JP2017218690A - Fabric electrode - Google Patents
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- JP2017218690A JP2017218690A JP2016113565A JP2016113565A JP2017218690A JP 2017218690 A JP2017218690 A JP 2017218690A JP 2016113565 A JP2016113565 A JP 2016113565A JP 2016113565 A JP2016113565 A JP 2016113565A JP 2017218690 A JP2017218690 A JP 2017218690A
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- 239000004744 fabric Substances 0.000 title claims abstract description 105
- 239000000835 fiber Substances 0.000 claims abstract description 91
- 238000009987 spinning Methods 0.000 claims abstract description 50
- 229920005989 resin Polymers 0.000 claims abstract description 23
- 239000011347 resin Substances 0.000 claims abstract description 23
- 229920001477 hydrophilic polymer Polymers 0.000 claims abstract description 19
- 238000001523 electrospinning Methods 0.000 claims description 8
- 238000000034 method Methods 0.000 claims description 7
- 239000004745 nonwoven fabric Substances 0.000 claims description 3
- 230000035699 permeability Effects 0.000 abstract description 7
- 238000010030 laminating Methods 0.000 abstract description 3
- 239000000243 solution Substances 0.000 description 41
- 229920003171 Poly (ethylene oxide) Polymers 0.000 description 24
- 239000004372 Polyvinyl alcohol Substances 0.000 description 17
- 229920002451 polyvinyl alcohol Polymers 0.000 description 17
- 229910052751 metal Inorganic materials 0.000 description 9
- 239000002184 metal Substances 0.000 description 9
- 238000011156 evaluation Methods 0.000 description 8
- 239000000463 material Substances 0.000 description 6
- 229920000642 polymer Polymers 0.000 description 6
- 239000007864 aqueous solution Substances 0.000 description 5
- 229920001778 nylon Polymers 0.000 description 5
- -1 polyethylene terephthalate Polymers 0.000 description 5
- 239000000853 adhesive Substances 0.000 description 4
- 230000001070 adhesive effect Effects 0.000 description 4
- 238000003475 lamination Methods 0.000 description 4
- 238000007747 plating Methods 0.000 description 4
- 239000002904 solvent Substances 0.000 description 4
- YMWUJEATGCHHMB-UHFFFAOYSA-N Dichloromethane Chemical compound ClCCl YMWUJEATGCHHMB-UHFFFAOYSA-N 0.000 description 3
- ZMXDDKWLCZADIW-UHFFFAOYSA-N N,N-Dimethylformamide Chemical compound CN(C)C=O ZMXDDKWLCZADIW-UHFFFAOYSA-N 0.000 description 3
- 238000005259 measurement Methods 0.000 description 3
- XLYOFNOQVPJJNP-UHFFFAOYSA-N water Substances O XLYOFNOQVPJJNP-UHFFFAOYSA-N 0.000 description 3
- HEDRZPFGACZZDS-UHFFFAOYSA-N Chloroform Chemical compound ClC(Cl)Cl HEDRZPFGACZZDS-UHFFFAOYSA-N 0.000 description 2
- PXHVJJICTQNCMI-UHFFFAOYSA-N Nickel Chemical compound [Ni] PXHVJJICTQNCMI-UHFFFAOYSA-N 0.000 description 2
- WYURNTSHIVDZCO-UHFFFAOYSA-N Tetrahydrofuran Chemical compound C1CCOC1 WYURNTSHIVDZCO-UHFFFAOYSA-N 0.000 description 2
- 238000000576 coating method Methods 0.000 description 2
- 230000000052 comparative effect Effects 0.000 description 2
- 230000000694 effects Effects 0.000 description 2
- 229920000728 polyester Polymers 0.000 description 2
- 229920000139 polyethylene terephthalate Polymers 0.000 description 2
- 239000005020 polyethylene terephthalate Substances 0.000 description 2
- 229920002972 Acrylic fiber Polymers 0.000 description 1
- OKTJSMMVPCPJKN-UHFFFAOYSA-N Carbon Chemical compound [C] OKTJSMMVPCPJKN-UHFFFAOYSA-N 0.000 description 1
- 229920000049 Carbon (fiber) Polymers 0.000 description 1
- 102000008186 Collagen Human genes 0.000 description 1
- 108010035532 Collagen Proteins 0.000 description 1
- RYGMFSIKBFXOCR-UHFFFAOYSA-N Copper Chemical compound [Cu] RYGMFSIKBFXOCR-UHFFFAOYSA-N 0.000 description 1
- 208000008454 Hyperhidrosis Diseases 0.000 description 1
- 239000004677 Nylon Substances 0.000 description 1
- 239000004952 Polyamide Substances 0.000 description 1
- 239000004698 Polyethylene Substances 0.000 description 1
- 239000002202 Polyethylene glycol Substances 0.000 description 1
- 239000004743 Polypropylene Substances 0.000 description 1
- 208000003251 Pruritus Diseases 0.000 description 1
- 150000001298 alcohols Chemical class 0.000 description 1
- 229910052782 aluminium Inorganic materials 0.000 description 1
- XAGFODPZIPBFFR-UHFFFAOYSA-N aluminium Chemical compound [Al] XAGFODPZIPBFFR-UHFFFAOYSA-N 0.000 description 1
- 210000003423 ankle Anatomy 0.000 description 1
- 230000005540 biological transmission Effects 0.000 description 1
- 239000000872 buffer Substances 0.000 description 1
- 229910052799 carbon Inorganic materials 0.000 description 1
- 239000004917 carbon fiber Substances 0.000 description 1
- 229920002301 cellulose acetate Polymers 0.000 description 1
- 239000011248 coating agent Substances 0.000 description 1
- 229920001436 collagen Polymers 0.000 description 1
