JPH052163Y2 - - Google Patents
Info
- Publication number
- JPH052163Y2 JPH052163Y2 JP1988131106U JP13110688U JPH052163Y2 JP H052163 Y2 JPH052163 Y2 JP H052163Y2 JP 1988131106 U JP1988131106 U JP 1988131106U JP 13110688 U JP13110688 U JP 13110688U JP H052163 Y2 JPH052163 Y2 JP H052163Y2
- Authority
- JP
- Japan
- Prior art keywords
- electrode
- conductive layer
- circuit
- base material
- silver conductive
- 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
- 239000000853 adhesive Substances 0.000 claims description 30
- 230000001070 adhesive effect Effects 0.000 claims description 30
- BQCADISMDOOEFD-UHFFFAOYSA-N Silver Chemical compound [Ag] BQCADISMDOOEFD-UHFFFAOYSA-N 0.000 claims description 28
- 239000000463 material Substances 0.000 claims description 28
- 229910052709 silver Inorganic materials 0.000 claims description 28
- 239000004332 silver Substances 0.000 claims description 28
- 229920001296 polysiloxane Polymers 0.000 claims description 15
- 239000011248 coating agent Substances 0.000 claims description 5
- 238000007639 printing Methods 0.000 claims description 3
- 239000000499 gel Substances 0.000 description 17
- WABPQHHGFIMREM-UHFFFAOYSA-N lead(0) Chemical compound [Pb] WABPQHHGFIMREM-UHFFFAOYSA-N 0.000 description 8
- XLYOFNOQVPJJNP-UHFFFAOYSA-N water Substances O XLYOFNOQVPJJNP-UHFFFAOYSA-N 0.000 description 5
- 238000000576 coating method Methods 0.000 description 4
- 230000000694 effects Effects 0.000 description 4
- 230000002028 premature Effects 0.000 description 4
- 206010040914 Skin reaction Diseases 0.000 description 3
- 230000008878 coupling Effects 0.000 description 3
- 238000010168 coupling process Methods 0.000 description 3
- 238000005859 coupling reaction Methods 0.000 description 3
- 239000003792 electrolyte Substances 0.000 description 3
- 239000000017 hydrogel Substances 0.000 description 3
- 238000009413 insulation Methods 0.000 description 3
- 238000012544 monitoring process Methods 0.000 description 3
- 229910052710 silicon Inorganic materials 0.000 description 3
- 239000010703 silicon Substances 0.000 description 3
- 230000035483 skin reaction Effects 0.000 description 3
- 231100000430 skin reaction Toxicity 0.000 description 3
- 206010036590 Premature baby Diseases 0.000 description 2
- 238000010586 diagram Methods 0.000 description 2
- 210000002216 heart Anatomy 0.000 description 2
- 238000004519 manufacturing process Methods 0.000 description 2
- 239000004745 nonwoven fabric Substances 0.000 description 2
- 230000037307 sensitive skin Effects 0.000 description 2
- 239000013464 silicone adhesive Substances 0.000 description 2
- HKZLPVFGJNLROG-UHFFFAOYSA-M silver monochloride Chemical compound [Cl-].[Ag+] HKZLPVFGJNLROG-UHFFFAOYSA-M 0.000 description 2
- 239000000758 substrate Substances 0.000 description 2
- OKTJSMMVPCPJKN-UHFFFAOYSA-N Carbon Chemical compound [C] OKTJSMMVPCPJKN-UHFFFAOYSA-N 0.000 description 1
- 239000012752 auxiliary agent Substances 0.000 description 1
- 230000015572 biosynthetic process Effects 0.000 description 1
- 210000004556 brain Anatomy 0.000 description 1
- 229910052799 carbon Inorganic materials 0.000 description 1
- 230000000747 cardiac effect Effects 0.000 description 1
- 239000004020 conductor Substances 0.000 description 1
- 238000005516 engineering process Methods 0.000 description 1
- 229910052751 metal Inorganic materials 0.000 description 1
- 239000002184 metal Substances 0.000 description 1
- 210000003205 muscle Anatomy 0.000 description 1
- 230000005855 radiation Effects 0.000 description 1
- 238000007789 sealing Methods 0.000 description 1
- 239000004447 silicone coating Substances 0.000 description 1
- 239000000126 substance Substances 0.000 description 1
Description
【考案の詳細な説明】
〔産業上の利用分野〕
本考案は生体用電極に関し、より詳しくは生体
の皮膚面に密着させることにより、生体内に発生
する微弱な生体電気の電気信号を外部に導出す
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, and more specifically, it is a device that transmits weak bioelectrical electrical signals generated within the living body to the outside by closely contacting the skin surface of the living body. The present invention relates to a biological electrode to be derived.
