JPH088910B2 - Biomedical electrode - Google Patents
Biomedical electrodeInfo
- Publication number
- JPH088910B2 JPH088910B2 JP3326640A JP32664091A JPH088910B2 JP H088910 B2 JPH088910 B2 JP H088910B2 JP 3326640 A JP3326640 A JP 3326640A JP 32664091 A JP32664091 A JP 32664091A JP H088910 B2 JPH088910 B2 JP H088910B2
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- JP
- Japan
- Prior art keywords
- silver
- strip
- biomedical electrode
- coated organic
- coated
- 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
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- Measurement And Recording Of Electrical Phenomena And Electrical Characteristics Of The Living Body (AREA)
Description
【０００１】[0001]
【産業上の利用分野】本発明は、生体に装着してインピ
ーダンスを測定するための生体用電極に係わり、更に詳
細には、呼吸循環系計測に用いられる生体用電極に関す
る。BACKGROUND OF THE INVENTION 1. Field of the Invention The present invention relates to a biomedical electrode for mounting on a living body to measure impedance, and more particularly to a biomedical electrode used for respiratory circulatory system measurement.
【０００２】[0002]
【従来の技術】生体の呼吸循環系計測には、胸部及び頸
部にそれぞれ巻回された帯状電極間に所定の電流を印加
し、これらの電極間の生体のインピーダンスを計測する
ことにより行われる。2. Description of the Related Art Measurement of the respiratory circulatory system of a living body is performed by applying a predetermined current between strip-shaped electrodes wound around the chest and neck and measuring the impedance of the living body between these electrodes. .
【０００３】前記の帯状電極は従来は図５に示すように
構成されていた。即ち、図５において、帯状の紙１の片
面に長手方向に平行にアルミニウムで形成された２本の
帯状電極２が設けられている。また、紙１の帯状電極２
が設けられた面には、帯状電極２の部分以外の面に接着
剤が塗布されている。そして、紙１を接着剤を介して被
検者の生体表面に接着して前述したように呼吸循環系計
測を行う。The above strip-shaped electrode has been conventionally constructed as shown in FIG. That is, in FIG. 5, two strip-shaped electrodes 2 made of aluminum are provided on one surface of a strip-shaped paper 1 in parallel with the longitudinal direction. Also, the strip electrode 2 of the paper 1
An adhesive is applied to a surface other than the portion of the strip electrode 2 on the surface provided with. Then, the paper 1 is adhered to the surface of the living body of the subject through an adhesive, and the respiratory circulation system is measured as described above.
【０００４】[0004]
【発明が解決しようとする課題】しかしながら、上記の
ように構成された従来の生体用電極によると、紙１が伸
縮しにくいため呼吸による体面周囲長の変化に追随せ
ず、このため測定値に誤差が発生するという問題があっ
た。また、帯状電極２を構成するアルミニウムの分極電
圧も高いため、測定の信頼性が低い欠点もあった。However, according to the conventional biomedical electrode configured as described above, since the paper 1 does not easily expand and contract, it is not possible to follow the change in the body surface perimeter due to breathing. There was a problem that an error occurred. Further, since the polarization voltage of aluminum forming the strip electrode 2 is high, there is a drawback that the measurement reliability is low.
【０００５】本発明は、上記の点に鑑みてなされたもの
であり、安定した信頼性の高い呼吸循環系計測を行うこ
とのできる生体用電極を提供することを目的とする。The present invention has been made in view of the above points, and an object of the present invention is to provide a biomedical electrode capable of performing stable and highly reliable respiratory circulatory system measurement.
【０００６】[0006]
【課題を解決するための手段】即ち、本発明によれば、
生体に装着してインピーダンスを計測する帯状の生体用
電極において、帯状の布部材の長手方向に銀被覆有機繊
維あるいは銀被覆有機繊維を含有する複数種の繊維で形
成された帯状電極を設けたことを特徴とする生体用電極
が与えられる。That is, according to the present invention,
In a strip-shaped biomedical electrode that is attached to a living body to measure impedance, a silver-covered organic fiber is attached to the longitudinal direction of the strip-shaped cloth member
There is provided a biomedical electrode characterized in that a band-shaped electrode formed of a plurality of kinds of fibers containing fibers or silver-coated organic fibers is provided.
