JP2020103502A - Wound dressing material and method of producing the same - Google Patents

Abstract

To provide a wound dressing material that provides a moist environment necessary for cell migration and proliferation, supplies ions such as calcium and boron to the wound surface to accelerate the wound healing process, and has a bactericidal property to prevent the critical colonization and infection of bacteria on the wound surface.SOLUTION: The wound dressing material is a fiber laminate comprising a hydrogel fiber layer containing organic fibers capable of forming a hydrogel and a glass fiber layer containing glass fibers including B2O3 and CaO as glass constituent components.SELECTED DRAWING: Figure 1

Description

The present invention relates to a wound dressing showing an excellent healing effect on wound surfaces such as cuts, lacerations, contusions, burns and pressure ulcers.

Conventionally, as a wound treatment, disinfection is first performed, and then the wound surface is protected with gauze. However, such a treatment method kills cells necessary for tissue regeneration by disinfection. Further, it has recently been revealed that the migration and proliferation of cells necessary for tissue regeneration are less likely to occur when the wound surface is dried.

Therefore, plastic surgeon Mutsumi Natsui et al. proposed a treatment method (moist wound healing) that maintains a moist environment on the wound surface and promotes cell proliferation instead of performing treatment using an antiseptic solution and gauze, and now this treatment method is used. Widely used. (Non-patent document 1)

A hydrocolloid wound dressing is currently in widespread use. The hydrocolloid wound dressing has a structure in which hydrophilic colloid particles are dispersed in a matrix polymer formed into a sheet. The matrix polymer is mainly composed of an elastomer and has elasticity and flexibility. Such a hydrocolloid wound dressing has a function of absorbing a blood or an exudate flowing out from the wound surface by a hydrophilic gel dispersed in an elastomer to swell and contact the wound surface to construct a moist environment.

In recent years, cotton-like wound-covering glass fibers have been developed which dissolve in blood or exudate flowing out from the wound surface and elute the glass component (Patent Document 1). Such a wound-covering glass fiber has a function in which ions such as calcium and boron promote cell proliferation, collagen regeneration and angiogenesis, and impart antibacterial properties.

Future Wound Treatment Mutsumi Nasai, Medical School (2003/08)

WO 2016/093211

The hydrocolloid wound dressing material has the effect of promoting migration and proliferation of cells necessary for tissue regeneration by creating a moist environment on the wound surface and making the pH of the wound surface weakly acidic, and it has the natural healing power of the patient. It is possible to bring out the maximum. However, for patients with low healing ability such as elderly people, when the wound is pressure ulcer, when the volume and area of the wound opening is large, or when continuous force is applied to the wound surface, treatment with hydrocolloid wound dressing is used. Even if you do, there is a problem that it takes a long time to heal.

Furthermore, in the case of diabetic patients, even if wound dressing is used, delayed wound healing occurs due to abnormal immune function, protein deficiency, lack of oxygen, etc. May cause serious complications.

In recent years, the policy of not using antiseptics for wound treatment has changed. More specifically, it is not necessary to disinfect when only the bacteria are colonized on the wound surface or when the bacteria grow but do not affect the host. However, use of disinfectants has become necessary when the number of bacteria is high and it is likely to progress to wound infection, or when bacteria enter the inside of tissues and cause actual damage to the host.

Wound-covering glass fibers can be expected to promote wound healing by promoting ions such as calcium and boron to promote cell proliferation, collagen regeneration and angiogenesis even when the patient's natural healing power is low. In addition, the effect of preventing the critical colonization of bacteria and infection by boron ions can be expected. However, since the glass fiber itself is a dry material, if the amount of blood or exudate is small, most of it is absorbed by the cotton-like glass fiber, and it is difficult for water to remain on the wound surface. Therefore, if the amount of blood or exudate is small, there is a problem that it is difficult to establish a moist environment.

As a method of solving this problem, there is a method of integrally using an organic gel capable of constructing a moist environment and a wound-covering glass fiber. However, in the organic gel, the glass component elutes in the gel when it contains water, and the effective elution behavior cannot be obtained when it is used on the wound surface. On the other hand, there is a problem that it cannot be used as a member of a wound dressing when formed into a sheet, for example, because it is hard and not flexible in a dry state.

The present invention has been made in view of the above circumstances, provides a moist environment necessary for cell migration and proliferation, and accelerates the wound healing process by supplying ions such as calcium and boron to the wound surface, An object of the present invention is to provide a wound dressing having bactericidal properties for preventing the critical colonization of bacteria and infection.

The wound dressing of the present invention is a fiber laminate having a hydrogel fiber layer containing organic fibers capable of forming hydrogel, and a glass fiber layer containing glass fibers containing B ₂ O ₃ and CaO as glass constituents. The hydrogel fiber layer is located on the wound surface side.

