JP3782947B2 - Bipolar electrode for living body and conductor connection structure thereof - Google Patents

Description

[0001]
[Industrial application fields]
The present invention relates to a biopolar electrode and a conductor connecting structure thereof. More particularly, the present invention relates to a treatment device or a slimming bioelectrode used for supplying pulsed currents of a low-frequency and a medium-frequency oscillator, and a structure connected to an electrical signal.
[0002]
[Prior art]
In general, a conductive rubber pad or a conductive polymer gel has been used for the biological electrode. Recently, a method using a conductive rubber pad has hardly been seen, and a method has been adopted in which a pair of electrodes made of an adhesive conductive polymer gel is directly attached to the skin or an affected skin area.
For example, Japanese Utility Model Publication No. 5-70552 discloses a device related to a biomedical electrode having a plurality of electrodes having the configuration shown in FIG. That is, it is comprised from the electroconductive adhesive 100, the electroconductive layer 200, the nonelectroconductive sheet-like object 300, and the external connection means 400, and the snap is stuck and fixed by the tape 500 in the figure. By constituting in this way, each electrode has a terminal protruding on the sheet-like material as a connecting means to the outside, and since it is integrated, it is said that adhesion to the skin and followability are good Yes.
[0003]
However, even in such a configuration, when the distance between the plurality of terminals is short, the distance of the conductive adhesive layer is also close, and the soft conductive adhesive layer sticks to each other by pressing pressure, There is a risk of short-circuiting between terminals. In addition, when a snap female type terminal in which two metal spring cap terminals are configured at the same time is attached to the electrode terminal having the above configuration, the center of the long side of the electrode is curved in a direction parallel to the short side. Is natural, but because it bends at the above-mentioned site where it is easy to bend on the skin, it also curves between the terminals of the two poles, and the snap female type terminal does not mesh properly, and the contact is disconnected or conductive There exists a problem that an adhesive layer becomes easy to peel from skin.
[0004]
Japanese Laid-Open Patent Publication No. 4-54972 discloses a method in which a conductive adhesive layer is connected to a device by a conductor in a structure in which a terminal portion is integrated at the same time. That is, there is a spring interposed between the conductive sheet and the insulating sheet for electrically connecting the electrode rod inserted into the cylinder of the case and the contact part of the substrate, and the main body case is attached to the affected part. Adhesive pad for affixing to the body is connected to the spring and the cylinder by pressing force, and since it is only connected via the cylinder part, it explains that it fits well with the curved part of the human body and fits Has been.
[0005]
However, although it is easy to adapt to a curved surface, it is always pressed by the spring, so naturally the thickness of the soft conductive adhesive layer part becomes thin, the contact impedance is lowered, and the current is partially Easy to flow. For this reason, there is a problem that the degree of electrical stimulation is different and uncomfortable feeling is likely to occur. Conventionally, the main unit (low-frequency, medium-frequency, etc. oscillation devices) and a plurality of biological electrodes are connected by a plurality of separated cords. For this reason, a plurality of lead wires are intertwined during use. In many cases, it takes time to connect to the terminal. In particular, when it is necessary to connect to a bipolar electrode having a plus electrode and a minus electrode, respectively, it is lacking in simplicity, but no contrivance has yet been found.
[0006]
[Problems to be solved by the invention]
As described above, conventionally, a biological electrode in which a plurality of electrodes are integrally arranged has been proposed, but there are still inconveniences in the actual usage. One of them is that when a snap is used for the electrode terminal as a means for connecting to the main unit, the conductor snap type terminal (snap female type terminal) will not mesh properly depending on the part of the human body to be attached. There is a problem that the conductive adhesive layer is easily detached from the skin.
[0007]
In addition, in the case of a bipolar electrode, when the positive electrode and the negative electrode are used separately, it is possible to easily determine which electrode is to connect with the conductor terminal so that the connection can be made quickly. It is also requested to make it.
Furthermore, in the manufacture of the bipolar electrode, in order to caulk the two terminals at the same time, a drilling process is performed on the base sheet. However, if misalignment occurs during the process, the engagement with the conductor terminal is hindered. Will come. This drilling process is often accompanied by an error of about ± 1 mm in a normal method, and it is necessary to increase the machining accuracy in order to suppress the variation. However, this leads to a decrease in production efficiency and, consequently, an increase in product cost. Therefore, a device for simply connecting the electrode terminal and the conductor terminal while allowing the above-described variation is desired.
[0008]
The object of the present invention is to solve these problems.