従来、一般によく知られているように、生体に
発生する生体電気は、心臓、脳、筋肉などの活動
によつて誘起されている。
BACKGROUND ART As is generally well known, bioelectricity generated in a living body is induced by the activities of the heart, brain, muscles, and the like.
特に心臓の活動によつて誘起され、皮膚面に誘
導された微弱な生体電気の電気信号は、外部の心
電計で心電図としてその波形を記録されることに
より、心臓の診断に供されている。 In particular, the weak bioelectric electrical signals induced by cardiac activity and guided to the skin surface are used to diagnose the heart by recording their waveforms as an electrocardiogram using an external electrocardiograph. .
そしてこの心電計は、人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電極を
密着させなければならない。 In this electrocardiograph, in order to electrically connect the human power section to the living body, the living body electrodes must be brought into close contact with the skin surface of the living body.
この皮膚面に密着させる従来の生体用電極１１
は、第８図に示すように粘着基材１２の下部表面
１２ａを皮膚面に密着させるため粘着性を帯びさ
せるとともに、その中央部が切欠されて開口１３
が形成されている。 Conventional biological electrode 11 that is brought into close contact with this skin surface
As shown in FIG. 8, the lower surface 12a of the adhesive base material 12 is made sticky in order to adhere to the skin surface, and the center portion thereof is cut out to form an opening 13.
is formed.
この粘着基材１２の上面側には、第９図に示す
ようにリード線接続ホツク１４が接合され、前記
開口１３を閉塞している。 As shown in FIG. 9, a lead wire connection hook 14 is bonded to the upper surface side of this adhesive base material 12 to close the opening 13. As shown in FIG.
このリード線接続ホツク１４は、上部にリード
線結合部１４ａが突設し、下部には銀一塩化銀
（Ag−Agcl）製の板状の電極部１５（第１０図）
が接続されている。 This lead wire connection hook 14 has a lead wire coupling part 14a protruding from the upper part, and a plate-shaped electrode part 15 made of silver monochloride (Ag-Agcl) at the lower part (FIG. 10).
is connected.
前記突設したリード線結合部１４ａは、第１０
図に示すように、リード線１６が接続されている
リード線接続体１７が挟持穴１７ａによつて挟持
連結され、そのリード線１６の他端は図示しない
心電計に接続される。 The protruding lead wire coupling portion 14a has a tenth
As shown in the figure, a lead wire connector 17 to which a lead wire 16 is connected is clamped and connected through a clamping hole 17a, and the other end of the lead wire 16 is connected to an electrocardiograph (not shown).
しかし、前記従来例の場合、リード線結合部１
４ａが突設されているので、装着のまま体を動か
すと皮膚面Ｍを傷める危険性がり、したがつて長
時間装着を必要とするモニター用には適さないと
いう課題があつた。
However, in the case of the conventional example, the lead wire coupling portion 1
Since 4a is protruded, there is a risk of damaging the skin surface M if you move your body while wearing it, so there is a problem that it is not suitable for use as a monitor that requires wearing it for a long time.
また、電極部１５は銀一塩化銀の板でできてい
るため重く、装着した皮膚面からずれ易いという
課題があつた。 Furthermore, since the electrode section 15 is made of a plate of silver monochloride, it is heavy and tends to easily slip off the skin surface on which it is attached.
さらに、重い電極部１５を皮膚面Ｍに安定させ
るため、粘着基材の粘着面積を大きくしなければ
ならず、電極部が大きくなり体の小さい未熟児、
幼児、小児用などには適さないという課題があつ
た。 Furthermore, in order to stabilize the heavy electrode part 15 on the skin surface M, the adhesive area of the adhesive base material must be increased, and the electrode part becomes large and small premature infants,
There was a problem that it was not suitable for infants and children.
