JPH09253219A - Medical thin layer flat electrode - Google Patents
Medical thin layer flat electrodeInfo
- Publication number
- JPH09253219A JPH09253219A JP8090520A JP9052096A JPH09253219A JP H09253219 A JPH09253219 A JP H09253219A JP 8090520 A JP8090520 A JP 8090520A JP 9052096 A JP9052096 A JP 9052096A JP H09253219 A JPH09253219 A JP H09253219A
- Authority
- JP
- Japan
- Prior art keywords
- adhesive
- conductive
- cloth
- electrode
- layer
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Pending
Links
- 239000000853 adhesive Substances 0.000 claims abstract description 40
- 230000001070 adhesive effect Effects 0.000 claims abstract description 40
- 239000004744 fabric Substances 0.000 claims abstract description 38
- 239000010410 layer Substances 0.000 claims abstract description 33
- 229920000728 polyester Polymers 0.000 claims abstract description 27
- 239000012790 adhesive layer Substances 0.000 claims abstract description 14
- -1 polyethylene terephthalate Polymers 0.000 claims abstract description 10
- 238000010998 test method Methods 0.000 claims abstract description 10
- 229920000139 polyethylene terephthalate Polymers 0.000 claims abstract description 4
- 239000005020 polyethylene terephthalate Substances 0.000 claims abstract description 4
- 239000002985 plastic film Substances 0.000 claims description 10
- 229920006255 plastic film Polymers 0.000 claims description 10
- 238000005259 measurement Methods 0.000 claims description 5
- 239000004033 plastic Substances 0.000 claims description 3
- 229920003023 plastic Polymers 0.000 claims description 3
- 239000011347 resin Substances 0.000 abstract description 5
- 229920005989 resin Polymers 0.000 abstract description 5
- 230000001225 therapeutic effect Effects 0.000 abstract description 3
- 210000000988 bone and bone Anatomy 0.000 abstract description 2
- 208000037265 diseases, disorders, signs and symptoms Diseases 0.000 abstract description 2
- 238000007689 inspection Methods 0.000 abstract description 2
- 210000004556 brain Anatomy 0.000 abstract 1
- 239000003795 chemical substances by application Substances 0.000 abstract 1
- 238000001727 in vivo Methods 0.000 abstract 1
- 230000003387 muscular Effects 0.000 abstract 1
- 229920002799 BoPET Polymers 0.000 description 14
- 239000011248 coating agent Substances 0.000 description 11
- 238000000576 coating method Methods 0.000 description 11
- 238000012360 testing method Methods 0.000 description 11
- 239000010408 film Substances 0.000 description 10
- 239000003973 paint Substances 0.000 description 7
- 239000004925 Acrylic resin Substances 0.000 description 4
- 229920000178 Acrylic resin Polymers 0.000 description 4
- 230000000052 comparative effect Effects 0.000 description 4
- 238000011156 evaluation Methods 0.000 description 4
- 239000000835 fiber Substances 0.000 description 4
- 239000000243 solution Substances 0.000 description 4
- XLYOFNOQVPJJNP-UHFFFAOYSA-N water Substances O XLYOFNOQVPJJNP-UHFFFAOYSA-N 0.000 description 4
- RYGMFSIKBFXOCR-UHFFFAOYSA-N Copper Chemical compound [Cu] RYGMFSIKBFXOCR-UHFFFAOYSA-N 0.000 description 3
- 239000004698 Polyethylene Substances 0.000 description 3
- 239000004743 Polypropylene Substances 0.000 description 3
- 229910052802 copper Inorganic materials 0.000 description 3
- 239000010949 copper Substances 0.000 description 3
- JEIPFZHSYJVQDO-UHFFFAOYSA-N iron(III) oxide Inorganic materials O=[Fe]O[Fe]=O JEIPFZHSYJVQDO-UHFFFAOYSA-N 0.000 description 3
- 239000000463 material Substances 0.000 description 3
- 229920001225 polyester resin Polymers 0.000 description 3
- 239000004645 polyester resin Substances 0.000 description 3
- 229920000573 polyethylene Polymers 0.000 description 3
- 229920001155 polypropylene Polymers 0.000 description 3
- QTBSBXVTEAMEQO-UHFFFAOYSA-M Acetate Chemical compound CC([O-])=O QTBSBXVTEAMEQO-UHFFFAOYSA-M 0.000 description 2
- XEEYBQQBJWHFJM-UHFFFAOYSA-N Iron Chemical compound [Fe] XEEYBQQBJWHFJM-UHFFFAOYSA-N 0.000 description 2
- PXHVJJICTQNCMI-UHFFFAOYSA-N Nickel Chemical compound [Ni] PXHVJJICTQNCMI-UHFFFAOYSA-N 0.000 description 2
- 230000006866 deterioration Effects 0.000 description 2
- 238000001035 drying Methods 0.000 description 2
- 239000002184 metal Substances 0.000 description 2
- 229910052751 metal Inorganic materials 0.000 description 2
- 239000004745 nonwoven fabric Substances 0.000 description 2
- 230000003449 preventive effect Effects 0.000 description 2
- 238000011160 research Methods 0.000 description 2
- 238000010008 shearing Methods 0.000 description 2
- 229920002379 silicone rubber Polymers 0.000 description 2
- 239000004945 silicone rubber Substances 0.000 description 2
- 241000270728 Alligator Species 0.000 description 1
- 208000019901 Anxiety disease Diseases 0.000 description 1
- OKTJSMMVPCPJKN-UHFFFAOYSA-N Carbon Chemical compound [C] OKTJSMMVPCPJKN-UHFFFAOYSA-N 0.000 description 1
- QPLDLSVMHZLSFG-UHFFFAOYSA-N Copper oxide Chemical compound [Cu]=O QPLDLSVMHZLSFG-UHFFFAOYSA-N 0.000 description 1