[0009]
[Means for Solving the Problems]
Therefore, the inventors of the present invention have completed the present invention as a result of intensive studies from various aspects in order to solve the above problems.
That is, the present invention includes the following inventions.
1) In a bipolar electrode for a living body having two independent conductive adhesive layers, an electrode element layer, a non-conductive base sheet supporting the two layers, and an electrode terminal portion, the electrode terminal portion is A biological bipolar electrode characterized in that it is electrically independent from each other and integrated through the non-conductive sheet, and has a punched portion at a substantially intermediate portion between the two electrode terminals.
[0010]
2) The bipolar electrode for living body according to 1) above, wherein the punched portion is symmetrical.
3) The bipolar electrode for a living body according to 1) above, wherein the punched portion has a shape capable of indicating the polarities of the two electrodes.
4) The bipolar electrode for living body according to 1) to 3) above, wherein the electrode terminal portion is constituted by a snap terminal.
[0011]
5) A connection structure for sending an electrical signal to the biological bipolar electrode according to any one of 1) to 4) above, wherein the two conductor side connections are connected to the electrode side connection terminals. The terminal is integrated while maintaining the same distance as the two electrode side connection terminals , and the conductor connection structure and the bipolar electrode for living body are connected to each other through the punched portion. The conductor connection structure for a bipolar electrode, wherein the conductor connection structure is fitted with a holding plate having a protrusion that can be attached to a recess formed in the conductor connection structure.
[0012]
The bipolar electrode for living body of the present invention is characterized in that a punched portion is formed at a substantially intermediate position between the two electrode terminal portions as described above. Even if the punching of the terminal for two poles causes a positional deviation of about ± 1 mm, for example, the punching portion functions as a correction portion, so that the connection operation with the two conductor terminals can be facilitated. Further, unlike the conventional case, since high accuracy is not required for drilling, the occurrence of defective products is reduced, which can contribute to improvement in production efficiency and reduction in product cost.
[0013]
Furthermore, when an electric signal (stimulus) is input from the main device, if there is a polarity of a positive pole or a negative pole, the punched portion has a shape that serves as a mark for specifying one of the polarities, It is possible to easily perform a predetermined connection without making a mistake.
The conductor connection structure of the present invention is characterized in that the two conductor terminals from the main device are integrated to form a connection structure and are connected to the two biological electrode terminals at the same time. Have. By being configured in this way, the connection at the time of use becomes easy, and the two electrode terminals do not come off from the conductor terminals depending on the shape of the human body part to be attached. As in the prior art, it is also possible to prevent a plurality of lead wires from being entangled with each other to deteriorate usability.
[0014]
DETAILED DESCRIPTION OF THE INVENTION
First, a specific example of the biopolar electrode of the present invention will be described with reference to the drawings.
FIG. 1 is a plan view showing an example of a living body bipolar electrode 1 of the present invention, and an elliptical punching portion 2 at a substantially intermediate portion between two electrode terminals 3 and 3 ′ arranged at regular intervals. An example in which is provided. 2 is a front view, FIG. 3 is a bottom view, FIG. 4 is a BB sectional view, and FIG. 5 is a CC sectional view. FIG. 6 is a cross-sectional view of the portion centering on the electrode terminal in FIG.
[0015]
The bipolar electrode for a living body of the present invention is formed by laminating two independent electrode element layers 5 and a conductive adhesive layer 6 on a non-conductive substrate sheet 4 and attaching the electrode terminal portion 3 so as to be integrated. And has a punched portion at a substantially middle portion between the two electrode terminals. FIG. 6 is a partial cross-sectional view centering on each electrode terminal portion, and electrical signals such as low and medium frequencies oscillated from the main device are conducted through the two electrode terminal portions 3 and 3 ′. .
[0016]
The electrode terminal portion 3 is fixed so as to traverse from the one side end to the other side end of the terminal portion that is caulked and connected so as to be sandwiched between the snap terminal 9 and the metal fixture 10. An insulating layer 8 attached with a width is attached. The insulating layer 8 has a function of protecting the metal fixture from coming into direct contact with the skin and protecting it from coming into contact with the outside air from oxidation and sulfurization.
In the example of FIG. 6, a peelable protective film 8 is laminated on the conductive pressure-sensitive adhesive layer 6, but this protective film is peeled off when applied to the human body.
