JPH04272754A - Adhesive dressing - Google Patents

Abstract

PURPOSE:To provide the adhesive dressing which is used for dressing the sutured part after a surgical operation, wounds, etc., is applicable to actively moving parts, such as joints of hands and feet, does not require an exchange at the time of bathing or in contact with water, and prevents the wound surface, etc., against infection with bacteria. CONSTITUTION:The above-mentioned purposes are achieved by the adhesive dressing consisting of the material which is formed by laminating a thermoplastic elastomer, adhesive layer, and hydrophilic porous film or a water- absorptive non-woven fabric as an intermediate layer and to which a metal having an antimicrobial property is applied, as shown in Fig.

Description

[Detailed description of the invention]

0001

FIELD OF THE INVENTION This invention relates to adhesive dressings. Specifically, it is made of a thermoplastic elastomer membrane, a hypoallergenic adhesive, and a porous membrane treated to make it hydrophilic, allowing air and water vapor to pass through, but preventing water from entering and bacterial infection. The present invention relates to an adhesive dressing suitable for.

0002

[Prior Art] Wound dressings used to treat sutures and wounds after surgery can be easily manipulated, and even after being applied, the joints of the hands and feet can be easily flexed and stretched. There is no need to change it when bathing or showering, and it is necessary to prevent bacterial infection of the wound.

[0003] Conventionally, gauze, absorbent cotton, etc. have been used, but since they quickly absorb exudate, the wound surface becomes dehydrated and dry, resulting in the formation of a scab. At this time, the gauze or the like sticks to the wound surface and becomes difficult to remove, causing pain to the patient such as bleeding when removed. Also,
If the exudate comes out to the surface through gauze or the like, there are drawbacks such as an increased possibility that bacteria will invade the wound and cause infection.

[0004] As an alternative to this, there is a dressing (Airstrip®, Smith & Nephew Limited) that combines a sponge-like pad made of a hygroscopic pad and a non-adhesive film with a waterproof bandage.
Adhesive dressings (Op-Site®, Smith & Nephew Limited) consisting of a polyurethane film with high water vapor permeability and an adhesive layer
d; Bioclusive (registered trademark), Johnso
n &Johnson; Tegoderm (registered trademark),
3M) etc. are commercially available and have some efficacy.

On the other hand, as seen in Japanese Patent Application Laid-Open No. 58-155854, there is a wound dressing made of a porous membrane film, but when used on wounds such as sutures and joints after surgery, the adhesive part Since there is no such substance, it is expected that there will be problems in adhesion to the skin, leading to bacterial infection.

[0006] Furthermore, since infection is likely to occur on the wound surface or at the sutured part of the wound, a cream base containing an antibacterial agent is used to prevent infection. However, if an antibacterial agent is applied to gauze, the gauze bandage will contain about 5.
% penetrates, and only about 21% reaches the wound surface. In addition, cream-based products are cumbersome to use, as they have to be applied to the wound surface every day.

[0007]

[Problem to be solved by the invention] From the above points,
In general, adhesive dressings require (1) good operability, (2) sterilization until use, and (3)
Adhesion is possible; (4) good air permeability; (5)
) Although it is desired that dressings meet requirements such as preventing infection by bacteria, there is currently no dressing that meets these requirements.

It is therefore an object of the present invention to provide a new adhesive dressing.

Another object of the present invention is to provide an adhesive dressing suitable for surgical use that is permeable to air and water vapor but prevents water intrusion and bacterial infection.

0010

[Means for Solving the Problem] The above object is an adhesive formed by laminating an adhesive layer on one side of a thermoplastic polyurethane elastomer membrane, and laminating a hydrophilic porous membrane on a part of the surface of the adhesive layer. This is achieved by sexual dressing.

[0011] The above object is achieved by laminating an adhesive layer on one side of a thermoplastic polyurethane elastomer membrane, laminating a water-absorbing nonwoven fabric on a part of the surface of the adhesive layer, and further layering a hydrophilic porous fabric on the fabric. This can also be achieved by adhesive dressings consisting of layered membranes.

