JPH0536402Y2 - - Google Patents
Info
- Publication number
- JPH0536402Y2 JPH0536402Y2 JP1987047090U JP4709087U JPH0536402Y2 JP H0536402 Y2 JPH0536402 Y2 JP H0536402Y2 JP 1987047090 U JP1987047090 U JP 1987047090U JP 4709087 U JP4709087 U JP 4709087U JP H0536402 Y2 JPH0536402 Y2 JP H0536402Y2
- Authority
- JP
- Japan
- Prior art keywords
- electrode
- living body
- base material
- biological
- lead wire
- 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.)
- Expired - Lifetime
Links
- 230000001070 adhesive effect Effects 0.000 claims description 26
- 239000000853 adhesive Substances 0.000 claims description 25
- 239000000463 material Substances 0.000 claims description 20
- 239000000126 substance Substances 0.000 claims description 11
- 239000004745 nonwoven fabric Substances 0.000 claims description 10
- 239000007788 liquid Substances 0.000 claims description 6
- 238000007639 printing Methods 0.000 claims description 5
- WABPQHHGFIMREM-UHFFFAOYSA-N lead(0) Chemical compound [Pb] WABPQHHGFIMREM-UHFFFAOYSA-N 0.000 description 17
- 239000006071 cream Substances 0.000 description 7
- 239000000017 hydrogel Substances 0.000 description 4
- 238000000034 method Methods 0.000 description 4
- 230000008878 coupling Effects 0.000 description 3
- 238000010168 coupling process Methods 0.000 description 3
- 238000005859 coupling reaction Methods 0.000 description 3
- 230000000694 effects Effects 0.000 description 3
- 229910052709 silver Inorganic materials 0.000 description 3
- 239000004332 silver Substances 0.000 description 3
- OKTJSMMVPCPJKN-UHFFFAOYSA-N Carbon Chemical compound [C] OKTJSMMVPCPJKN-UHFFFAOYSA-N 0.000 description 2
- 239000003795 chemical substances by application Substances 0.000 description 2
- 239000004020 conductor Substances 0.000 description 2
- 238000010586 diagram Methods 0.000 description 2
- 239000003792 electrolyte Substances 0.000 description 2
- 229910002804 graphite Inorganic materials 0.000 description 2
- 239000010439 graphite Substances 0.000 description 2
- 210000002216 heart Anatomy 0.000 description 2
- 229910052751 metal Inorganic materials 0.000 description 2
- 239000002184 metal Substances 0.000 description 2
- -1 polyethylene Polymers 0.000 description 2
- 229920001817 Agar Polymers 0.000 description 1
- 208000002330 Congenital Heart Defects Diseases 0.000 description 1
- 108010010803 Gelatin Proteins 0.000 description 1
- 239000004698 Polyethylene Substances 0.000 description 1
- 239000004743 Polypropylene Substances 0.000 description 1
- 229920005830 Polyurethane Foam Polymers 0.000 description 1
- 229910021607 Silver chloride Inorganic materials 0.000 description 1
- 239000008272 agar Substances 0.000 description 1
- 210000004556 brain Anatomy 0.000 description 1
- 238000005516 engineering process Methods 0.000 description 1
- 239000008273 gelatin Substances 0.000 description 1
- 229920000159 gelatin Polymers 0.000 description 1
- 235000019322 gelatine Nutrition 0.000 description 1
- 235000011852 gelatine desserts Nutrition 0.000 description 1
- 230000005831 heart abnormality Effects 0.000 description 1
- 235000015110 jellies Nutrition 0.000 description 1
- 239000008274 jelly Substances 0.000 description 1
- 238000004519 manufacturing process Methods 0.000 description 1