The wound dressing material of the present invention having the above structure has biocompatibility. Further, the organic fiber absorbs blood or exudate flowing out from the wound surface, swells and gels. Such an organic gel builds a three-dimensional crosslinked structure that is crosslinked by covalent bonds, ionic bonds, hydrogen bonds, and intermolecular forces, retains moisture in the structure, and wets even if the amount of exudate is small. Easy to build environment.

Further, glass fibers containing B ₂ O ₃ and CaO as glass constituents dissolve B (boron), which is dissolved in blood or exudate and has a bactericidal effect on Ca (calcium) that is a nutrient of cells and bacteria. Elute. Such ions are diffused in the organic gel and supplied to the wound surface, which makes it possible to accelerate the wound healing process and impart bactericidal properties to prevent critical colonization and infection of bacteria on the wound surface. The wound dressing of the present invention can heal a wound early by combining these effects.

In the present invention, the organic fiber capable of forming a hydrogel preferably contains at least one selected from the group consisting of synthetic resins, proteins and saccharides.

In the present invention, the organic fiber capable of forming a hydrogel is a group consisting of polyvinyl alcohol, polyvinylpyrrolidone, polyethylene oxide, polyethylene glycol, carboxymethyl cellulose, gelatin, collagen, tamarind seed gum, guar gum, locust bean gum, starch and pullulan. It is preferable to contain at least one selected from the above.

In the present invention, it is preferable that the organic fibers capable of forming the hydrogel contain 80% or more by mass of polyvinyl alcohol.

In the present invention, glass fibers, in mass% of oxide _{equivalent, SiO 2 5~70%, B 2} O 3 5~40%, preferably made of glass containing 1 to 50% CaO.

If the above configuration is adopted, Ca and B that promote wound treatment can be sufficiently supplied to the wound surface.

In the present invention, containing glass fibers, in mass% of oxide equivalent, further _{0~20% MgO, Na 2 O 0~20} %, K 2 O 0~40%, the _P 2 O 5 0 to 20% It is preferably made of glass.

In the present invention, the specific surface area of the glass fiber is preferably 0.01 m ² /g or more. Here, the “specific surface area” means that the sample to be measured is dried at a temperature of 300° C. for 3 hours or more under a vacuum of 0.05 Torr or less, and thereafter, the adsorption isotherm of only the adsorption side of nitrogen at the liquid nitrogen temperature. Is measured and the adsorption isotherm is analyzed by the BET method.

In the present invention, the glass fiber has a density of 0.256 weight of glass powder classified into a particle size of 300 to 500 μm, the theoretical value of the inorganic ion concentration of Na ⁺ is 142.0 mM, and K ⁺ is 5.0 mM. , Mg ²⁺ is 1.5 mM, Ca ²⁺ is 2.5 mM, Cl ⁻ is 148.8 mM, and HPO ^{4 −} is adjusted to be 1.0 mM. In the dissolution test with stirring once a day, it is preferable that the simulated body fluid has a B concentration of 0.1 to 70 mM and a Ca concentration of 3 to 20 mM.

In the present invention, the average fiber diameter of the glass fibers is preferably 100 nm to 10 μm. Here, the "average fiber diameter" means that the secondary electron image or the backscattered electron image of the glass fiber is picked up using a scanning electron microscope, and the length measurement function of the scanning electron microscope is used to measure 50 glass fibers. It means the average value obtained by measuring the diameter.

If the above configuration is adopted, Ca and B that promote wound treatment can be sufficiently supplied to the wound surface.

In the present invention, the theoretical value of the inorganic ion concentration of a sample of 230 mg is 142.0 mM for Na ⁺ , 5.0 mM for K ⁺ , 1.5 mM for Mg ²⁺ , 2.5 mM for Ca ²⁺ , and 148 for Cl ⁻ . In a dissolution test in which the simulated body fluid was immersed in 43 ml of the simulated body fluid at 37° C. adjusted to 8 mM and 1.0 mM of HPO ^4- for 16 hours, the B concentration in the simulated body fluid was 0.1 to 70 mM and the Ca concentration was 10 mM. It is preferably 3.0 to 20 mM.

If the above configuration is adopted, Ca and B that promote wound treatment can be sufficiently supplied to the wound surface.

In the present invention, the fiber laminate has a first surface on the wound surface side and a second surface on the opposite side to the wound surface, and the moisture non-absorbing member is on the second surface of the fiber laminate. Is preferably provided.

In the present invention, the moisture non-absorbing member is preferably provided on the second surface of the fiber laminate so that the peripheral edge of the moisture non-absorbing member protrudes from the fiber laminate.