The present invention is the adhesive dressing described above, wherein the adhesive layer is a one-component thermally crosslinkable acrylic adhesive. The present invention also provides an adhesive dressing in which the hydrophilic porous membrane is made of polyolefin or halogenated polyolefin by graft polymerization of alkoxyalkyl acrylate and/or alkylacrylamide to impart hydrophilicity. The present invention further provides silver, which is a metal having antibacterial properties, in any of the thermoplastic polyurethane elastomer membrane, adhesive layer, hydrophilic porous membrane, and water-absorbing nonwoven fabric.
It is an adhesive dressing that has antibacterial properties by depositing copper or zinc.

[0013]

[Operation] Next, the adhesive dressing of the present invention will be explained with reference to the drawings.

The adhesive dressing of the present invention is shown in FIG.
), a hypoallergenic adhesive layer 2 is laminated on a thermoplastic elastomer membrane 3, and a part of the surface on which this adhesive layer 2 is laminated is attached to the skin defect site when using the adhesive dressing. By laminating a porous membrane 1 that has undergone hydrophilic treatment on the part that comes into direct contact with the skin, and depositing an antibacterial metal 4 on this if necessary, it adheres well to the wound surface and prevents infection of the wound. By using a porous membrane that has been treated with hydrophilic treatment on the part that contacts the defective area, it prevents excessive drying that occurs when using conventional gauze, etc., and creates a hydrated and lubricated state that provides adhesiveness to the defective skin area. Epidermal regeneration can be promoted without the dressing sticking.

The adhesive dressing of the present invention is also shown in FIG.
As shown in (B), a hypoallergenic adhesive layer 2 is laminated on a thermoplastic elastomer membrane 3, and a part of the surface on which this adhesive layer is laminated is damaged when using the adhesive dressing. By laminating a water-absorbing fabric 5 on the part that comes into direct contact with the body part, laminating a hydrophilic-treated porous membrane 1 on top of this fabric 5, and depositing an antibacterial metal 4 on this if necessary. It adheres well to the wound surface without allowing exudate to accumulate even on a wound surface with a lot of exudate, and because it has antibacterial properties, it prevents bacteria from infecting the wound even if exudate leaks to the surface. In addition, by using a porous membrane that has been treated with hydrophilic treatment in the area that comes into contact with the skin defect, it prevents excessive dryness that would normally occur when using gauze, etc. Epidermal regeneration can be promoted without the adhesive dressing sticking to the site.

Those known as thermoplastic elastomers include styrene-diene thermoplastic block copolymers,
Examples include thermoplastic polyester-ether copolymers and thermoplastic polyurethane elastomers. The thermoplastic elastomer used in the present invention is preferably a thermoplastic polyurethane elastomer. In the thermoplastic polyurethane elastomer, diisocyanates as hard segments include, for example, ethylene diisocyanate, hexamethylene diisocyanate, tolylene diisocyanate, phenylene diisocyanate, dimethyl-diphenylmethane diisocyanate, isophorone diisocyanate, 4
-4' diphenylmethane diisoanate, etc., 4-4' diphenylmethane diisoanate is preferably used for thermoplastic polyurethane elastomers, and polyols as soft segments, such as polyalkylene polyols, polyether polyols, polycaprolactam, polycarbonate, etc. It is a segmented polyurethane made of esters, etc., and chain extenders such as ethylene glycol, propylene glycol, 1,4-butanediol, and butanediol, etc. It is generally used for medical purposes and has water vapor permeability. In thermoplastic polyurethane elastomers, the polyol as a component is preferably
It is a thermoplastic polyurethane elastomer that is a polyether polyol.

The porous membrane used in the present invention is a porous membrane of polyolefin or halogenated polyolefin, and considering its general purpose and low cost, polyethylene, polypropylene, polyvinylidene chloride, polyvinylidene fluoride, A porous membrane made of chlorinated polyethylene, etc.
Preferably it is polypropylene.