- 238000005259 measurement Methods 0.000 description 1
- 239000000203 mixture Substances 0.000 description 1
- 210000003205 muscle Anatomy 0.000 description 1
- 229920002401 polyacrylamide Polymers 0.000 description 1
- 229920000728 polyester Polymers 0.000 description 1
- 229920000573 polyethylene Polymers 0.000 description 1
- 229920001155 polypropylene Polymers 0.000 description 1
- 239000011496 polyurethane foam Substances 0.000 description 1
- 239000000843 powder Substances 0.000 description 1
- 239000011347 resin Substances 0.000 description 1
- 229920005989 resin Polymers 0.000 description 1
- HKZLPVFGJNLROG-UHFFFAOYSA-M silver monochloride Chemical compound [Cl-].[Ag+] HKZLPVFGJNLROG-UHFFFAOYSA-M 0.000 description 1
- 239000002904 solvent Substances 0.000 description 1
Description
【考案の詳細な説明】
〔産業上の利用分野〕
本考案は生体から微弱電圧を導出するために用
いられる生体用電極に係わり、特に生体へ密着し
易く、廉価に制作できる生体用電極に関するもの
である。[Detailed description of the invention] [Field of industrial application] The present invention relates to a biological electrode used to derive a weak voltage from a living body, and particularly to a biological electrode that can be easily attached to a living body and manufactured at a low cost. It is.
周知のように生体に発生する生体電気は、心
臓、脳、筋肉などの活動によつて誘導されてい
る。
As is well known, bioelectricity generated in a living body is induced by the activities of the heart, brain, muscles, etc.
特に心臓に発生した生体電気は、生体の皮膚面
に誘導された微弱電圧を外部の心電計で記録し、
心臓の異常を診断している。そしてこの心電計は
入力部を生体と電気的に結合させるために生体の
皮膚の表面に生体用電極を密着しなければならな
い。 In particular, bioelectricity generated in the heart is measured by recording the weak voltage induced on the skin of the living body using an external electrocardiograph.
Diagnosing heart abnormalities. In order to electrically connect the input section to the living body, this electrocardiograph requires a living body electrode to be brought into close contact with the surface of the living body's skin.
この皮膚の表面に密着される従来の電極を、第
６図、第７図に従つて説明すると、図中１は生体
用電極である。 The conventional electrode that is brought into close contact with the surface of the skin will be explained with reference to FIGS. 6 and 7. In the figure, reference numeral 1 indicates a biological electrode.
この生体用電極１は略円盤状の貼着基材２を有
している。この貼着基材２は第８図に示されるよ
うに生体用電極１を生体の皮膚面Ｍに密着させる
ために第７図に示されるようにその表面２ａに貼
着性を帯びさせているものであるとともに、その
中央部が切欠されて開口３が形成されている。 This biological electrode 1 has a substantially disc-shaped adhesive base material 2. As shown in FIG. 7, this adhesive base material 2 has adhesive properties on its surface 2a in order to bring the biological electrode 1 into close contact with the skin surface M of the living body as shown in FIG. In addition, the central portion thereof is cut out to form an opening 3.
この貼着基材２の上面側（表面側）には、第６
図に示されるようにリード線接続ホツク４が接合
され、前記開口３を閉塞している。このリード線
接続ホツク４は上面側にリード線結合部４ａが突
設し、下面側には第７図に示されるようにAg−
Agcl製の板状の電極部５が接続されている。こ
の突設したリード線結合部４ａには、第８図に示
されるようにリード線６が接続されているリード
線接続体７が連結され、リード線６の他端は心電
計（図示せず）に接続されている。 On the upper surface side (surface side) of this adhesive base material 2, a sixth
As shown in the figure, a lead wire connection hook 4 is joined and closes the opening 3. This lead wire connection hook 4 has a lead wire coupling portion 4a protruding from the upper surface side, and an Ag-bonding portion 4a protruding from the lower surface side as shown in FIG.
