JPH01175836A - Manufacture for bioinduction electrode - Google Patents
Manufacture for bioinduction electrodeInfo
- Publication number
- JPH01175836A JPH01175836A JP62336068A JP33606887A JPH01175836A JP H01175836 A JPH01175836 A JP H01175836A JP 62336068 A JP62336068 A JP 62336068A JP 33606887 A JP33606887 A JP 33606887A JP H01175836 A JPH01175836 A JP H01175836A
- Authority
- JP
- Japan
- Prior art keywords
- base material
- electrode
- electrolyte
- separator
- electrode element
- 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.)
- Granted
Links
- 238000004519 manufacturing process Methods 0.000 title claims abstract description 13
- 239000000463 material Substances 0.000 claims abstract description 56
- 239000003792 electrolyte Substances 0.000 claims abstract description 33
- 239000000853 adhesive Substances 0.000 claims abstract description 29
- 230000001070 adhesive effect Effects 0.000 claims abstract description 29
- 230000006698 induction Effects 0.000 claims description 20
- 238000000034 method Methods 0.000 claims description 6
- 230000000694 effects Effects 0.000 claims description 4
- 238000001035 drying Methods 0.000 claims description 2
- WABPQHHGFIMREM-UHFFFAOYSA-N lead(0) Chemical compound [Pb] WABPQHHGFIMREM-UHFFFAOYSA-N 0.000 abstract description 9
- 229910052751 metal Inorganic materials 0.000 abstract description 3
- 239000002184 metal Substances 0.000 abstract description 3
- 229920003002 synthetic resin Polymers 0.000 abstract description 3
- 239000000057 synthetic resin Substances 0.000 abstract description 3
- 230000002093 peripheral effect Effects 0.000 abstract description 2
- 238000003860 storage Methods 0.000 abstract description 2
- 239000011247 coating layer Substances 0.000 abstract 1
- 239000000428 dust Substances 0.000 abstract 1
- 239000006071 cream Substances 0.000 description 5
- 239000000017 hydrogel Substances 0.000 description 4
- 239000011230 binding agent Substances 0.000 description 2
- 238000007796 conventional method Methods 0.000 description 2
- 210000002216 heart Anatomy 0.000 description 2
- 238000005259 measurement Methods 0.000 description 2
- 239000000843 powder Substances 0.000 description 2
- 229910001316 Ag alloy Inorganic materials 0.000 description 1
- 229920001817 Agar Polymers 0.000 description 1
- 208000002330 Congenital Heart Defects Diseases 0.000 description 1
- 108010010803 Gelatin Proteins 0.000 description 1
- 229920005830 Polyurethane Foam Polymers 0.000 description 1
- 239000008272 agar Substances 0.000 description 1
- 229910000808 amorphous metal alloy Inorganic materials 0.000 description 1
- 210000004556 brain Anatomy 0.000 description 1
- 238000006243 chemical reaction Methods 0.000 description 1
- 238000001816 cooling Methods 0.000 description 1
- 238000010586 diagram Methods 0.000 description 1
- 238000011156 evaluation 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
- 239000012943 hotmelt Substances 0.000 description 1
- 235000015110 jellies Nutrition 0.000 description 1
- 239000008274 jelly Substances 0.000 description 1
- 239000000203 mixture Substances 0.000 description 1
- 210000003205 muscle Anatomy 0.000 description 1
- 239000004745 nonwoven fabric Substances 0.000 description 1
- 229920002401 polyacrylamide Polymers 0.000 description 1
- 239000011496 polyurethane foam Substances 0.000 description 1
- 238000003825 pressing Methods 0.000 description 1
- 230000035807 sensation Effects 0.000 description 1
- 239000004332 silver Substances 0.000 description 1
- 230000037380 skin damage Effects 0.000 description 1
- 238000012546 transfer Methods 0.000 description 1
- 230000007704 transition Effects 0.000 description 1
Abstract
Description
【発明の詳細な説明】
〔産業上の利用分野〕
本発明は生体からの微弱電圧を検出するために用いられ
る生体用誘導電極の製造方法に関するものである。DETAILED DESCRIPTION OF THE INVENTION [Industrial Field of Application] The present invention relates to a method for manufacturing a biological induction electrode used for detecting weak voltage from a biological body.