- 239000005751 Copper oxide Substances 0.000 description 1
- 229920000742 Cotton Polymers 0.000 description 1
- 229920002430 Fibre-reinforced plastic Polymers 0.000 description 1
- 239000004820 Pressure-sensitive adhesive Substances 0.000 description 1
- BQCADISMDOOEFD-UHFFFAOYSA-N Silver Chemical compound [Ag] BQCADISMDOOEFD-UHFFFAOYSA-N 0.000 description 1
- FAPWRFPIFSIZLT-UHFFFAOYSA-M Sodium chloride Chemical compound [Na+].[Cl-] FAPWRFPIFSIZLT-UHFFFAOYSA-M 0.000 description 1
- 238000010521 absorption reaction Methods 0.000 description 1
- 239000003522 acrylic cement Substances 0.000 description 1
- 239000000956 alloy Substances 0.000 description 1
- 229910045601 alloy Inorganic materials 0.000 description 1
- 230000000843 anti-fungal effect Effects 0.000 description 1
- 229940121375 antifungal agent Drugs 0.000 description 1
- 230000036506 anxiety Effects 0.000 description 1
- 239000012298 atmosphere Substances 0.000 description 1
- 230000000740 bleeding effect Effects 0.000 description 1
- 229910052799 carbon Inorganic materials 0.000 description 1
- 239000006229 carbon black Substances 0.000 description 1
- 239000011247 coating layer Substances 0.000 description 1
- 239000004020 conductor Substances 0.000 description 1
- 239000000470 constituent Substances 0.000 description 1
- 229910000431 copper oxide Inorganic materials 0.000 description 1
- 210000003792 cranial nerve Anatomy 0.000 description 1
- 238000003745 diagnosis Methods 0.000 description 1
- 239000000428 dust Substances 0.000 description 1
- 238000002567 electromyography Methods 0.000 description 1
- 230000007613 environmental effect Effects 0.000 description 1
- 239000011151 fibre-reinforced plastic Substances 0.000 description 1
- 239000006261 foam material Substances 0.000 description 1
- 238000009413 insulation Methods 0.000 description 1
- 229910052742 iron Inorganic materials 0.000 description 1
- 239000012948 isocyanate Substances 0.000 description 1
- 238000010030 laminating Methods 0.000 description 1
- 239000010985 leather Substances 0.000 description 1
- 238000004519 manufacturing process Methods 0.000 description 1
- 150000002736 metal compounds Chemical class 0.000 description 1
- 238000000034 method Methods 0.000 description 1
- 239000000203 mixture Substances 0.000 description 1
- 210000003205 muscle Anatomy 0.000 description 1
- 229910052759 nickel Inorganic materials 0.000 description 1
- 230000000149 penetrating effect Effects 0.000 description 1
- 239000002504 physiological saline solution Substances 0.000 description 1
- 229920001495 poly(sodium acrylate) polymer Polymers 0.000 description 1
- 229920000058 polyacrylate Polymers 0.000 description 1
- 229920000515 polycarbonate Polymers 0.000 description 1
- 239000004417 polycarbonate Substances 0.000 description 1
- 229920000642 polymer 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
- 239000000843 powder Substances 0.000 description 1
- 230000001846 repelling effect Effects 0.000 description 1
- 229910052709 silver Inorganic materials 0.000 description 1
- 239000004332 silver Substances 0.000 description 1
- 239000011780 sodium chloride Substances 0.000 description 1
- NNMHYFLPFNGQFZ-UHFFFAOYSA-M sodium polyacrylate Chemical compound [Na+].[O-]C(=O)C=C NNMHYFLPFNGQFZ-UHFFFAOYSA-M 0.000 description 1
- 239000000126 substance Substances 0.000 description 1
- 239000000758 substrate Substances 0.000 description 1
- 229920003002 synthetic resin Polymers 0.000 description 1
- 239000000057 synthetic resin Substances 0.000 description 1
- KKEYFWRCBNTPAC-UHFFFAOYSA-L terephthalate(2-) Chemical compound [O-]C(=O)C1=CC=C(C([O-])=O)C=C1 KKEYFWRCBNTPAC-UHFFFAOYSA-L 0.000 description 1
- 229920002803 thermoplastic polyurethane Polymers 0.000 description 1
- 239000010409 thin film Substances 0.000 description 1
- XOLBLPGZBRYERU-UHFFFAOYSA-N tin dioxide Chemical compound O=[Sn]=O XOLBLPGZBRYERU-UHFFFAOYSA-N 0.000 description 1
- 229910001887 tin oxide Inorganic materials 0.000 description 1
- 230000000007 visual effect Effects 0.000 description 1
- 230000037303 wrinkles Effects 0.000 description 1
Landscapes
- Electrotherapy Devices (AREA)
- Measurement And Recording Of Electrical Phenomena And Electrical Characteristics Of The Living Body (AREA)
Abstract
Description
【０００１】[0001]
【発明の属する技術分野】本発明は、骨関節系、筋肉
系、脳神経系等の器質的または、機能的障害の治療に用
いる低周波治療器や、心電計、筋電計、脳波計等の検査
・診断機器等において、微弱電流を体内に通電するため
の電極に関し、詳しくは、皮膚面との密着性に優れた医
療用薄層電極に関する。BACKGROUND OF THE INVENTION 1. Field of the Invention The present invention relates to a low frequency therapeutic device for treating organic or functional disorders such as bone joint system, muscle system, cranial nerve system, electrocardiograph, electromyography, electroencephalograph, etc. The present invention relates to an electrode for applying a weak current to the body in the inspection / diagnosis device, etc., and more particularly to a medical thin-layer electrode having excellent adhesion to the skin surface.