A plate-shaped electrode section 5 made of Agcl is connected. A lead wire connector 7 to which a lead wire 6 is connected as shown in FIG. 8 is connected to the protruding lead wire coupling portion 4a, and the other end of the lead wire 6 is connected to an electrocardiograph (not shown). ).
以上のような構成の生体用電極１を利用して心
電図を記録するには、先ず第８図に示されるよう
に生体用電極１の貼着基材２を生体の皮膚面Ｍに
接着し、続いてリード線接続体７の嵌合凹溝７ａ
を、生体用電極１のリード線接続ホツク４に突設
されているリード線結合部４ａに嵌合することに
より、リード線接続体７を生体用電極１に連結し
て、電極部５から導出される微弱電圧をリード線
６を介して心電計（図示せず）に記録する。
In order to record an electrocardiogram using the biological electrode 1 configured as described above, first, as shown in FIG. 8, the adhesive base material 2 of the biological electrode 1 is adhered to the skin surface M of the biological body. Next, the fitting groove 7a of the lead wire connection body 7
is fitted into the lead wire coupling portion 4a protruding from the lead wire connection hook 4 of the biomedical electrode 1, thereby connecting the lead wire connecting body 7 to the biomedical electrode 1 and leading it out from the electrode portion 5. The weak voltage generated is recorded on an electrocardiograph (not shown) via the lead wire 6.
又は予め生体用電極１のリード線接続ホツク４
に突設されているリード結合部４ａに、リード線
接続体７の嵌合凹溝７ａを嵌合して、リード線接
続体７が連結された生体用電極１を、生体の皮膚
面Ｍに密着して心電図を記録してもよいものであ
る。 Or, connect the lead wire connection hook 4 of the biological electrode 1 in advance.
The fitting groove 7a of the lead wire connection body 7 is fitted into the lead connection portion 4a protruding from the body, and the biomedical electrode 1 to which the lead wire connection body 7 is connected is attached to the skin surface M of the living body. Electrocardiograms may be recorded in close contact.
ところでこのようにしていずれの方法でも心電
図の測定が可能であるが、このような生体用電極
１は殆どの場合一回の測定で廃棄処分にしてい
る。しかしながら生体用電極１の電極部５は前記
したようにAg−Agclのような高価な金属を使用
しておる。また直接生体から微弱電圧を導出する
電極部５とこの電極部５で導出した電圧を心電計
に導くリード線接続体及びリード線（即ち回路
部）とは別々の部品であるため組立て工程が複雑
になり制作費が高価になるという問題点があつ
た。特に生体電極１は多数個使用されるためコス
トの問題は無視できないものであり、より廉価で
制作できる生体用電極１の開発が待たれていた。 Although it is possible to measure an electrocardiogram using any of the methods described above, in most cases, such a biological electrode 1 is discarded after one measurement. However, as described above, the electrode portion 5 of the biological electrode 1 uses an expensive metal such as Ag-Agcl. Furthermore, since the electrode part 5 that directly derives weak voltage from the living body and the lead wire connection body and lead wire (i.e. circuit part) that lead the voltage derived from this electrode part 5 to the electrocardiograph are separate parts, the assembly process is simplified. The problem was that it was complicated and the production cost was high. In particular, since a large number of biological electrodes 1 are used, the problem of cost cannot be ignored, and the development of a biological electrode 1 that can be manufactured at a lower cost has been awaited.
さらに生体用電極１は、重病患者のような場合
には、背中にも貼着しなければならないので、横
臥状態の重病患者は背中に生体用電極１が当た
り、不快感を与えるとともに従来使用されている
生体用電極は生体にフイツトしないという欠点も
あつた。 Furthermore, in the case of a seriously ill patient, the biomedical electrode 1 must also be attached to the back of the patient, so if the patient is lying down, the biomedical electrode 1 may come into contact with his or her back, causing discomfort and not being conventionally used. The biological electrode used in this study also had the disadvantage that it did not fit the living body.
