JP2014076390A - Isolation sheet - Google Patents

Abstract

PROBLEM TO BE SOLVED: To provide a mounting method for a cardiac muscle action potential measuring device capable of reducing a sense of attachment discomfort felt by a patient or a subject when the cardiac muscle action potential measuring device is mounted, in which the measuring device is caused not to directly contact the skin of the patient.SOLUTION: An isolation sheet includes: a non-conductive sheet 11 with a hole 121 that penetrates in a thickness direction; and a conductive gel layer 13 having a laminated part which is a lower side part 112 of the non-conductive sheet 11 laminated in a position including the hole 121, a filled part filled in the hole 121, and a thin layer part, which is an upper side part 111 of the non-conductive sheet 11 laminated in a position including the hole 121.

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 directly attach Holter electrocardiographs to patients and subjects without the use of lead wires.

JP-T-2001-506154

  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 time 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.

  The present invention relates to an isolation sheet disposed between an electrode of a myocardial potential measuring device and skin. The separator sheet includes a non-conductive sheet having holes penetrating in the thickness direction, at least a laminated portion laminated at a position on the skin side of the non-conductive sheet and including the holes, the non-conductive sheet A hole-in-portion that is located in the hole of the conductive sheet and is continuous with the laminated portion, and an upper portion on the electrode side of the non-conductive sheet that is laminated at a position including the hole and continues to the hole-in-portion A conductive gel layer having a thin layer portion.

  The non-conductive sheet may have a plurality of the holes.

  The isolation sheet further includes an insulator layer laminated on the skin side of the laminated portion of the conductive gel layer, and in the cross-section along the thickness direction of the non-conductive sheet, the insulator layer The width in the width direction orthogonal to the thickness direction is narrower than the width of the laminated portion of the conductive gel layer, and wider than the region where the holes are arranged in the non-conductive sheet, and the electrode contact in the width direction. The said insulator layer may be arrange | positioned in the position which covers a part.

  An adhesive layer may be provided on the lower side of the non-conductive sheet.

  Examples of the pressure-sensitive adhesive layer include those formed from an acrylic pressure-sensitive adhesive.

  Examples of the non-conductive sheet include those formed from a polyurethane material.

  Examples of the conductive gel layer include those formed from a hydrogel material.

  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.

FIG. 1 is a schematic view showing an example of an isolation sheet used in the present invention. FIG. 2 is a schematic view showing another embodiment of the isolation sheet used in the present invention.

  Hereinafter, preferred embodiments of the present invention will be described. In addition, this embodiment is only one embodiment of this invention, and it cannot be overemphasized that an embodiment can be changed in the range which does not change the summary of this invention.

  An isolation sheet for preventing direct contact between the skin and the myocardial potential measuring device is affixed to the skin, and the myocardium using Surget (registered trademark) 10 (trade name, manufactured by Livertape Pharmaceutical Co., Ltd.) from above the isolation sheet. Fix the potential measuring device. 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 an isolation sheet according to the first embodiment.
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 hole 121 of the electrode contact portion 12, An adhesive layer 113 made of an acrylic 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 131 may protrude to the upper portion 111 side of the nonconductive sheet 11. In this case, the protruding portion just sandwiches the nonconductive 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 electrode contact portion 12 can be formed by punching holes 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 has completely penetrated through the gap of the porous material, the conductive gel layer 13 is formed on the electrode contact portion 12, and the conductive gel layer 13 is not blocked by the holes 121 of the electrode 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, a polypolymer, 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 ultrathin film having a thickness of 10 microns: Surget (registered trademark) 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. 2 is a schematic view of an isolation sheet according to the second embodiment.
First, the device wearing part of the 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 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 polyurethane material having 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 hole 102 and the conductive sheet 103 fixed to the lower side portion 1012 of the non-conductive sheet 101.

DESCRIPTION OF SYMBOLS 1 Separation sheet 11 Nonelectroconductive sheet 111 Upper part 112 Lower part 113 Adhesive layer 12 Electrode contact part 121 Hole 13, 131 Conductive gel layer 14 Insulator layer 141 Upper part 142 Lower side 143 Adhesive layer 10 Isolation sheet 101 non-conductive sheet 1011 upper side part 1012 lower side part 102 hole 103 conductive sheet 104 adhesive layer

Claims (7)

An isolation sheet placed between the electrode of the myocardial potential measuring device and the skin,
A non-conductive sheet having holes penetrating in the thickness direction;
At least a laminated part laminated at a position on the skin side of the non-conductive sheet and including the hole, an in-hole part located in the hole of the non-conductive sheet and continuing to the laminated part And a conductive gel layer having a thin layer portion that is laminated at a position including the holes and is an upper portion on the electrode side of the non-conductive sheet.   The isolation sheet according to claim 1, wherein the non-conductive sheet has a plurality of the holes. It further comprises an insulator layer laminated on the skin side of the laminated portion of the conductive gel layer,
In the cross section along the thickness direction of the non-conductive sheet, the width of the insulator layer in the width direction perpendicular to the thickness direction is narrower than the width of the laminated portion of the conductive gel layer, and the non-conductive sheet The isolation sheet according to claim 1, wherein the insulator layer is disposed at a position that is wider than a region where the hole is disposed and covers the electrode contact portion in the width direction.   The isolation sheet according to any one of claims 1 to 3, wherein an adhesive layer is provided on a lower side portion of the non-conductive sheet.   The isolation sheet according to claim 4, wherein the pressure-sensitive adhesive layer is formed from an acrylic pressure-sensitive adhesive.   The isolation sheet according to any one of claims 1 to 5, wherein the non-conductive sheet is formed of a polyurethane material. The isolation sheet according to any one of claims 1 to 6, wherein the conductive gel layer is formed of a hydrogel material.

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