【０００２】[0002]
【従来の技術】従来、低周波治療器等の導子として用い
られる平板状電極としては、スポンジ、布製のものを、
水や生理的食塩水に浸して皮膚面に密着させて用いた
り、導電性カーボンを配合した導電性シリコーンゴムが
使用されてきた。しかし、水や食塩水を用いる場合では
触感が悪く、また、部分的に、はじいたり、乾燥したり
して、密着状態が不均一となり、測定結果に影響を及ぼ
す場合が生じていた。また、導電性シリコーンゴムを用
いる場合では、反撥弾性が強過ぎて、特に、体表面の起
伏部位における密着性が問題で、端部が浮きあがったり
する場合があった。このような問題の解決のため、電極
の薄層化による密着性の改良が提案されてきた。例え
ば、実開平３−５３２５８号公報記載の考案は、片面に
不織布を一体に裏打ちした絶縁性合成樹脂製フィルムの
他面に、導電性インクを介して、導電性ゲル層を積層し
た薄形電極を提示している。この考案は、「ポリエステ
ルシートは、使用時に、シワが発生し易い上、やや弾性
があるため、剥離し易くなる」とされ、「インク塗着性
が良好で、かつ、柔軟性のあるプラスチックフィルムと
しては、ポリエチレン又はポリプロピレンが好ましい
が、それ自体では、保形性がなく、却って使用し難い欠
点がある」とし不織布の裏打ちにより、これを改良する
旨の記述がある。2. Description of the Related Art Conventionally, as a flat plate electrode used as a conductor of a low-frequency therapeutic device or the like, a sponge or cloth electrode is used.
It has been used by immersing it in water or physiological saline so as to be in close contact with the skin surface, or using a conductive silicone rubber containing conductive carbon. However, when water or saline was used, the touch was poor, and the adhesion was non-uniform due to partial repelling or drying, which sometimes affected the measurement results. Further, in the case of using the conductive silicone rubber, the impact resilience is too strong, and in particular, the adhesion at the undulating portion of the body surface is a problem, and the edges may rise. In order to solve such a problem, it has been proposed to improve the adhesion by thinning the electrode. For example, the invention described in Japanese Utility Model Laid-Open No. 3-53258 discloses a thin electrode in which a conductive gel layer is laminated on the other surface of an insulating synthetic resin film, which is integrally lined with a non-woven fabric on one surface, through conductive ink. Is presented. This invention is said to be "a polyester sheet is easily wrinkled during use and is slightly elastic so that it is easily peeled off", and "a plastic film having good ink-coating properties and flexibility. For that, polyethylene or polypropylene is preferable, but it has a drawback that it is not shape-retaining and is rather difficult to use on its own. "
【０００３】[0003]
【発明が解決しようとする課題】本発明者らは、医療用
薄層平板電極の構造に関して、研究を重ねてきた中で、
プラスチックフィルムがポリエチレンやポリプロピレン
では、布体や導電層に対する接着性の確保がむつかしい
こと、平板電極が、体表面各部位の起伏に十分対応し得
る可撓性を持つためには、プラスチックフィルムの材
質、厚み、布体の材質、繊維組織の設定の必要性がある
ことおよび、好ましくは両者の接着性を一定水準以上に
高めること等の複雑な技術課題を解決すべく鋭意、研究
に専念した結果、実施可能な皮膚面密着性の優れた薄層
電極構成を創出するに至り、本発明を完成した。DISCLOSURE OF THE INVENTION The inventors of the present invention have conducted extensive research on the structure of a medical thin-layer flat plate electrode.
When the plastic film is polyethylene or polypropylene, it is difficult to secure the adhesiveness to the cloth body or the conductive layer, and in order for the flat plate electrode to be flexible enough to deal with the undulations of various parts of the body surface, the plastic film material , The thickness, the material of the cloth, the need to set the fiber structure, and the result of earnestly devoted to the research to solve the complicated technical problems such as increasing the adhesiveness of the two to a certain level or more. The present invention has been completed by creating a practicable thin-layer electrode structure having excellent adhesion to the skin surface.
【０００４】[0004]
【課題を解決するための手段】本発明は、 プラスチッ
クフィルムの片面に布体が、他面に導電層が積層されて
なる、皮膚面に密着させて用いる医療用薄層平板電極に
おいて、プラスチックフィルムが、厚さ２〜３８μｍの
ポリエチレンテレフタレートフィルムで、布体が、接着
剤により該プラスチックフィルムに接合されたポリエス
テル製布で、および、導電層の少なくとも皮膚面密着部
分が導電性粘着剤で構成され、かつ、接着剤によりプラ
スチックフイルムに接合されたポリエステル製布のＴ字
形剥離接着強さがＪＩＳ Ｋ ６８５４に規定の試験方
法で０．１５ｋｇｆ／２５ｍｍ以上であり、かつ、測定
温度４０℃において、荷重３００ｇでの該接着剤層のク
リープ破壊時間がＪＩＳ Ｋ ６８５９に規定の試験方
法で２０分以上である密着性に優れた医療用薄層平板電
極である。DISCLOSURE OF THE INVENTION The present invention relates to a thin film medical plate electrode for use in close contact with the skin surface, wherein a plastic body is laminated on one side with a conductive layer and the other side is laminated with a conductive layer. Is a polyethylene terephthalate film having a thickness of 2 to 38 μm, the cloth body is a polyester cloth joined to the plastic film with an adhesive, and at least the skin surface contact portion of the conductive layer is composed of a conductive adhesive agent. In addition, the T-shaped peel adhesion strength of the polyester cloth joined to the plastic film by the adhesive is 0.15 kgf / 25 mm or more by the test method specified in JIS K 6854, and the load is applied at the measurement temperature of 40 ° C. The creep rupture time of the adhesive layer at 300 g is 20 minutes or more by the test method specified in JIS K 6859. It is a medical thin layer flat plate electrode with excellent properties.
【０００５】[0005]
【発明の実施の形態】以下、本発明の内容を詳述する。
本発明の医療用薄層平板電極の使用に際しては、端部を
ワニ口クリップなどで挟んで使用する場合もあるが、好
ましくは接続用スナップを用いる。本発明の説明図面は
接続用スナップを用いた状態を示すものである。DETAILED DESCRIPTION OF THE INVENTION The details of the present invention will be described below.
When using the medical thin-layer flat plate electrode of the present invention, the end portion may be sandwiched by an alligator clip or the like, but a snap for connection is preferably used. The explanatory drawing of the present invention shows a state in which a snap for connection is used.
