JP2010075601A - Method of mounting myocardial action potential measuring instrument - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To provide a method of mounting a myocardial action potential measuring instrument which can reduce a feeling of pasting incongruity of a patient or a subject when the myocardial action potential measuring instrument is mounted, and a method of mounting the myocardial action potential measuring instrument which is designed not to directly come into contact with the skin of the patient. <P>SOLUTION: The method of mounting the myocardial action potential measuring instrument includes pasting a separation sheet to prevent the skin from directly coming into contact with the myocardial action potential measuring instrument, and fixing the myocardial action potential measuring instrument by using a very thin self-adhesive film which is highly stretchable, highly waterproof, and well screens out bacteria from above the separation sheet. <P>COPYRIGHT: (C)2010,JPO&INPIT

Description

  The present invention relates to a method for mounting a myocardial action potential measuring device, for example, by attaching a myocardial action potential measuring device such as a Holter electrocardiograph to the skin of a patient or a subject.

Holter electrocardiogram is a test method that evaluates cardiac function by continuously recording an electrocardiogram for each beat for a long period of time under the normal conditions of daily life. It is developing as a method for accurately and faithfully extracting abnormalities in cardiovascular function.
Currently, a multimedia card is used as the recording medium for the Holter electrocardiograph, the power source is only one AAA alkaline battery, a disposable electrode is used and no induction cable is required. The weight and weight have been reduced, and it has become possible to attach a Holter electrocardiograph directly to a patient or subject without a lead wire.

  However, even though the size and weight have been reduced, the Holter electrocardiograph is uncomfortable when it is applied to the skin of a patient or subject (hereinafter simply referred to as “patient”). In addition, since the electrocardiogram is recorded continuously for a long period of 24 hours or more, further reduction of the uncomfortable feeling is desired. For this purpose, it is necessary to further reduce the size of the myocardial action potential measuring device including the Holter electrocardiograph and to improve the wearing method of the device. In addition, unlike the disposable bioelectrode, the myocardial action potential measuring device is used repeatedly, so that it is necessary not to directly contact the patient's skin in order to prevent cross infection.

  The present invention has been made in view of the above circumstances, and an object of the present invention is to provide a method for mounting a myocardial action potential measurement device that can reduce the discomfort of a patient or subject when the myocardial action potential measurement device is mounted. To do. It is another object of the present invention to provide a method for mounting a myocardial action potential measuring device in which the measuring device is not in direct contact with the patient's skin.

In the method for mounting the myocardial action potential measuring device of the present invention, an isolation sheet for preventing direct contact between the skin and the myocardial potential measuring device is attached to the skin. The myocardial potential measuring device is fixed by using an extremely thin adhesive film having excellent properties.
Here, the separator sheet has an upper part and a lower part, and is provided with an adhesive layer on the lower part, and is porous corresponding to the position of the electrode of the myocardial potential measuring device fixed from above the separator sheet. Preferably comprising a non-conductive sheet provided with an electrode contact portion, and a conductive gel layer formed on the lower side of the non-conductive sheet and a small hole in the electrode contact portion. The potential measuring device is fixed so that the position of the electrode of this device and the position of the electrode contact portion of the separator sheet overlap. The pressure-sensitive adhesive layer is preferably formed from an acrylic pressure-sensitive adhesive. The non-conductive sheet is preferably formed from a polyurethane material, and the conductive gel layer is preferably formed from a hydrogel material. Further, as the adhesive film, Surget 10 (trade name, manufactured by Riba Tape Pharmaceutical Co., Ltd.) is preferable.
The isolation sheet may further include an extremely thin insulator layer having an upper portion and a lower portion, and having an adhesive layer on the upper portion, and the insulator layer is a non-conductive sheet. The conductive gel layer is narrower than the conductive gel layer formed on the lower side and has a wider width than the electrode contact part, and is fixed to the lower part of the conductive gel layer so as to cover the electrode contact part.
The isolation sheet has an upper part and a lower part, is provided with an adhesive layer on the lower part, and has a width wider than that of the electrode corresponding to the position of the myocardial potential measuring device fixed from above the isolation sheet. A non-conductive sheet provided with a narrow hole, and one end fixed to the lower portion of the non-conductive sheet so as to close the hole through the hole of the non-conductive sheet and the other end non-conductive sheet It may comprise a conductive sheet fixed to the upper side portion. In this case, the myocardial potential measuring device is fixed so that the position of the electrode of the device and the position of the conductive sheet overlap. The pressure-sensitive adhesive layer is preferably made of an acrylic pressure-sensitive adhesive, and the non-conductive sheet is preferably made of a polyurethane material. )) Is preferred.