周知のように生体に発生する生体電気は、心臓、脳、筋
肉の活動によって誘起されている。As is well known, bioelectricity generated in living organisms is induced by the activities of the heart, brain, and muscles.
特に心臓に発生した生体電気は、生体の皮膚面に誘起さ
れた微弱電流を外部の心電計で記録し、、心臓の異常を
診断している。In particular, bioelectricity generated in the heart is used to diagnose heart abnormalities by recording weak currents induced on the skin of a living body using an external electrocardiograph.
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面に生体用誘導電極を密着しなけれ
ばならない。In this electrocardiograph, in order to electrically connect the input section to the living body, the living body's induction electrode must be brought into close contact with the skin surface of the living body.
この生体用誘導電極の優劣は、電極対の間の電位差を高
入力インピーダンスの電圧計で測定した時の値（電極対
電圧又はオフセット電圧）、電極を電解質に接触させた
状態で界面が電気化学的に平衡状態に達するまでの過渡
期における上記電圧の変動特性（初期ドリフト特性）、
電極表面の汚れや不均一性に起因する電極電位の変動特
性（雑音特性）、電極対に交流入力を印加した時のイン
ピーダンス特性、電極対に外部信号を与えた時のインピ
ーダンス及びオフセット電圧の変動特性（除細動耐性）
等を比較し、その総合的評価に基づいて決定される。The superiority of this biological induction electrode is determined by the value when the potential difference between the electrode pair is measured with a high input impedance voltmeter (electrode pair voltage or offset voltage), and when the electrode is in contact with the electrolyte, the interface is electrochemically The fluctuation characteristics of the above voltage during the transition period until reaching an equilibrium state (initial drift characteristics),
Fluctuation characteristics of electrode potential due to dirt or non-uniformity on the electrode surface (noise characteristics), impedance characteristics when AC input is applied to the electrode pair, fluctuations in impedance and offset voltage when an external signal is applied to the electrode pair Characteristics (defibrillation resistance)
etc. and is determined based on the comprehensive evaluation.
この電極特性を支配する要因としては、電極素子材料、
電解質の組成及び均一性は勿論のこと、電極素子と電解
質及び皮膚との電気的、機械的接触状況も多大な影響を
有する０例えば電極と測定器間をつなぐリード線の動き
によって、電極素子、電解質及び皮膚の相対的位置関係
が変化し、大きな測定誤差を招くおそれがある。従って
生体用誘導電極を構成する部材を組み立てて生体用誘導
電極を製造することは非常に重要なものとなる。The factors governing this electrode property include the electrode element material,
Not only the composition and uniformity of the electrolyte, but also the electrical and mechanical contact between the electrode element, the electrolyte, and the skin have a significant influence.For example, the movement of the lead wire between the electrode and the measuring instrument may cause The relative positional relationship between the electrolyte and the skin may change, leading to large measurement errors. Therefore, it is very important to manufacture a living body induction electrode by assembling the members constituting the living body induction electrode.
従来電解質を角いた生体用誘導電極を組み立てて生体用
誘導電極を製造する方法は、ホットメルなどの接着剤或
いは粘着剤を使用しており、そのため電極素子、電解質
、支持基材、粘着基材の相互の接合が不均一となり易い
。Conventional methods for producing biological induction electrodes by assembling electrolyte squares have used adhesives or adhesives such as hot melt, which has made the electrode elements, electrolytes, support base materials, and adhesive base materials difficult to assemble. Mutual bonding tends to be uneven.
また電解質と接合剤との化学反応によって、電解質が変
質するなどの電極特性の不安定要因となるとともに、電
解質を介して接合剤が皮膚面に直接接触して、皮膚障害
をひき起こすことがある。In addition, the chemical reaction between the electrolyte and the binder may cause the electrolyte to change in quality, causing unstable electrode properties, and the binder may come into direct contact with the skin via the electrolyte, causing skin damage. .