加えて、リード線１６が個別に独立のため、複
数の電極部１５を取り付ける場合、操作が煩雑で
誤操作の原因となり、操作性が悪いなどの課題が
あつた。 In addition, since the lead wires 16 are individually independent, when attaching a plurality of electrode sections 15, there are problems such as complicated operation, causing erroneous operation, and poor operability.
その上電極、リード線が金属のため心電図モニ
ター時のレントゲン撮影に電極の陰影が現れ、不
都合であつた。 Furthermore, since the electrodes and lead wires are metal, shadows from the electrodes appear on X-ray images taken during electrocardiogram monitoring, which is inconvenient.
本考案はこのような課題を解決することを目的
とする。 The present invention aims to solve such problems.
上記目的を達成するため、本考案は次のような
生体用電極を提供する。すなわち本考案は、
(1) 複数の電極部と回路部とコネクタとを有し生
体内から微弱な電気信号を導出する生体用電極
であつて、前記電極部は貼着基材に印刷され前
記生体内から微弱な電気信号を導出するための
網目状銀導電層と、この網目状銀導電層と接し
生体の皮膚面に当接する含水性ゲルと、前記貼
着基材と前記網目状銀導電層とを被覆している
シリコン等被覆材と前記含水ゲルの周囲を囲繞
している絶縁性のシリコン等の粘着剤とからな
り、前記回路部は前記粘着基材に印刷形成され
た網目状銀導電層と線状銀導電層とからなる複
数の回路を有し、前記貼着基材と前記複数の回
路はシリコン等被覆材で覆われ、前記網目状銀
導電層は前記電極部近傍の回路を、前記線状銀
導電層は前記電極部近傍以外の回路をそれぞれ
形成し、前記回路部は幹状部と複数に分岐した
枝状部とからなり、この複数の枝状部は各先端
部にそれぞれ前記電極部を接続するとともに、
前記コネクタは前記回路部の幹状部の一端に接
続され、同コネクタの複数の端子は前記複数の
電極の配列と同一配列としたことを特徴する、
生体用電極。
In order to achieve the above object, the present invention provides the following biological electrode. That is, the present invention provides: (1) an electrode for living body that has a plurality of electrode parts, a circuit part, and a connector and derives a weak electrical signal from within a living body, wherein the electrode part is printed on an adhesive base material; a mesh-like silver conductive layer for deriving a weak electrical signal from within a living body; a hydrous gel that is in contact with the mesh-like silver conductive layer and in contact with the skin surface of the living body; the adhesive base material; and the mesh-like silver conductive layer. The circuit portion is made of a coating material such as silicon that covers the hydrogel and an adhesive such as insulating silicon that surrounds the hydrogel, and the circuit portion is formed of a silver mesh printed on the adhesive base material. It has a plurality of circuits consisting of a conductive layer and a linear silver conductive layer, the adhesive base material and the plurality of circuits are covered with a covering material such as silicone, and the mesh silver conductive layer is a circuit in the vicinity of the electrode portion. The linear silver conductive layer forms a circuit other than the vicinity of the electrode part, and the circuit part consists of a trunk part and a branch part branched into a plurality of parts, and the plurality of branch parts are connected to each tip part. Connecting the electrode portions to the respective electrodes,
The connector is connected to one end of the trunk portion of the circuit portion, and the plurality of terminals of the connector are arranged in the same arrangement as the plurality of electrodes.
Biological electrode.
(2) 前記複数の電極部数は３個である、請求項１
の生体用電極。(2) Claim 1, wherein the number of the plurality of electrode parts is three.
biological electrodes.
(3) 前記複数の電極部数は６個である、請求項１
の生体用電極、
である。(3) The number of the plurality of electrodes is six, as claimed in claim 1.
This is a bioelectrode.
上記構成において、本考案の電極部を皮膚面に
当接すると皮膚面と電極部は電解物質である含水
性ゲルによつて接触抵抗を減じ、生体内の微弱電
圧を取り出し易い状態になる。
In the above configuration, when the electrode part of the present invention is brought into contact with the skin surface, the contact resistance between the skin surface and the electrode part is reduced by the electrolyte, ie, the hydrous gel, and the weak voltage inside the living body becomes easily extracted.