- 229910052802 copper Inorganic materials 0.000 description 1
- 239000010949 copper Substances 0.000 description 1
- 238000010586 diagram Methods 0.000 description 1
- 239000003792 electrolyte Substances 0.000 description 1
- 239000011888 foil Substances 0.000 description 1
- PCHJSUWPFVWCPO-UHFFFAOYSA-N gold Chemical compound [Au] PCHJSUWPFVWCPO-UHFFFAOYSA-N 0.000 description 1
- 229910052737 gold Inorganic materials 0.000 description 1
- 239000010931 gold Substances 0.000 description 1
- 238000007654 immersion Methods 0.000 description 1
- 230000010354 integration Effects 0.000 description 1
- 230000007803 itching Effects 0.000 description 1
- 239000007788 liquid Substances 0.000 description 1
- 238000004519 manufacturing process Methods 0.000 description 1
- VNWKTOKETHGBQD-UHFFFAOYSA-N methane Chemical compound C VNWKTOKETHGBQD-UHFFFAOYSA-N 0.000 description 1
- 229910052759 nickel Inorganic materials 0.000 description 1
- 239000003960 organic solvent Substances 0.000 description 1
- 150000003904 phospholipids Chemical class 0.000 description 1
- 229920000747 poly(lactic acid) Polymers 0.000 description 1
- 229920000058 polyacrylate Polymers 0.000 description 1
- 229920002239 polyacrylonitrile Polymers 0.000 description 1
- 229920002647 polyamide Polymers 0.000 description 1
- 229920000515 polycarbonate Polymers 0.000 description 1
- 239000004417 polycarbonate Substances 0.000 description 1
- 229920000573 polyethylene Polymers 0.000 description 1
- 229920001223 polyethylene glycol Polymers 0.000 description 1
- 239000004626 polylactic acid Substances 0.000 description 1
- 238000006116 polymerization reaction Methods 0.000 description 1
- 229920001155 polypropylene Polymers 0.000 description 1
- 229920002635 polyurethane Polymers 0.000 description 1
- 239000004814 polyurethane Substances 0.000 description 1
- 229920000915 polyvinyl chloride Polymers 0.000 description 1
- 239000004800 polyvinyl chloride Substances 0.000 description 1
- 229920000036 polyvinylpyrrolidone Polymers 0.000 description 1
- 239000001267 polyvinylpyrrolidone Substances 0.000 description 1
- 235000013855 polyvinylpyrrolidone Nutrition 0.000 description 1
- 150000003839 salts Chemical class 0.000 description 1
- 230000035945 sensitivity Effects 0.000 description 1
- 229910052709 silver Inorganic materials 0.000 description 1
- 239000004332 silver Substances 0.000 description 1
- 230000035900 sweating Effects 0.000 description 1
- YLQBMQCUIZJEEH-UHFFFAOYSA-N tetrahydrofuran Natural products C=1C=COC=1 YLQBMQCUIZJEEH-UHFFFAOYSA-N 0.000 description 1
- 229920003169 water-soluble polymer Polymers 0.000 description 1
- 239000002759 woven fabric Substances 0.000 description 1
- 210000000707 wrist Anatomy 0.000 description 1
Landscapes
- Measurement And Recording Of Electrical Phenomena And Electrical Characteristics Of The Living Body (AREA)
- Laminated Bodies (AREA)
- Treatments For Attaching Organic Compounds To Fibrous Goods (AREA)
- Spinning Methods And Devices For Manufacturing Artificial Fibers (AREA)
- Nonwoven Fabrics (AREA)
Abstract
Description
本発明は、例えば、生体用センサーの電極として使用するものであって、非導電性布帛と導電性布帛との接着性に優れた布帛電極に関する。 The present invention relates to a fabric electrode that is used as, for example, an electrode of a biosensor and has excellent adhesion between a non-conductive fabric and a conductive fabric.
生体センサーの例として、心電図用電極を手首、足首に金属スナップ付き電極を固定し、胸には粘着剤を介して皮膚に密着させている。このようなものとして電気的に独立した複数の電極が、非導電性シート状物を介して一体化された生体医学用電極が知られている。より具体的には、例えば食塩などの電解質を溶解した含水ゲルを導電性接着剤とすることや、シート状の導電性接着剤でよいこと、電子電導層としては金属箔や導電性金属を蒸着したりすることや、導電性インクをコーティングすることで形成すること、また、非導電性シート状物としてはポリエチレンテレフタレート、ポリ塩化ビニル、ポリエチレン、ポリプロピレンなどのフィルムが使用できることが開示されている（特許文献１）。このような生体医学用電極によれば、複数の電極が非導電性シート状物を介して一体化していることにより皮膚への密着面積が大きく、皮膚への追従性もよい。 As an example of a biosensor, an electrode for electrocardiogram is fixed to the wrist and ankle with an electrode with a metal snap, and the chest is brought into close contact with the skin via an adhesive. As such, a biomedical electrode is known in which a plurality of electrically independent electrodes are integrated through a non-conductive sheet-like material. More specifically, for example, a water-containing gel in which an electrolyte such as salt is dissolved may be used as a conductive adhesive, or a sheet-like conductive adhesive may be used. A metal foil or a conductive metal is deposited as an electronic conductive layer. It is disclosed that a film such as polyethylene terephthalate, polyvinyl chloride, polyethylene, and polypropylene can be used as the non-conductive sheet-like material. Patent Document 1). According to such a biomedical electrode, since the plurality of electrodes are integrated through the non-conductive sheet-like material, the contact area with the skin is large and the followability to the skin is good.