さらに複数の面接合を行う場合には、その接合数に応じ
た回数の接合工程を要し、時間と経費を要する等の問題
点があった。Furthermore, when a plurality of surfaces are bonded, a number of bonding steps are required depending on the number of bondings, which causes problems such as time and expense.
そこでこの発明は、以上の問題点に着目してなされたも
ので
生体内微弱電流を導出するための電極素子と、この電極
素子の効果を補助するための電解質と、生体の皮膚面と
直接密着する粘着基材と、前記電極素子を固定する支持
基材と、前記粘着基材の粘着性を維持するためのセパレ
ータと、前記電解質の乾燥を防止するためのカバーとに
よって構成される生体用誘導電極の製造方法であって、
前記電極素子と電解質を固定する支持基材と、セパレー
タ付き粘着基材及びカバーとを重ねた状態で加圧すると
ともに、超音波振動を与えることによって、粘着基材と
支持基材及びセパレータとカバーとを同時に接合して生
体用誘導電極を組立てることを特徴とする、生体用誘導
電極の製造方法という手段を提供して、従来のものと同
等以上の接合強度をもたらしめ、且つ複数面の接合を単
一工程にて処理し、コスト低減に役立つことのできる生
体用誘導電極を得ることを目的とする。Therefore, this invention was made by focusing on the above problems, and includes an electrode element for deriving a weak current in the living body, an electrolyte for assisting the effect of this electrode element, and an electrode element that is directly attached to the skin surface of the living body. a support base material for fixing the electrode element, a separator for maintaining the adhesiveness of the adhesive base material, and a cover for preventing the electrolyte from drying out. A method for manufacturing an electrode, the method comprising:
The supporting base material for fixing the electrode element and the electrolyte, the adhesive base material with a separator, and the cover are stacked together and pressurized, and ultrasonic vibration is applied to the adhesive base material, the supporting base material, the separator, and the cover. The present invention provides a method for producing a biological induction electrode, which is characterized by assembling a biological induction electrode by simultaneously bonding two electrodes, which provides a bonding strength equal to or higher than conventional ones, and which can bond multiple surfaces. The purpose is to obtain a biological induction electrode that can be processed in a single step and that can help reduce costs.
電極素子（−電解質を接し、粘着基材に支持基材の一端
部を接し、その他端部は前記電極素子に接し、粘着基材
にセパレータを接し、セパレータにカバーを接した生体
用誘導電極を、アンビルの電極収納口にセットし、上部
から超音波ホーンを当てて１．適当な圧力下で上下方向
超音波振動を与えると、前記電極素子と電解質を固定し
た支持基材とセパレータ付き粘着基材とカバーとが同時
に接合でき、生体用誘導電極が製造できる。Electrode element (-A biological induction electrode in which an electrolyte is in contact, one end of a support base is in contact with an adhesive base material, the other end is in contact with the electrode element, a separator is in contact with an adhesive base material, and a cover is in contact with the separator. , set it in the electrode storage opening of the anvil, and apply an ultrasonic horn from above to apply vertical ultrasonic vibration under appropriate pressure. Then, the supporting base material with the electrode element and electrolyte fixed thereon, and the adhesive base with separator The material and the cover can be joined at the same time, and a biological induction electrode can be manufactured.
（実施例〕
本発明の実施例について、以下図面に従って本発明の構
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。(Example) Regarding an example of the present invention, how the configuration of the present invention is actually embodied will be described below with reference to the drawings, together with its operation.
第２図は本発明の生体用誘導電極Ａの断面図で、電極素
子、粘着基材、支持基材、電解質等の各部品で構成され
ている。FIG. 2 is a sectional view of the living body induction electrode A of the present invention, which is composed of various parts such as an electrode element, an adhesive base material, a support base material, and an electrolyte.
この各構成部品を説明すると、図中１は電極素子で、こ
の電極素子はリード線端子（図示せず）が取り付けられ
る頭部１１と、この頭部１１の下側に形成された首部１
２と、この首部１２の下側に形成される底部１３とから
構成されるもので、合成樹脂を基材１４とし、その外周
面には銀、アモルファス合金等の金属粉末がコーティン
グ［１５としてコーティングされ導電性が付与されてい
る。To explain each component, 1 in the figure is an electrode element, and this electrode element includes a head 11 to which a lead wire terminal (not shown) is attached, and a neck 1 formed on the lower side of the head 11.