また、絶縁性のシリコン等粘着剤は、絶縁性を
保ちつつ電極部を皮膚面に粘着して保持する。 In addition, an insulating adhesive such as silicone adheres and holds the electrode portion to the skin surface while maintaining insulation properties.
シリコン等被覆材は前記含水ゲル以外の部分を
絶縁して電気的外乱を防ぐとともに耐水性を有す
る。 The coating material, such as silicone, insulates the portion other than the hydrous gel to prevent electrical disturbances and has water resistance.
網目状銀導電層はその網目からレントゲン線を
透過する。 The networked silver conductive layer transmits X-ray radiation through its network.
回路部の各回路は、各電極部で導出した生体の
微弱電圧を前記電極部配列と同じ配列のコネクタ
の各端子に伝達する。 Each circuit of the circuit section transmits the weak voltage of the living body derived from each electrode section to each terminal of the connector having the same arrangement as the electrode section arrangement.
回路部の枝状部は独立させ、その先端にそれぞ
れ電極部を取り付けてあるので電極間相互の間隔
は可変である。 Since the branch parts of the circuit part are made independent and have electrode parts attached to their tips, the mutual spacing between the electrodes is variable.
実施例１について、以下図面にしたがつて本考
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。第１図は本考案の一実
施例の平面説明図で、一部切欠したものである。
Regarding Embodiment 1, how the configuration of the present invention is actually implemented will be explained below with reference to the drawings, along with its operation. FIG. 1 is an explanatory plan view of one embodiment of the present invention, with a portion cut away.
図中、１は電極部で、この電極部１は生体皮膚
面に密着して生体内に発生する微弱な電気信号を
体外に導出するものである。 In the figure, reference numeral 1 denotes an electrode section, and this electrode section 1 is in close contact with the skin surface of a living body to lead out a weak electrical signal generated within the living body to the outside of the body.
前記電極部１には回路部２が一体形成されてい
る。 A circuit section 2 is integrally formed with the electrode section 1 .
この回路部２は、複数の回路２ａを帯状の平面
上に集束させた幹状部２ｂと、１回路ごとに分岐
独立させた複数の枝状部２ｃとに大別される。 The circuit section 2 is roughly divided into a trunk section 2b in which a plurality of circuits 2a are converged on a band-shaped plane, and a plurality of branch sections 2c in which each circuit is branched independently.
そして前記電極部１は、前記回路部２の枝状部
２ｃの先端に取り付けられる。 The electrode portion 1 is attached to the tip of the branch portion 2c of the circuit portion 2.
また、回路部２の幹状部の一端には、外部心電
計などの測定器と接続するためのコネクタ３が設
けられ、そのコネクタ３内の複数の端子３ａは前
記電極部１の配列順序と同一の配列とすることに
よつて、電極部装着位置と測定器との対応を正確
に、かつ、迅速に行うことができる。 Further, a connector 3 for connecting to a measuring device such as an external electrocardiograph is provided at one end of the trunk portion of the circuit portion 2, and a plurality of terminals 3a in the connector 3 are arranged in the order in which the electrode portion 1 is arranged. By using the same arrangement, it is possible to accurately and quickly match the electrode mounting position and the measuring instrument.
第２図〜第７図は同実施例の構成の分解説明図
であり、まず、第２図は不織布による貼着基材４
を示し、この貼着基材４の一端にはコネクタ３用
の基板であるフイルム３ｂが接着により取り付け
られている。 2 to 7 are exploded explanatory views of the configuration of the same embodiment. First, FIG. 2 shows the adhesive base material 4 made of nonwoven fabric.
A film 3b, which is a substrate for the connector 3, is attached to one end of the adhesive base material 4 by adhesive.
つぎに、第３図の５は網目状銀導電層で、この
網目状銀導電層５は前記貼着基材４の電極部１お
よびその電極部近傍の回路部２の１部に印刷され
る。 Next, 5 in FIG. 3 is a mesh-like silver conductive layer, and this mesh-like silver conductive layer 5 is printed on the electrode part 1 of the adhesive base material 4 and a part of the circuit part 2 in the vicinity of the electrode part. .
同網目状銀導電層５は、銀の網目からレントゲ
ン線を透過させるように構成され、患者に本考案
の電極部を装着のまま、レントゲン撮影ができる
ようになつている。 The mesh-like silver conductive layer 5 is configured to allow X-ray rays to pass through the silver mesh, so that X-ray photography can be performed while the electrode unit of the present invention is attached to the patient.