【０００６】先ず、本発明の医療用薄層平板電極の構成
態様を図１〜３により説明する 。図１は、所定厚みの
ポリエチレンテレフタレートフィルム（以下、ＰＥＴフ
ィルム）と略記する）３の片面に、接着剤２により接合
されたポリエステル製布１が、また、他面に導電性塗膜
４と導電性粘着剤５とよりなる導電層が積層され、か
つ、接続用スナップ７が付設され、本発明の電極Ｐが構
成される。更に、要すれば、導電性粘着剤層表面にセパ
レータ６が付設されてもよい。First, the constitutional aspect of the medical thin layer plate electrode of the present invention will be explained with reference to FIGS. FIG. 1 shows a polyester terephthalate film (hereinafter abbreviated as PET film) 3 having a predetermined thickness, on one side of which a polyester cloth 1 bonded by an adhesive 2 is formed, and on the other side of which a conductive coating film 4 and a conductive film 4 are formed. The conductive layer composed of the conductive adhesive 5 is laminated, and the connection snap 7 is additionally provided to form the electrode P of the present invention. Furthermore, if necessary, the separator 6 may be attached to the surface of the conductive pressure-sensitive adhesive layer.
【０００７】図２においては、図１の構成態様における
導電層のうち、導電性塗膜層を設けない場合の態様を示
す。該態様は、導電性能が低下したり、ノイズが入る可
能性がある。FIG. 2 shows a mode in which the conductive coating layer is not provided among the conductive layers in the configuration mode of FIG. In this mode, there is a possibility that the conductive performance is deteriorated or noise is introduced.
【０００８】図３においては、図１の構成態様に防錆テ
ープ８を附設した場合の態様を示す。導電性粘着剤層に
吸湿水分が含まれていたり、含水ゲルからなる導電性粘
着剤を用いた場合、これらの層に接する接続用スナップ
の表面が錆び導電性能が低下したり、ノイズが入るおそ
れがある。それを防止するために防錆テープ８の附設が
必要である。FIG. 3 shows an embodiment in which a rust preventive tape 8 is added to the embodiment shown in FIG. If the conductive adhesive layer contains hygroscopic moisture, or if you use a conductive adhesive composed of hydrous gel, the surface of the connection snap contacting these layers may rust and reduce the conductive performance, or noise may enter. There is. In order to prevent this, it is necessary to attach a rust preventive tape 8.
【０００９】本発明に使用するＰＥＴフィルムの厚みは
薄いほど体表面起伏部位への追従性が良いが、薄すぎる
と製造での作業性が悪くなる為、２〜３８μｍが好まし
い範囲である。The thinner the PET film used in the present invention, the better the conformability to the undulating portion of the body surface, but if it is too thin, the workability in the production is deteriorated, so that the preferable range is 2 to 38 μm.
【００１０】本発明においては、ＰＥＴフィルムの片面
に接着剤層を介してポリエステル製布が接合、積層され
る。本発明においては、ポリエステル製布は織布、ニッ
ト、不織布のいずれの場合も含まれる。In the present invention, a polyester cloth is bonded and laminated on one side of the PET film via an adhesive layer. In the present invention, the polyester cloth includes any of woven cloth, knitted cloth and non-woven cloth.
【００１１】ポリエステル以外の繊維よりなる布体、例
えばアセテート布は水分の吸湿によりカールしやすく作
業上問題がでてくること、綿布はカビがはえやすいこ
と、また繊維の種類の如何に拘らず、不織布は表面のケ
バ立ちが多く、印刷されたものは見栄えが良くない。ポ
リエステル製布ではこの様な問題がなく、また接着剤と
の親和性も良いことから選定した。Cloths made of fibers other than polyester, such as acetate cloth, tend to curl due to absorption of moisture, which causes problems in work, and cotton cloth is prone to mold, and regardless of the type of fiber. However, the non-woven fabric has a lot of fluff on the surface, and the printed one does not look good. Polyester cloth was selected because it does not have such problems and has good affinity with adhesives.
【００１２】次に、上記ポリエステル製布をＰＥＴフィ
ルムへ接合させる接着剤層について説明する。ポリエス
テル製布とＰＥＴフィルムとの接着力が弱いと、ポリエ
ステル製布とＰＥＴフイルムとの間のはがれや、電極板
を折りまげたり、何回も使用するとシワが入りやすく、
また、積層体を貫通して附設した接続用スナップが、回
路接続操作をくり返すうちに、ガタがきてうきが生じや
すくなる。Next, the adhesive layer for bonding the polyester cloth to the PET film will be described. If the adhesive force between the polyester cloth and the PET film is weak, peeling between the polyester cloth and the PET film, the electrode plate may be folded, and wrinkles may easily occur if used many times.
In addition, the connection snap penetrating through the laminated body is liable to rattle as the circuit connecting operation is repeated, which makes it more likely to cause anxiety.
