JP2017164284A - Living-body attachable medical instrument and medical sensor aid - Google Patents

Abstract

PROBLEM TO BE SOLVED: To suppress occurrence of itching at an attachment region of a subject during use of a medical instrument without creating extra work for a health professional before attachment of the medical instrument.SOLUTION: A living-body attachable medical instrument has a main body having a living-body attachment part for attaching the medical instrument to a living body, the main body has a surface layer contacting the living body during use of the medical instrument, and the surface layer contains an anti-inflammatory substance. With respect to a medical sensor aid that is attachable to the living body with a medical sensor to be used for measuring biological information, a main body of the medical sensor aid has a surface layer contacting the living body during use of the medical sensor and the surface layer contains the anti-inflammatory substance.SELECTED DRAWING: Figure 2

Description

  The present invention relates to a medical device that can be worn on a living body, and a medical sensor auxiliary tool.

  In the medical field, when measuring biological information from a subject, various medical sensors corresponding to the type of the biological information are attached to the body surface of the subject and used. One example is a bioelectrode used for electrocardiogram examination for examining an electrocardiogram abnormality such as arrhythmia or ischemic heart disease.

  Some medical sensors are provided with a living body mounting portion for mounting the body on a living body. For example, in the case of a bioelectrode, generally, an adhesive part or a suction cup that can be attached or adsorbed to the skin of a living body is provided on the main body. In the medical sensor main body, at least the surface layer of the living body mounting portion is in contact with the living body during use of the medical sensor.

  In the case of such a contact-type medical sensor, when the medical sensor is attached to a living body, predetermined pre-processing may be performed depending on the purpose. Specifically, for example, in the case of a bioelectrode, in order to improve the electrical contact between the conductive gel and the skin surface, a skin treatment such as applying keratin cream to the electrode mounting site on the skin surface immediately before mounting is performed. It is conventionally known (see, for example, Patent Document 1).

Japanese Utility Model Publication No. 3-107942 Japanese Patent No. 4375758 Japanese Patent Laying-Open No. 2015-224217

  As described above, when the contact-type medical sensor is used, the pre-processing necessary for ensuring the measurement accuracy and thus the inspection accuracy cannot be omitted even if it is troublesome for the examiner (that is, a medical worker). .

  By the way, when using a medical sensor such as a biological electrode, it is desirable from the viewpoint of the subject that the living body sensor mounting site does not itch and a comfortable mounting feeling is sustained. However, if the health care worker performs an allowance to reduce itching in addition to the necessary pretreatment, it is a burden on the health care worker.

  The object of the present invention is to be able to wear a living body, which can suppress the occurrence of stagnation in the wearing site of the subject during use of the medical device, without causing the medical staff to take extra time before wearing the living body. Medical device and medical sensor aid.

The medical device that can be worn on the living body of the present invention,
A main body having a living body mounting portion for mounting the medical instrument on a living body;
The main body has a surface layer that comes into contact with a living body during use of the medical device,
The surface layer contains an anti-inflammatory substance.

The medical sensor auxiliary tool of the present invention comprises:
A medical sensor auxiliary tool that can be worn with a medical sensor used to measure biological information,
The body of the medical sensor auxiliary tool has a surface layer that comes into contact with a living body during use of the medical sensor,
The surface layer contains an anti-inflammatory substance.

  ADVANTAGE OF THE INVENTION According to this invention, it can suppress that a medical staff wears a mounting | wearing site | part of a subject during use of a medical device, without making a medical worker take extra time before the medical device is mounted | worn with the living body.

The disassembled perspective view which shows the structure of the bioelectrode which concerns on Embodiment 1 of this invention. Sectional drawing which shows the principal part of the bioelectrode which concerns on Embodiment 1 typically. Sectional drawing which shows typically the cross section of the principal part of the 1st modification of the bioelectrode which concerns on Embodiment 1. FIG. Sectional drawing which shows typically the cross section of the principal part of the 2nd modification of the bioelectrode which concerns on Embodiment 1. FIG. Sectional drawing which shows typically the cross section of the principal part of the 3rd modification of the bioelectrode which concerns on Embodiment 1. FIG. Sectional drawing which shows typically the cross section of the principal part of the 4th modification of the bioelectrode which concerns on Embodiment 1. FIG. Sectional drawing which shows typically the cross section of the principal part of the 5th modification of the bioelectrode which concerns on Embodiment 1. FIG. (A) Bottom view schematically showing bottom surface of main part of sixth modification of bioelectrode according to embodiment 1, (b) Cross section of main part of sixth modification of bioelectrode according to embodiment 1. Sectional view schematically showing (A) Bottom view schematically showing bottom surface of main part of seventh modification of bioelectrode according to Embodiment 1, (b) Cross section of main part of seventh modification of bioelectrode according to Embodiment 1. Sectional view schematically showing The disassembled perspective view which shows the structure of the bioelectrode which concerns on Embodiment 2 of this invention. Sectional drawing which shows the principal part of the bioelectrode which concerns on Embodiment 2 typically. Sectional drawing which shows typically the principal part of the 1st modification of the bioelectrode which concerns on Embodiment 2. FIG. Sectional drawing which shows typically the principal part of the 2nd modification of the bioelectrode which concerns on Embodiment 2. FIG. Sectional drawing which shows typically the principal part of the 3rd modification of the bioelectrode which concerns on Embodiment 2. FIG. (A) The perspective view which shows the structure of the bioelectrode which concerns on Embodiment 3 of this invention, (b) The perspective view which shows the structure of the bioelectrode cover which concerns on Embodiment 3, (c) The bioelectrode to the bioelectrode The perspective view which shows the state which attached the cover The side view which shows typically the side surface of the principal part of the bioelectrode cover which concerns on Embodiment 3.

  Hereinafter, embodiments of the present invention will be described in detail with reference to the drawings. Note that in the drawings, the entire structure shown in the drawing may be schematically shown by omitting, simplifying, or exaggerating the number, shape, or dimension of each member, but this is to facilitate understanding of the embodiment. Therefore, the present invention should not be construed as limited to the contents shown in the drawings.

(Embodiment 1)
Hereinafter, as Embodiment 1 of the present invention, a case where the present invention is applied to a medical device that can be worn on a living body, more specifically, a medical sensor used for measurement of biological information from a subject will be described. In the present embodiment, a bioelectrode used for electrocardiogram measurement will be described as an example of a medical sensor.

[overall structure]
FIG. 1 is an exploded perspective view showing the configuration of the biological electrode 100 according to the present embodiment. In the present embodiment, the “upper surface” means a surface that faces in a direction opposite to the surface of the biological electrode 100 attached to the subject, and the “lower surface” means the subject of the biological electrode 100. It means the surface that goes in the direction of the surface to be attached.