しかしながら、従来の心電図用電極はゲル状やシート状の導電性接着剤で、フィルムである非導電性シート状物を積層していることから、肌に触れた際に肌との馴染が劣ることから違和感を覚え、通気性もないことから汗や痒みが生じるおそれがあった。さらに、心電図用電極の装着時には、肌からの脱落のおそれがあった。 However, the conventional electrocardiogram electrode is a gel-like or sheet-like conductive adhesive, and since it is laminated with a non-conductive sheet-like material that is a film, the familiarity with the skin is poor when touching the skin There was a risk of sweating and itching because of the lack of breathability. Furthermore, when the electrocardiogram electrode was worn, there was a risk of falling off the skin.
本発明は、かかる技術的背景に鑑みてなされたものであって、通気性があって肌に触れた際の違和感を抑制でき、布帛電極の装着時には肌との密着性にも優れ、生体への追従時の布帛電極の剥離や脱落が生じ難い布帛電極を提供することを目的とする。 The present invention has been made in view of such a technical background, has air permeability, can suppress a sense of incongruity when touching the skin, has excellent adhesion to the skin when the fabric electrode is worn, and is applied to a living body. It is an object of the present invention to provide a fabric electrode in which the fabric electrode is unlikely to peel off or drop off during follow-up.
前記目的を達成するために、本発明は以下の手段を提供する。 In order to achieve the above object, the present invention provides the following means.
［１］少なくとも親水性高分子を含む紡糸溶液を紡糸してなる繊維を含む非導電性繊維層が、導電性布帛層に積層されてなることを特徴とする布帛電極。 [1] A fabric electrode, wherein a non-conductive fiber layer containing fibers obtained by spinning a spinning solution containing at least a hydrophilic polymer is laminated on a conductive fabric layer.
［２］少なくとも親水性高分子を含む樹脂が少なくとも一部に付着してなる導電性布帛層と、非導電性繊維層とが積層されてなることを特徴とする布帛電極。 [2] A fabric electrode comprising a conductive fabric layer formed by adhering at least a part of a resin containing a hydrophilic polymer and a non-conductive fiber layer.
［３］前記非導電性繊維層は、少なくとも親水性高分子を含む紡糸溶液を紡糸してなる繊維を含む層である前項２に記載の布帛電極。 [3] The fabric electrode according to item 2 above, wherein the non-conductive fiber layer is a layer containing fibers obtained by spinning a spinning solution containing at least a hydrophilic polymer.
［４］前記非導電性繊維層は、エレクトロスピニング法により積層された層である前項１〜３のいずれか１項に記載の布帛電極。 [4] The fabric electrode according to any one of items 1 to 3, wherein the non-conductive fiber layer is a layer laminated by an electrospinning method.
［５］前記非導電性繊維層を構成する繊維の太さが、１０ｎｍ〜１００００ｎｍの繊維で形成された不織布層である前項１〜４のいずれか１項に記載の布帛電極。 [5] The fabric electrode according to any one of [1] to [4], wherein the fiber constituting the nonconductive fiber layer is a nonwoven fabric layer formed of fibers having a thickness of 10 nm to 10000 nm.
［６］前記導電性布帛層は、体積固有抵抗値が１０４Ω・ｃｍ以下である前項１〜５のいずれか１項に記載の布帛電極。 [6] The fabric electrode according to any one of [1] to [5], wherein the conductive fabric layer has a volume resistivity value of 10 4 Ω · cm or less.
［１］の発明では、布帛電極の非導電性繊維層を肌に当てて用いることから、通気性があって肌に触れた際の違和感を抑制できる。しかも、布帛電極の装着時には肌との密着性にも優れ、生体への追従時の布帛電極の剥離や脱落が生じ難い布帛電極とすることができる。 In the invention of [1], since the non-conductive fiber layer of the fabric electrode is used while being applied to the skin, it is breathable and can suppress a sense of incongruity when touching the skin. In addition, when the fabric electrode is attached, the fabric electrode is excellent in adhesion to the skin, and the fabric electrode can be hardly peeled off or dropped off when following the living body.
［２］の発明では、［１］の効果に加え、導電性布帛層には、少なくとも親水性高分子を含む樹脂が少なくとも一部に付着してなるので少なくとも親水性高分子を含む樹脂が非導電性繊維層の足場になるので、非導電性繊維層と導電性布帛層を、さらに強固に一体化することができる。 In the invention of [2], in addition to the effect of [1], a resin containing at least a hydrophilic polymer is attached to at least a part of the conductive fabric layer. Since it becomes a scaffold for the conductive fiber layer, the non-conductive fiber layer and the conductive fabric layer can be more firmly integrated.
［３］の発明では、前記非導電性繊維層は、少なくとも親水性高分子を含む紡糸溶液を紡糸してなる繊維を含む層なので、肌に触れた際の違和感をさらに抑制できるとともに肌との密着性を向上させることができる。 In the invention of [3], since the non-conductive fiber layer is a layer containing a fiber formed by spinning a spinning solution containing at least a hydrophilic polymer, it is possible to further suppress discomfort when touching the skin and Adhesion can be improved.
［４］の発明では、前記非導電性繊維層は、エレクトロスピニング法により積層された層なので、導電性布帛層との一体化を十分に向上させることができるとともに通気性に優れる。 In the invention of [4], since the non-conductive fiber layer is a layer laminated by an electrospinning method, integration with the conductive fabric layer can be sufficiently improved and air permeability is excellent.