【００１３】このようにポリエステル布とＰＥＴフィル
ムとの間の接着性が悪いと実用性や外観が悪くなる。こ
のようなポリエステル布と、ＰＥＴフィルムとの間のう
きやはがれをなくすためには、一定水準以上の接着力が
望まれる。従って、Ｔ型剥離接着強さがＪＩＳ Ｋ ６
８５４に規定の試験方法で０．１５ｋｇｆ／２５ｍｍ以
上であることが好ましい。また、電極を曲げて使用する
度に、上記接着層に剪断力が負荷されることになり、こ
のようなくり返し剪断に対する接着層の抵抗力（クリー
プ破壊時間）はクリープ試験によって評価することがで
きる。上記の接着層としては、測定温度４０℃におい
て、荷重３００ｇでの該接着剤層のクリープ破壊時間が
ＪＩＳ Ｋ ６８５９に規定の試験方法で２０分以上で
あることが望ましい。２０分未満の接着剤ではポリエス
テル布の表面からにじみ出し、またポリエステル布やＰ
ＥＴフィルムの周辺からも接着剤がはみ出し、ホコリな
どが付着して外観状悪くなるばかりでなく、はみ出した
り、にじみ出た接着剤が衣類に付くことにより皮膚への
接着性にも良い影響を与えない。従ってクリープ破壊時
間は最低でも２０分以上は必要である。If the adhesiveness between the polyester cloth and the PET film is poor as described above, the practicality and appearance are deteriorated. In order to eliminate such peeling and peeling between the polyester cloth and the PET film, an adhesive force of a certain level or higher is desired. Therefore, the T-type peel adhesion strength is JIS K 6
It is preferably 0.15 kgf / 25 mm or more according to the test method prescribed in 854. Further, each time the electrode is bent and used, a shearing force is applied to the adhesive layer, and the resistance force (creep rupture time) of the adhesive layer to such repeated shearing can be evaluated by a creep test. . As the above-mentioned adhesive layer, it is desirable that the creep rupture time of the adhesive layer at a measurement temperature of 40 ° C. and a load of 300 g is 20 minutes or more by the test method specified in JIS K 6859. If the adhesive is less than 20 minutes, it will ooze out from the surface of the polyester cloth, or the polyester cloth or P
Not only does the adhesive squeeze out from around the ET film and dust adheres to it, but the appearance also deteriorates, and the squeeze-out and bleeding adhesive does not affect the adhesion to the skin. . Therefore, the creep rupture time must be at least 20 minutes.
【００１４】本発明の医療用電極の電極板に使用される
接着剤は、プラスチックフィルムと布体とを確実に接合
できるものであればその材質に制限はないが、溶液型ポ
リエステル樹脂系接着剤やアクリル系樹脂接着剤等が好
ましい。溶液型ポリエステル樹脂系接着剤は比較的広範
囲の基材に対して高い接着性を示すので、ポリエステル
はもとよりポリ塩化ビニルやポリカーボネート、繊維強
化プラスチックなどのプラスチック類、繊維、皮革、フ
ォーム材料にも優れた接着性を示す。また、この皮膜は
強く柔軟性がある。この接着剤の接着性は劣化条件でも
良好な状態であり、さらに耐電圧、高絶縁性にも優れて
いる。The adhesive used for the electrode plate of the medical electrode of the present invention is not limited in its material as long as it can reliably bond the plastic film and the cloth, but a solution type polyester resin adhesive An acrylic resin adhesive or the like is preferable. Solution type polyester resin adhesives have high adhesion to a relatively wide range of substrates, so they are excellent not only for polyester but also for polyvinyl chloride, polycarbonate, plastics such as fiber reinforced plastics, fibers, leather, and foam materials. Shows good adhesion. Also, this coating is strong and flexible. The adhesive property of the adhesive is in a good state even under deterioration conditions, and is also excellent in withstand voltage and high insulation.
【００１５】アクリル系樹脂接着剤は優れた接着性を有
し、高温、光線環境温度、環境湿度などの劣化条件でも
高い保存安定性がある。The acrylic resin adhesive has excellent adhesiveness and has high storage stability even under deterioration conditions such as high temperature, light environment temperature, and environmental humidity.
【００１６】次に、ＰＥＴフィルムの他面に設ける導電
層としては、先ず、導電性塗料による塗膜層を、次い
で、その上に導電性粘着層を設けることにより、形成す
ることができる。また、これとは別の構成として、図２
に示すように導電性塗膜層を設けないで、直接、ＰＥＴ
フィルムに導電性粘着層を形成することもできる。Next, a conductive layer provided on the other surface of the PET film can be formed by first providing a coating film layer of a conductive paint and then providing a conductive adhesive layer thereon. Further, as another configuration different from this, FIG.
Directly without PET layer as shown in
A conductive adhesive layer can be formed on the film.
【００１７】本発明に用いられる導電性塗料はカーボン
ブラック、ニッケル、銀、銅、鉄等の導電性金属や合金
あるいは、酸化錫、酸化銅等の導電性金属化合物の粉
体、繊維体、フレーク等を樹脂溶液中に含有する塗料で
ある。The conductive paint used in the present invention is a conductive metal or alloy such as carbon black, nickel, silver, copper or iron, or a powder of conductive metal compound such as tin oxide or copper oxide, fibrous body, flakes. It is a paint containing the above in a resin solution.
【００１８】なお、この導電性塗料から得られる塗膜
は、本発明の医療用薄層平板電極においてはその電気抵
抗値を１０ ００Ω以下とすることが好ましい。また、上
記電極板の塗料形成面に設けられる導電性粘着剤を構成
する構成物質はウレタン系樹脂、アクリル系樹脂などあ
るが特に限定はない。導電性粘着剤の電気抵抗値も１０
００Ω以下、さらに好ましくは５００Ω以下とすること
が微弱電流の検出可能性の理由から好ましい。A coating film obtained from this conductive paint
Is the electrical resistance of the medical thin-layer flat plate electrode of the present invention.
10 resistance It is preferably set to 00Ω or less. Also on
Consists of a conductive adhesive provided on the paint forming surface of the electrode plate
The constituent substances used include urethane resin and acrylic resin.
However, there is no particular limitation. The electric resistance value of the conductive adhesive is also 10
00Ω or less, more preferably 500Ω or less
Is preferable because of the detectability of the weak current.
【００１９】[0019]
実施例１〜３ 、比較例１〜７ アクリル系樹脂接着剤Ａ〜Ｈの８種類（日東電工社製）
または溶液型ポリエステル系樹脂接着剤２種類（東亜合
成社製、商品名ＰＥＳシリーズ）１００重量部に、イソ
シアネート化合物（日本ポリウレタン工業社製、商品名
コロネートＨＸ）５重量部加え十分に混合したものを、
導電性塗料を塗布したＰＥＴフィルム（２５μｍ厚）の
塗料形成面の逆の方に塗布、乾燥して、ポリエステル布
と積層して電極板を作成した。この電極板の塗料形成面
に、１０重量％以上の水分を含有するポリアクリル酸ナ
トリウム系の高分子からなる導電性粘着剤を設けて医療
用電極を作製した。Examples 1 to 3 and Comparative Examples 1 to 7 Eight kinds of acrylic resin adhesives A to H (manufactured by Nitto Denko Corporation)
Alternatively, 100 parts by weight of two types of solution type polyester resin adhesive (manufactured by Toagosei Co., Ltd., trade name PES series) and 5 parts by weight of an isocyanate compound (manufactured by Nippon Polyurethane Industry Co., Ltd., trade name Coronate HX) are mixed thoroughly. ,
A PET film (25 μm thick) coated with a conductive coating was applied to the opposite side of the coating forming surface, dried, and laminated with a polyester cloth to form an electrode plate. A conductive electrode made of a sodium polyacrylate-based polymer containing 10% by weight or more of water was provided on the coating surface of the electrode plate to prepare a medical electrode.