In the present invention, this porous membrane is subjected to hydrophilic treatment. Hydrophilic monomers and/or hydrophilic pommaries used therein include acrylic acid, methyl acrylate, ethyl acrylate, 2-hydroxyethyl (meth)acrylate, 2-hydroxypropyl (meth)acrylate, 3-hydroxypropyl (meth)acrylate. Hydroxyalkyl acrylates such as methoxyethyl (meth)acrylate, alkoxyalkyl acrylates such as meexyethyl (meth)acrylate, ethylaminoethyl (meth)acrylate, dimethylaminoethyl (meth)acrylate, diethylaminoethyl (meth)acrylate, dimethylaminopropyl Alkylaminoalkyl (meth)acrylates such as (meth)acrylates, acrylamide, methacrylamide, diacetone (meth)acrylamide, dimethylacrylamide,
Dialkyl (meth)acrylamides such as diethyl acrylamide, isopropylacrylamide, dimethyl methacrylamide, diethyl methacrylamide, vinyl silane, vinyl pyridine, etc., one or more of these monomers are used, and preferably a monomer that can be easily graft polymerized. Moreover, it is a polymer of alkoxyalkyl acrylate and/or alkyl acrylamide monomers because of its good biocompatibility.

Methods for chemically bonding this hydrophilic monomer to the porous membrane include a chemical grafting method, a radiation grafting method, a glow discharge grafting method, etc. In the present invention, a kind of glow discharge grafting method is used. A plasma-initiated surface grafting method is preferably used.

[0020] Plasma-initiated surface graft polymerization is carried out in an atmosphere of argon, nitrogen, air, hydrogen, etc. in an atmosphere of 0.01 to 0.
irradiate with plasma under a pressure of 5 torr, preferably 0.1 to 0.2 torr for 1 to 300 seconds, preferably 5 to 20 seconds, simultaneously or thereafter supplying the hydrophilic monomer in gaseous or liquid form, The reaction is carried out at a temperature of -50°C, preferably 20-25°C, for 1-200 minutes, preferably 2-10 minutes.

As the adhesive used in the present invention, acrylic acid ester copolymers such as acrylic acid, 2-ethylhexyl acrylate, and butyl acrylate are generally used for medical purposes. It has good adhesion with the thermoplastic polyurethane elastomer membrane and the porous membrane or fabric that is the component of the present invention, and does not peel off from the thermoplastic polyurethane elastomer membrane during use, and can be used in direct contact with the skin. A one-component thermally crosslinkable acrylic adhesive is preferred because it does not have a negative effect on the skin and can be easily peeled off from the skin after use or when replaced. The thickness of the adhesive layer is 5 to 50 μm, preferably 1
It is 0 to 20 μm.

[0022] The metal used as the antibacterial agent in the present invention includes silver, copper, zinc, etc., and silver is preferred from the viewpoint of antibacterial properties. Two or more types of metals may be present on the film surface, and silver oxide (monovalent), silver oxide (bivalent)
, oxides such as copper oxide (monovalent), copper oxide (bivalent), zinc oxide, iron-zinc oxide, iron-copper oxide, silver chloride, copper chloride (monovalent),
It may be in the form of halides such as zinc chloride, silver bromide, copper bromide (monovalent), silver iodide, copper iodide (bivalent), and the like. Note that methods for making these metals exist in the film include sputtering method, ion beam method, vacuum evaporation, etc.
Although not particularly limited, a sputtering method is preferable.

[0023] Furthermore, the part where the metal is present may be any layer of thermoplastic polyurethane elastomer, fabric, or porous membrane, but is preferably a porous membrane because it is preferable to be close to the infected wound surface. The metal may be deposited before or after the porous film is laminated, but from the viewpoint of ease of manufacture and vapor deposition, it is preferable to deposit the metal on the porous membrane alone before lamination.