［５］の発明では、前記非導電性繊維層を構成する繊維の太さが、１０ｎｍ〜１００００ｎｍの繊維で形成された不織布層であるから、肌への密着性を一層向上させることができて、生体への追従時の布帛電極の剥離や脱落が格段に生じ難いとともに、優れた通気性を有する。 In the invention of [5], since the thickness of the fibers constituting the nonconductive fiber layer is a nonwoven fabric layer formed of fibers of 10 nm to 10000 nm, the adhesion to the skin can be further improved. In addition, the fabric electrode is hardly peeled off or dropped off when following the living body, and has excellent air permeability.
［６］の発明では、前記導電性布帛層は、体積固有抵抗値が１０４Ω・ｃｍ以下なので、すなわち低い抵抗値を有しているので、心電図用等の電極において、感度の高い計測が可能となる。 In the invention of [6], the conductive fabric layer has a volume resistivity value of 10 4 Ω · cm or less, that is, has a low resistance value. Therefore, highly sensitive measurement can be performed on an electrode for an electrocardiogram or the like. It becomes possible.
次に、本発明に係る布帛電極の一実施形態について図にもとづいて説明する。図１において、第１の発明の布帛電極は、少なくとも親水性高分子を含む紡糸溶液を紡糸してなる繊維を含む非導電性繊維層２が導電性布帛層３に積層されてなる。すなわち、紡糸溶液に溶かす樹脂は、溶媒に溶解できる樹脂であれば特に限定されず、親水性高分子を含む。 Next, an embodiment of a fabric electrode according to the present invention will be described with reference to the drawings. In FIG. 1, the fabric electrode of the first invention is formed by laminating a non-conductive fiber layer 2 containing fibers obtained by spinning a spinning solution containing at least a hydrophilic polymer on a conductive fabric layer 3. That is, the resin dissolved in the spinning solution is not particularly limited as long as it is a resin that can be dissolved in a solvent, and includes a hydrophilic polymer.
第２の発明の布帛電極１は、少なくとも親水性高分子を含む樹脂（図示せず）が少なくとも一部に付着してなる導電性布帛層３と、非導電性繊維層２とが積層されてなることを特徴とする。少なくとも親水性高分子を含む樹脂を導電性布帛層３に付着させるには、例えば少なくとも親水性高分子を含む樹脂液中に導電性布帛層３を浸す浸漬法、導電性布帛層３にロールコーターやナイフコーターを用いて塗布するコーティング法、版を用いて印捺するプリント法等の方法を挙げることができる。 The fabric electrode 1 of the second invention is formed by laminating a conductive fabric layer 3 in which a resin (not shown) containing at least a hydrophilic polymer is attached to at least a part and a non-conductive fiber layer 2. It is characterized by becoming. In order to attach a resin containing at least a hydrophilic polymer to the conductive fabric layer 3, for example, an immersion method in which the conductive fabric layer 3 is immersed in a resin liquid containing at least a hydrophilic polymer, a roll coater is applied to the conductive fabric layer 3. And a coating method in which coating is performed using a knife coater and a printing method in which printing is performed using a plate.
前記樹脂の付着量（乾燥状態）は、０．５ｇ／ｍ２〜２０．０ｇ／ｍ２に設定されるのが好ましい。０．５ｇ／ｍ２以上とすることで、非導電性繊維層２の足場となるともに、２０．０ｇ／ｍ２以下とすることで、通気性を保持することができる。 Adhered amount of the resin (dry) is preferably set to 0.5g / m 2 ~20.0g / m 2 . By setting it as 0.5 g / m < 2 > or more, it becomes a scaffold of the nonelectroconductive fiber layer 2, and it can maintain air permeability by setting it as 20.0 g / m < 2 > or less.
また、非導電性繊維層２は、少なくとも親水性高分子を含む紡糸溶液を紡糸してなる繊維を含む層であるのが好ましい。 The non-conductive fiber layer 2 is preferably a layer containing fibers formed by spinning a spinning solution containing at least a hydrophilic polymer.
非導電性繊維層２は、エレクトロスピニング法（図２参照）により積層された層であるのが好ましい。アース９された導電性布帛層３と、紡糸溶液５のシリンジ（またはタンク）４との間に高電圧電源８によって高電圧を印加することで、紡糸溶液５が紡糸口６から導電性布帛層３の表面に向かって噴出する。そして、紡糸溶液５は、導電性布帛層３の表面に到達するまでの間に、紡糸溶液５中の溶媒が揮発しながら樹脂噴出７となり、紡糸溶液５中の樹脂の繊維が形成されて導電性布帛層３の表面に積層される。 The nonconductive fiber layer 2 is preferably a layer laminated by an electrospinning method (see FIG. 2). A high voltage is applied between the grounded 9 conductive fabric layer 3 and the syringe (or tank) 4 of the spinning solution 5 by a high voltage power source 8, so that the spinning solution 5 is fed from the spinning port 6 to the conductive fabric layer. 3 spouts toward the surface. Then, until the spinning solution 5 reaches the surface of the conductive fabric layer 3, the solvent in the spinning solution 5 volatilizes and becomes a resin jet 7 so that resin fibers in the spinning solution 5 are formed and conductive. Is laminated on the surface of the conductive fabric layer 3.
なお、印加する高電圧８は、特に限定されないが、０ｋＶ〜４０ｋＶに設定するのが好ましい。また、前記紡糸口６の内径は０．４ｍｍ〜１．２０ｍｍに設定するのが好ましい。紡糸溶液５の噴出速度は、０．０１ｍｌ／分〜１．２ｍｌ／分に設定するのが好ましい。 The applied high voltage 8 is not particularly limited, but is preferably set to 0 kV to 40 kV. The inner diameter of the spinning port 6 is preferably set to 0.4 mm to 1.20 mm. The ejection speed of the spinning solution 5 is preferably set to 0.01 ml / min to 1.2 ml / min.