  In FIG. 1, the bioelectrode 100 mainly includes a base material 110, an electrode portion 120, a conductive gel layer 130, a disk-shaped nonwoven fabric 140, an annular nonwoven fabric 150, and a separator 160. An adhesive layer 141 containing an adhesive is provided on the lower surface of the disk-shaped nonwoven fabric 140, and an adhesive layer 151 containing an adhesive is also provided on the lower surface of the annular nonwoven fabric 150.

  Each of the base material 110 and the electrode portion 120 has an elongated portion that is elongated and functions as a lead wire that transmits an electrocardiogram signal detected from the subject to a recording device (not shown). .

  The substrate 110 is made of a film-like film material such as polyethylene terephthalate (PET) and has a pair of upper and lower surfaces. An electrode part 120 is provided on the lower surface of the base material 110, and the base material 110 forms the core of the sensor part and the lead wire of the biological electrode 100. A shield film may be formed on the upper surface of the substrate 110 as a countermeasure against electromagnetic waves and static electricity to the electrode part 120.

  The electrode unit 120 is made of a material such as silver-silver chloride (Ag—AgCl), and is disposed between the lower surface of the substrate 110 and the conductive gel layer 130. The electrode unit 120 detects an electrocardiogram signal transmitted from the conductive gel layer 130 and transmits it to a recording device (not shown).

  The conductive gel layer 130 is a gel layer having conductivity, adhesiveness, and hygroscopic expansion. The conductive gel layer 130 is adhered to the lower surface of the base material 110 with the electrode portion 120 interposed between the upper surface side gel portion 131 and the lower surface of the base material 110. The conductive gel layer 130 is adhered to the lower surface of the disk-shaped nonwoven fabric 140 by its own adhesive force and the adhesive force of the adhesive layer 141 applied to the disk-shaped nonwoven fabric 140. The surface area of the conductive gel layer 130 is larger than the surface area of the base material 110, and the conductive gel layer 130 has a region protruding from the peripheral edge of the base material 110. In addition, the conductive gel layer 130 adheres to the chest portion, which is the attachment site of the subject, by the adhesive strength of the conductive gel layer 130, and the adhesive strength of the adhesive layer 141 applied to the disk-shaped nonwoven fabric 140. And the adhesive force of the adhesive layer 151 applied to the annular nonwoven fabric 150 (or the adhesive force of only the adhesive layer 151 applied to the annular nonwoven fabric 150), the adhesion position of the lower surface side gel portion 132 to the chest Is securely fixed. When the biological electrode 100 is used, the conductive gel layer 130 transmits an electrocardiogram signal (electrical excitation of the heart), which is a minute electromotive force generated by the activity of the subject's heart, to the electrode unit 120.

  In addition, the conductive gel layer 130 does not necessarily have adhesiveness. In that case, the conductive gel layer 130 only contacts without being adhered to the chest when the biological electrode 100 is mounted.

  In order to maintain the shape of the conductive gel layer 130 between the upper surface side gel part 131 and the lower surface side gel part 132 of the conductive gel layer 130, the surface area substantially the same as that of the upper surface side gel part 131 and the lower surface side gel part 132. An intermediate base material 133 is provided which is a very thin mesh-like nonwoven fabric having More specifically, the conductive gel layer 130 is formed by causing the gel to exude from the one surface side (front side) of the intermediate base material 133 to the other surface side (back side) of the intermediate base material 133. Therefore, in the conductive gel layer 130, the upper surface side gel portion 131, the lower surface side gel portion 132, and the intermediate base material 133 are integrally formed, and these are not separated. That is, the upper surface side gel part 131 and the lower surface side gel part 132 do not move relative to the intermediate base material 133.

  The disk-shaped nonwoven fabric 140 covers and protects the members of the bioelectrode 100. That is, the disk-shaped nonwoven fabric 140 functions as a covering material that covers each member of the biological electrode 100 and covers the attachment site of the subject when the biological electrode 100 is attached to the subject. The disk-shaped non-woven fabric 140 has a large number of ventilation pores (not shown), and the moisture absorbed by the conductive gel layer 130 due to sweating of the subject through these pores is evaporated to the outside air. .

  The annular nonwoven fabric 150 exposes a part of the gel layer 130 from the lower surface side gel part 132 of the conductive gel layer 130 and covers the remaining part. More specifically, the annular nonwoven fabric 150 has a circular opening 152, and the conductive gel layer 130 is sandwiched between the disk-shaped nonwoven fabric 140 while exposing a part of the conductive gel layer 130 through the opening 152. Secure with. The upper surface of the annular nonwoven fabric 150 is bonded to the lower surface of the disk-shaped nonwoven fabric 140 by an adhesive layer 141 applied to the disk-shaped nonwoven fabric 140. Moreover, the cyclic | annular nonwoven fabric 150 affixes the bioelectrode 100 on a subject's chest by the adhesive layer 151 apply | coated to the lower surface.

  The separator 160 is made of, for example, a resin film that does not allow moisture to pass through. Each lower surface (each surface) of the conductive gel layer 130 and the pressure-sensitive adhesive layers 141 and 151 (or the conductive gel layer 130 and the pressure-sensitive adhesive layer 151) before use. In a sealed state, the bioelectrode 100 is prevented from drying when not in use to prevent a decrease in adhesive force. When the bioelectrode 100 is used, the separator 160 is peeled off from the surfaces of the conductive gel layer 130 and the pressure-sensitive adhesive layers 141 and 151 (or the conductive gel layer 130 and the pressure-sensitive adhesive layer 151), and this surface is applied to the chest of the subject. By being attached, the biological electrode 100 is attached to the subject.

  The overall configuration of the biological electrode 100 has been described above.

  In the above description, the bioelectrode 100 according to the present embodiment is configured such that the conductive gel layer 130 and the adhesive layers 141 and 151 can contact the chest, but the outer diameter of the annular nonwoven fabric 150 is a disc. If the biomedical electrode 100 is used, only the pressure-sensitive adhesive layer 151 constitutes the surface layer in contact with the chest while the bioelectrode 100 is used, and the outer diameter of the annular non-woven fabric 150 is a disc. If the diameter is smaller than the non-woven fabric 140, both the pressure-sensitive adhesive layers 141 and 151 constitute the surface layer that comes into contact with the chest together with the conductive gel layer 130 during use of the bioelectrode 100. When the bioelectrode 100 employs a configuration that does not use the annular nonwoven fabric 150, only the pressure-sensitive adhesive layer 141 constitutes a surface layer that contacts the chest with the conductive gel layer 130.

[Main part configuration]
Next, the configuration of the main part of the biological electrode 100 will be described. Here, a case where the conductive gel layer 130 and the pressure-sensitive adhesive layer 151 constitute a surface layer that comes into contact with a living body (that is, a subject) during use of the biological electrode 100 will be described as an example.