第３図の６はカーボンで、このカーボン６は電
気の良導体であり、回路部２の回路２ａおよびコ
ネクター３の端子３ａを形成する。 Reference numeral 6 in FIG. 3 is carbon, which is a good electrical conductor and forms the circuit 2a of the circuit section 2 and the terminal 3a of the connector 3.
第４図は粘着基材４と網目状銀導電層５と線状
銀導電層６とを絶縁性のシリコン等被覆材７で覆
つた状態を示している。 FIG. 4 shows a state in which the adhesive base material 4, the mesh silver conductive layer 5, and the linear silver conductive layer 6 are covered with an insulating covering material 7 such as silicon.
これは生体用電極を外部と電気的に絶縁し、無
用な電気的外乱を排除して、生体から導出した微
弱な電気信号の波形を忠実に心電計などの測定器
に伝達するための絶縁被覆であるとともに、生体
用電極の耐水性を高めるものである。 This insulation electrically insulates biological electrodes from the outside, eliminates unnecessary electrical disturbances, and faithfully transmits the waveforms of weak electrical signals derived from living organisms to measuring instruments such as electrocardiographs. It not only serves as a coating but also enhances the water resistance of the biological electrode.
なお、この場合、電極部１の一部は網目状銀導
電層５を絶縁被覆せずに空けておく。 In this case, a part of the electrode section 1 is left open without the mesh-shaped silver conductive layer 5 being insulated.
つぎに第５図は、導電性の含水性ゲル８を前記
電極部１の一部の前記被覆せずに空けておいたと
ころへ貼着し、その周囲を囲むように絶縁性のシ
リコン等粘着材であるシリコンゲル９を、電極部
１の前記シリコン等被覆材７に貼着してなる図で
ある。 Next, in FIG. 5, a conductive water-containing gel 8 is pasted on a part of the electrode part 1 that is left uncovered, and an insulating adhesive such as silicone is applied so as to surround it. 2 is a diagram in which silicone gel 9, which is a material, is adhered to the covering material 7, such as silicone, of the electrode section 1. FIG.
このシリコンゲル９は、その強い粘着性により
電極部１を皮膚面に粘着保持させるためのもので
ある。 This silicone gel 9 is used to adhesively hold the electrode portion 1 on the skin surface due to its strong adhesiveness.
前記シリコンゲル９は皮膚反応が少ないので、
長時間皮膚面に粘着させても皮膚面を傷めること
がなく、皮膚の弱い未熟児、幼児にもモニター用
として使用することができる。 Since the silicone gel 9 has little skin reaction,
It does not damage the skin surface even if it is left on the skin for a long period of time, and can be used as a monitor for premature infants and infants who have sensitive skin.
また、前記含水ゲル８は電解物質による電極補
助部材であり、生体の皮膚面に当接してその保水
性により長時間にわたり接触抵抗を減じ、生体内
から微弱な電気信号を効率よく導出して前記網目
状銀導電層５に伝える。 In addition, the hydrogel 8 is an electrode auxiliary member made of an electrolytic substance, and when it comes into contact with the skin surface of a living body, its water retention property reduces contact resistance for a long time, and efficiently derives weak electrical signals from within the living body. The information is transmitted to the reticulated silver conductive layer 5.
第６図は含水性ゲル８を含む電極部１の表面を
剥離フイルムで覆つた図で、通常、使用前はこの
ようにして粘着面を空気と遮断することによつ
て、電解物質よりなる含水性ゲル８の保水性を維
持することによる導電性と粘着性、シリコンゲル
９の粘着性と絶縁性を保護するとともに、その電
極部１の扱いを容易にし、使用時にこの剥離フイ
ルムを剥がして用いることによつて、前記粘着機
能などを長時間保持し、生体用電極の商品価値を
高めようとするものである。 FIG. 6 shows the surface of the electrode part 1 containing the hydrous gel 8 covered with a release film. Normally, before use, by sealing off the adhesive surface from air in this way, the electrolyte containing the hydrous gel 8 is covered with a release film. In addition to protecting the conductivity and adhesiveness by maintaining the water retention properties of the silicone gel 8 and the adhesiveness and insulation properties of the silicone gel 9, it also facilitates handling of the electrode portion 1, and the release film is peeled off when used. In particular, the purpose is to maintain the adhesive function for a long time and increase the commercial value of the biological electrode.