また、エレクトロスピニング法による繊維の太さは、紡糸溶液５中の樹脂濃度、印加する高電圧８、紡糸口６の内径や紡糸溶液５の噴出量、さらに紡糸口６と導電性布帛層３との距離などの条件を調整することで制御することができる。 The thickness of the fiber by the electrospinning method is the resin concentration in the spinning solution 5, the high voltage 8 to be applied, the inner diameter of the spinning port 6, the ejection amount of the spinning solution 5, and the spinning port 6 and the conductive fabric layer 3. It can be controlled by adjusting conditions such as the distance.
前記紡糸溶液に溶かす樹脂としては、ポリアミド、ポリウレタン、ポリ乳酸、ナイロン、ポリアクリルニトリル、ポリカーボネート、ポリエチレンテレフタレート、酢酸セルロース、コラーゲン等を例示できる。 Examples of the resin dissolved in the spinning solution include polyamide, polyurethane, polylactic acid, nylon, polyacrylonitrile, polycarbonate, polyethylene terephthalate, cellulose acetate, and collagen.
なお、前記親水性高分子としては、ポリビニルアルコール、ポリアクリル酸塩、ポリエチレングリコール、ポリエチレンオキサイド、ポリビニルピロリドン等の水溶性ポリマー、リン脂質ポリマー等を挙げることができる。これらからなる群から選ばれる１つまたは複数であるのが好ましい。 Examples of the hydrophilic polymer include water-soluble polymers such as polyvinyl alcohol, polyacrylate, polyethylene glycol, polyethylene oxide, and polyvinylpyrrolidone, phospholipid polymers, and the like. It is preferably one or more selected from the group consisting of these.
前記溶媒としては、クロロホルム、ジメチルホルムアミド、ジクロロメタン、テトラヒドロフラン等の有機溶媒、アルコール、緩衝液、水等を挙げることができる。前記溶媒は、前記樹脂を溶かすことができれば特に限定されず、前記樹脂に応じて定まるものである。なかでも取扱い易い水に溶ける樹脂を用いるのが好ましい。 Examples of the solvent include organic solvents such as chloroform, dimethylformamide, dichloromethane, and tetrahydrofuran, alcohols, buffers, water, and the like. The solvent is not particularly limited as long as it can dissolve the resin, and is determined according to the resin. Among them, it is preferable to use a resin that is easy to handle and is soluble in water.
前記非導電性繊維層２を構成する繊維の太さ（直径）は、１０ｎｍ〜１００００ｎｍ（１０μｍ）の繊維で形成された層であるのが好ましい。１０ｎｍ以上であることで安定した連続繊維となるし、１００００ｎｍ（１０μｍ）以下であることで、繊維の表面積効果が顕著になり、非導電性繊維層２の面を肌に当てた際の違和感をさらに抑制できるうえに通気性に優れる。なかでも、非導電性繊維層２を構成する繊維の太さは２００ｎｍ〜５，０００ｎｍであるのがより好ましい。さらに２００ｎｍ〜１０００ｎｍであるのが最も好ましい。 The thickness (diameter) of the fibers constituting the non-conductive fiber layer 2 is preferably a layer formed of fibers of 10 nm to 10000 nm (10 μm). When it is 10 nm or more, it becomes a stable continuous fiber, and when it is 10000 nm (10 μm) or less, the surface area effect of the fiber becomes remarkable, and there is a sense of incongruity when the surface of the non-conductive fiber layer 2 is applied to the skin. In addition to being able to suppress, it has excellent breathability. Especially, it is more preferable that the thickness of the fiber which comprises the nonelectroconductive fiber layer 2 is 200 nm-5,000 nm. Furthermore, it is most preferable that it is 200 nm-1000 nm.
また、前記非導電性繊維層２の積層量（乾燥状態）は、０．１ｇ／ｍ２〜３．０ｇ／ｍ２に設定されるのが好ましい。０．５ｇ／ｍ２以上とすることで肌への密着性を確保することができるとともに、３．０ｇ／ｍ２以下とすることで通気性を保有した構造とすることができる。 Moreover, it is preferable that the lamination amount (dry state) of the said nonelectroconductive fiber layer 2 is set to 0.1 g / m < 2 > -3.0 g / m < 2 >. Adhesiveness to the skin can be secured by setting it to 0.5 g / m 2 or more, and a structure having air permeability can be obtained by setting it to 3.0 g / m 2 or less.
前記非導電性繊維層２を構成する繊維の太さ（直径）は、走査型電子顕微鏡、透過型電子顕微鏡、原子間力顕微鏡、走査型トンネル顕微鏡にいずれかの顕微鏡を用いて繊維をナノスケールで撮影した画像（写真を含む）を形態観察することによって測定されるものである。 The thickness (diameter) of the fibers constituting the non-conductive fiber layer 2 is nanoscaled using any one of a scanning electron microscope, a transmission electron microscope, an atomic force microscope, and a scanning tunnel microscope. It is measured by morphologically observing images (including photographs) taken with the above.
前記導電性布帛層３としては、特に限定されないが、例えば、金属メッキ繊維で構成された布帛、導電性繊維が含侵された又は表面に付着された布帛、金属糸で構成された布帛、炭素繊維で構成された布帛などが挙げられる。布帛の形態としては、編地、織布、布帛等を挙げることができる。なかでも、前記導電性布帛層３は、金属メッキ繊維で編成された編地で構成されるのが好ましい。 The conductive fabric layer 3 is not particularly limited. For example, a fabric composed of metal-plated fibers, a fabric impregnated with or adhered to the conductive fibers, a fabric composed of metal yarns, carbon Examples thereof include fabrics composed of fibers. Examples of the form of the fabric include knitted fabric, woven fabric, and fabric. Especially, it is preferable that the said conductive fabric layer 3 is comprised with the knitted fabric knitted by the metal plating fiber.