【０００７】ここに、銀被覆有機繊維とは、天然及び合
成の有機繊維、即ち、綿、麻、再生セルロース、ポリア
ミド、アクリル、ポリオレフィン、ポリエステル等の繊
維で、太さが0.1 〜15ｄ（ｄ＝デニール）のものに、銀
を被覆したものである。有機繊維の太さが、0.1 ｄより
細いと所定の膜厚を得るための銀の被覆量を多く必要と
し比重も大きくなり、また、15ｄより太いと所定の膜厚
を得るための銀の被覆量は減らせるが、繊維が硬くなり
可撓性が失われる。The term "silver coated organic fiber" as used herein means a natural or synthetic organic fiber, that is, a fiber such as cotton, hemp, regenerated cellulose, polyamide, acrylic, polyolefin or polyester, and has a thickness of 0.1 to 15 d (d = Denier) coated with silver. If the thickness of the organic fiber is smaller than 0.1 d, a large amount of silver coating is required to obtain a predetermined film thickness and the specific gravity becomes large. If the thickness is larger than 15 d, a silver coating is obtained to obtain a predetermined film thickness. The amount can be reduced, but the fibers become stiff and lose flexibility.
【０００８】本発明において、有機繊維を銀で被覆する
方法は、無電解めっき法で、そのほかの方法として真空
蒸着法等があるが、無電解めっき法が量産性に優れてい
る。銀の被覆量は、５〜50重量％（銀重量／銀被覆有機
繊維重量）で、銀の被覆量が５重量％より少ないと分極
電圧が高くなり、また、50重量％より多いと比重が大き
くなり分極電圧もそれ以上の低下が望めなくなる。In the present invention, the method of coating the organic fiber with silver is an electroless plating method, and other methods include a vacuum vapor deposition method, but the electroless plating method is excellent in mass productivity. The silver coating amount is 5 to 50% by weight (silver weight / silver coated organic fiber weight), and if the silver coating amount is less than 5% by weight, the polarization voltage becomes high, and if it is more than 50% by weight, the specific gravity becomes high. It becomes so large that the polarization voltage cannot be expected to drop further.
【０００９】銀被覆有機繊維あるいは銀被覆有機繊維を
含有する複数種の繊維で形成された帯状電極の形態とし
ては、銀被覆有機繊維のみからなる不織布、銀被覆有機
繊維を含んだ不織布、銀被覆有機繊維のみからなる糸を
織り布、編み布としたもの、銀被覆有機繊維を含んだ糸
を織り布、編み布としたもの等である。また、これらを
帯状の布部材と接合する方法としては、予め帯状電極と
し布部材に接着する方法（図１及び図２）。布部材と連
続して一体に不織布化、織り込み、編み込む方法（図
４）等が用いられる。 Silver-coated organic fibers or silver-coated organic fibers
The form of the strip-shaped electrode formed of a plurality of kinds of fibers to be contained includes a non-woven fabric made only of silver-coated organic fibers, a non-woven fabric containing silver-coated organic fibers, a woven fabric made of only silver-coated organic fibers, a knitted fabric, Woven fabrics, knitted fabrics, etc. made of yarn containing silver-coated organic fibers . As a method of joining these to a strip-shaped cloth member, a method of previously forming a strip-shaped electrode and adhering it to the cloth member (FIGS. 1 and 2). A method (FIG. 4) or the like in which a non-woven fabric, a weave, and a braid are continuously and integrally formed with the fabric member is used.
【００１０】[0010]
【作用】上記の構成によると、生体用電極の基体が布部
材で構成されているので、呼吸などによる体面周囲長さ
の変化に追従しやすく、その変化の計測値に対する影響
を少なくすることができる。また、電極として銀被覆有
機繊維を用いているので、分極電圧も低く、安定した信
頼性の高い呼吸循環系計測を行うことができる。According to the above structure, since the base body of the biomedical electrode is made of the cloth member, it is easy to follow the change in the body surface perimeter due to respiration and the effect of the change on the measured value can be reduced. it can. In addition, since the silver-coated organic fiber is used as the electrode, the polarization voltage is low, and stable and highly reliable respiratory circulatory system measurement can be performed.
【００１１】以下、本発明の実施例を図面を参照して説
明する。Embodiments of the present invention will be described below with reference to the drawings.