Although the present invention has been generally described above, a better understanding can be obtained by reference to certain specific embodiments. These examples are provided herein for illustrative purposes only and are not limiting unless otherwise specified.

According to the present invention, the following effects can be expected. That is, according to the method for mounting the myocardial action potential measuring device of the present invention, the myocardial action potential measuring device is not in direct contact with the skin, and the isolation sheet is interposed between the skin and the patient. Infection can be prevented. In addition, since an ultra-thin adhesive film excellent in stretchability, waterproofness, and bactericidal properties is used for attaching the device to the skin, it is possible to reduce the patient's uncomfortable feeling when the device is attached.

An isolation sheet for preventing direct contact between the skin and the myocardial potential measuring device is attached to the skin, and the myocardial potential measuring device is attached to the skin using Surget 10 (trade name, manufactured by Riba Tape Pharmaceutical Co., Ltd.). Fix it. The isolation sheet has an upper part and a lower part, and has an acrylic adhesive layer on the lower part, and is porous according to the position of the electrode of the myocardial potential measuring device fixed from above the isolation sheet. A non-conductive sheet made of polyurethane provided with an electrode contact portion, and a conductive gel layer made of a hydrogel material formed in a lower portion of the non-conductive sheet and a small hole in the electrode contact portion. It becomes. The myocardial potential measuring device is fixed so that the position of the electrode of this device and the position of the electrode contact portion of the isolation sheet overlap. The separator sheet further includes an extremely thin insulator layer having an upper portion and a lower portion, and having an adhesive layer on the upper portion. The insulator layer is a non-conductive sheet. The conductive gel layer is narrower than the conductive gel layer formed on the lower side and has a wider width than the electrode contact part, and is fixed to the lower part of the conductive gel layer so as to cover the electrode contact part.

First, Example 1 will be described with reference to FIG.
FIG. 1 is a schematic view of a release sheet used in the present invention.
First, a myocardial potential measuring device (hereinafter simply referred to as “device”) attached to a patient's skin S is wiped with alcohol or the like to sufficiently remove dirt, body fat, keratin, etc. on the skin S, and then FIG. The isolation sheet 1 as shown in FIG. Next, the apparatus (not shown) is placed on the isolation sheet 1, and the position of the electrode of the apparatus overlaps the position of the electrode contact portion 12 of the isolation sheet 1 using an adhesive film (not shown). To the skin S.

The isolation sheet 1 has an upper part 111 and a lower side part 112, and a polyurethane material provided with a porous electrode contact part 12 corresponding to the position of the electrode of the device fixed from above the isolation sheet 1 A non-conductive sheet 11 made of the above, and conductive gel layers 13 and 131 made of a hydrogel material respectively formed in the lower portion 112 of the non-conductive sheet 11 and the small holes 121 of the electrode contact portion 12. A pressure-sensitive adhesive layer 113 made of an acrylic pressure-sensitive adhesive is provided on the lower side of the non-conductive sheet. Preferably, an extremely thin insulator layer 14 is fixed to the lower portion of the conductive gel layer 13 so as to cover the electrode contact portion 12. Here, the conductive gel layer 113 may protrude to the upper portion 111 side of the non-conductive sheet 11, and in this case, the protruding portion just sandwiches the non-conductive sheet 11 with the conductive gel layer 13. Further, it is preferable to form a thin layer shape.