The amount of metal to be present is not particularly limited, but from the viewpoint of cost or secondary contamination due to eluted metal, the metal atom/carbon atom ratio as determined by the X-ray photoelectron spectrum of the film surface is 0.02 to 5. It is preferably within the range of .0, more preferably from 0.1 to 2.0. When the metal atom/carbon atomic ratio exceeds 5.0, the metal abundance ratio on the membrane surface becomes excessive, and although it has antibacterial properties, the pore size is reduced by the attached metal and the membrane loses its inherent water vapor permeability. I end up. Furthermore, if an excessive amount of metal adheres and the metal becomes a thin film, not only will the pores be clogged and the metal layer peeled off due to impact, etc., but it will also be uneconomical. Conversely, if the metal atom/carbon atom ratio is less than 0.02, stable antibacterial properties may be lost.

The fabric used in the present invention is for absorbing exudate from the wound surface, and includes non-woven fabrics, woven fabrics, knitted fabrics, etc. More conveniently, gauze, absorbent cotton, etc. may be used, but antibacterial and Urethane or cellulose-based nonwoven fabrics, which are generally used for medical purposes, are suitable from the viewpoint of appropriate moisture retention and water absorption. The thickness of the fabric is 0.1 to 5.0 mm
, preferably 0.5 to 2.0 mm.

The adhesive dressing of the present invention is manufactured, for example, as follows.

First, a predetermined amount of liquid paraffin is added to polyolefin, such as polypropylene powder, and the mixture is melt-kneaded and pelletized. The pellets are melted at 150 to 200°C, extruded using an extruder equipped with a T-die, introduced into a cooling fixation liquid, cooled and fixed, and formed into a film. Liquid paraffin, which is an impurity in the film, is extracted. C., preferably about 135.degree. C. in air for about 2 minutes to obtain a polypropylene porous membrane. Plasma-initiated surface graft polymerization of methoxyethyl acrylate was applied to the membrane to obtain a porous polypropylene membrane imparted with hydrophilic properties.

[0028] Metal (silver) was vapor-deposited on this porous membrane to impart antibacterial properties.

On the other hand, in order to obtain a thermoplastic polyurethane elastomer film, a thermoplastic elastomer, such as a thermoplastic polyurethane elastomer, is dissolved in a solvent such as a mixed solution of tetrahydrofuran and dimethyl formaldehyde, and then the thermoplastic elastomer solution, such as a polyurethane solution, is dissolved. obtain. This polyurethane solution is then applied onto a release paper, such as a silicone-based release paper, using a precision layering tool (
applicator) to a uniform thickness. After coating, the coating is left at room temperature and then transferred to a dryer at 60 to 100°C, where it is cured for 1 to 10 hours, preferably 2 to 4 hours, to obtain a thermoplastic elastomer film, such as a polyurethane film. The film thickness after drying is not particularly limited, but is preferably 10 to 200 μm, particularly 30 to 50 μm.

[0030] A one-component thermal crosslinking type acrylic adhesive is applied to this thermoplastic elastomer film using an applicator to form an adhesive layer with a thickness of 20 μm.

Next, the thermoplastic elastomer membrane coated with this adhesive is laminated with a porous polypropylene membrane which has been treated to be hydrophilic and has antibacterial properties, thereby obtaining the adhesive dressing of the present invention.

[0032] Thereafter, if necessary, this is sterilized with ethylene oxide gas or gamma rays to obtain the adhesive dressing of the present invention.

[0033]

EXAMPLES Next, the present invention will be explained in more detail with reference to Examples.

Example 1 First, a porous membrane was prepared. 100 parts by weight of a mixture of polypropylene with a melt flow index of 30 and 0.3 (mixing weight ratio 100:40), liquid paraffin (
400 parts by weight of average molecular weight 324) and 0.3 parts by weight of 1,3,2,4-bis(p-ethylbenzylidene) sorbitol as a crystal nucleating agent were placed in a twin-screw extruder at 150 parts by weight.
The mixture was melt-kneaded at ~200°C and pelletized. The pellets are melted at 150 to 200°C using the above-mentioned twin-screw extruder and extruded into a film through a T-die with a slit width of 0.6 mm in the air. Cooling fixation liquid 1,1,2- by roller
The mixture is introduced into trichloro-1,2,2-trifluoroethane, cooled and fixed, and then wound up. The wound film was cut into a certain size, fixed both vertically and horizontally, and immersed in 1,1,2-trichloro-1,2,2,-trifluoroethane for 10 minutes four times in total to form a film. Liquid paraffin, which is an impurity in the product, was extracted and heat treated in air at 135° C. for about 2 minutes to obtain a polypropylene porous membrane with an average pore diameter of 0.6 μm and a film thickness of 140 μm.