If the above configuration is adopted, it becomes easy to retain blood and exudate on the wound surface.

In the present invention, it is preferable that the moisture non-absorptive member is made of a polymer film including an adhesive layer and a support layer.

In the present invention, the polymer film, at least one support layer selected from the group consisting of polyurethane, polypropylene, polyisobutylene, polyisoprene, polystyrene, polybutylene terephthalate, an acrylic adhesive, a urethane adhesive, a silicone adhesive It is preferable to include at least one pressure-sensitive adhesive layer selected from the group consisting of agents.

If the above configuration is adopted, it becomes easy to obtain sufficient adhesive force for fixing the fiber laminate to the skin.

The method for producing a wound dressing according to the present invention comprises laminating an organic fiber capable of forming a hydrogel and a glass fiber containing B ₂ O ₃ and CaO as glass constituents and compressing the fiber to form a highly non-woven fabric. It is characterized by having a step of forming into a body.

In the method of the present invention, it is preferable to further laminate a non-moisture absorbing member on the surface opposite to the wound surface of the fiber laminate.

It is a schematic sectional drawing which shows one embodiment of this invention.

Hereinafter, the wound dressing of the present invention will be described in detail. FIG. 1 shows one embodiment of the wound dressing of the present invention. In the figure, 1 is a hydrogel fiber layer containing an organic fiber capable of forming a hydrogel (hereinafter, simply referred to as hydrogel fiber), 2 is a glass fiber containing a glass fiber containing B ₂ O ₃ and CaO as glass components. Represents a layer. However, the wound dressing of the present invention is not limited to the embodiment of FIG. 1, and for example, another layer between the hydrogel fiber layer and the glass fiber layer, for example, an organic acid containing an organic acid, a polysaccharide or the like is used. A pH-adjusting fiber layer containing fibers may be provided.

The wound dressing of FIG. 1 is a fiber laminate in which a hydrogel fiber layer 1 and a glass fiber layer 2 are laminated in this order from the wound surface side. The hydrogel fiber layer and the glass fiber layer are both non-woven fabrics, and the organic fiber and the glass fiber are entangled at the interface between both layers. Here, the “nonwoven fabric” refers to a cotton-like compressed body in which a large number of fibers are irregularly entangled and formed into a sheet or cloth. Hydrogel fibers gel when contacted with blood or exudate and build a moist environment on the wound surface. Further, blood or exudate that has passed through the hydrogel fiber layer is absorbed by the glass fiber and elutes Ca (calcium), which is a nutrient for cells, and B (boron), which has a bactericidal effect on bacteria. Ca and B are supplied to the wound surface via the gelled hydrogel fiber layer, which makes it possible to accelerate the wound healing process and impart bactericidal properties to prevent critical colonization and infection of bacteria on the wound surface.

(1) Hydrogel fiber layer In the wound dressing of the present invention, the hydrogel fiber layer 1 contains an organic fiber capable of forming a hydrogel. More specifically, it is composed of a non-woven body of hydrogel fibers. The hydrogel fiber layer absorbs blood and exudate to form a hydrogel and provides a moist environment on the wound surface. Further, since it has a fiber structure, blood or exudate is passed therethrough and supplied to the glass fiber layer. Further, Ca or B eluted from the glass fiber layer can be supplied to the wound surface.

The hydrogel fiber layer is provided on the most wound surface side of the fiber laminate. By providing the hydrogel fiber layer closest to the wound surface, a wet environment can be provided on the wound surface. Further, it is possible to avoid the inconvenience caused by the glass fiber layer coming into contact with the wound surface. “Inconvenience due to contact with the wound surface” refers to, for example, adhesion between the glass fiber layer and the wound surface, discomfort caused by contact of the glass beads or the like contained in the glass fiber layer with the skin.

The hydrogel fiber preferably contains a synthetic resin, protein, saccharide and the like.

Specifically, it is preferable to contain at least one polymer selected from the group consisting of polyvinyl alcohol, polyvinylpyrrolidone, polyethylene oxide, and polyethylene glycol. For example, the hydrogel fiber may contain 80% or more by weight of polyvinyl alcohol.

Further, the hydrogel fiber contains a protein such as gelatin, collagen, tamarind seed gum, guar gum, locust bean gum, starch, pullulan or the like or a neutral polysaccharide or the like instead of or together with the above polymer. Good.

(2) Glass Fiber Layer The glass fiber layer 2 contains glass fibers containing B ₂ O ₃ and CaO as glass constituent components. More specifically, it is composed of a glass fiber non-woven fabric containing B ₂ O ₃ and CaO as glass constituents. The use of fibrous glass fibers facilitates circulation of blood and exudate. It can also provide flexibility to the wound dressing.