【００２０】実施例４〜５ 、比較例８〜１３ アクリル系接着剤（日東電工社製）を導電性塗料を塗布
したＰＥＴフィルムの塗料形成面の逆の方に厚みが１５
μｍになる様に、塗布、乾燥して、ポリエステルまたは
アセテートなどの布と積層して電極板を作成した。この
電極板の塗料形成面に、１０重量％以上の水分を含有す
る上記実施例および比較例に用いたアクリル系高分子か
らなる導電性粘着剤を設けてて医療用電極を作製した。
上記の実施例、比較例で作製した医療用電極を用いて以
下の評価試験を行った。Examples 4 to 5, Comparative Examples 8 to 13 Acrylic adhesive (manufactured by Nitto Denko Corporation) coated with a conductive paint has a thickness of 15 on the side opposite to the paint forming surface of the PET film.
An electrode plate was prepared by coating and drying so as to have a thickness of μm, and laminating it with a cloth such as polyester or acetate. A conductive electrode containing the acrylic polymer used in the above Examples and Comparative Examples containing 10% by weight or more of water was provided on the coating surface of this electrode plate to prepare a medical electrode.
The following evaluation tests were conducted using the medical electrodes prepared in the above Examples and Comparative Examples.
【００２１】表１に導電性粘着剤の配合を変えた場合の
評価試験の結果を、表２に布体の種類やＰＥＴフィルム
の厚みを変えた場合の評価試験の結果を示す。Table 1 shows the results of the evaluation test when the composition of the conductive adhesive was changed, and Table 2 shows the results of the evaluation test when the kind of cloth and the thickness of the PET film were changed.
【表１】 [Table 1]
【００２２】[0022]
【表２】 [Table 2]
【００２３】評価は下記の判定基準により行った。 ＜剥離力＞ＪＩＳ−Ｋ ６８５４の「接着剤の剥離接着
強さ試験方法」に準じる。試験片の形状は幅２５ｍｍで
長さ１５０ｍｍとする。剥離方法はＴ型剥離とし、試験
機の引張強さは３００ｍｍ／ｍｉｎとする。（電極板の
みで試験した）The evaluation was performed according to the following criteria. <Peeling force> According to JIS-K 6854 “Test method for peeling adhesive strength of adhesive”. The shape of the test piece is 25 mm in width and 150 mm in length. The peeling method is T-type peeling, and the tensile strength of the tester is 300 mm / min. (Tested with the electrode plate only)
【００２４】＜クリープ破壊時間＞ＪＩＳ−Ｋ ６８５
９の「接着剤のクリープ試験方法」に準じて行った。試
験片は圧着部分が長さ１３ｍｍ、幅２５ｍｍとしその圧
着部分の両側６７ｍｍの余裕を作る。つかみ部分は長さ
４０ｍｍである。荷重３００ｇとし４０℃雰囲気で試験
した。（電極のみで試験した）<Creep Rupture Time> JIS-K685
The test was carried out in accordance with 9 "Adhesive Creep Test Method". The pressure-bonded portion of the test piece has a length of 13 mm and a width of 25 mm, and a margin of 67 mm on both sides of the pressure-bonded portion is made. The grip portion has a length of 40 mm. The load was 300 g and the test was conducted in an atmosphere of 40 ° C. (Tested with electrodes only)
【００２５】＜浮き＞導電性粘着剤を設ける前の電極板
にスナップを植込みそのスナップを外部装置との接続用
の端子で５００回脱着するとき、スナップ周辺に浮きが
あるか目視にて観察した。 ○…まったく浮きがみられない。 △…少し浮きがみられる。 ×…ポリエステル布がＰＥＴフィルムからはがれてい
る。<Float> When a snap was implanted on the electrode plate before the conductive adhesive was provided and the snap was detached 500 times with a terminal for connection to an external device, it was visually observed whether there was a float around the snap. . ○: There is no floating at all. △: A little floating is seen. X: The polyester cloth is peeled off from the PET film.
【００２６】＜接着剤の裏抜け性＞電極板のみで試験す
る。試験片は２０ｍｍ×２０ｍｍとし、これに２ｋｇの
荷重をかけ７０℃に１週間おき、ポリエステル布の表面
の接着剤の裏抜け性を目視にて観察した。 ○…変化なし。 △…接着剤の裏抜けが少しある。 ×…完全に接着剤が裏抜けしている。<Strikethrough of Adhesive> The test is performed only on the electrode plate. The test piece was 20 mm × 20 mm, a load of 2 kg was applied thereto, and the test piece was left at 70 ° C. for 1 week, and the strike-through property of the adhesive on the surface of the polyester cloth was visually observed. ○: No change. Δ: There is some strikethrough of the adhesive. X: The adhesive has completely penetrated.