  As a material for forming the non-conductive sheet 11, polyurethane which is excellent in stretchability and flexibility, is very flexible and has a little uncomfortable feeling during pasting, and polyethylene can also be used. The electrical contact portion 12 can be formed by punching a hole in the non-conductive sheet 11, but is preferably formed from a porous material made of the same resin foam material as the non-conductive sheet 11. When the hydrogel material completely penetrates through the gap of the porous material, the conductive gel layer 13 is formed on the electrical contact portion 12, and the conductive gel layer 13 is not blocked by the holes 121 of the electrical contact portion 12. Moored on the conductive sheet 11.

  The conductive gel layer 13 is formed of a hydrogel material formed from an aqueous mixture of, for example, polyalcohol, a prepolymer terminated with an aliphatic diisocyanate, a diamine based on polyethylene oxide and sodium chloride. And has a high absorbency capable of holding a large amount of fluid. And it is possible to prevent the material from drying over a long storage period due to its high absorbency. The polyhydric alcohol is selected from the group consisting of polypropylene alcohol, polyethylene glycol and glycerin. As the aliphatic diisocyanate, those containing hexamethylene diisocyanate, isophorone diisocyanate, tetramethylene diisocyanate and decamethylene diisocyanate can be used.

  The acrylic pressure-sensitive adhesive is less likely to be rashed and has high adhesion. Therefore, it is suitable for cases where sticking over a long period of time is required, and usually, for example, an ethyl acetate solution of an acrylic ester-methacrylic ester copolymer, an ethyl acetate solution of an acrylic ester-vinyl pyrrolidone copolymer, An ethyl acetate solution of an acrylate ester-acrylic acid copolymer is employed.

  Since the adhesive film needs to stick the device to the skin for a long time, as the adhesive of the isolation sheet, an acrylic adhesive that has high adhesion and is not easily irritated, is used. In addition, in order to reduce the uncomfortable feeling at the time of sticking, and avoid the occurrence of stuffiness and bacteria generated when sticking for a long time, preferably as a film to be used as a base material, it is stretchable, waterproof, and antibacterial. An ultra-thin polyurethane film having excellent water vapor permeability is used. As such an adhesive film, a commercially available ultra-thin film having a thickness of 10 microns: Surget 10 (trade name, manufactured by Riba Tape Pharmaceutical Co., Ltd.) is suitable.

  The insulator layer 14 is a film in which an adhesive layer 143 is provided on an upper portion 141 of a non-conductive film having an upper portion 141 and a lower portion 142. By providing the insulator layer 14, the patient's skin and device are provided. Can be prevented to reduce the effects of noise that occurs when the patient moves. This insulator layer 14 has a width narrower than that of the conductive gel layer 13 formed on the lower side portion 112 of the nonconductive sheet 11 and wider than that of the electrode contact portion 12, and a lower portion of the conductive gel layer 13. It is fixed so that the electrode contact part 12 may be covered. In general, polyethylene, polypropylene, or the like is used as a material for forming the film of the insulator layer 14. In addition to the acrylic pressure-sensitive adhesive, a rubber-based pressure-sensitive adhesive can be used as a material for forming the pressure-sensitive adhesive layer 143.

Next, Example 2 will be described with reference to FIG.
FIG. 1 is a schematic view of a release sheet used in the present invention.
First, after wiping the device wearing part of the patient's skin S with alcohol or the like to sufficiently remove dirt, body fat, and keratin, etc. on the skin S, an isolation sheet 10 as shown in FIG. wear. Next, the apparatus is placed on the isolation sheet 10 and fixed to the skin S using an adhesive film (not shown) so that the position of the electrode of the apparatus overlaps the position of the conductive sheet 103 of the isolation sheet 10. To do.
The isolation sheet 10 has an upper side portion 1011 and a lower side portion 1012. The lower side portion 1012 includes an adhesive layer 104, and corresponds to the position of the electrode of the device fixed from above the isolation sheet 10. A non-conductive sheet 101 made of a polyurethane material provided with a hole 102 narrower than the electrode, and one end of the non-conductive sheet penetrating the hole 102 of the non-conductive sheet 101 and closing the hole 102 101 includes a conductive sheet 103 that is fixed to the lower portion 1012 of the 101 and has the other end fixed to the upper portion 1011 of the non-conductive sheet 101. The pressure-sensitive adhesive layer 104 is made of an acrylic pressure-sensitive adhesive, and is not provided on the portion of the hole 102 and the portion of the conductive sheet 103 fixed to the lower side portion 1012 of the non-conductive sheet 101.