  FIG. 2 is a cross-sectional view schematically showing a main part of the biological electrode 100 according to the present embodiment.

  As described above, the surface layer that comes into contact with the living body during use of the biological electrode 100 includes the conductive gel layer 130 and the adhesive layer 151. In the present embodiment, only the pressure-sensitive adhesive layer 151 among these layers contains the antihistamine substance AH. That is, the adhesive layer 151 includes a material obtained by mixing an antihistamine substance AH with an adhesive. An outer periphery in which the adhesive layer 151 is disposed around the conductive gel layer 130 in the region of the disk-shaped nonwoven fabric 140 as a coating material by mixing the antihistamine substance AH with the adhesive constituting the adhesive layer 151. In the region, the antihistamine substance AH can be evenly dispersed throughout.

  As antihistamine substance AH, stevia fermented extract or its oil-soluble component etc. are mentioned, for example (for example, refer patent documents 2, 3).

  In the adhesive layer 151, the antihistamine substance AH is preferably enclosed in microcapsules and mixed with the adhesive as particles. An example of a microcapsule is a liposome. Liposomes are microcapsules having a diameter of 25 to 1000 nm having a structure in which a plurality of phospholipid membranes are layered to imitate the lipid bilayer membrane of a cell membrane. In addition to the antihistamine substance AH, a moisturizing component (such as hydrolyzed collagen) may be encapsulated in the particles.

[effect]
The antihistamine substance AH contained in the pressure-sensitive adhesive layer 151, particularly the antihistamine substance AH contained near the surface of the pressure-sensitive adhesive layer 151, can flow little by little in the pressure-sensitive adhesive layer 151, and during use of the bioelectrode 100. Gradually, it penetrates into the skin of the subject's chest through the surface of the pressure-sensitive adhesive layer 151 together with moisture in the pressure-sensitive adhesive layer 151. The antihistamine substance AH that has penetrated into the skin exhibits an antihistamine action in the skin. Since the antihistamine substance AH can permeate into the skin gradually from the adhesive layer 151 over time, the antihistamine action can be maintained for a long time. It is possible to suppress the occurrence of itchiness. When the method of gradually oozing out the antihistamine substance AH from the microcapsule after penetrating into the skin, the antihistamine action can be maintained for a longer time. In addition, it is not necessary to perform additional treatment for suppressing itching before the bioelectrode 100 is mounted.

  In particular, a part of the antihistamine substance AH (eg, stevia fermentation extract oil-soluble component (such as triterpene)) is encapsulated in the liposome and mixed with the adhesive layer 151, and the remaining antihistamine substance AH (eg, stevia fermentation extract) is added to the liposome. When the adhesive layer 151 is mixed without being encapsulated in the anti-histamine action, the anti-histamine action of the latter can be exerted in a short time, and the anti-histamine action of the former can be exerted with a delay. Can be kept constant.

  In the present embodiment, the antihistamine substance AH is contained in the pressure-sensitive adhesive layer 151 among the surface layers that come into contact with the living body during use of the biological electrode 100. The pressure-sensitive adhesive layer 151 is a portion where it is easy to cause itching by sticking firmly to the skin. Thus, it can be expected that the occurrence of itch is more reliably suppressed by including the antihistamine substance AH directly in the portion where itch is easily generated.

  Further, in this embodiment, by setting the amount of the antihistamine substance AH contained in the conductive gel layer 130 to 0, the influence on the conductivity, which is the most important characteristic in terms of the function of the conductive gel layer 130, can be surely avoided. can do.

  In the present embodiment, the anti-histamine AH that exhibits an antihistamine action as an anti-inflammatory substance is exemplified as an anti-inflammatory substance. However, any anti-histamine substance that exhibits an anti-inflammatory action can be used. Even a substance different from the substance AH can be used.

In this embodiment, the bioelectrode 100 used for electrocardiogram measurement is taken as an example of a medical sensor. However, a medical sensor used for biometric information measurement is a sensor different from the bioelectrode 100. However, it can be adopted. Examples of medical sensors that can be employed differently from the biological electrode 100 include, for example, an impedance electrode that is attached to the body surface of the subject and used for measuring the respiratory waveform of the subject, a finger of the subject, Examples thereof include a pulse oximeter that is attached to the ear or nose and used for measuring the SpO ₂ of the subject.

  Hereinafter, modifications of the present embodiment will be described focusing on differences from the contents of the present embodiment.

(Modification 1 of Embodiment 1)
FIG. 3 is a cross-sectional view schematically showing a main part of Modification 1 of biological electrode 100 according to Embodiment 1.

  In the present modification, only the conductive gel layer 130 among the surface layers that come into contact with the living body during use of the biological electrode 100 contains the antihistamine substance AH. That is, the conductive gel layer 130 includes a material obtained by mixing an antihistamine substance AH with a gel having conductivity. By mixing the anti-histamine substance AH with the gel constituting the conductive gel layer 130, the entire region of the disc-shaped non-woven fabric 140 as a coating material in the central region where the conductive gel layer 130 is disposed is antihistamine. The substance AH can be evenly dispersed.

  The antihistamine substance AH contained in the conductive gel layer 130, particularly the antihistamine substance AH contained in the vicinity of the surface of the conductive gel layer 130, can flow little by little in the conductive gel layer 130. Gradually, it penetrates into the skin of the subject's chest through the surface of the conductive gel layer 130 together with moisture in the conductive gel layer 130. Therefore, as in the first embodiment, this modified example 1 also suppresses the occurrence of itchiness at the wearing site of the subject during use of the bioelectrode 100 without causing the medical staff to take extra time. can do.

  Since the gel constituting the conductive gel layer 130 is generally lower in viscosity than the adhesive constituting the pressure-sensitive adhesive layer 151, the antihistamine substance AH is contained in the conductive gel layer 130 rather than inside the pressure-sensitive adhesive layer 151. The inside is easier to flow. In addition, the conductive gel layer 130 is more likely to penetrate moisture into the skin than the adhesive layer 151. Therefore, the antihistamine substance AH can be more easily penetrated into the skin by containing the antihistamine substance AH in the conductive gel layer 130 than by containing the antihistamine substance AH in the adhesive layer 151.

  Further, in this modification, by setting the amount of the antihistamine substance AH to be contained in the pressure-sensitive adhesive layer 151 to 0, the influence on the pressure-sensitive adhesiveness, which is the most important characteristic of the pressure-sensitive adhesive layer 151, is surely avoided. be able to. Since adhesiveness can be reliably ensured in the outer peripheral region, it is possible to maintain the difficulty of peeling as the entire bioelectrode 100.