【００２７】＜導電性＞電極パッドの電気抵抗値は、ポ
リエステル製セパレータを剥離し、試料の表裏面を銅板
にてサンドイッチしたのち、各銅板を金属コードにて挟
み、ヒューレトパッカード製ＬＣＲメーターにて印可電
圧１Ｖ、測定周波数１ＫＨｚの条件下でインピータンス
を測定した。 ○…５００Ω以下 △…５００〜１０００Ω ×…１０００Ω以上<Electrical Conductivity> The electrical resistance of the electrode pad was measured by peeling the polyester separator, sandwiching the front and back surfaces of the sample with copper plates, sandwiching each copper plate with a metal cord, and then using a Huret Packard LCR meter. Impedance was measured under the conditions of an applied voltage of 1 V and a measurement frequency of 1 KHz. ○: 500Ω or less Δ: 500 to 1000Ω ×: 1000Ω or more
【００２８】＜折りまげ時の浮き＞試料を折りまげた
後、もどした時にポリエステル布面に浮きがあるかを目
視にて確認した。 ○…浮きがみられない。 △…浮きはみられないが、折りまげた所に線がはいり、
すぐには消えない。 ×…折りまげた所が浮く。<Float at Folding> When the sample was folded and then returned, it was visually confirmed whether there was a float on the polyester cloth surface. ○: No floating is seen. △: There is no floating, but a line is inserted at the folded part,
It will not disappear immediately. ×: The folded part floats.
【００２９】＜表面のケバ立ち＞肩に８時間貼りつけた
後、表面のケバ立ちについて目視で観察した。 ○…貼る前とほぼ同じ。 △…少しだがケバ立ちがみられる。 ×…かなりケバ立ちがある。<Surface Blushing> After sticking on the shoulder for 8 hours, the surface blushing was visually observed. ○: Almost the same as before sticking. △… Slightly fluffy. ×: There is a lot of flapping.
【００３０】＜カール性＞試料がカールしているかを目
視にて観察した。 ○…まったくカールしない。 △…少しカールする。 ×…カールが大きい。<Curl Property> Whether the sample was curled was visually observed. ○: Does not curl at all. △: A little curled. C: Large curl.
【００３１】＜はがれ性＞皮フに貼り付けはがれがある
かを目視にて観察した。 ○…皮フにしっかりついている。 △…端が浮く。 ×…はがれた。<Peelability> It was adhered to the skin and visually observed for peeling. ○: It is firmly attached to the skin. △: The edge floats. ×: It peeled off.
【００３２】＜接着剤はみだし性＞皮フに貼り付け、接
着剤のはみだしがあるかを目視にて観察した。 ○…ない。 △…少しある。 ×…かなりある。<Adhesive Adhesion Protrusion> The adhesive was attached to a skin and visually inspected for any adhesive protrusion. ○… No. △: There is a little. ×: There are quite a few.
【００３３】＜防カビ＞ 高湿度条件 ４０℃ ９０％ＲＨの恒温室内に７日間おきにカビの有
無を目視にて観察した。 ○…カビがまったくでてこない。 △…少しでてくる。 ×…かなりでてくる。 表１，２の結果より明らかなように、本発明の医療用薄
層平板電極を用いた場合は従来技術の問題点を解決して
いる。<Antifungal> High humidity conditions Visual observation was conducted every 7 days in a thermostatic chamber at 40 ° C. and 90% RH. ○: No mold appears. △… It's coming soon. ×: It comes out quite a lot. As is clear from the results of Tables 1 and 2, when the medical thin-layer flat plate electrode of the present invention is used, the problems of the prior art are solved.
【００３４】[0034]
【発明の効果】以上説明したように、本発明によって、
医療用薄層平板電極の構造に関して、プラスチックフィ
ルムがポリエチレンやポリプロピレンのものにおいて、
布体や導電層に対する接着性を確保し、平板電極が、体
表面各部位の起伏に十分対応し得る可撓性を持つことが
実施可能な皮膚面密着性の優れた薄層電極構成を創出す
ることができた。As described above, according to the present invention,
Regarding the structure of medical thin layer flat plate electrode, if the plastic film is polyethylene or polypropylene,
Creates a thin-layer electrode configuration with excellent skin surface adhesion that secures adhesiveness to the cloth and conductive layer and allows the flat plate electrode to have flexibility enough to deal with the undulations of various parts of the body surface. We were able to.
【００３５】[0035]
【図１】本発明医療用薄層平板電極の構成態様を例示す
る断面図である。FIG. 1 is a cross-sectional view illustrating a constitutional aspect of a medical thin-layer plate electrode of the present invention.
【図２】本発明の医療用薄層平板電極の他の構成態様を
例示する断面図である。FIG. 2 is a cross-sectional view illustrating another configuration aspect of the medical thin-layer plate electrode of the present invention.
【図３】本発明の医療用薄層平板電極の他の構成態様を
例示する断面図である。FIG. 3 is a cross-sectional view illustrating another configuration aspect of the medical thin-layer plate electrode of the present invention.
Ｐ 本発明の電極 １ ポリエステル製布 ２ 接着剤層 ３ ＰＥＴフィルム ４ 導電性塗膜 ５ 導電性粘着剤層 ６ セパレータ ７ 接続用スナップ ８ 防錆テープ P Electrode of the present invention 1 Polyester cloth 2 Adhesive layer 3 PET film 4 Conductive coating film 5 Conductive adhesive layer 6 Separator 7 Snap for connection 8 Anticorrosion tape
Claims (2)
他面に導電層が積層されてなる、皮膚面に密着させて用
いる医療用薄層平板電極において、プラスチックフィル
ムが、厚さ２〜３８μｍのポリエチレンテレフタレート
フィルムで、布体が、接着剤により該プラスチックフィ
ルムに接合されたポリエステル製布で、および、導電層
の少なくとも皮膚面密着部分が導電性粘着剤で構成さ
れ、かつ、接着剤によりプラスチックフイルムに接合さ
れたポリエステル製布のＴ字形剥離接着強さがＪＩＳ
Ｋ ６８５４に規定の試験方法で０．１５ｋｇｆ／２５
ｍｍ以上であり、かつ、測定温度４０℃において、荷重
３００ｇでの該接着剤層のクリープ破壊時間がＪＩＳ
Ｋ ６８５９に規定の試験方法で２０分以上である密着
性に優れた医療用薄層平板電極。1. A cloth body is provided on one side of a plastic film,
In a medical thin-layer flat plate electrode having a conductive layer laminated on the other surface, which is used in close contact with the skin surface, the plastic film is a polyethylene terephthalate film having a thickness of 2 to 38 μm, and the cloth body is made of the plastic with an adhesive. T-shaped peeling adhesive strength of polyester cloth bonded to a film, and at least the skin surface contact portion of the conductive layer made of a conductive adhesive and bonded to a plastic film with an adhesive Is JIS
0.15 kgf / 25 by the test method specified in K 6854
The creep rupture time of the adhesive layer under a load of 300 g at a measurement temperature of 40 ° C. or more according to JIS
A medical thin-layer flat plate electrode having excellent adhesion which is 20 minutes or more by the test method specified in K 6859.