【００１２】[0012]
【実施例１】アクリル繊維（1.5 ｄ×38mm）に、無電解
めっき法を用いて銀を30重量％被覆した。得られた銀30
重量％被覆アクリル繊維（1.5 ｄ×38mm）を50ｇ／ｍ2
の不織布に加工し10mm幅でスリットしたものを図１及び
図２に示したように不織布に接着し生体用電極４を構成
した。図において、11は不織布、編み布等、伸縮性を有
した布部材で帯状に構成された基体を示し、12，13は銀
被覆有機繊維で形成された帯状電極を示す。得られた生
体用電極14を用いて呼吸循環系計測を行う方法を図３に
示した。１個の生体用電極14aを被検者の胸部に巻回
し、他の１個の生体用電極14b を被検者の頸部に巻回す
る。生体用電極14a 及び14b のそれぞれの帯状電極13a
，12b を電源15の両極に接続し、帯状電極13b ，12a
をインピーダンス測定器16の両極に接続する。このよう
にして帯状電極13b ，12a の間のインピーダンスを測定
器16により計測することにより被検者の呼吸循環系計測
を行った結果、基体11及び帯状電極12，13が伸縮性を有
するため、呼吸などによる被検者の体面周囲長の変化に
よる計測値の変動を少なくすることができ、連続測定が
可能であった。また、帯状電極を銀被覆有機繊維で形成
したので分極電圧が低く、安定した信頼性の高い呼吸循
環系計測を行うことができた。Example 1 An acrylic fiber (1.5 d × 38 mm) was coated with 30% by weight of silver by using an electroless plating method. Obtained silver 30
Wt% coated acrylic fiber (1.5 d × 38mm) with 50 g / m 2
The non-woven fabric was processed and slit into a width of 10 mm, and the non-woven fabric was bonded to the non-woven fabric as shown in FIGS. In the figure, reference numeral 11 denotes a strip-shaped base made of a stretchable cloth member such as non-woven fabric or knitted cloth, and 12 and 13 denote strip-shaped electrodes formed of silver-coated organic fibers. FIG. 3 shows a method for measuring the respiratory circulatory system using the obtained biomedical electrode 14. One living body electrode 14a is wound around the subject's chest, and the other one living body electrode 14b is wrapped around the subject's neck. The strip electrodes 13a of the biomedical electrodes 14a and 14b, respectively.
, 12b are connected to both poles of the power supply 15, and strip electrodes 13b, 12a
Is connected to both electrodes of the impedance measuring device 16. In this way, the impedance between the strip electrodes 13b, 12a is measured by the measuring device 16 to measure the respiratory circulatory system of the subject. As a result, the base 11 and the strip electrodes 12, 13 have elasticity, It was possible to reduce fluctuations in measured values due to changes in the body surface circumference of the subject due to breathing, etc., and continuous measurement was possible. In addition, since the strip electrodes were made of silver-coated organic fiber, the polarization voltage was low, and stable and reliable respiratory circulatory system measurement could be performed.
【００１３】[0013]
【実施例２】実施例１で得られた銀30重量％被覆アクリ
ル繊維（1.5ｄ×38mm）を銀を被覆していないアクリル
繊維（1.5 ｄ×38mm）に50重量％混合し、80ｇ／ｍ2 の
不織布に加工し10mm幅でスリットしたものを図１及び図
２に示したように不織布に接着し生体用電極を構成し
た。得られた生体用電極を用いて実施例１と同様に呼吸
循環系計測を行った結果、呼吸などによる被検者の体面
周囲長の変化による計測値の変動を少なくすることがで
き、連続測定が可能であった。また、帯状電極を銀被覆
有機繊維で形成したので分極電圧が低く、安定した信頼
性の高い呼吸循環系計測を行うことができた。Example 2 30% by weight of the silver-coated acrylic fiber (1.5 d × 38 mm) obtained in Example 1 was mixed with 50% by weight of an acrylic fiber (1.5 d × 38 mm) not coated with silver to obtain 80 g / m 2. The non-woven fabric No. 2 was processed and slit into a width of 10 mm, and the non-woven fabric was bonded to the non-woven fabric as shown in FIGS. Using the obtained biomedical electrode, the respiratory circulation system was measured in the same manner as in Example 1. As a result, it is possible to reduce fluctuations in measured values due to changes in the body surface circumference of the subject due to respiration, etc., and to perform continuous measurement. Was possible. In addition, since the strip electrodes were made of silver-coated organic fiber, the polarization voltage was low, and stable and reliable respiratory circulatory system measurement could be performed.