(Modification 2 of Embodiment 1)
FIG. 4 is a cross-sectional view schematically showing the main part of Modification 2 of biological electrode 100 according to Embodiment 1.

  This modification is a combination of the structure of Embodiment 1 and the structure of Modification 1. That is, the antihistamine substance AH is contained in both the conductive gel layer 130 and the pressure-sensitive adhesive layer 151 that constitute the surface layer that comes into contact with the living body during use of the biological electrode 100.

  In this case, both the effect obtained by the configuration of Embodiment 1 and the effect obtained by the configuration of Modification 1 can be realized. For example, in this modification, the antihistamine substance AH can penetrate into the skin both from the central region where the conductive gel layer 130 is disposed and from the outer peripheral region where the adhesive layer 151 is disposed around the central region.

  In this modification, the concentration of the antihistamine substance AH in the conductive gel layer 130 may be lower than the concentration of the antihistamine substance AH in the adhesive layer 151, as shown in the figure. Conversely, it may be high or equivalent. What is necessary is just to determine the density | concentration in each area | region based on the desired characteristic.

(Modification 3 of Embodiment 1)
FIG. 5 is a cross-sectional view schematically showing a main part of Modification 3 of biological electrode 100 according to Embodiment 1.

  Although this modification is common to Modification 1 of Embodiment 1 in that the antihistamine substance AH is contained in the surface layer in the central region, it is made of an antihistamine substance-containing material instead of being mixed with the conductive gel layer 130. This is different from Modification 1 of Embodiment 1 in that the antihistamine substance-containing material layer 171 is applied to the entire surface of the conductive gel layer 130.

  That is, in this modification, the antihistamine substance AH is applied to the entire surface of the conductive gel layer 130. As described above, since the antihistamine substance-containing material layer 171 is applied to the entire surface of the conductive gel layer 130, the antihistamine substance-containing material layer 171 of the present modification is at least similar to the gel of the conductive gel layer 130. It is necessary to include a conductive material.

  In the present modification, the antihistamine substance AH can be concentratedly arranged near the surface of the surface layer without being dispersedly arranged in the thickness direction of the surface layer, so that penetration into the skin can be facilitated.

  The configuration of this modified example can be implemented in combination with the configuration of the first embodiment or the configurations of the modified examples 1 and 2 as appropriate.

(Modification 4 of Embodiment 1)
FIG. 6 is a cross-sectional view schematically showing a main part of Modification 4 of biological electrode 100 according to Embodiment 1.

  Although this modification is common to Modification 3 of Embodiment 1 in that it uses an antihistamine substance-containing material layer 172 made of an antihistamine substance-containing material, instead of applying to the entire surface of the conductive gel layer 130, It is different from Modification 3 of Embodiment 1 in that it is applied to the entire surface of the pressure-sensitive adhesive layer 151.

  That is, in this modification, the antihistamine substance AH is adhered to the entire surface of the adhesive layer 151. Thus, since the antihistamine substance-containing material layer 172 is applied to the entire surface of the adhesive layer 151, the antihistamine substance-containing material layer 172 of the present modification is similar to the adhesive of the adhesive layer 151. It is necessary to include at least an adhesive material.

  In this modification, as in Modification 3 of Embodiment 1, the antihistamine substance AH can be concentrated and arranged near the surface of the surface layer without being dispersedly arranged in the thickness direction of the surface layer. Penetration can be facilitated.

  The configuration of this modified example can be implemented in combination with the configuration of the first embodiment or the configurations of the modified examples 1 and 2 as appropriate.

(Modification 5 of Embodiment 1)
FIG. 7 is a cross-sectional view schematically showing a main part of Modification 5 of biological electrode 100 according to Embodiment 1.

  This modification is common to Modification 4 of Embodiment 1 in that the antihistamine substance-containing material layer 173 is applied to the surface of the pressure-sensitive adhesive layer 151, but not the entire surface of the pressure-sensitive adhesive layer 151. It differs from Modification 4 of Embodiment 1 in that it is applied to a part of the surface.

  That is, in this modification, the antihistamine substance AH is attached to a part of the surface of the adhesive layer 151. Thus, since the antihistamine substance-containing material layer 173 is applied to a part of the surface of the adhesive layer 151, the antihistamine substance-containing material layer 173 of the present modification is the same as the adhesive of the adhesive layer 151. However, since it does not necessarily cover the entire surface, the necessity for the antihistamine substance-containing material layer 173 to be sticky is a modification of the first embodiment. This is lower than that of the anti-histamine substance-containing material layer 172.

  In this modification, the antihistamine substance AH can be concentratedly arranged near the surface of the surface layer without being dispersedly arranged in the thickness direction of the surface layer, similarly to the modifications 3 and 4 of the first embodiment. Can be easily penetrated into.

  The configuration of this modified example can be implemented in combination with the configuration of the first embodiment or the configurations of the modified examples 1 and 2 as appropriate.

(Modification 6 of Embodiment 1)
FIG. 8A is a bottom view schematically showing the bottom surface of the main part of the sixth modified example of the biological electrode 100 according to Embodiment 1, and FIG. 8B is a sectional view taken along the line VIII-VIII. It is.

  This modification is common to Modification 3 of Embodiment 1 in that the antihistamine substance-containing material layer 174 is applied to the surface of the conductive gel layer 130, but not the entire surface of the conductive gel layer 130. It differs from Modification 3 of Embodiment 1 in that it is applied to a part of the surface.

  That is, in this modification, the antihistamine substance AH is attached to a part of the surface of the conductive gel layer 130. As described above, since the antihistamine substance-containing material layer 174 is applied to a part of the surface of the conductive gel layer 130, the antihistamine substance-containing material layer 174 of this modification is similar to the gel of the conductive gel layer 130. However, it is preferable to include at least a conductive material, but the entire surface is not covered. Therefore, the necessity for the antihistamine substance-containing material layer 174 to be conductive is the third modification of the first embodiment. This is lower than the antihistamine substance-containing material layer 171.

  In this modification, the antihistamine substance-containing material layer 174 is arranged in a ring shape, but the arrangement may be different, for example, a spot shape.

  The configuration of this modified example can be implemented in combination with the configuration of the first embodiment or the configurations of the modified examples 1, 2, 4, and 5 as appropriate.

(Modification 7 of Embodiment 1)
FIG. 9A is a bottom view schematically showing the bottom surface of the main part of the seventh modified example of the biological electrode 100 according to Embodiment 1, and FIG. 9B is a sectional view taken along the line IX-IX. It is.

  This modification is common to Modifications 1, 3, and 6 of Embodiment 1 in that the antihistamine substance-containing material layer 175 is used on the surface layer of the central region. Instead of being applied to the surface of the gel layer 130, it is embedded in the conductive gel layer 130, and is different from the first, third, and sixth modifications of the first embodiment.