2 and a bottom part 13 formed on the lower side of this neck part 12. The base material 14 is made of synthetic resin, and the outer peripheral surface thereof is coated with metal powder such as silver or amorphous alloy [coated as 15]. and is given electrical conductivity.
この基材１４を合成樹脂製としたことは、大量生産に適
し、コストを低廉化できることと、軽量化による生体の
皮膚面に対する装着の安定化と、熱の伝達を阻止し、装
着時の皮膚面における冷感防止を図るためである。また
基材１４の外周面に金属の粉末をコーティングしたのは
、基材１４の外周面に凹凸が形成されて有効面積が増大
したため、電極性が良好になるためである。The base material 14 is made of synthetic resin, which is suitable for mass production and can reduce costs.It is also light in weight, which stabilizes the attachment to the skin of the living body, and prevents heat transfer, making it suitable for mass production. This is to prevent a cold sensation on the surface. Further, the reason why the outer circumferential surface of the base material 14 is coated with metal powder is that unevenness is formed on the outer circumferential surface of the base material 14 to increase the effective area and improve polarity.
この頭部１１の下側にある首部１２は頭部１１より細く
形成される。この首部１２の下側には底部１３が首部１
２より広く形成され、電極素子１は全体として傘型状を
なしている。A neck portion 12 located below the head 11 is formed to be thinner than the head 11. On the underside of this neck 12, a bottom 13 is attached to the neck 1.
2, and the electrode element 1 has an umbrella shape as a whole.
２は粘着基材で生体用誘導電極Ａを直接皮膚の表面に密
着させるもので、その上下両面に粘着剤が塗布された高
分子材料製の不織布のリング状の伸縮材料で且つイオン
導電性を有する電解質で構成されている。2 is an adhesive base material that brings the biological induction electrode A into direct contact with the surface of the skin, and is made of a ring-shaped stretchable material made of a nonwoven fabric made of a polymeric material with adhesive applied to both its upper and lower surfaces, and has ion conductivity. It is made up of electrolytes.
３は支持基材で硬質性であり、その一端部は前記粘着基
材２の上面に接し、その他端部は前記電極素子１の頭部
１１及び底部１３を押圧係止している。Reference numeral 3 denotes a support base material which is rigid, and one end thereof is in contact with the upper surface of the adhesive base material 2, and the other end thereof presses and locks the head 11 and bottom 13 of the electrode element 1.
そしてこの頭部１１及び底部１３を押圧係止することに
より、頭部１１にリード線端子（図示せず）が連結され
たときに、クリップ型電極が何らかの外圧を受けて揺動
しても、支持基材３で電極素子１を強固に支持できるの
で、例えリード線端子が揺動しても、電極素子１はリー
ド線端子Ｂの揺動に応じて動くことはなくなり、その結
果生体用誘導電極Ａは皮膚面から心電図測定中に剥離す
ることはない。By pressing and locking the head 11 and the bottom 13, even if the clip-type electrode swings under some external pressure when a lead wire terminal (not shown) is connected to the head 11, Since the support base material 3 can firmly support the electrode element 1, even if the lead wire terminal swings, the electrode element 1 will not move in response to the swing of the lead wire terminal B, and as a result, the biological guidance Electrode A does not peel off from the skin surface during electrocardiogram measurement.
４は硬質性の支持基材３の底部に接着される電解質であ
っ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も有している。この電解質４を
生体の皮膚面に密着すると、皮膚面に誘起された微弱電
圧は、電解質４から電極素子１に導かれ、電極素子１か
らリード線端子へ導かれ、このリード線端子に連結され
ているリード線を介して心電計に導かれ、心電図が記録
できる。Reference numeral 4 denotes an electrolyte and hydrogel layer that is adhered to the bottom of the rigid support base material 3. This hydrogel layer is made of gelatin, agar, polyacrylamide, etc., and has considerable adhesiveness and conductivity. It also has When this electrolyte 4 is brought into close contact with the skin surface of a living body, the weak voltage induced on the skin surface is guided from the electrolyte 4 to the electrode element 1, from the electrode element 1 to the lead wire terminal, and connected to this lead wire terminal. The electrocardiogram can be recorded by leading to an electrocardiograph via a lead wire attached to the electrocardiogram.