【００１４】[0014]
【実施例３】ポリエステル繊維（２ｄ×51mm）に、無電
解めっき法を用いて銀を20重量％被覆した。得られた銀
20重量％被覆ポリエステル繊維（２ｄ×51mm）を20番手
の糸とした後に、10mm幅で60ｇ／ｍ2 の編み布に加工し
たものを図１及び図２に示したように編み布に接着し生
体用電極を構成した。得られた生体用電極を用いて実施
例１と同様に呼吸循環系計測を行った結果、呼吸などに
よる被検者の体面周囲長の変化による計測値の変動を少
なくすることができ、連続測定が可能であった。また、
帯状電極を銀被覆有機繊維で形成したので分極電圧が低
く、安定した信頼性の高い呼吸循環系計測を行うことが
できた。Example 3 Polyester fiber (2d × 51 mm) was coated with 20% by weight of silver by using an electroless plating method. Obtained silver
20% by weight coated polyester fiber (2d x 51mm) was made into 20th count yarn and processed into a knitted fabric with a width of 10mm and a weight of 60g / m 2 and glued to the knitted fabric as shown in Figs. A biomedical electrode was constructed. As a result of performing respiratory circulatory system measurement in the same manner as in Example 1 using the obtained biomedical electrode, it is possible to reduce fluctuations in measured values due to changes in the body surface perimeter of the subject due to respiration, etc., and perform continuous measurement. Was possible. Also,
Since the strip electrodes were made of silver-coated organic fiber, the polarization voltage was low, and stable and reliable respiratory circulatory system measurement could be performed.
【００１５】[0015]
【実施例４】実施例３で得られた銀20重量％被覆ポリエ
ステル繊維（２ｄ×51mm）を銀を被覆していないポリエ
ステル繊維（２ｄ×51mm）に40重量％混合し、20番手の
糸とした後に、80ｇ／ｍ2 の織り布に加工したものを10
mm幅でバイアスカットし図１及び図２に示したように編
み布に接着し生体用電極を構成した。得られた生体用電
極を用いて実施例１と同様に呼吸循環系計測を行った結
果、呼吸などによる被検者の体面周囲長の変化による計
測値の変動を少なくすることができ、連続測定が可能で
あった。また、帯状電極を銀被覆有機繊維で形成したの
で分極電圧が低く、安定した信頼性の高い呼吸循環系計
測を行うことができた。Example 4 40% by weight of 20% by weight silver-covered polyester fiber (2d × 51 mm) obtained in Example 3 was mixed with silver-uncoated polyester fiber (2d × 51 mm) to obtain a 20th yarn. And then processed into 80g / m 2 woven cloth for 10
Bias cut was performed with a width of mm, and as shown in FIGS. 1 and 2, it was adhered to a knitted cloth to form a biomedical electrode. As a result of performing respiratory circulatory system measurement in the same manner as in Example 1 using the obtained biomedical electrode, it is possible to reduce fluctuations in measured values due to changes in the body surface perimeter of the subject due to respiration, etc., and perform continuous measurement. Was possible. In addition, since the strip electrodes were made of silver-coated organic fiber, the polarization voltage was low, and stable and reliable respiratory circulatory system measurement could be performed.