[0017]
The two electrodes in the present invention are electrically independent, and each is disposed on two separated conductive layers (electrode element layer, conductive adhesive layer). This will be described with reference to the bottom view of FIG. 3 and the CC cross-sectional view of FIG. As shown in this CC cross-sectional view, that is, a cross-sectional view seen from the surface of the conductive paste layer, the electrode element layers 5 and 5 ′ are independent through the S-shaped electrical insulating portion 11 at the center of the base sheet. The electrode terminals 3 and 3 'are attached to each of them, and a punching portion 2 is provided between 3 and 3'. The electrical insulating part 11 is left as a non-printing part when the conductive paste is printed on the non-conductive base sheet to form the electrode element layer, and the two electrodes located in the central part are made independent. In order to enlarge the conductive area as much as possible, it is advantageous to use the S-shape as shown in FIG. Conductive pressure-sensitive adhesive layers 6 and 6 ′ having an area smaller than that of the electrode element portions are laminated from the respective end portions of the electrode element layers 5 and 5 ′ (see the bottom view of FIG. 3). Two independent conductive adhesive layers 6, 6 ′ are laminated so as not to reach the portion where the electrode terminals 3, 3 ′ are located, and are separated by an insulating layer 11.
[0018]
The punched portion 2 is located at a substantially intermediate portion between the two electrode terminals 3 and 3 ′, and the size thereof is usually 0.05 to 5.0 cm ² depending on the distance between the electrode terminals. And preferably in the range of 0.10 to 3.50 cm ² . If it is smaller than this range, it is not sufficient for the function of compensating the misalignment in the drilling process of the two-pole terminals, and if it is larger than this range, the area of the electrode element layer is reduced. The control range of the degree of stimulation will be reduced. The shape of the punched portion is in principle arbitrary as long as the above function can be achieved. For example, if the shape of the pad is a rectangle, the punched portion is formed in a symmetrical shape such as an ellipse or a rectangle in a direction that harmonizes with the pad. In addition, when the two electrode terminals have different polarities, by providing direction to the punched portion, it can be a mark indicating a positive pole or a negative pole.
[0019]
For example, by punching into the shape of an isosceles triangle so that the apex indicates an electrode terminal having a specific polarity, the polarity can be easily identified, and the cost for printing and displaying the polarity can be reduced. You can also.
As mentioned above, as a preferable embodiment of the bipolar electrode for living body of the present invention, a non-conductive base sheet, an electrode element layer divided into two parts including an insulating part in the central part, and a central part thereof Two electrode terminal portions, which are provided so as to be paired at regular intervals across the non-printed portion of the conductive paste, and are connected by crimping so as to be sandwiched between a snap terminal and a metal fixture, and a metal portion of the terminal portion An insulating layer attached with a certain width so as to cross the heel side of the tool from one side end to the other side end, and a conductive adhesive layer having an area smaller than that of the electrode element layer on both sides thereof. A part of the agent layer covers the insulating layer, and the two electrode terminal portions are integrally formed at a place where the two electrode terminal portions are separated from the conductive adhesive layer, and between the two electrode terminals. It consists of the structure which provided the punching part in the approximate center part.
[0020]
When the biopolar electrode is attached to the human body, the two electrode-side snap terminals are connected to the two conductor-side snaps led from the main device, respectively. A conductor connection structure is also provided.
This conductor connection structure, as described above, is integrated with two conductor terminals and is very easy to connect. The conductor connection structure S has two snap female terminals, and an embodiment thereof is shown in FIGS. FIG. 7 shows two terminals that are completely fixed to form a two-pole integrated type, in which (a) shows a plan view and (b) shows a side sectional view. The electrical signal from the main device is sent to the two poles separately, and the conductor wires 14 are combined and coated so as not to short-circuit each conductor wire, and connected to the connection structure S. The connection structure S is formed by integrally forming two conductor-side terminals (female-type snaps) 12 and 12 ′ at the same interval as the electrode-side snaps 3 and 3 ′. Conductor wires are respectively connected to the female snaps 12, 12 '. In using the biomedical electrode, the electrode-side terminals 3 and 3 ′ are fitted to the female snaps 12 and 12 ′. In this way, the lead wires from the main device have no branches and can be connected to the electrode terminals very easily without being congested. When there is polarity, it is possible to respond by changing the pattern shape and color on the case of the two terminals. Since the integrated direction is the terminal arrangement direction and the short side direction in which the electrodes are difficult to bend, there is no concern of terminal engagement, contact disconnection, or peeling of the conductive adhesive layer from the skin.
