method described above, and a wearing test was conducted. The results are also shown in Table 1 below.

[0044] [Example 6] A plain weave fabric was obtained by scouring and presetting a fabric made from 4 dtex monofilament PET fibers for both the warp and weft. The fabric was then subjected to a metal coating process using Ag electroless plating to obtain a conductive cloth with an Ag film on the fiber surface. The physical properties of the obtained conductive cloth are shown in Table 1 below. Electrodes were prepared using the obtained conductive cloth according to the electrode preparation method described above, and a wearing test was conducted. The results are also shown in Table 1 below.

[0045] [Comparative Example 1] Conductive PET fabric Sui-10-511M (manufactured by Seiren Co., Ltd.) with a metal coating made of Cu and Ni alloy was obtained and evaluated. The evaluation of physical properties and the results of the wearing test are shown in Table 1 below.

[0046] Comparative Example 2 Conductive PET fabric Sui-10-70X (manufactured by Seiren Co., Ltd.) with a metal coating made of Cu and Ni alloy was obtained and evaluated. The evaluation of physical properties and the results of wearing are shown in Table 1 below.

[0047] Comparative Example 3 The fabric was made by weaving 100 dtex 36 filament PET fiber in both the warp and weft in a twill weave, and after scouring and presetting, one side of the fabric was vacuum-deposited to obtain a conductive fabric with an Ag film on the surface. The physical properties and wear test results of the obtained conductive fabric are shown in Table 1 below.

[0048] The results of the above examples and comparative examples are summarized in Table 1 below. [Table 1]

[0049] As shown in Table 1, the thickness of the conductive metal coating layer around the fibers appearing on the surface of the fabric is 0.10 μm or more and 1.0 μm or less, and the bending stiffness (B) is 0.10 × 10 -4 Nm 2 It was found that the conductive fabrics of Examples 1 to 6, which have a surface resistance of 1 kΩ / □ or less and a surface roughness mean deviation (SMD) of 1.50 μm or less, are comfortable to wear and have high electrocardiogram sensing performance. On the other hand, for Comparative Examples 1 and 2, although the electrocardiogram signal results met the acceptance criteria, the bending rigidity was high and the texture of the fabric was poor, resulting in poor comfort when worn. Furthermore, for Comparative Example 3, the bending rigidity was 0.10×10 -4 Nm 2 Although the thickness was in the range of 0.075 μm or less, making it comfortable to wear, it was found that the film thickness was insufficient at 0.075 μm, resulting in insufficient conductivity and a lack of sensing performance. Therefore, it can be seen that by using the conductive fabric of the present invention in a bioelectrode, motion artifacts can be suppressed when acquiring bioinformation, and both a highly comfortable texture and high sensing performance can be achieved. [Industrial Applicability]

[0050] The bioelectrode of the present invention can be used as a conductive fabric for a bioelectrode in a bioinformation measuring device for acquiring cardiac potential, myoelectric potential, electroencephalogram, skin surface electrical resistance, and other bioelectric information, and is particularly suitable for use in a wearable device for measuring cardiac potential. Furthermore, a bioelectrode using the conductive fabric of the present invention can also be used as an electrode for electrical stimulation therapy (e.g., potential therapy, low-frequency therapy, or EMS (Electrical Muscle Stimulation)). Furthermore, the bioelectrode using the conductive fabric of the present invention is not limited to use in humans, but can also be applied to animals.

Claims

1. A conductive cloth for a bioelectrode having fibers on at least one side thereof with a conductive metal coating layer having a thickness of 0.10 μm or more and 1.0 μm or less around the periphery thereof, the conductive cloth being a woven fabric, and the bending rigidity (B) of the woven fabric is 0.10×10 －４ Nm ２ / m or less, the surface resistance of one side is 1 kΩ / □ or less, the surface roughness mean deviation (SMD) of one side is 1.50 μm or less, and the conductive metal coating layer is used by being attached to the skin surface of a living body.

2. The fineness of the yarn constituting the woven fabric is 1 dtex or more and 100 dtex or less, and the woven fabric satisfies the following formula: [Equation 1] {In the formula, N ｗ is the warp density (counts / 2.54 cm), and D ｗ is the warp fineness (dtex), and N ｆ is the weft density (counts / 2.54 cm), and D ｆ 2. The conductive cloth for a bioelectrode according to claim 1, wherein a cover factor (CF) expressed by the following formula {where dtex is the weft fineness (dtex)} is 500 or more and 2000 or less.

3. 3. The conductive cloth for a bioelectrode according to claim 1, wherein the weight fraction of silver (Ag) in the elemental composition of the conductive metal coating layer is 50 mass % or more.

4. A bioelectrode comprising the conductive fabric for a bioelectrode according to claim 1 or 2.

5. A biological information measuring device comprising the bioelectrode according to claim 4.

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