また上記電極部５を直接皮膚の表面に密着させ
ると皮膚の表面の接触抵抗により、正確な微弱電
圧が測定でき難いので、第８図に示されるように
予め皮膚面Ｍにクリーム８等を塗布して微弱電圧
を測定しているが、このように微弱電圧を測定す
る毎にクリームを塗布することは面倒で非能率で
あるという問題点もあつた。 Furthermore, if the electrode section 5 is directly brought into close contact with the skin surface, it is difficult to measure an accurate weak voltage due to the contact resistance of the skin surface, so as shown in FIG. 8, cream 8 or the like is applied to the skin surface M in advance. However, there was a problem in that it was troublesome and inefficient to apply cream every time a weak voltage was measured.
そこでこの考案は、以上の問題点に着目してな
されたものであつて
不織布製の貼着基材に液状の導電性物質を印刷
含浸させることにより形成した電極部と回路部と
を少くとも備え、この電極部は生体と密着して生
体の皮膚抵抗を低下させるために電解物質が塗布
され、前記回路部は前記電極部に接続するととも
に、絶縁性のある粘着剤を塗布して生体に密着で
きるようにした、生体用電極
という手段を提供して、上記問題点を解決するこ
とを目的とするものである。
This invention was devised in view of the above problems, and includes at least an electrode part and a circuit part formed by printing and impregnating a liquid conductive substance on an adhesive base material made of non-woven fabric. , this electrode part is coated with an electrolytic substance in order to come into close contact with the living body and reduce the skin resistance of the living body, and the circuit part is connected to the electrode part and is also coated with an insulating adhesive so as to be brought into close contact with the living body. The object of the present invention is to provide a biological electrode that can be used to solve the above problems.
以上の構成において、生体用電極の電極部を生
体の皮膚面に接するとともに、不織布製の貼着基
材の貼着剤を生体の皮膚面に接すると、生体内の
微弱電圧は電極部から導出されて回路部から心電
計へ導かれ、心電図が記録される。
In the above configuration, when the electrode part of the biological electrode is brought into contact with the skin surface of the living body and the adhesive of the nonwoven adhesive base material is brought into contact with the skin surface of the living body, the weak voltage inside the living body is derived from the electrode part. The electrocardiogram is then guided from the circuit to the electrocardiograph, where the electrocardiogram is recorded.
以下図面に従つて本考案の構成が実際上どのよ
うに具体化されるかをその作用とともに説明す
る。
Hereinafter, how the configuration of the present invention is actually implemented will be explained with reference to the drawings, along with its operation.
第１図は本考案の一実施例に従う生体用電極の
斜視図、第２図は第１図の生体用電極の断面図で
あつて、図中１０は生体用電極である。 FIG. 1 is a perspective view of a biological electrode according to an embodiment of the present invention, and FIG. 2 is a sectional view of the biological electrode of FIG. 1, where 10 is the biological electrode.
この生体用電極１０は貼着基材１１を有してい
る。この貼着基材１１はポリエチレン、ポリエス
テル、ポリプロピレン、パルプ等製の不織布を使
用している。１２は生体から微弱電圧を導出させ
るたの電極部である。 This biological electrode 10 has an adhesive base material 11 . This adhesive base material 11 uses a nonwoven fabric made of polyethylene, polyester, polypropylene, pulp, or the like. Reference numeral 12 denotes an electrode portion for deriving a weak voltage from the living body.
この電極部１２は、銀又は銀と塩化銀の混合、
銀と導電性黒鉛の混合、或は黒鉛を、導電性の金
属粉とし、これを樹脂と溶剤で混合してペースト
又はインク状即ち液状とした導電性物質である導
電性インクと前記貼着基材１１に印刷又は含浸さ
せて密着させる。 This electrode part 12 is made of silver or a mixture of silver and silver chloride.