[0021]
FIGS. 8A and 8B show another embodiment, which can be advantageously used when the two electrodes are divided into a positive electrode and a negative electrode. That is, an isosceles triangular recess is formed between the two poles of this connection structure, and the apex thereof serves as a mark indicating a specific electrode of the two poles. On the other hand, the punched portion formed between the electrode side terminals is also punched in a shape matching the concave portion of the connection structure. At the time of connection, the electrode side snap and the polarity are matched, and from the electrode pad side, as shown in FIG. That is, the convex part of the pressing plate communicates with the punched part of the electrode pad (not shown) and fits into the concave part of the connection structure, whereby a firm and firm connection can be achieved. The pressing plate 13 is manufactured using a non-conductive substrate, for example, a polypropylene resin. According to this structure, since the stress received by pulling or the like is applied not only to the terminal portion but also to the portion sandwiching the through hole, it is effective for substantial stress relaxation and a more reliable connection structure can be provided.
[0022]
Hereinafter, each configuration of the present invention will be further described.
The non-conductive base sheet is usually made of a resin film, and the material thereof is not particularly limited, but the distance between the two terminals can be kept constant when applied to the human skin. A film that is not stretchable and has a relatively high waist strength is preferred. As such a resin film, it is preferable to use a film having a thickness of 10 to 500 μm, such as polyethylene terephthalate (PET), polyethylene, polyvinyl chloride, and polypropylene. In particular, it is preferable to use a PET film having high waist strength and easy printing, or a film obtained by laminating polyethylene to a PET film when flexibility is required.
[0023]
The electrode element portion is formed using an appropriate conductive material. Examples of such conductive materials include silver, silver-silver chloride mixtures, metals such as nickel, molybdenum, zinc, and aluminum, carbon black, graphite, and the like alone or in combination of two or more. Examples thereof include conductive paste adjusted together with a binder. As the electrode element layer, a resistance material of 100 Ω / cm ² or less is used for pattern printing by adjusting the film thickness. These resistances can be widely adjusted depending on the difference in metal type and particle size difference.
[0024]
Any conductive adhesive layer can be used as long as it has conductivity and is less irritating to the skin and has adhesive strength, and is not particularly limited. Polyacrylamide, sodium polyacrylate, polyacrylic acid derivatives such as polyacrylate, poly-N-vinylamide derivatives such as polyvinylpyrrolidone and poly-N-vinylacetamide, polyurethane, etc. as a matrix, water, electrolyte salts, etc. A conductive pressure-sensitive adhesive gel containing can be suitably used.
[0025]
Examples of the insulating layer include an insulating synthetic resin film, a nonwoven fabric, a woven fabric, a hydrophilic treatment imparted with surface polarity, and a non-water-permeable treatment. It is non-permeable and needs to have adhesiveness with the conductive adhesive layer, and preferably has no water absorption and water content. When the synthetic resin film is used as the insulating layer used for the purpose of the present invention, it is necessary to have polarity. Examples of a method for increasing the adhesive strength with the conductive pressure-sensitive adhesive layer include a method of roughening the surface by adding a hydrophilic treatment or a filler. In this case, even a nonpolar film can be used. That is, since the nonwoven fabric has water permeability in order to increase the flexibility of the base material, a non-water-permeable treatment is suitable, and the best combination of adhesive strength and flexibility is selected. In the present invention, a polyethylene non-woven fabric (trade name: Tyvek), which has no polarity but is non-woven processed in terms of surface area and water impermeability, was suitable. Moreover, you may form by coating the coating film of a flexible insulating resin on the surface of the said electrode element part, without limiting to the said film.
[0026]
Since the snap terminal and the metal fixture do not directly contact the conductive adhesive layer in the configuration of the present invention, they may be conductive, durable, and hardly corrosive. However, the diameter of the collar portion of the metal fixture is preferably 4 to 18 mm in order to make use of the printing accuracy of the conductive paste.
It is preferable to set the printing area of the entire conductive paste and the area ratio of the conductive adhesive layer that overlaps the printed area to a range of 1.09 to 2.05. That is, when the area ratio is less than 1.09, the interval between the non-conductive portions becomes extremely small, which is the limit of printing accuracy, and at the same time, the conductive adhesive layers are stuck with each other by pressing pressure and short-circuited. Since it may exist, it is not preferable. Moreover, when the said area ratio exceeds 2.05, since the area which a conductive adhesive layer occupies becomes small and the electric current value with respect to skin concentrates on an area with small, it comes to be accompanied by unpleasant electrical stimulation, it is not preferable.