【００１６】[0016]
【実施例５】アラミド繊維（３ｄ×51mm）に、無電解め
っき法を用いて銀を20重量％被覆した。得られた銀20重
量％被覆アラミド繊維（３ｄ×51mm）を銀を被覆してい
ないアラミド繊維（３ｄ×51mm）と交互に連続使用して
不織布加工を行い、図４に示した布部材、電極一体構造
の100 ｇ／ｍ2 の生体用電極を構成した。得られた生体
用電極を用いて実施例１と同様に呼吸循環系計測を行っ
た結果、呼吸などによる被検者の体面周囲長の変化によ
る計測値の変動を少なくすることができ、連続測定が可
能であった。また、帯状電極を銀被覆有機繊維で形成し
たので分極電圧が低く、安定した信頼性の高い呼吸循環
系計測を行うことができた。Example 5 Aramid fiber (3d × 51 mm) was coated with 20% by weight of silver by using an electroless plating method. The obtained 20% by weight silver-covered aramid fiber (3d × 51 mm) and aramid fiber not coated with silver (3d × 51 mm) were continuously used alternately to fabricate a nonwoven fabric, and the cloth member and electrode shown in FIG. A 100 g / m 2 biomedical electrode having an integral structure was constructed. As a result of performing respiratory circulatory system measurement in the same manner as in Example 1 using the obtained biomedical electrode, it is possible to reduce fluctuations in measured values due to changes in the body surface perimeter of the subject due to respiration, etc., and perform continuous measurement. Was possible. In addition, since the strip electrodes were made of silver-coated organic fiber, the polarization voltage was low, and stable and reliable respiratory circulatory system measurement could be performed.
【００１７】[0017]
【比較例１】図５に示した従来の紙を基体としアルミニ
ウムを帯状電極とした生体用電極を用いて実施例１と同
様に呼吸循環系計測を行った結果、被検者の呼吸などに
よる体面周囲長の変化に伴って計測値が変動したため連
続測定が困難であった。また、分極電圧が高いため安定
した呼吸循環系計測を行うことができなかった。[Comparative Example 1] The respiratory circulation system was measured in the same manner as in Example 1 using the conventional biomedical electrode made of aluminum and the strip electrode as shown in FIG. It was difficult to measure continuously because the measured values fluctuated with the change of the perimeter of the body surface. In addition, stable polarization measurement could not be performed because of high polarization voltage.
【００１８】[0018]
【発明の効果】以上説明したように、本発明によれば、
生体用電極を帯状の布部材の長手方向に銀被覆有機繊維
で形成された帯状電極を設けて構成したので、被検者の
体面周囲長の変化による計測値への変動を少なくするこ
とができ、安定した連続測定が可能となる。また、電極
の分極電圧が低く、安定した信頼性の高い呼吸循環系計
測を行うことができる。As described above, according to the present invention,
Since the biological electrode is configured by providing a strip-shaped electrode formed of silver-coated organic fiber in the longitudinal direction of the strip-shaped cloth member, it is possible to reduce fluctuations in the measured values due to changes in the body surface perimeter of the subject. It enables stable and continuous measurement. In addition, the polarization voltage of the electrodes is low, and stable and highly reliable respiratory circulatory system measurement can be performed.
【図１】本発明の生体用電極の一実施例の構成を示す平
面図。FIG. 1 is a plan view showing the configuration of an embodiment of a biomedical electrode of the present invention.
【図２】図１の側面図。FIG. 2 is a side view of FIG.
【図３】図１に示す生体用電極を用いて呼吸計測を行な
う方法を示す説明図。FIG. 3 is an explanatory diagram showing a method of performing respiration measurement using the biomedical electrode shown in FIG.
【図４】本発明の他の実施例の構成を示す側面図。FIG. 4 is a side view showing the configuration of another embodiment of the present invention.
【図５】従来の生体用電極の一例の構成を示す説明図。FIG. 5 is an explanatory diagram showing a configuration of an example of a conventional biomedical electrode.
１１…基体（布部材） 11 ... Base (cloth member)
───────────────────────────────────────────────────── フロントページの続き (72)発明者 今井 浩之 埼玉県大宮市北袋町１丁目297番地 三菱 マテリアル株式会社 新素材開発センター 内 (56)参考文献 特開 昭61−8027（ＪＰ，Ａ) 特開 平２−142534（ＪＰ，Ａ) 特開 昭49−52488（ＪＰ，Ａ) ─────────────────────────────────────────────────── ─── Continuation of the front page (72) Inventor Hiroyuki Imai 1-297 Kitabukuro-cho, Omiya City, Saitama Mitsubishi Materials Corporation New Material Development Center (56) Reference Japanese Patent Laid-Open No. 61-8027 (JP, A) Special Features Kaihei 2-142534 (JP, A) JP-A-49-52488 (JP, A)
Claims (5)
帯状の生体用電極において、帯状の布部材の長手方向に
銀被覆有機繊維あるいは銀被覆有機繊維を含有する複数
種の繊維によって形成された帯状電極を設けたことを特
徴とする生体用電極。1. A strip-shaped electrode for a living body, which is mounted on a living body to measure impedance, in a longitudinal direction of a strip-shaped cloth member.