A conductive ink, which is a conductive material made by mixing silver and conductive graphite, or graphite as a conductive metal powder, and mixing it with a resin and a solvent to form a paste or ink, that is, a liquid, and the adhesive base. The material 11 is printed or impregnated to make it adhere closely.
ここで導電性インクが印刷又は含浸される貼着
基材１１は第３図に示されるように不織布製であ
るので、表面の状態が凹凸でポーラス状に穴があ
いており、印刷又は含浸した導電性インクは中に
浸透していき易く導電性インクの選択が容易であ
り、結果的に表面積が広くなり皮膚表面に対する
電気抵抗も当然低くなるものである。 The adhesive base material 11 on which the conductive ink is printed or impregnated is made of non-woven fabric as shown in FIG. Conductive ink easily penetrates into the skin, making it easy to select a conductive ink, resulting in a larger surface area and naturally lower electrical resistance to the skin surface.
また不織布は、皮膚への感触がよく馴染み易い
ものである。 In addition, nonwoven fabrics have a good feel and are easy to blend into the skin.
この導電性インクを貼着基材１１に印刷又は含
浸させて電極部１２を形成すると当時に導電性イ
ンクを貼着基材１１に線状に印刷又は含浸させて
回路部１３を第１図、第２図、第４図に示される
ように形成する。この回路部１３はその一端は電
極部１２に接続するとともに、その他端はコネク
ター（図示せず）を介して心電計（図示せず）に
連結している。 This conductive ink is printed or impregnated on the adhesive base material 11 to form the electrode part 12, and at that time, the conductive ink is printed or impregnated in a line on the adhesive base material 11 to form the circuit part 13 as shown in FIG. It is formed as shown in FIGS. 2 and 4. One end of this circuit section 13 is connected to the electrode section 12, and the other end is connected to an electrocardiograph (not shown) via a connector (not shown).
このように貼着基材１１へ単に導電性インクを
印刷、含浸させるのみで、電極部も回路部も同時
に一体化して形成できるとともに、その結果電極
部と回路部とは別個に制作することがないので、
生体用電極を廉価に製造できるものである。 In this way, by simply printing and impregnating the adhesive base material 11 with conductive ink, the electrode part and the circuit part can be formed simultaneously and integrally, and as a result, the electrode part and the circuit part can be manufactured separately. Since there is no,
This allows biological electrodes to be manufactured at low cost.
１４は前記電極部１２に塗布された電解物質で
あつて、含水ゲル層であり、この含水ゲル層はゼ
ラチン、寒天、ポリアクリルアミド等で製造さ
れ、かなりの粘着性を有するとともに導電性を有
している。 Reference numeral 14 is an electrolytic substance applied to the electrode portion 12, which is a hydrogel layer. This hydrogel layer is made of gelatin, agar, polyacrylamide, etc., and has considerable adhesiveness and conductivity. ing.
この電解物質１４を生体の皮膚面に密着する
と、表面に誘起された微弱電圧を電極部１２に導
くものである。この電解物質１４は電極部１２を
直接皮膚の表面に密着させると皮膚の表面の接触
抵抗により、正確な微弱電圧が測定できないの
で、予め皮膚面にクリーム等を塗布して接触抵抗
を弱めそのクリーム上に電極部１２を接触して微
弱電圧を測定していたが、このように微弱電圧を
測定する毎にクリームを塗布することは面倒で非
能率であるので、電極部１２にクリームの働きを
する含水ゲル層を接着していちいちクリームを塗
布する不便を除去するようにしたものである。こ
の電解物質１４としては、含水ゲル層に代えてゼ
リーを含浸させたポリウレタン・フオーム層を使
用することもある。 When this electrolyte 14 is brought into close contact with the skin surface of a living body, a weak voltage induced on the surface is guided to the electrode section 12. If this electrolytic substance 14 is used, it is impossible to accurately measure a weak voltage due to the contact resistance of the skin surface if the electrode part 12 is brought into direct contact with the skin surface. Therefore, cream or the like is applied to the skin surface in advance to weaken the contact resistance. The weak voltage was measured by contacting the electrode part 12 on top of the electrode part 12, but it is troublesome and inefficient to apply cream every time a weak voltage is measured in this way, so we decided to apply cream to the electrode part 12. This method eliminates the inconvenience of applying cream each time by adhering the hydrogel layer. As the electrolyte 14, a polyurethane foam layer impregnated with jelly may be used instead of the hydrogel layer.