１に記載の医療用薄層平板電極。2. The medical thin layer plate electrode according to claim 1, further comprising a connection snap.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP8090520A JPH09253219A (en) | 1996-03-18 | 1996-03-18 | Medical thin layer flat electrode |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP8090520A JPH09253219A (en) | 1996-03-18 | 1996-03-18 | Medical thin layer flat electrode |
Publications (1)
| Publication Number | Publication Date |
|---|---|
| JPH09253219A true JPH09253219A (en) | 1997-09-30 |
Family
ID=14000733
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| JP8090520A Pending JPH09253219A (en) | 1996-03-18 | 1996-03-18 | Medical thin layer flat electrode |
Country Status (1)
| Country | Link |
|---|---|
| JP (1) | JPH09253219A (en) |
Cited By (5)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US7668580B2 (en) | 2005-10-20 | 2010-02-23 | Samsung Electronics Co., Ltd. | Electrode for living body and device for detecting living signal |
| WO2016093194A1 (en) * | 2014-12-08 | 2016-06-16 | 日本電信電話株式会社 | Bioelectrode and garment |
| JP2018100473A (en) * | 2015-01-14 | 2018-06-28 | 東洋紡株式会社 | Method to manufacture clothing equipped with electrode and wiring |
| CN112930028A (en) * | 2021-01-28 | 2021-06-08 | 优尔爱(常州)医疗科技有限公司 | Flexible electrode with ductility and preparation method |
| EP3951035A4 (en) * | 2019-03-29 | 2023-05-10 | Toyobo Co., Ltd. | Garment |
-
1996
- 1996-03-18 JP JP8090520A patent/JPH09253219A/en active Pending
Cited By (12)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US7668580B2 (en) | 2005-10-20 | 2010-02-23 | Samsung Electronics Co., Ltd. | Electrode for living body and device for detecting living signal |
| US8214009B2 (en) | 2005-10-20 | 2012-07-03 | Samsung Electronics Co., Ltd. | Electrode for living body and device for detecting living signal |
| US8473025B2 (en) | 2005-10-20 | 2013-06-25 | Samsung Electronics Co., Ltd. | Electrode for living body and device for detecting living signal |
| WO2016093194A1 (en) * | 2014-12-08 | 2016-06-16 | 日本電信電話株式会社 | Bioelectrode and garment |
| JPWO2016093194A1 (en) * | 2014-12-08 | 2017-08-31 | 日本電信電話株式会社 | Bioelectrode and clothing |
| KR20170102460A (en) * | 2014-12-08 | 2017-09-11 | 니폰 덴신 덴와 가부시끼가이샤 | Bioelectrode and Garment |
| JP2018153666A (en) * | 2014-12-08 | 2018-10-04 | 日本電信電話株式会社 | Bioelectrode and garment |
| US10799136B2 (en) | 2014-12-08 | 2020-10-13 | Nippon Telegraph And Telephone Corporation | Bioelectrode and garment |
| JP2018100473A (en) * | 2015-01-14 | 2018-06-28 | 東洋紡株式会社 | Method to manufacture clothing equipped with electrode and wiring |
| EP3951035A4 (en) * | 2019-03-29 | 2023-05-10 | Toyobo Co., Ltd. | Garment |
| CN112930028A (en) * | 2021-01-28 | 2021-06-08 | 优尔爱(常州)医疗科技有限公司 | Flexible electrode with ductility and preparation method |
| CN112930028B (en) * | 2021-01-28 | 2022-11-29 | 优尔爱(常州)医疗科技有限公司 | Flexible electrode with ductility and preparation method |
Similar Documents
| Publication | Publication Date | Title |
|---|---|---|
| JPS6317455Y2 (en) | ||
| JP2570183Y2 (en) | Biomedical electrode structure | |
| US6276054B1 (en) | Method of manufacturing a disposable electrode | |
| US20090290279A1 (en) | Grounding electrode | |
| EP0740525B1 (en) | Biomedical conductor containing inorganic oxides and biomedical electrodes prepared therefrom | |
| JP7402560B2 (en) | Biopotential measurement method | |
| JP3717368B2 (en) | electrode | |
| JP3992360B2 (en) | Conductive adhesive tape | |
| JPH077924Y2 (en) | Medical electrode | |
| JPH09253219A (en) | Medical thin layer flat electrode | |
| JP4441747B2 (en) | Biological electrode material | |
| TWI811310B (en) | Laminated body for biosensor and biosensor | |
| EP3237056B1 (en) | Biomedical electrode comprising discontinuous primer layer | |
| JPH07222805A (en) | Thin electrode for living body | |
| EP4154746A1 (en) | Clothing-type biometric data measurement device and manufacturing method thereof | |
| JPH11406A (en) | Electrode with snap for human body | |
| JP2790795B2 (en) | Biological electrode | |
| JP7331357B2 (en) | Connector structure, wearable terminal, and biological information measurement system | |
| JP3313534B2 (en) | Electrode element and biological electrode using the same | |
| JPH0663157A (en) | Medical electrode plate and medical electrode | |
| JP7230486B2 (en) | Connector structure, wearable terminal, and biological information measurement system | |
| US12011911B2 (en) | Isotropic non-aqueous electrode sensing material | |
| JP3737871B2 (en) | Limb lead electrode pad | |
| JPH0638906U (en) | Biomedical electrodes | |
| JP6932060B2 (en) | Elastic wiring board, manufacturing method of elastic wiring board and elastic wiring board with electronic parts |