[0035] The film was exposed to 0.1 to 0 in an argon atmosphere.
．． The pressure was reduced to 2 torr, plasma was irradiated for 10 to 15 seconds, then methoxyethyl acrylate was supplied in gaseous form, and the reaction conditions were plasma-initiated surface graft polymerization at a temperature of 25°C for 5 minutes to give hydrophilicity. A porous membrane was obtained.

Further, silver is deposited by sputtering on this hydrophilic porous membrane made of polypropylene. First, a hydrophilic polypropylene porous membrane was placed on a substrate support facing the target (cathode), and after reducing the pressure to 10-5 torr in an argon atmosphere, the shutter was opened and silver was sputtered for 5 seconds. Deposited.

Next, tetrahydrofuran (THF) 11
Urethane resin (
Leathermin P-2045R (Dainichiseika Chemical Co., Ltd.) was dissolved to obtain a 20% by weight urethane resin solution.

This 20% by weight urethane resin solution is layered onto a silicone release paper to a uniform thickness using a precision layering tool (applicator). After coating, it was left to stand at room temperature for 15 minutes, and then transferred to a dryer at 100°C, where it was cured for 2 to 3 hours. A thermoplastic polyurethane elastomer having a thickness of 30 μm after curing was obtained.

[0039] A one-component thermal crosslinking type acrylic adhesive (AV-61
00, manufactured by Showa Kobunshi Co., Ltd.) using a precision layering tool (applicator) to form an adhesive layer with a thickness of 20 μm.

Finally, on the adhesive layer side of the thermoplastic polyurethane elastomer membrane coated with the adhesive layer prepared as described above, a porous membrane made of polypropylene on which silver was vapor-deposited to impart hydrophilic properties was laminated. An adhesive dressing was obtained.

Example 2 Polyvinylidene fluoride powder (Mitsubishi Yuka Co., Ltd. K)
A solution of 18 parts by weight of ynar K301), 3.8 parts by weight of acetone and 8.3 parts by weight of dimethylformamide was cast onto a polyethylene terephthalate film, and then cast in a 1,1,2-trifluoroethane bath for 50 minutes. The mixture was soaked for a minute and dried in a hot air dryer to obtain a porous membrane made of polyvinylidene fluoride having an average pore diameter of 0.45 μm and a film thickness of 135 μm.

Similar to Example 1, the film was irradiated with plasma for 5 seconds in an argon atmosphere at a reduced pressure of 0.2 torr, and then methoxyethyl acrylate was supplied in gaseous form and heated at 20° C. and 1.0 torr. , plasma-initiated surface graft polymerization was carried out for 5 minutes to obtain a porous polypropylene membrane imparted with hydrophilic properties.

Further, silver is deposited by sputtering on this hydrophilic porous membrane made of polyvinylidene fluoride. First, a porous membrane made of polyvinylidene fluoride that has been given hydrophilic properties is placed on a substrate support stand on a collector (anode) facing a target (cathode), and heated for 10-5 minutes in an argon atmosphere.
After reducing the pressure to torr, open the shutter and
A voltage was applied to the collector (anode) for 0 seconds to deposit silver by sputtering.

Next, tetrahydrofuran (THF) 11
Urethane resin (
Leathermin P-2045R (Dainichisei Chemical Co., Ltd.) was dissolved to obtain a 20% urethane resin solution.

[0045] This 20% urethane resin solution was layered onto a silicone release paper to a uniform thickness using a precision layering tool (applicator). After coating, it was left to stand at room temperature for 15 minutes, and then transferred to a dryer at 100°C, where it was cured for 2 to 3 hours. A thermoplastic polyurethane elastomer having a thickness of 30 μm after curing was obtained.