１５は前記回路部１３を絶縁する絶縁剤で、１
６は貼着基材１１を、第５図に示されるように生
体の皮膚面Ｍへ貼着するための粘着剤である。 15 is an insulating agent for insulating the circuit section 13;
Reference numeral 6 denotes an adhesive for adhering the adhesion base material 11 to the skin surface M of the living body as shown in FIG.
次に以上の構成の生体用電極１０の使用法を説
明すると、生体用電極１０を第５図に示すように
その電極部１２を電解物質１４を介して生体の皮
膚面に接し、不織布製の貼着基材１１の粘着剤１
６を皮膚面に密着すると、生体内の微弱電圧は電
極部１２から導出されて回路部１３により心電計
（図示せず）へ導かれ心電図を記録することがで
きる。 Next, to explain how to use the biological electrode 10 having the above configuration, as shown in FIG. Adhesive 1 of adhesive base material 11
6 is brought into close contact with the skin surface, the weak voltage in the living body is derived from the electrode section 12 and guided to an electrocardiograph (not shown) by the circuit section 13, so that an electrocardiogram can be recorded.
以上本考案によれば、不織布製の貼着基材に液
状の導電性物質を印刷含浸させることにより、電
極部及び回路部が形成できるので、生体用電極が
廉価で制作できる。
As described above, according to the present invention, the electrode part and the circuit part can be formed by printing and impregnating a non-woven adhesive base material with a liquid conductive substance, so that a biological electrode can be produced at a low cost.
また液状の導電物質を印刷含浸させて電極部と
回路部を一体的に形成することができるので、組
立て工程が能率よくなるとともに、電気的特性が
安定した電極が得られる。 Further, since the electrode portion and the circuit portion can be integrally formed by printing and impregnating a liquid conductive material, the assembly process becomes efficient and an electrode with stable electrical characteristics can be obtained.
さらに貼着基材として不織布を使用しているの
で、不織布の表面の状態が凹凸でポーラス状に穴
があいており、そのため液状の導電物質が含浸し
易くなり、結果的に導電性物質の表面積が広くな
り、皮膚表面に対する抵抗値が低下できると同時
に、不織布そのものは生体の皮膚への接触がよく
馴染み易く生体へフイツトし易い、その結果生体
用電極として好適である。 Furthermore, since non-woven fabric is used as the adhesive base material, the surface of the non-woven fabric is uneven and has porous holes, which makes it easy for liquid conductive substances to soak in, resulting in a surface area of conductive substances. The resistance value against the skin surface can be lowered, and at the same time, the non-woven fabric itself has good contact with the skin of a living body and is easy to fit onto the living body.As a result, it is suitable as a living body electrode.
加えて電極部に生体の皮膚抵抗を低下させるた
めの電解物質が塗布されているので、生体用電極
を皮膚面に密着させる際に、生体にクリーム等を
一々塗布する必要性がなくなり、使用するのに面
倒でない等の利点がある。 In addition, since the electrode part is coated with an electrolytic substance to reduce the skin resistance of the living body, there is no need to apply cream etc. to the living body each time the living body electrode is brought into close contact with the skin surface. It has the advantage that it is not troublesome.