[0027]
On the base sheet, S-shaped non-printing portions are formed so that the central portions of the electrodes are staggered from one end to the other end in the direction in which the conductive paste is arranged in the terminals. Further, the electrode element portion is spaced from the upper and lower sides by a snap terminal and a metal fixture, and a terminal portion is formed. The snap terminal and the metal fixture have a diameter of 4 to 18 mm, and are covered with an insulating tape from the one end to the other end in the direction in which the terminal portion is arranged, and the end of the insulating tape is 0.5 mm or more, preferably 0.8 mm. The conductive adhesive layer is overlapped and adhered with a width of 5 to 10 mm. If the width is less than 0.5 mm, there is substantially no pasting accuracy, the electrode element layer is easily exposed, and the conductive adhesive layer and the insulating tape are likely to be peeled off due to bending or the like. Also, if it exceeds 10 mm, the conductive area increases, and it becomes difficult to absorb the dimensional variation due to the stress concentration at the center of the electrode due to the bending, so that it rebounds and the adhesion of the curved portion becomes worse. It is not preferable. A conductive adhesive layer is affixed on the whole electrode part other than the part of the said space | interval.
[0028]
The width of the insulating tape covered in the direction in which the terminal portion is arranged may be pasted with a width that covers the metal fixture of the terminal portion, but is about 6 to 25 mm including the adhesive width with the conductive adhesive layer. Is set. The distance between the terminals is set to 5 to 50 mm. If the distance is less than 5 mm, the formation accuracy of the non-printed portion by the conductive paste becomes a limit, and if it exceeds 50 mm, the conductor cord tends to be entangled. Preferably, production efficiency and usability are improved at 20 to 30 mm.
[0029]
Each electrode element part is integrally formed by pattern printing. For pattern printing, for example, screen printing or gravure printing is preferably employed, but is not particularly limited. The electrode element portion formed by printing may have a thickness of 2 to 30 μm, preferably 5 to 15 μm in a dry state after printing. The conductive adhesive layer has a thickness of 0.1 to 2.5 mm, preferably 0.2 to 1.5 mm. The conductive adhesive layer covers the entire surface of the electrode element part except for the part covered with the insulating tape, thereby improving the adhesion between the electrode element part and the skin.
[Brief description of the drawings]
FIG. 1 is a plan view showing an example of a biological bipolar electrode of the present invention.
FIG. 2 is a front view showing an example of a biological bipolar electrode of the present invention.
FIG. 3 is a bottom view showing an example of a biological bipolar electrode of the present invention.
4 is a cross-sectional view taken along line BB in FIG.
FIG. 5 is a cross-sectional view taken along the line CC in FIG.
FIG. 6 is a partial cross-sectional view with an electrode terminal as a center.
FIG. 7 is a plan view (a) and a side sectional view (b) showing an example of a connection structure for a bipolar electrode for a living body.
FIG. 8A is a plan view and FIG. 8B is a side sectional view showing an example of a connection structure for a bipolar electrode for a living body.
FIG. 9 shows an example of a conventional biomedical electrode.
[Explanation of symbols]
1 Bipolar electrode for living body 2 Punching part 3, 3 'electrode side terminal (snap)
4 Base sheet 5, 5 ′ electrode element layer 6, 6 ′ conductive adhesive layer 7 Protective film 8 Insulating layer 9 Snap 10 Snap fixing bracket 11 Electrical insulating part 12, 12 ′ Conductor side snap (female snap)
13 Holding plate 14 Conductor wire S Conductor connection structure

Claims (5)

In a bipolar electrode for a living body having two independent conductive adhesive layers, an electrode element layer, a non-conductive base sheet supporting the two layers, and an electrode terminal portion, the electrode terminal portions are electrically connected to each other. Bipolar electrode for living body characterized by being independent and integrated via the non-conductive sheet, and having a punched portion at a substantially intermediate portion between the two electrode terminals. 2. The bipolar electrode for living body according to claim 1, wherein the punched portion is symmetrical. 2. The bipolar electrode for living body according to claim 1, wherein the punched portion has a shape capable of indicating the polarities of the two electrodes. The bipolar electrode for a living body according to any one of claims 1 to 3, wherein the electrode terminal portion is constituted by a snap terminal. A connection structure for sending an electrical signal to the biological bipolar electrode according to any one of claims 1 to 4, wherein the two conductor-side connection terminals connected to the electrode-side connection terminal are: The conductor connection structure is integrated with the two electrode-side connection terminals while maintaining the same distance , and the conductor connection structure and the bipolar electrode for living body are connected to each other via the punched portion. The conductor connection structure for a bipolar electrode according to claim 1, wherein the conductor connection structure is fitted with a holding plate having a protrusion that can be attached to a recess formed in the structure.

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