この電解質４は、電極素子１の底部１３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素子ｌ
の底部１３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、支持基材３の底部１３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
。When using this electrolyte 4, if the bottom part 13 of the electrode element 1 is directly brought into close contact with the skin surface, accurate weak voltage cannot be measured due to the contact resistance of the skin surface. Therefore, apply cream or the like to the skin surface in advance to reduce the contact resistance. Weak the cream and place the electrode element l on it.
The weak voltage was measured by touching the bottom part 13 of the supporting base material 3, but it is troublesome and inefficient to apply cream every time a weak voltage is measured in this way, so a cream was applied to the bottom part 13 of the support base material 3. By adhering a functional hydrogel layer, it eliminates the inconvenience of applying cream each time.
この電解質としては、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
。As the electrolyte, a polyurethane foam layer impregnated with jelly may be used instead of the hydrogel layer.
６は生体用誘導電極Ａを保護しているカバーである。こ
のカバー６は使用に際してはセパレータ５の一端に形成
されている着脱片５ａを指でつまんで剥離するものであ
る。6 is a cover that protects the biological induction electrode A. When the cover 6 is used, it is peeled off by pinching a removable piece 5a formed at one end of the separator 5 with fingers.
次に上記の構成の各部品を組立てて生体用誘導電極Ａの
製造方法を説明する。Next, a method of manufacturing the living body induction electrode A by assembling each component having the above configuration will be described.
先ず第２図に示されるようにアンビル８の電極収納口８
ａに、電極素子１、粘着基材２、支持基材３、電解質４
、セパレータ５、カバー６を第１図のようにセットする
。次いでリング状の先端形状７ａを有する超音波ホーン
７をアンビル８上に重ねてから超音波ホーンを当てて、
適当な圧力下のもとて上下方向の超音波振動を与えると
、電極素子１と電解質４を固定した支持基材とセパレー
タ付き粘着基材とカバーとが同時に短時間で接合できる
。First, as shown in FIG.
a, electrode element 1, adhesive base material 2, support base material 3, electrolyte 4
, separator 5, and cover 6 as shown in FIG. Next, the ultrasonic horn 7 having a ring-shaped tip 7a is stacked on the anvil 8, and then the ultrasonic horn is applied.
By applying ultrasonic vibration in the vertical direction under appropriate pressure, the supporting base material to which the electrode element 1 and electrolyte 4 are fixed, the adhesive base material with separator, and the cover can be bonded simultaneously in a short time.
この場合の接合条件は、
加圧カニ２０〜６０ｋｇ／ａＪ
超音波振動数： ２０ＫＩＩｚ
超音波振動二０．４〜０．６秒
超音波停止後の加圧上冷却時間＝０．５〜２．０秒であ
る。The bonding conditions in this case are as follows: Pressure crab 20-60kg/aJ Ultrasonic vibration frequency: 20KIIz Ultrasonic vibration 20.4-0.6 seconds Pressurization cooling time after stopping ultrasonic waves = 0.5-2. It is 0 seconds.
なお超音波ホーン先端端部７Ａに、微細な凹凸加工を施
すことにより、接合面積を増やして接合強度を向上させ
ることができる。Note that by applying fine irregularities to the tip end portion 7A of the ultrasonic horn, the bonding area can be increased and the bonding strength can be improved.
以上本発明によれば、電極素子、電解質、粘着基材、支
持基材、セパレータ、カバー等を重ねた状態で加圧する
と同時に超音波振動を与えるようにしたので、電極素子
と電解質を固定した支持基材とセパレータ付き粘着基材
とカバーとが同時に接合することができ、その結果従来
上記の部品を接着剤でいちいち接着していたものと比較
して、短時間に効率よ（生体用誘導電極を製造できる。As described above, according to the present invention, since the electrode element, electrolyte, adhesive base material, support base material, separator, cover, etc. are applied in a stacked state and ultrasonic vibration is applied at the same time, the electrode element and electrolyte are fixed. The support base material, the adhesive base material with a separator, and the cover can be bonded simultaneously, resulting in a faster and more efficient bonding process (compared to the conventional method of bonding the above components one by one with adhesive). Electrodes can be manufactured.