前記金属メッキ繊維を構成する金属（メッキ材）としては、特に限定されないが、例えば銀、金、銅、ニッケル、アルミニウム等を挙げることができる。また、前記金属メッキ繊維を構成する繊維（メッキされる芯繊維）としては、特に限定されないが、例えば、ナイロン繊維、ポリエステル繊維、アクリル繊維、炭素繊維等を挙げることができる。 Although it does not specifically limit as a metal (plating material) which comprises the said metal plating fiber, For example, silver, gold | metal | money, copper, nickel, aluminum etc. can be mentioned. Further, the fiber constituting the metal-plated fiber (core fiber to be plated) is not particularly limited, and examples thereof include nylon fiber, polyester fiber, acrylic fiber, and carbon fiber.
前記金属メッキ繊維としては、特に限定されないが、例えば、表面が銀メッキされたナイロン繊維、表面が銀メッキされたポリエステル繊維、表面が銅メッキされたナイロン繊維等を挙げることできる。 The metal-plated fiber is not particularly limited, and examples thereof include nylon fiber whose surface is silver-plated, polyester fiber whose surface is silver-plated, and nylon fiber whose surface is copper-plated.
前記金属メッキ繊維の太さは、特に限定されないが、５ｄｔｅｘ〜３００ｄｔｅｘに設定されるのが好ましい。 Although the thickness of the said metal plating fiber is not specifically limited, It is preferable to set to 5 dtex-300 dtex.
前記導電性布帛層は、体積固有抵抗値が１０４Ω・ｃｍ以下なので、すなわち低い抵抗値を有しているので、心電図用等の電極において、感度の高い計測が可能となる。 The conductive fabric layer has a volume specific resistance value of 10 4 Ω · cm or less, that is, has a low resistance value, so that measurement with high sensitivity can be performed in an electrode for an electrocardiogram or the like.
次に、本発明の具体的な実施例について説明するが、本発明はこれらの実施例のものに特に限定されるものではない。 Next, specific examples of the present invention will be described, but the present invention is not particularly limited to these examples.
＜使用材料＞
導電性布帛・・・編地（表面が銀メッキされたナイロン繊維からなる編地）、大きさたて５ｃｍ×よこ５ｃｍ、厚さ０．１ｍｍ
親水性高分子・・・ポリエチレンオキサイド（ＰＥＯ）（重量平均分子量５００，０００）、ポリビニルアルコール（ＰＶＡ）（重合度１，７００、重量平均分子量７５，０００）
高分子溶液Ａ・・・ポリエチレンオキサイド（ＰＥＯ） ２質量％水溶液
高分子溶液Ｂ・・・ポリビニルアルコール（ＰＶＡ） ２質量％水溶液
紡糸溶液Ａ・・・ポリエチレンオキサイド（ＰＥＯ） ２質量％水溶液
紡糸溶液Ｂ・・・ポリエチレンオキサイド（ＰＥＯ） ３質量％水溶液
紡糸溶液Ｃ・・・ポリビニルアルコール（ＰＶＡ） １０質量％水溶液
<Materials used>
Conductive fabric: knitted fabric (knitted fabric made of nylon fibers whose surface is silver-plated), size 5 cm x width 5 cm, thickness 0.1 mm
Hydrophilic polymer: polyethylene oxide (PEO) (weight average molecular weight 500,000), polyvinyl alcohol (PVA) (polymerization degree 1,700, weight average molecular weight 75,000)
Polymer solution A: Polyethylene oxide (PEO) 2 mass% aqueous solution Polymer solution B: Polyvinyl alcohol (PVA) 2 mass% aqueous solution Spin solution A: Polyethylene oxide (PEO) 2 mass% aqueous solution Spin solution B ... Polyethylene oxide (PEO) 3% by weight aqueous solution Spinning solution C ... Polyvinyl alcohol (PVA) 10% by weight aqueous solution
＜実施例１＞
室内（温度２０℃、湿度４０％）において、図２に示すように紡糸溶液Ａをシリンジ（またはタンク）４の中に投入して、アースされた編地（導電性布帛３）とシリンジ（またはタンク）４との間に高電圧電源８によって２０ｋＶの電圧を印加することで、紡糸溶液Ａを紡糸口６（内径：０．４０ｍｍ）から噴出（噴出速度：０．０８ｍｌ／分）させて、噴出した紡糸溶液Ａが樹脂噴出７を経てポリエチレンオキサイド繊維となって、編地（導電性布帛３）の表面に積層された。
こうして得られた布帛電極１の非導電性繊維層を構成する繊維、すなわちポリエチレンオキサイド繊維の太さ（直径）は、５００ｎｍ〜９００ｎｍの範囲であり、ポリエチレンオキサイド繊維の積層量（乾燥状態）は１．１ｇ／ｍ２であった。
繊維の太さ（直径）は布帛電極の非導電性繊維層２の側表面を走査型電子顕微鏡を用いてナノスケールで撮影した写真を観察することによって求めた。密着性評価は、「４」で合格であった。
<Example 1>
In a room (temperature 20 ° C., humidity 40%), as shown in FIG. 2, the spinning solution A is put into a syringe (or tank) 4, and a grounded knitted fabric (conductive fabric 3) and syringe (or By applying a voltage of 20 kV with the high voltage power supply 8 between the tank 4) and the spinning solution A is ejected from the spinning port 6 (inner diameter: 0.40 mm) (ejection speed: 0.08 ml / min), The spun spinning solution A became a polyethylene oxide fiber through the resin jet 7 and was laminated on the surface of the knitted fabric (conductive fabric 3).