第７図は本考案の他の実施例を示す平面説明図
であり、この実施例が前記一実施例と異なる点
は、電極部１の数が、前記一実施例では３個であ
つたのに対し、この実施例では６個となつている
点である。 FIG. 7 is an explanatory plan view showing another embodiment of the present invention, and this embodiment differs from the previous embodiment in that the number of electrode parts 1 is three in the previous embodiment. In contrast, in this embodiment, there are six.
これは、前記一実施例では、未熟児、幼児など
において、必要な個所についてのみ長時間モニタ
ーしたい場所に便利なように構成されているもの
である。 In the above-mentioned embodiment, this is configured to be convenient in a place where it is desired to monitor only necessary parts for a long time in premature babies, infants, etc.
これに対して本実施例で電極部を６個としたの
は、胸部用電極は、心電図をとるとき、胸部皮膚
面上の定められた６点の位置（図示せず）に６個
の電極部１を取り付ける必要があるからである。 On the other hand, the reason why the number of electrode parts in this embodiment is six is that when taking an electrocardiogram, six electrodes are placed at six predetermined positions (not shown) on the chest skin surface. This is because it is necessary to attach part 1.
以上実施例について説明したように、本考案は
複数の電極部と回路部とコネクタとを有し、粘着
基材に網目状銀導電層と線状銀導電層を印刷して
回路を構成し、電極部においては網目状銀導電層
に含水性ゲルを補助剤として用いることによつて
導電性の向上と安定、軽量化を図り、かつ皮膚反
応の少ないシリコン製の粘着剤で電極部を長時間
にわたり、皮膚面に確実に粘着させることができ
るものである。 As described above in the embodiments, the present invention has a plurality of electrode parts, circuit parts, and connectors, and a circuit is constructed by printing a mesh silver conductive layer and a linear silver conductive layer on an adhesive base material. In the electrode part, a water-containing gel is used as an auxiliary agent in the mesh silver conductive layer to improve conductivity, stabilize it, and make it lighter in weight.A silicone adhesive that causes little skin reaction is used to keep the electrode part in place for a long time. It can be reliably adhered to the skin surface.
また、回路部は幹状部と枝状部とにより構成し
幹状部ては複数の回路を集約して扱いを容易に
し、枝状部では先端の電極部間の間隔調整を可能
とさせ、不特定の患者の体格への適応性を広めた
ものである。 In addition, the circuit portion is composed of a trunk portion and a branch portion, and the trunk portion consolidates multiple circuits to facilitate handling, and the branch portion allows adjustment of the spacing between the electrode portions at the tip. It is widely adaptable to unspecified patient physiques.
さらに、枝分かれした複数の電極部の配列順位
とコネクタの端子配列順位とを同一に揃え、電極
部装着作業が正確、かつ迅速にできるようにした
ものである。 Furthermore, the order of arrangement of the plurality of branched electrode parts and the arrangement order of the terminals of the connector are made the same, so that the electrode part attachment work can be performed accurately and quickly.
以上、本考案によれば、電極部は貼着基材と網
目状銀導電層と含水ゲルとシリコン等被覆材とシ
リコン等粘着材で構成したので軽量とすることが
でき、皮膚面に粘着した場合ずれ落ちる心配はな
く長時間安定保持できるのでモニター用に適す
る。
As described above, according to the present invention, the electrode part is composed of an adhesive base material, a mesh silver conductive layer, a hydrous gel, a coating material such as silicone, and an adhesive material such as silicone, so it is lightweight and does not adhere to the skin surface. It is suitable for monitor use because it can be held stably for a long time without worrying about it falling off.
また、電極部は軽量のため、粘着面が小さくて
もよく、したがつて小型化でき、未熟児や幼児な
どにも適する。 In addition, since the electrode part is lightweight, the adhesive surface may be small, so it can be miniaturized and is suitable for premature infants and infants.