第１図は本発明の生体用誘導電極の製造方法の説明図、
第２図は生体用誘導電極の断面図である。
Ａ・・・・・・生体用誘導電極、
１・・・・・・電極素子、
２・・・・・・粘着基材、
３・・・・・・支持基材、
４・・・・・・電解質、
５・・・・・・セパレータ、
６・・・・・・カバー、
７・・・・・・超音波ホーン、
８・・・・・・アンビル。FIG. 1 is an explanatory diagram of the method for manufacturing a biological induction electrode of the present invention,
FIG. 2 is a sectional view of the biological induction electrode. A... Biological induction electrode, 1... Electrode element, 2... Adhesive base material, 3... Support base material, 4... - Electrolyte, 5... Separator, 6... Cover, 7... Ultrasonic horn, 8... Anvil.
Claims (1)
電極素子の効果を補助するための電解質と、生体の皮膚
面に直接密着する粘着基材と、前記電極素子及び電解質
を固定する支持基材と、前記粘着基材の粘着性を維持す
るためのセパレータと、前記電解質の乾燥を防止するた
めのカバーとによって構成される生体用誘導電極の製造
方法であって、前記電極素子と電解質を固定する支持基
と、セパレータ付き粘着基材及びカバーとを重ねた状態
で加圧するとともに、超音波振動を与えることによって
、粘着基材と支持基材及びセパレータとカバーとを同時
に接合して生体用誘導電極を組立てることを特徴とする
、生体用誘導電極の製造方法。An electrode element for deriving a weak current from within a living body, an electrolyte for assisting the effect of this electrode element, an adhesive base material that adheres directly to the skin surface of the living body, and a support base for fixing the electrode element and electrolyte. a separator for maintaining the adhesiveness of the adhesive base material, and a cover for preventing the electrolyte from drying; The supporting base to be fixed, the adhesive base material with a separator, and the cover are stacked together and pressurized, and ultrasonic vibrations are applied to simultaneously bond the adhesive base material, the support base material, the separator, and the cover, and the adhesive base material and the support base material, the separator, and the cover are bonded together. A method for producing a biological induction electrode, the method comprising assembling an induction electrode.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP62336068A JPH0712351B2 (en) | 1987-12-29 | 1987-12-29 | Method for manufacturing living body induction electrode |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP62336068A JPH0712351B2 (en) | 1987-12-29 | 1987-12-29 | Method for manufacturing living body induction electrode |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| JPH01175836A true JPH01175836A (en) | 1989-07-12 |
| JPH0712351B2 JPH0712351B2 (en) | 1995-02-15 |
Family
ID=18295362
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| JP62336068A Expired - Lifetime JPH0712351B2 (en) | 1987-12-29 | 1987-12-29 | Method for manufacturing living body induction electrode |
Country Status (1)
| Country | Link |
|---|---|
| JP (1) | JPH0712351B2 (en) |
Citations (2)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JPS58116338A (en) * | 1981-12-22 | 1983-07-11 | フランツ・メデイカル・デイヴエロツプメント・リミテツド | Biomedical skin electrode with long life and current transmitting method |
| JPS6086303U (en) * | 1983-11-17 | 1985-06-14 | 日東電工株式会社 | disposable electrodes |
-
1987
- 1987-12-29 JP JP62336068A patent/JPH0712351B2/en not_active Expired - Lifetime
Patent Citations (2)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JPS58116338A (en) * | 1981-12-22 | 1983-07-11 | フランツ・メデイカル・デイヴエロツプメント・リミテツド | Biomedical skin electrode with long life and current transmitting method |
| JPS6086303U (en) * | 1983-11-17 | 1985-06-14 | 日東電工株式会社 | disposable electrodes |
Also Published As
| Publication number | Publication date |
|---|---|
| JPH0712351B2 (en) | 1995-02-15 |
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