第１図は本考案の一実施例である生体用電極の
斜視図、第２図は第１図の−線断面図、第３
図は不織布の貼着基材の斜視図、第４図は第１図
の平面図、第５図は本考案の生体用電極の使用説
明図、第６図、第７図、第８図は従来の生体用電
極の説明図である。
１０……生体用電極、１１……不織布製貼着基
材、１２……電極部、１３……回路部、１４……
電解物質、１５……絶縁剤、１６……粘着剤。
Fig. 1 is a perspective view of a biological electrode that is an embodiment of the present invention, Fig. 2 is a sectional view taken along the - line in Fig. 1, and Fig. 3 is a sectional view taken along the line -
The figure is a perspective view of a nonwoven fabric adhesive base material, Figure 4 is a plan view of Figure 1, Figure 5 is an explanatory diagram of the use of the biological electrode of the present invention, and Figures 6, 7, and 8 are FIG. 2 is an explanatory diagram of a conventional biological electrode. DESCRIPTION OF SYMBOLS 10... Biomedical electrode, 11... Nonwoven fabric adhesive base material, 12... Electrode part, 13... Circuit part, 14...
Electrolytic substance, 15...Insulating agent, 16...Adhesive.
Claims (1)
含浸させることにより形成した電極部と回路部と
を少くとも備え、この電極部は生体と密着して生
体の皮膚抵抗を低下させるために電解物質が塗布
され、前記回路部は前記電極部に接続するととも
に、絶縁性のある粘着剤を塗布して生体に密着で
きるようにしたことを特徴とする、生体用電極。 It comprises at least an electrode part and a circuit part formed by printing and impregnating a liquid conductive substance on an adhesive base material made of non-woven fabric, and this electrode part is in close contact with a living body to lower the skin resistance of the living body. 1. An electrode for living body, characterized in that an electrolytic substance is applied, the circuit part is connected to the electrode part, and an insulating adhesive is applied so that it can be brought into close contact with a living body.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP1987047090U JPH0536402Y2 (en) | 1987-03-30 | 1987-03-30 |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP1987047090U JPH0536402Y2 (en) | 1987-03-30 | 1987-03-30 |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| JPS63154005U JPS63154005U (en) | 1988-10-11 |
| JPH0536402Y2 true JPH0536402Y2 (en) | 1993-09-14 |
Family
ID=30867362
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| JP1987047090U Expired - Lifetime JPH0536402Y2 (en) | 1987-03-30 | 1987-03-30 |
Country Status (1)
| Country | Link |
|---|---|
| JP (1) | JPH0536402Y2 (en) |
Cited By (1)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| WO2016143666A1 (en) * | 2015-03-12 | 2016-09-15 | タツタ電線株式会社 | Biomedical electrode device |
Citations (2)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JPS5926604B2 (en) * | 1978-02-03 | 1984-06-29 | 北興化学工業株式会社 | Sterilizing composition for agriculture and horticulture |
| JPS61107792A (en) * | 1984-10-31 | 1986-05-26 | 東芝シリコ−ン株式会社 | Formation of circuit base fabric |
Family Cites Families (1)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JPS5926604U (en) * | 1982-08-12 | 1984-02-18 | セノ−株式会社 | Biological electrode |
-
1987
- 1987-03-30 JP JP1987047090U patent/JPH0536402Y2/ja not_active Expired - Lifetime
Patent Citations (2)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JPS5926604B2 (en) * | 1978-02-03 | 1984-06-29 | 北興化学工業株式会社 | Sterilizing composition for agriculture and horticulture |
| JPS61107792A (en) * | 1984-10-31 | 1986-05-26 | 東芝シリコ−ン株式会社 | Formation of circuit base fabric |
Cited By (2)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| WO2016143666A1 (en) * | 2015-03-12 | 2016-09-15 | タツタ電線株式会社 | Biomedical electrode device |
| JPWO2016143666A1 (en) * | 2015-03-12 | 2017-12-28 | タツタ電線株式会社 | Biological electrode device |
Also Published As
| Publication number | Publication date |
|---|---|
| JPS63154005U (en) | 1988-10-11 |
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