さらに、電極部と回路部とは同一の貼着基材に
一体的に印刷形成したので、ホツクなどの突起物
が無くなり、皮膚を傷めるおそれが無くなつた。 Furthermore, since the electrode part and the circuit part are integrally printed on the same adhesive base material, there are no protrusions such as hooks, and there is no risk of damaging the skin.
また、そのため長時間装着によるモニター用に
も適し、その他接続クリツプが不要となり扱い易
くなつた上、接続品質が向上した。 This also makes it suitable for monitoring when worn for long periods of time, making it easier to handle as no other connection clips are required, and improving connection quality.
加えて、前記一体形成は大量生産に適するか
ら、生産コストを下げることができる。 In addition, since the integral formation is suitable for mass production, production costs can be reduced.
その上、電極部は網目状銀導電層に電解物質の
含水性ゲルを装着したので、その保水性により長
時間皮膚面との接触抵抗を減じ、生体の微弱な電
気信号を効率よく外部に導出することができる。 In addition, the electrode part has a water-containing electrolyte gel attached to the mesh-like silver conductive layer, so its water retention property reduces contact resistance with the skin surface for a long time, and efficiently guides weak electrical signals from the living body to the outside. can do.
また、電極部の粘着剤は皮膚反応の少ないシリ
コンゲルを用いたので、皮膚の弱い未熟児や幼児
でも、長時間モニターが可能となつた。 In addition, because the adhesive used in the electrode part is silicone gel, which causes little skin reaction, even premature infants and young children with sensitive skin can be monitored for long periods of time.
また、電極部と電極部近傍の回路は網目状銀導
電層としたので、その網目からレントゲン線を透
過でき、電極を装着のままレントゲン撮影が可能
となつた。 In addition, since the electrode portion and the circuit near the electrode portion are made of a mesh-like silver conductive layer, X-ray rays can pass through the mesh, making it possible to take X-ray images with the electrode attached.
その上、回路部の幹状部は複数の回路を集約し
て印刷したので扱い易くなつた。 Furthermore, the main part of the circuit section was printed with multiple circuits consolidated, making it easier to handle.
また、回路部の枝状部は分岐独立させ、その先
端に電極部をそれぞれ取り付けたので、各電極部
相互の間隔が可変となり、患者の体格、形状に柔
軟に対応して電極部を装着できる。 In addition, since the branch parts of the circuit part are branched independently and electrode parts are attached to their tips, the distance between each electrode part can be changed, and the electrode parts can be attached flexibly according to the patient's physique and shape. .
また、各電極部とコネクタの各端子とは配列順
位を同一に構成したので、電極部の装着が正確
に、かつ迅速にできるなど操作性が向上した。 Furthermore, since each electrode part and each terminal of the connector are arranged in the same order, the electrode part can be attached accurately and quickly, improving operability.
請求項２の考案は電極部が３個で構成のため、
未熟児や幼児などのモニター用に便利である。 Since the invention of claim 2 is composed of three electrode parts,
It is convenient for monitoring premature babies and infants.
請求項３の考案は電極部が６個のため、胸部用
電極として便利である、などの効果がある。 The invention according to claim 3 has advantages such as being convenient as a chest electrode because there are six electrode parts.
第１図は本考案の一実施例の平面説明図、第２
図〜第７図は同実施例の構成の分解説明図、第７
図は本考案の他の実施例を示す図、第８図〜第１
０図は従来例を示す図である。
１……電極部、２……回路部、２ａ……回路、
２ｂ……幹状部、２ｃ……枝状部、３……コネク
タ、３ａ……端子、４……貼着基材（不織布によ
る）、５……網目状銀導電層、６……線状銀導電
層、７……絶縁性のシリコン製被覆材、８……含
水性ゲル、９……シリコンゲル（シリコン製粘着
剤）。
FIG. 1 is a plan view of one embodiment of the present invention;
7 is an exploded view of the configuration of the embodiment, and FIG.
The figures show another embodiment of the present invention.
FIG. 1 is a diagram showing a conventional example. 1: electrode portion, 2: circuit portion, 2a: circuit,
2b... trunk portion, 2c... branch portion, 3... connector, 3a... terminal, 4... adhesive substrate (nonwoven fabric), 5... mesh-like silver conductive layer, 6... linear silver conductive layer, 7... insulating silicone coating material, 8... hydrous gel, 9... silicone gel (silicone adhesive).