  The antihistamine substance-containing material layer 175 of this embodiment is a member in which a fiber string kneaded with the antihistamine substance AH is knitted in a mesh shape. The use of such a member containing the antihistamine substance AH may be embedded in the adhesive layer 151 instead of being embedded in the conductive gel layer 130, but the conductive gel layer in which the antihistamine substance AH is more likely to flow. Embedding in 130 is advantageous in that the antihistamine substance AH can reach the skin faster.

  In FIG. 9, the antihistamine substance-containing material layer 175 is embedded in the deepest part of the conductive gel layer 130, but may be embedded in a position other than the deepest part. Further, the shape may not be a mesh shape, and the arrangement of the antihistamine substance-containing material layer 175 in the conductive gel layer 130 may be arranged as long as the characteristics of the conductive gel layer 130, particularly the conductivity, are not hindered. May be. It goes without saying that the antihistamine substance-containing material layer 175 may have the same characteristics as the conductive gel layer 130, in particular, conductivity.

  Further, as exemplified in the first embodiment, when the conductive gel layer 130 has an intermediate base material 133 (see FIG. 1), the intermediate base material 133 is made of an antihistamine substance-containing material. The layer 175 may be used. In this case, an increase in the number of parts can be avoided.

(Other variations of the first embodiment)
In the above-described embodiment and modifications, the region where the concentration of the antihistamine substance AH is differentiated is divided in the radial direction, but the manner of division can be variously changed. For example, the antihistamine substance AH may be contained in a band-shaped region crossing the region of the covering material, and the antihistamine substance AH may not be contained in the remaining region.

  In the present embodiment and each modification described above, the antihistamine substance AH is mixed with at least one of the conductive gel layer 130 area and the adhesive layer 151 area, or the antihistamine substance-containing material is mixed. Although the layers 171 to 175 are deposited or embedded, the antihistamine substance AH only needs to be contained in at least a part of the surface layer region. That is, for example, the surface layer region is divided into a region of the conductive gel layer 130, a region of the adhesive layer 151, and a region different from any of these regions, and the antihistamine substance-containing material layer is formed in a region different from any of these regions. It may be provided.

(Embodiment 2)
The second embodiment of the present invention will be described below.

[overall structure]
FIG. 10 is an exploded perspective view showing a configuration of biological electrode 200 according to the present embodiment. In the present embodiment, the “upper surface” means a surface that faces in a direction opposite to the surface of the biological electrode 200 attached to the subject, and the “lower surface” means the subject of the biological electrode 200. It means the surface that goes in the direction of the surface to be attached.

  In FIG. 10, the biological electrode 200 mainly includes a base material 210, an electrode part 220, a conductive gel layer 230, a silver film 240, a carbon film 250, a resist film 260, a nonwoven fabric 270, and a separator 280. Have.

  The base material 210, the electrode part 220, the silver film 240, the carbon film 250, and the resist film 260 each have an elongated portion that is elongated and the elongated portion records an electrocardiogram signal detected from the subject. It functions as a lead wire for transmission (not shown).

  The substrate 210 is made of a film-like film material such as PET, and has a pair of upper and lower surfaces. The base member 210 is provided with an electrode part 220 on its lower surface, and a silver film 240, a carbon film 250, and a resist film 260 on its upper surface, and forms the core of the sensor part and the lead wire of the biological electrode 200.

  The electrode unit 220 is made of a material such as silver-silver chloride (Ag—AgCl), and is disposed between the lower surface of the substrate 210 and the conductive gel layer 230. The electrode unit 220 detects an electrocardiogram signal transmitted from the conductive gel layer 230 and transmits it to a recording device (not shown).

  The conductive gel layer 230 is a gel layer having conductivity, adhesiveness, and hygroscopic expansion. The conductive gel layer 230 has the electrode part 220 interposed between the upper surface side gel part 231 and the lower surface of the base material 210, and covers the lower surface of the base material 210 with the adhesive force of the conductive gel layer 230 on the base material 210. Glued. The surface area of the conductive gel layer 230 is larger than the surface area of the substrate 210, and the conductive gel layer 230 has a region protruding from the peripheral edge of the substrate 210, specifically, the same region as the nonwoven fabric 270. The conductive gel layer 230 is bonded to the lower surface of the nonwoven fabric 270 by its own adhesive force and the adhesive force of the adhesive layer 271 applied to the lower surface of the nonwoven fabric 270. The conductive gel layer 230 has its lower surface side gel portion 232 bonded to the chest of the subject by its own adhesive force, and its position is fixed. When the biological electrode 200 is used, the conductive gel layer 230 transmits an electrocardiogram signal (heart electrical excitation), which is a minute electromotive force generated by the activity of the subject's heart, to the electrode unit 220.

  Between the upper gel portion 231 and the lower gel portion 232 of the conductive gel layer 230, an intermediate base material 233, which is an extremely thin mesh-like nonwoven fabric, is provided in order to maintain the shape of the conductive gel layer 230. .

  The silver film 240 is provided, for example, by printing at a position facing the electrode unit 220 on the upper surface of the substrate 210. The silver film 240 shields electromagnetic waves generated outside the biological electrode 200 and reduces the influence of noise on the electrode unit 220 due to the electromagnetic waves. The silver film 240 has an extremely small electric resistance value and prevents static electricity (charging) in the biological electrode 200.

  The carbon film 250 is provided on the upper surface of the substrate 210 by, for example, printing so as to cover the silver film 240, that is, to completely cover the upper surface and side surfaces of the silver film 240. The carbon film 250 has an electric resistance value (about 1000 times) that is significantly larger than that of the silver film 240, and, like the silver film 240, shields electromagnetic waves and reduces the influence of noise on the electrode portion 220. . Further, the carbon film 250 covers the silver film 240 to prevent the silver film 240 from being chemically bonded to other substances such as oxygen and sulfur to be deteriorated. Note that a film of a conductive material such as aluminum or copper may be formed instead of the carbon film 250.

  On the upper surface of the substrate 210, the printing area of the silver film 240 is significantly smaller than the printing area of the carbon film 250. More specifically, the silver film 240 is printed in an extremely thin fine line shape at a position facing the electrode portion 220 on the upper surface of the base 210, and the carbon film 250 covers the silver film 240 and covers the base 210. It is printed on the top surface. As a result, the carbon film 250 can enjoy the extremely high electromagnetic wave shielding ability and antistatic ability of the silver film 240. That is, the carbon film 250 can exhibit electromagnetic wave shielding ability and static electricity prevention ability higher than those of the carbon film 250 itself. As described above, the silver film 240 and the carbon film 250 function as a high-performance conductive shield film of the electrode unit 220 provided on the upper surface of the substrate 210.