The fibers constituting the non-conductive fiber layer of the fabric electrode 1 thus obtained, that is, the thickness (diameter) of the polyethylene oxide fiber is in the range of 500 nm to 900 nm, and the lamination amount (dry state) of the polyethylene oxide fiber is 1. 0.1 g / m 2 .
The thickness (diameter) of the fiber was determined by observing a photograph taken on a nanoscale of the side surface of the non-conductive fiber layer 2 of the fabric electrode using a scanning electron microscope. The adhesion evaluation was “4” and passed.
＜実施例２＞
編地（導電性布帛３）を高分子溶液Ａに浸漬し、温度４５℃の温風乾燥機内に１時間静置し乾燥させた。なお、ポリエチレンオキサイド（ＰＥＯ）の付着量（乾燥状態）は１４ｇ／ｍ２であった。その後、実施例１において、エレクトロスピニング用紡糸溶液として、紡糸溶液Ａに替えて紡糸溶液Ｃを用いた以外は実施例１同様にして、ポリエチレンオキサイド（ＰＥＯ）が付着した編地（導電性布帛３）の表面に紡糸溶液Ｃが樹脂噴出７を経てポリビニルアルコール繊維となって積層された。
こうして得られた布帛電極１の非導電性繊維層を構成する繊維、すなわちポリビニルアルコール繊維の太さ（直径）は、３００ｎｍ〜７００ｎｍの範囲であり、ポリビニルアルコール繊維の積層量（乾燥状態）は１．３ｇ／ｍ２であった。密着性評価は、「５」で合格であった。
<Example 2>
The knitted fabric (conductive fabric 3) was immersed in the polymer solution A, and left to stand in a hot air dryer having a temperature of 45 ° C. for 1 hour to be dried. In addition, the adhesion amount (dry state) of polyethylene oxide (PEO) was 14 g / m 2 . Thereafter, in Example 1, except that the spinning solution C was used in place of the spinning solution A as the spinning solution for electrospinning, the knitted fabric (conductive fabric 3) to which polyethylene oxide (PEO) was adhered was used in the same manner as in Example 1. The spinning solution C was laminated on the surface as a polyvinyl alcohol fiber through the resin jet 7.
The thickness (diameter) of the fibers constituting the non-conductive fiber layer of the fabric electrode 1 thus obtained, that is, the polyvinyl alcohol fiber is in the range of 300 nm to 700 nm, and the lamination amount (dry state) of the polyvinyl alcohol fiber is 1. It was 3 g / m 2 . The adhesion evaluation was “5” and passed.
＜実施例３＞
実施例２において、エレクトロスピニング用紡糸溶液として、紡糸溶液Ｃに替えて紡糸溶液Ｂを用いた以外は実施例２同様にして、ポリエチレンオキサイド（ＰＥＯ）が付着した編地（導電性布帛３）の表面に紡糸溶液Ｂが樹脂噴出７を経てポリエチレンオキサイド繊維となって積層された。
こうして得られた布帛電極１の非導電性繊維層を構成する繊維、すなわちポリエチレンオキサイド繊維の太さ（直径）は、６００ｎｍ〜９００ｎｍの範囲であり、ポリエチレンオキサイド繊維の積層量（乾燥状態）は１．１ｇ／ｍ２であった。密着性評価は、「３」で合格であった。
<Example 3>
In Example 2, a knitted fabric (conductive fabric 3) to which polyethylene oxide (PEO) was adhered was obtained in the same manner as in Example 2 except that the spinning solution B was used instead of the spinning solution C as the spinning solution for electrospinning. The spinning solution B was laminated on the surface as polyethylene oxide fibers through the resin jet 7.
The thickness (diameter) of the fibers constituting the non-conductive fiber layer of the fabric electrode 1 thus obtained, that is, the polyethylene oxide fibers is in the range of 600 nm to 900 nm, and the amount of polyethylene oxide fibers laminated (dry state) is 1. 0.1 g / m 2 . The adhesion evaluation was “3” and passed.
＜実施例４＞
実施例２において、編地（導電性布帛３）を浸漬する溶液として、高分子溶液Ａに替えて高分子溶液Ｂを用いた以外は実施例２と同様にして、ポリビニルアルコール（ＰＶＡ）が付着した編地（導電性布帛３）の表面に紡糸溶液Ｂが樹脂噴出７を経てポリビニルアルコール繊維となって積層された。
こうして得られた布帛電極１の非導電性繊維層を構成する繊維、すなわちポリビニルアルコール繊維の太さ（直径）は、３００ｎｍ〜７００ｎｍの範囲であり、ポリビニルアルコール繊維の積層量（乾燥状態）は１．５ｇ／ｍ２であった。
密着性評価は、「５」で合格であった。
<Example 4>
In Example 2, polyvinyl alcohol (PVA) was adhered in the same manner as in Example 2 except that the polymer solution B was used instead of the polymer solution A as the solution in which the knitted fabric (conductive fabric 3) was immersed. The spinning solution B was laminated on the surface of the knitted fabric (conductive fabric 3) as a polyvinyl alcohol fiber through the resin jet 7.