Silver-coated organic fibers or a plurality containing silver-coated organic fibers
A biomedical electrode, characterized in that a band-shaped electrode formed of seed fibers is provided.
あるいは銀被覆有機繊維を含有する複数種の繊維によっ
て形成された帯状電極が布部材と連続して不織布加工、
織り加工あるいは編み加工により一体化されたことを特
徴とする請求項１に記載の生体用電極。2. A silver-coated organic fiber on a portion of a strip-shaped cloth member.
Or by multiple types of fibers containing silver coated organic fibers
The strip-shaped electrode formed by continuous processing with the cloth member is a non-woven fabric,
The biomedical electrode according to claim 1, wherein the biomedical electrode is integrated by weaving or knitting.
ール) であることを特徴とする請求項１又は請求項２に
記載の生体用電極。3. The biomedical electrode according to claim 1, wherein the thickness of the silver-coated organic fiber is 0.1 to 15 d (d = denier).
であることを特徴とする請求項１又は請求項２に記載の
生体用電極。。4. The silver coated amount of the silver coated organic fiber is 5 to 50% by weight.
The biomedical electrode according to claim 1 or 2, wherein .
の間のインピーダンスを計測する呼吸循環系計測に用い
られる請求項１又は請求項２に記載の生体用電極。5. The biomedical electrode according to claim 1 or 2, which is wound around a chest and a neck of a living body and is used for respiratory circulatory system measurement for measuring impedance therebetween.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP3326640A JPH088910B2 (en) | 1991-11-15 | 1991-11-15 | Biomedical electrode |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP3326640A JPH088910B2 (en) | 1991-11-15 | 1991-11-15 | Biomedical electrode |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| JPH05137699A JPH05137699A (en) | 1993-06-01 |
| JPH088910B2 true JPH088910B2 (en) | 1996-01-31 |
Family
ID=18190045
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| JP3326640A Expired - Lifetime JPH088910B2 (en) | 1991-11-15 | 1991-11-15 | Biomedical electrode |
Country Status (1)
| Country | Link |
|---|---|
| JP (1) | JPH088910B2 (en) |
Cited By (1)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JPH0647012A (en) * | 1992-07-30 | 1994-02-22 | Kanai Hiroyuki | Bioelectrode |
Families Citing this family (6)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| DE69727986T2 (en) * | 1997-11-26 | 2005-01-05 | E-Z-Em, Inc. | DETECTION OF EXTRAS |
| JP2000000221A (en) * | 1998-06-15 | 2000-01-07 | Gunze Ltd | Sheet for electrode |
| JP3711236B2 (en) * | 2000-11-24 | 2005-11-02 | フクダ電子株式会社 | Bioelectric signal induction sensor and bioelectric signal recording system |
| DE102013108810A1 (en) * | 2013-08-14 | 2015-02-19 | Capical Gmbh | Textile capacitive electrode, process for its preparation and use |
| US11723573B2 (en) | 2017-01-25 | 2023-08-15 | National Institute Of Advanced Industrial Science And Technology | Stretchable raised electrode and method of manufacturing thereof |
| JP7315346B2 (en) * | 2019-03-15 | 2023-07-26 | 帝人フロンティア株式会社 | Sheet electrodes and clothing |
Family Cites Families (3)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| IT991982B (en) * | 1972-07-24 | 1975-08-30 | Medical Plstic Inc | IMPROVEMENT IN ELECTRODES FOR THE DETECTION OF BIOELECTRIC SIGNALS |
| JPS618027A (en) * | 1984-06-22 | 1986-01-14 | 株式会社 八木商店 | Electrode for being mounted to human body |
| JP2691358B2 (en) * | 1988-11-22 | 1997-12-17 | ジーイー横河メディカルシステム株式会社 | Biological signal acquisition and transmission device |
-
1991
- 1991-11-15 JP JP3326640A patent/JPH088910B2/en not_active Expired - Lifetime
Cited By (1)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JPH0647012A (en) * | 1992-07-30 | 1994-02-22 | Kanai Hiroyuki | Bioelectrode |
Also Published As
| Publication number | Publication date |
|---|---|
| JPH05137699A (en) | 1993-06-01 |
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