  The resist film 260 seals a shield film made of the silver film 240 and the carbon film 250. That is, the resist film 260 is provided on the upper surface of the base 210 so as to completely cover the upper surface and side surfaces of the shield film made of the silver film 240 and the carbon film 250. The resist film 260 is a non-conductive insulating film, and blocks electrical conduction from the upper surface side of the base 210 to the silver film 240 and the carbon film 250, and thus to the electrode part 220.

  The nonwoven fabric 270 covers and protects each member of the bioelectrode 200. That is, the non-woven fabric 270 functions as a covering material that covers each member of the biological electrode 200 and covers the attachment site of the subject when the biological electrode 200 is attached to the subject. The nonwoven fabric 270 has a large number of ventilation pores (not shown), and moisture absorbed by the conductive gel layer 230 due to sweating of the subject is evaporated to the outside air through these pores. In addition, the non-woven fabric 270 adheres the biological electrode 200 to the chest of the subject with an adhesive layer 271 made of an adhesive applied to the lower surface thereof.

  The separator 280 is made of, for example, a resin film that does not allow moisture to pass through. The separator 280 is adhered to the lower surface of the conductive gel layer 230 before use, and prevents the bioelectrode 200 from drying when the bioelectrode 200 is not used. To prevent the loss of When the biological electrode 200 is used, the separator 280 is peeled off from the surface of the conductive gel layer 230, and this surface is attached to the chest of the subject, so that the biological electrode 200 is attached to the subject.

  The overall configuration of the biological electrode 200 has been described above.

  In the present embodiment, the diameter of the nonwoven fabric 270 and the diameter of the conductive gel layer 230 are the same. Therefore, only the conductive gel layer 230 comes into contact with the chest during use of the bioelectrode 200. That is, the present embodiment is different from the first embodiment in that an adhesive layer that adheres to the subject is not provided separately from the conductive gel layer 130. Therefore, the conductive gel layer 230 of this embodiment is required to have the same degree of adhesiveness as that of the pressure-sensitive adhesive layer 151 described in the first embodiment.

[Main part configuration]
Next, the configuration of the main part of the biological electrode 200 will be described.

  FIG. 11 is a cross-sectional view schematically showing a main part of the biological electrode 200 according to the present embodiment.

  As described above, the conductive gel layer 230 is the only surface layer that comes into contact with the living body during use of the biological electrode 200. In the present embodiment, the conductive gel layer 230 contains the antihistamine substance AH. The details of the antihistamine substance AH are the same as those in the first embodiment, and a detailed description thereof is omitted here.

  That is, the conductive gel layer 230 includes a material obtained by mixing a gel having conductivity and the antihistamine substance AH. By mixing the antihistamine substance AH with the gel constituting the conductive gel layer 230, the antihistamine substance AH can be evenly dispersed in the entire region of the nonwoven fabric 270 as the covering material.

[effect]
The antihistamine substance AH contained in the conductive gel layer 230, in particular, the antihistamine substance AH contained near the surface of the conductive gel layer 230 can flow little by little in the conductive gel layer 230. Gradually, it penetrates into the skin of the subject's chest through the surface of the conductive gel layer 230 together with moisture in the conductive gel layer 230. The antihistamine substance AH that has penetrated into the skin exhibits an antihistamine action in the skin. Since the antihistamine substance AH can permeate into the skin from the conductive gel layer 230 little by little over time, the antihistamine action can be maintained for a long time, and the wearing site of the subject during use of the bioelectrode 200 It is possible to suppress the occurrence of itchiness. When the method of gradually oozing out the antihistamine substance AH from the microcapsule after penetrating into the skin, the antihistamine action can be maintained for a longer time. In addition, it is not necessary to perform additional treatment for suppressing itching before the bioelectrode 200 is mounted.

  In particular, as described in the first embodiment, a part of the antihistamine substance AH (for example, stevia fermented extract oil-soluble component (such as triterpene)) is encapsulated in the liposome and mixed with the conductive gel layer 230, and the remaining antihistamine is mixed. When the substance AH (for example, stevia fermented extract) is mixed with the conductive gel layer 230 without being encapsulated in the liposome, the antihistamine action by the latter can be exhibited in a short time, and the antihistamine action by the former can be exhibited with a delay. And the degree of antihistamine action can be kept constant over a long period of time.

  Moreover, in this Embodiment, since antihistamine substance AH is contained in the whole surface layer which contacts a biological body during use of living body electrode 200, it exhibits an antihistamine action to the whole wearing part of a subject. Can do.

  Hereinafter, modifications of the present embodiment will be described focusing on differences from the contents of the present embodiment.

(Modification 1 of Embodiment 2)
FIG. 12 is a cross-sectional view schematically showing a main part of Modification 1 of biological electrode 200 according to Embodiment 2.

  In this modification, the conductive gel layer 230 (see FIGS. 10 and 11) is divided into an outer peripheral region side (outer peripheral conductive gel layer 230a) and a central region side (central conductive gel layer 230b). Of these, only the outer peripheral conductive gel layer 230a contains the antihistamine substance AH. In addition, the outer peripheral side conductive gel layer 230a and the center side conductive gel layer 230b are mutually the same in the point containing the gel which has electroconductivity, adhesiveness, and a hygroscopic expansion property. That is, the outer peripheral side conductive gel layer 230a includes a material obtained by mixing a gel having conductivity and the antihistamine substance AH. By mixing the antihistamine substance AH with the gel only in the outer peripheral region while leaving the central region, priority is given to exerting antihistamine action in the outer peripheral region, and priority is given to avoiding influence on conductivity and adhesiveness in the central region. be able to.

  Incidentally, as a method of forming the outer peripheral side conductive gel layer 230a and the central side conductive gel layer 230b, for example, not only the outer peripheral portion of the outer peripheral side conductive gel 230a but also the annular portion serving as the boundary with the central side conductive gel layer 230b is banked. First, the stock solution of the outer conductive gel layer 230a is poured into the outer peripheral region to be gelled, and the bank is removed, and the stock solution of the central conductive gel layer 230b is poured into the central region to be gelled.

  For example, if the outer peripheral side conductive gel layer 230a and the central side conductive gel layer 230b are formed by such a method, the outer peripheral side conductive gel layer 230a is preliminarily adhered to each other without interposing another member. Even if only the antihistamine substance AH is contained, the antihistamine substance AH can be diffused into the central region where the central conductive gel layer 230b is disposed as time passes. Therefore, actually, an antihistamine action can be exhibited also in the central region.

(Modification 2 of Embodiment 2)
FIG. 13 is a cross-sectional view schematically showing a main part of Modification 2 of biological electrode 200 according to Embodiment 2.