[0046] A one-component thermal crosslinking type acrylic adhesive (AV-61) was applied to this thermoplastic polyurethane elastomer film.
00, manufactured by Showa Kobunshi Co., Ltd.) was applied using a precision layering tool (applicator) to form an adhesive layer with a thickness of 20 μm.

Finally, on the adhesive layer side of the thermoplastic polyurethane elastomer membrane coated with the adhesive layer prepared as described above, a porous membrane made of polyvinylidene fluoride, which has been given hydrophilic properties by vapor deposition of silver, is stretched. Combined to obtain an adhesive dressing.

Example 3 First, by the same method as in Example 1, a hydrophilic porous polypropylene membrane having a thickness of 140 μm was obtained. Further, silver was deposited by sputtering on this hydrophilic polypropylene porous membrane.

Next, by the same method as in Example 1, a one-component thermal crosslinking type acrylic adhesive (AV-6100, manufactured by Showa Kobunshi Co., Ltd.) was applied to the thermoplastic polyurethane elastomer film using a precision layering tool (applicator). ) to obtain a polyurethane film having an adhesive layer with a thickness of 20 μm.

Finally, the cellulose-based non-woven fabric Heise Gauze (manufactured by Asahi Kasei Corporation) and the polypropylene porous membrane on which the silver produced as described above has been vapor-deposited to impart hydrophilic properties are spot-fused at 150 to 200°C. The surface of the adhesive layer of the thermoplastic polyurethane elastomer membrane coated with an adhesive layer was attached to the surface of the nonwoven fabric to obtain an adhesive dressing.

[0051]

[Effects of the Invention] The adhesive dressing of the present invention consists of a thermoplastic polyurethane elastomer membrane, an adhesive layer, and a porous membrane treated to make it hydrophilic, or a water-absorbing nonwoven fabric as an intermediate layer. By adding antibacterial properties when necessary, it allows air and water vapor to pass through, but prevents moisture from entering and infection by bacteria, and there is no need to replace it when the patient takes a bath or shower. It can prevent infection to the wound.

Furthermore, by using a thermoplastic polyurethane elastomer, it can be applied to parts that are subject to rapid movement such as joints.

[Brief explanation of the drawing]

FIG. 1(A) is a sectional view showing one embodiment of the adhesive dressing of the present invention, and FIG. 1(B) is a sectional view showing another embodiment of the adhesive dressing of the present invention. .

[Explanation of symbols]

1... Hydrophilic porous membrane, 2...adhesive layer, 3... Elastomer membrane, 4...metal particles, 5...Nonwoven fabric.

Claims (6)

[Claims] 1. An adhesive dressing comprising a thermoplastic polyurethane elastomer membrane, an adhesive layer laminated on one side, and a hydrophilic porous membrane laminated on a part of the surface of the adhesive layer. Claim 2: An adhesive layer is laminated on one side of a thermoplastic polyurethane elastomer membrane, a water-absorbing nonwoven fabric is laminated on a part of the surface of the adhesive layer, and a hydrophilic porous membrane is further layered on the fabric. Adhesive dressing made of laminated layers. 3. The adhesive dressing according to claim 1, wherein the adhesive layer is a one-component thermally crosslinkable acrylic adhesive. 4. The hydrophilic porous membrane is obtained by graft polymerizing an alkoxyalkyl acrylate and/or an alkyl acrylamide to a polyolefin or a halogenated polyolefin to impart hydrophilicity. Adhesive dressing as described. Claim 5: Claim 1, wherein antibacterial metals such as silver, copper, or zinc are deposited on either the thermoplastic polyurethane elastomer membrane and adhesive layer, or the hydrophilic porous membrane to impart antibacterial properties. or an adhesive dressing according to any one of claims 2 to 3. Claim 6: Claim 2, wherein a water-absorbing nonwoven fabric is made to have antibacterial properties by vapor-depositing silver, copper, or zinc, which are metals that have antibacterial properties.
Adhesive dressings as described in .