It is the schematic which shows the Example of the peeling sheet used for this invention. It is the schematic which shows the other Example of the peeling sheet used for this invention.

Explanation of symbols

DESCRIPTION OF SYMBOLS 1 Release sheet 11 Nonelectroconductive sheet 111 Upper side part 112 Lower side part 113 Adhesive layer 12 Electrode contact part 121 Small hole 13, 131 Conductive gel layer 14 Insulator layer 141 Upper side part 142 Lower side part 143 Adhesive layer 10 Peeling Sheet 101 Non-conductive sheet 1011 Upper part 1012 Lower part 102 Hole 103 Conductive sheet 104 Adhesive layer

Claims (11)

An isolation sheet for preventing direct contact between the skin and the myocardial potential measuring device is affixed to the skin, and an ultrathin adhesive film excellent in stretchability, waterproofness and antibacterial properties is applied from above the isolation sheet. A method for mounting a myocardial potential measuring device, which fixes the myocardial potential measuring device. The isolation sheet has an upper part and a lower part, and has a pressure-sensitive adhesive layer on the lower part, and is porous according to the position of the electrode of the myocardial potential measuring device fixed from above the isolation sheet. A myocardial potential measuring device comprising: a non-conductive sheet provided with an electrode contact portion; and a conductive gel layer formed in a lower portion of the non-conductive sheet and a small hole in the electrode contact portion. The method according to claim 1, wherein the position of the electrode of the device and the position of the electrode contact portion of the separator sheet are fixed to overlap each other. The method according to claim 2, wherein the pressure-sensitive adhesive layer is formed from an acrylic pressure-sensitive adhesive. The method according to claim 2 or 3, wherein the non-conductive sheet is formed from a polyurethane material. The method according to claim 2, wherein the conductive gel layer is formed from a hydrogel material. The method according to any one of claims 1 to 5, wherein the adhesive film is Surget 10 (trade name, manufactured by Riba Tape Pharmaceutical Co., Ltd.). A conductive layer formed on the lower side of the non-conductive sheet, further comprising an ultrathin insulating layer having an upper portion and a lower portion, and having an adhesive layer on the upper portion; The method according to claim 2, which is narrower than the conductive gel layer and wider than the electrode contact portion, and is fixed so as to cover the electrode contact portion on the lower portion of the conductive gel layer. The isolation sheet has an upper part and a lower part, is provided with an adhesive layer on the lower part, and is wider than the electrode corresponding to the position of the electrode of the myocardial potential measuring device fixed from above the isolation sheet. A non-conductive sheet having a narrow hole, and one end fixed to the lower side of the non-conductive sheet so as to close the hole through the hole of the non-conductive sheet and the other end non-conductive The method according to claim 1, further comprising a conductive sheet fixed to an upper portion of the sheet, wherein the myocardial potential measuring device is fixed so that the position of the electrode of the device and the position of the conductive sheet overlap. The method according to claim 8, wherein the pressure-sensitive adhesive layer is formed from an acrylic pressure-sensitive adhesive. The method according to claim 8 or 9, wherein the non-conductive sheet is formed from a polyurethane material. The method according to any one of claims 8 to 10, wherein the adhesive film is Surget 10 (trade name, manufactured by Riba Tape Pharmaceutical Co., Ltd.).

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