Claims (1)
体内から微弱な電気信号を導出する生体用電極
であつて、前記電極部は貼着基材に印刷され前
記生体内から微弱な電気信号を導出するための
網目状銀導電層と、この網目状銀導電層と接し
生体の皮膚面に当接する含水性ゲルと、前記貼
着基材と前記網目状銀導電層とを被覆している
シリコン等被覆材と前記含水ゲルの周囲を囲繞
している絶縁性のシリコン等の粘着剤とからな
り、前記回路部は前記貼着基材に印刷形成され
た網目状銀導電層と線状銀導電層とからなる複
数の回路を有し、前記貼着基材と前記複数の回
路はシリコン等被覆剤で覆われ、前記網目状銀
導電層は前記電極部近傍の回路を、前記線状銀
導電層は前記電極部近傍以外の回路をそれぞれ
形成し、前記回路部は幹状部と複数に分岐した
枝状部とからなり、この複数の枝状部は各先端
部にそれぞれ前記電極部を接続するとともに、
前記コネクタは前記回路部の幹状部の一端に接
続され、同コネクタの複数の端子は前記複数の
電極の配列と同一配列としたことを特徴する、
生体用電極。 (2) 前記複数の電極部数は３個である、請求項１
の生体用電極。 (3) 前記複数の電極部数は６個である、請求項１
の生体用電極。[Claims for Utility Model Registration] (1) A biological electrode that has a plurality of electrode parts, a circuit part, and a connector and derives a weak electrical signal from within a living body, wherein the electrode part is attached to an adhesive base material. a printed mesh silver conductive layer for deriving weak electrical signals from within the living body; a hydrous gel that is in contact with the mesh silver conductive layer and in contact with the skin surface of the living body; the adhesive base material and the mesh. The circuit portion is formed by printing on the adhesive base material, and the circuit portion is formed by printing on the adhesive base material. The adhesive base material and the plurality of circuits are covered with a coating agent such as silicone, and the network silver conductive layer is connected to the electrode. The linear silver conductive layer forms a circuit near the electrode portion, and the circuit portion includes a trunk portion and a branch portion branched into a plurality of branches. connects the electrode portion to each tip portion, and
The connector is connected to one end of the trunk portion of the circuit portion, and the plurality of terminals of the connector are arranged in the same arrangement as the plurality of electrodes.
Biological electrode. (2) Claim 1, wherein the number of the plurality of electrode parts is three.
biological electrodes. (3) Claim 1, wherein the number of the plurality of electrode parts is six.
biological electrodes.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP1988131106U JPH052163Y2 (en) | 1988-10-05 | 1988-10-05 |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP1988131106U JPH052163Y2 (en) | 1988-10-05 | 1988-10-05 |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| JPH0251506U JPH0251506U (en) | 1990-04-11 |
| JPH052163Y2 true JPH052163Y2 (en) | 1993-01-20 |
Family
ID=31386863
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| JP1988131106U Expired - Lifetime JPH052163Y2 (en) | 1988-10-05 | 1988-10-05 |
Country Status (1)
| Country | Link |
|---|---|
| JP (1) | JPH052163Y2 (en) |
Families Citing this family (6)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| EP1264610B1 (en) * | 1997-11-26 | 2006-03-01 | E-Z-EM, Inc. | Extravasation Detection |
| JP5186506B2 (en) * | 2007-09-25 | 2013-04-17 | 朝倉染布株式会社 | Electrode sheet and method for producing electrode sheet |
| JP5485631B2 (en) * | 2009-09-30 | 2014-05-07 | フクダ電子株式会社 | Biological electrode |
| JP5759208B2 (en) * | 2011-03-03 | 2015-08-05 | フクダ電子株式会社 | Biological electrode |
| JP6567800B2 (en) * | 2013-12-26 | 2019-08-28 | フクダ電子株式会社 | Biological electrode |
| JP5847217B2 (en) * | 2014-02-20 | 2016-01-20 | フクダ電子株式会社 | Biological electrode |
-
1988
- 1988-10-05 JP JP1988131106U patent/JPH052163Y2/ja not_active Expired - Lifetime
Also Published As
| Publication number | Publication date |
|---|---|
| JPH0251506U (en) | 1990-04-11 |
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