  In this modification, contrary to Modification 1 of Embodiment 2, only the central side conductive gel layer 230b contains the antihistamine substance AH. That is, the central conductive gel layer 230b includes a material obtained by mixing a gel having conductivity and the antihistamine substance AH. By mixing the antihistamine substance AH with the gel only in the central region while leaving the outer peripheral region, priority is given to exerting antihistamine action in the central region, and priority is given to avoiding the influence on conductivity and adhesiveness in the peripheral region. be able to. Since the adhesiveness in the outer peripheral region can be reliably ensured, it is possible to maintain the difficulty of peeling as the entire bioelectrode 200.

  Further, as in the first modification of the second embodiment, when the outer peripheral side conductive gel layer 230a and the central side conductive gel layer 230b are formed in close contact with each other without interposing another member, the central side in advance Even if the antihistamine substance AH is contained only in the conductive gel layer 230b, the antihistamine substance AH can be diffused into the outer peripheral region where the outer peripheral conductive gel layer 230a is disposed as time passes. Therefore, in practice, the antihistamine action can be exhibited also in the outer peripheral region.

(Modification 3 of Embodiment 2)
FIG. 14 is a cross-sectional view schematically showing a main part of Modification 3 of biological electrode 200 according to Embodiment 2.

  This modification is a combination of the modifications 1 and 2 of the second embodiment. That is, the antihistamine substance AH is contained in both the outer peripheral side conductive gel layer 230a and the central side conductive gel layer 230b constituting the surface layer that comes into contact with the living body during use of the biological electrode 200.

  In this case, any of the effects obtained by the configurations of the first and second modifications of the second embodiment can be realized. For example, in this modification, the antihistamine substance AH is allowed to penetrate into the skin both from the central region where the central conductive gel layer 230b is disposed and from the peripheral region where the peripheral conductive gel layer 230a is disposed around the central region. Can do.

  In this modification, the concentration of the antihistamine substance AH in the central conductive gel layer 230b may be lower than the concentration of the antihistamine substance AH in the outer conductive gel layer 230a as shown in the figure. On the contrary, it may be high. Although these concentrations may be equal to each other, in this case, it is advantageous to make some characteristics different, for example, by making the adhesive force different between the central conductive gel layer 230b and the outer peripheral conductive gel layer 230a. Needless to say, even when the concentrations of the antihistamine AH in each region are not equal to each other, the adhesive strength of each region may be different. What is necessary is just to determine the density | concentration of the antihistamine substance AH in each area | region based on the desired characteristic.

(Other Modifications of Embodiment 2)
The structure in which the antihistamine substance-containing material layer is deposited on the conductive gel layer 230 as described in the modified examples 3 to 6 of the first embodiment, and the anti-histamine described in the modified example 7 of the first embodiment. A configuration in which a member containing the histamine substance AH is embedded in the conductive gel layer 230 can be employed as a modification of the biological electrode 200 according to the second embodiment.

  Further, in the above-described embodiment and each of the modifications, the region where the concentration of the antihistamine substance AH is differentiated is divided in the radial direction, but the manner of division can be variously changed. For example, the antihistamine substance AH may be contained in a band-shaped region crossing the region of the covering material, and the antihistamine substance AH may not be contained in the remaining region.

  Further, in the present embodiment and each modification described above, the antihistamine substance AH is mixed with at least a part of the region of the conductive gel layer 230, or the antihistamine substance-containing material layer is attached or embedded. However, the antihistamine AH only needs to be contained in at least a part of the surface region. That is, for example, the surface layer region may be divided into a region of the conductive gel layer 230 and a region different from this, and an antihistamine substance-containing material layer may be provided in a region different from the region of the conductive gel layer 230. .

(Embodiment 3)
Hereinafter, as a third embodiment of the present invention, a medical sensor auxiliary tool that can be attached to a living body together with a medical sensor used for measuring biological information, more specifically, covers the suction cup portion of an adsorption-type biological electrode and covers the living body. The case where this invention is applied to the bioelectrode cover attached to an electrode is demonstrated.

  FIG. 15A is a perspective view showing the configuration of the biological electrode 300 according to the present embodiment, and FIG. 15B is a perspective view showing the configuration of the biological electrode cover 350 according to the present embodiment. FIG. 15C is a perspective view showing a state in which the bioelectrode cover 350 is attached to the bioelectrode 300. In the present embodiment, the “upper surface” means a surface that faces in the direction opposite to the body surface of the subject when the biological electrode 300 is attached to the subject, and the “lower surface” means the biological electrode. It means a surface that faces the direction of the body surface of the subject when 300 is attached to the subject.

  In FIG. 15A, the biological electrode 300 includes a grip part 310, an electrode part 320, and a lead wire connection part 330.

  The grip portion 310 is a member that can be picked when the bioelectrode 300 is gripped, and is a hollow sphere made of rubber, for example. A cylindrical body is continuously provided at the lower portion, and the electrode part 320 is connected to the cylindrical body. The electrode part 320 is a conductive, e.g., metal bowl-shaped electrode (more specifically, a bowl-shaped shape). A cylindrical body that can be inserted into the cylindrical body of the gripping section 310 is provided on the top of the electrode section 320. When the electrode part 320 is connected to the grip part 310 by inserting a cylindrical body, the internal space of the electrode part 320 communicates with the internal space of the grip part 310. Therefore, when the biological electrode 300 is attached to the subject, the electrode portion 320 (or the lower surface portion 360 of the biological electrode cover 350 placed thereon) (see FIG. 15 (b))) is brought into close contact with the chest which is the wearing site of the subject and the gripping part 310 is released, the skin of the chest is brought into the electrode part 320 as the gripping part 310 swells due to its elastic restoring force. The bioelectrode 300 is absorbed by the skin.

  Connected to the lead wire connecting portion 330 is a lead wire (not shown) for transmitting an electrocardiogram signal detected from the subject through the electrode portion 320 to a recording device (not shown).

  In FIG. 15B, the bioelectrode cover 350 has a columnar gripping portion on the outer periphery of a hollow truncated cone shape having a lower surface portion 360 having an opening (not shown) in the center and an upper surface portion 370 having an opening 371 in the center. 380 has a projecting configuration. The bioelectrode cover 350 is integrally formed of a material having conductivity and flexibility (flexibility).

  When the gripping part 380 is picked and the edge of the opening 371 on the side facing the gripping part 380 is picked and the opening 371 is widened by separating them, the electrode part 320 is accommodated in the internal space of the bioelectrode cover 350 through the opening 371. By doing so, the bioelectrode cover 350 can be covered with the electrode part 320 (refer FIG.15 (c)). That is, the upper surface portion 370 of the bioelectrode cover 350 functions as a bioelectrode attachment portion.