The thickness (diameter) of the fibers constituting the non-conductive fiber layer of the fabric electrode 1 thus obtained, that is, the polyvinyl alcohol fiber is in the range of 300 nm to 700 nm, and the lamination amount (dry state) of the polyvinyl alcohol fiber is 1. 0.5 g / m 2 .
The adhesion evaluation was “5” and passed.
＜実施例５＞
実施例４において、エレクトロスピニング用紡糸溶液として、紡糸溶液Ｃに替えて紡糸溶液Ｂを用いた以外は実施例４同様にして、ポリビニルアルコール（ＰＶＡ）が付着した編地（導電性布帛３）の表面に紡糸溶液Ｂが樹脂噴出７を経てポリエチレンオキサイド繊維となって積層された。
こうして得られた布帛電極１の非導電性繊維層を構成する繊維、すなわちポリエチレンオキサイド繊維の太さ（直径）は、３００ｎｍ〜７００ｎｍの範囲であり、ポリエチレンオキサイド繊維の積層量（乾燥状態）は１．３ｇ／ｍ２であった。密着性評価は、「５」で合格であった。
<Example 5>
In Example 4, a knitted fabric (conductive fabric 3) adhered with polyvinyl alcohol (PVA) was used in the same manner as in Example 4 except that the spinning solution B was used instead of the spinning solution C as the spinning solution for electrospinning. The spinning solution B was laminated on the surface as polyethylene oxide fibers through the resin jet 7.
The thickness (diameter) of the fibers constituting the non-conductive fiber layer of the fabric electrode 1 thus obtained, that is, the polyethylene oxide fibers is in the range of 300 nm to 700 nm, and the amount of the polyethylene oxide fibers laminated (dry state) is 1. It was 3 g / m 2 . The adhesion evaluation was “5” and passed.
＜比較例１＞
実施例１において、導電性布帛として用いたのと同じ編地を布帛電極とした。密着性評価は、「１」で不合格であった。
<Comparative Example 1>
In Example 1, the same knitted fabric used as the conductive fabric was used as the fabric electrode. The adhesion evaluation was “1”, which was unacceptable.
＜密着性評価試験＞
布帛電極の非導電性繊維層の面を手の甲に載せた後、もう一方の手で布帛電極を５秒間押し当てたのち、手の甲を下側にして、布帛電極が手の甲から剥がれ落ちるまでの時間をストップウオッチで計測した。この落下するまでの時間を、下記の５段階で評価し、「３」の評価以上を合格とした。
「５」・・・４５秒以上保持したもの。
「４」・・・３０秒以上４５秒未満保持したもの。
「３」・・・１５秒以上３０秒未満保持したもの。
「２」・・・１５秒未満で落下したもの。
「１」・・・肌に密着せずに落下したもの。
<Adhesion evaluation test>
After placing the surface of the non-conductive fiber layer of the fabric electrode on the back of the hand, press the fabric electrode with the other hand for 5 seconds, and then set the back of the hand to the lower side until the fabric electrode peels off the back of the hand. Measured with a stopwatch. The time until this drop was evaluated in the following five stages, and an evaluation of “3” or higher was regarded as acceptable.
“5”: held for 45 seconds or more.
“4”: held for 30 seconds or more and less than 45 seconds.
“3”: held for 15 seconds or more and less than 30 seconds.
“2”: Dropped in less than 15 seconds.
“1”: Dropped without touching the skin.
実施例１〜５の布帛電極は、いずれも布帛電極の装着時には肌との密着性にも優れるとともに通気性のあるものであった。一方、比較例の電極は、肌に密着できずに落下してしまった。しかも、銀メッキされた糸が直接肌に触れ、著しい違和感を感じるものであった。 The fabric electrodes of Examples 1 to 5 were both excellent in adhesion to the skin and breathable when the fabric electrode was mounted. On the other hand, the electrode of the comparative example was dropped without being able to adhere to the skin. Moreover, the silver-plated thread directly touched the skin and felt a very uncomfortable feeling.
本発明に係る布帛電極は、通気性があって肌に触れた際の違和感を抑制でき、布帛電極の装着時には肌との密着性にも優れ、生体への追従時の布帛電極の剥離や脱落が生じ難いので生体センサーの電極として好適に使用できる。生体センサーとしては、心電図測定用などがある。 The fabric electrode according to the present invention has air permeability and can suppress a sense of incongruity when touching the skin, has excellent adhesion to the skin when the fabric electrode is mounted, and the fabric electrode is peeled off or detached when following the living body. Can be suitably used as an electrode of a biosensor. Examples of biosensors include electrocardiogram measurement.
１・・・布帛電極
２・・・非導電性繊維層（親水性高分子繊維を含む）
３・・・導電性布帛層
４・・・シリンジ（またはタンク）
５・・・紡糸溶液
６・・・紡糸口
７・・・樹脂噴出
８・・・高電圧電源
９・・・アース
DESCRIPTION OF SYMBOLS 1 ... Fabric electrode 2 ... Nonelectroconductive fiber layer (a hydrophilic polymer fiber is included)
3 ... conductive fabric layer 4 ... syringe (or tank)
5 ... Spinning solution 6 ... Spinning port 7 ... Resin jet 8 ... High voltage power supply 9 ... Earth
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Cited By (4)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN108611763A (en) * | 2018-04-09 | 2018-10-02 | 河南工程学院 | Static Spinning PET/ melt-blown PP non-woven fabrics heats compound production method |
| CN110495876A (en) * | 2019-09-29 | 2019-11-26 | 联想(北京)有限公司 | A kind of electrocardio textile electrode |
| JP2020024850A (en) * | 2018-08-07 | 2020-02-13 | Ｊｘ金属株式会社 | Composite solid electrolyte and all-solid lithium ion battery |
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