  In the bioelectrode cover 350, the upper surface portion 370 is provided with an opening 371, and the lower surface portion 360 is also provided with an opening (not shown). The biological electrode 300 can be adsorbed to the skin by the same method as described above even in the state where the part 320 is covered. At this time, the lower surface portion 360 of the bioelectrode cover 350 functions as a surface layer that comes into contact with the living body during use of the bioelectrode 300.

  In the present embodiment, the bioelectrode cover 350 is made of, for example, a material in which an electrolytic gel obtained by mixing an antihistamine substance AH (see FIG. 16) with a urethane resin porous body is impregnated. The details of the antihistamine substance AH are the same as in the first and second embodiments, and thus detailed description thereof is omitted here.

  The bioelectrode cover 350 includes a material obtained by mixing a material having conductivity and flexibility (flexibility) with an antihistamine substance AH. In this way, the antihistamine substance AH is mixed with the main body of the bioelectrode cover 350 that can be attached to the bioelectrode 300, so that the entire lower surface portion 360 that constitutes the surface layer that comes into contact with the living body during use of the bioelectrode 300 is resistant. The histamine substance AH can be evenly dispersed.

  The antihistamine AH contained in the lower surface portion 360, particularly the antihistamine AH contained near the surface of the lower surface portion 360, can flow little by little in the electrolytic gel soaked in the body of the bioelectrode cover 350. During the use of 300, the skin of the subject's chest gradually penetrates through the surface of the lower surface portion 360 together with the moisture in the electrolytic gel. The antihistamine substance AH that has penetrated into the skin exhibits an antihistamine action in the skin. Since the antihistamine substance AH can permeate into the skin gradually from the lower surface portion 360 of the bioelectrode cover 350 over time, the antihistamine action can be maintained for a long time. It is possible to prevent itchiness from occurring in the person's wearing site. When the method of gradually oozing out the antihistamine substance AH from the microcapsule after penetrating into the skin, the antihistamine action can be maintained for a longer time. In addition, it is not necessary to perform additional treatment for suppressing itching before the bioelectrode 300 is attached.

  In particular, as described in the first and second embodiments, a part of the antihistamine substance AH (for example, stevia fermentation extract oil-soluble component (such as triterpene)) is encapsulated in liposomes and mixed with the main body of the bioelectrode cover 350, When the remaining antihistamine substance AH (eg, stevia fermented extract) is mixed with the body of the bioelectrode cover 350 without encapsulating in liposomes, the antihistamine action by the latter is exhibited in a short time, and the antihistamine action by the former is exhibited. It can be exerted with a delay, and the degree of antihistamine action can be kept constant for a long time.

  Moreover, in this Embodiment, since antihistamine substance AH is contained in the whole surface layer which contacts a biological body during use of biological electrode 300, it exhibits an antihistamine action with respect to the whole wearing part of a subject. Can do.

  Note that the antihistamine substance AH may be mixed only on the lower surface portion 360 of the bioelectrode cover 350 or locally on the lower surface portion 360.

  In the present embodiment, the bioelectrode cover 350 that assists the bioelectrode is taken as an example of the medical sensor assisting device. However, if the instrument has a function of assisting the medical sensor, the bioelectrode cover 350 and Can be used even if they are different. Examples of the medical sensor auxiliary tool that can be used differently from the bioelectrode cover 350 include a double-sided tape material that can be attached to the body surface of the subject together with the heart sound microphone.

  While the present invention has been described with reference to preferred embodiments and modifications thereof, it is apparent that various modifications can be made by those skilled in the art without departing from the spirit of the present invention.

  INDUSTRIAL APPLICABILITY The present invention can be suitably used in a medical instrument used by being attached to a living body during use and a medical sensor auxiliary tool that can be attached to a living body together with a medical sensor used for measuring biological information.

100, 200, 300 Bioelectrode 110, 210 Base material 120, 220, 320 Electrode part 130, 230 Conductive gel layer 230a Outer peripheral side conductive gel layer 230b Central side conductive gel layer 140 Disc-shaped nonwoven fabric 150 Annular nonwoven fabric 151 Adhesive layer 171 , 172, 173, 174, 175 Antihistamine substance-containing material layer 270 Non-woven fabric 350 Bioelectrode cover 360 Lower surface part 370 Upper surface part AH Antihistamine substance

Claims (12)

A medical device that can be worn on a living body,
A main body having a living body mounting portion for mounting the medical instrument on a living body;
The main body has a surface layer that comes into contact with a living body during use of the medical device,
The surface layer contains an anti-inflammatory substance,
Medical devices that can be worn on the body. The anti-inflammatory substance is an antihistamine;
The medical device which can be mounted | worn with the living body of Claim 1. The antihistamine substance includes stevia fermented extract and / or stevia fermented extract oil-soluble component,
The medical device which can be mounted | worn with the living body of Claim 2. It is a medical sensor used for measuring biological information.
The medical device which can be mounted | worn with the living body of Claim 1. A bioelectrode used for electrocardiogram measurement,
The medical device which can be mounted | worn with the living body of Claim 1. The surface layer includes a first region and a second region;
The concentration of the antihistamine substance in the surface layer is different between the first region and the second region.
The medical device which can be mounted | worn with the living body of Claim 1. The surface layer includes a central region in which a conductive gel layer is disposed in a region of a covering material that covers a mounting site, and an outer peripheral region in which a pressure-sensitive adhesive layer is disposed around the conductive gel layer in the region of the covering material. Have
The surface layer of at least one of the central region and the outer peripheral region contains the antihistamine substance,
The medical device which can be mounted | worn with the living body of Claim 5. The antihistamine substance is mixed with the conductive gel of the conductive gel layer in the central region, or is deposited on at least a part of the surface of the conductive gel, or the member containing the antihistamine substance is the conductive gel. Buried in the layer,
The medical device which can be mounted | worn with the biological body of Claim 7. The antihistamine substance is mixed with the pressure-sensitive adhesive of the pressure-sensitive adhesive layer in the outer peripheral region, or is applied to at least a part of the surface of the pressure-sensitive adhesive.
The medical device which can be mounted | worn with the biological body of Claim 7. The surface layer is a conductive gel layer disposed over the entire region of the covering material covering the mounting site,
The surface layer of the central region excluding the outer peripheral region in the region of the coating material contains the antihistamine substance.
The medical device which can be mounted | worn with the living body of Claim 5. The antihistamine substance is mixed with the conductive gel of the conductive gel layer in the central region, or is deposited on at least a part of the surface of the conductive gel, or the member containing the antihistamine substance is the conductive gel. Buried in the layer,
The medical device which can be mounted | worn with the living body of Claim 10. A medical sensor auxiliary tool that can be worn with a medical sensor used to measure biological information,
The body of the medical sensor auxiliary tool has a surface layer that comes into contact with a living body during use of the medical sensor,
The surface layer contains an anti-inflammatory substance,
Medical sensor aids.

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