In the wound dressing of the present invention, glass fibers, in mass% of oxide _{equivalent, SiO 2 5~70%, B 2} O 3 5~40%, preferably made of glass containing 1 to 50% CaO .. Hereinafter, the action of each glass component and the reason for defining the content will be described. In the description of the content range of each component,% indication means mass %.

SiO ₂ is a component forming the skeleton of the glass network structure. It is also a component that increases the viscosity of glass. The content of SiO ₂ is preferably 5 to 70%, 10 to 50%, 15 to 45%, 25 to 45%, 30 to 43%, and particularly 33 to 43%. If the content of SiO ₂ is too large, the dissolution rate of glass with respect to blood or exudate of glass decreases. Further, the fiberizing temperature (the temperature corresponding to the viscosity of 10 ^1.0 dPa·s) becomes high, and the cost for fiberizing increases. If the content of SiO ₂ is too small, the viscosity of the glass lowers, the liquidus viscosity remarkably lowers, and the amount of glass beads, glass flakes, etc. mixed in when molded into glass fibers increases.

Like SiO ₂ , B ₂ O ₃ is a component that forms the skeleton of the glass network structure, but it does not raise the melting temperature of glass like SiO ₂ , but rather acts to lower the melting temperature. In addition, it is a component that exerts a bactericidal effect by being dissolved in blood or exudate. The content of B ₂ O ₃ is 5 to 40%, preferably 10 to 35%, 11 to 30%, 12 to 27%, and particularly preferably 12 to 22%. If the content of B ₂ O ₃ is too small, critical colonization of bacteria on the wound surface and bactericidal property for preventing infection cannot be obtained. If the content of B ₂ O ₃ is too high, the melting rate of glass will be extremely increased, and it will be necessary to frequently replace the wound dressing.

CaO is a component that reduces the viscosity of glass, and is a component that exhibits an effect of promoting cell growth when it is dissolved in blood or exudate. The content of CaO is 1 to 50%, preferably 5 to 40%, 8 to 35%, 10 to 30%, 15 to 30%, and particularly preferably 15 to 25%. If the content of CaO is too small, it becomes difficult to obtain the effect of promoting cell growth. When the content of CaO is too large, the liquidus temperature becomes high and the glass is devitrified during melting, and it becomes difficult to obtain a homogeneous glass.

Further, in addition to SiO ₂ , B ₂ O ₃ and CaO, it is preferable to contain MgO, Na ₂ O, K ₂ O and P ₂ O ₅ .

MgO is a component that acts as a flux that facilitates melting of glass raw materials, and at the same time, it is very effective in lowering the melting temperature, which improves the breakage of glass during melting and makes a homogeneous glass. It is a useful ingredient. The MgO content is preferably 0 to 20%, 0 to 10%, and particularly preferably 0.5 to 8%. If the MgO content is too high, the viscosity of the glass will decrease and the liquidus viscosity will decrease. Therefore, when glass fibers are produced by a method such as a melt blow method, the amount of glass beads, glass flakes, etc. mixed in is too large. To increase.

Na ₂ O is a component that lowers the viscosity of the glass and thereby enhances the meltability and moldability of the glass. The content of Na ₂ O is preferably 0 to 20%, 1 to 15%, and particularly preferably 2 to 10%. If the content of Na ₂ O is too high, the viscosity of the glass is lowered or the liquidus viscosity is significantly lowered. Therefore, when glass fibers are produced by a method such as a melt blow method, glass beads, glass flakes, etc. The mixed amount of is increased.

K ₂ O is a component that lowers the viscosity of glass and thereby enhances the meltability and moldability of glass. The content of K ₂ O is preferably 0 to 40%, 5 to 30%, 7 to 20%, and particularly preferably 7 to 15%. If the content of K ₂ O is too high, the viscosity of the glass is lowered or the liquidus viscosity is significantly lowered. Therefore, when glass fibers are produced by a method such as a melt blow method, glass beads and glass flakes are used. And the like will increase.

P ₂ O ₅ is a component that vitrifies by itself and forms a network of glass. The content of P ₂ O ₅ is 0 to 20%, preferably 1 to 8%, 2.5 to 8%, 2.5 to 6%, and particularly preferably 3.2 to 5%. If the content of P ₂ O ₅ is too high, the viscosity of the glass is lowered or the liquidus viscosity is significantly lowered. Therefore, when glass fibers are produced by a method such as a melt blow method, glass beads and glass flakes are used. And the like will increase.

The melting rate of glass changes depending on the molar ratio (B/Si) of Si (silicon) and B (boron) in the glass composition. The larger the value of B/Si, the larger the proportion of B in the glass network, the lower the chemical durability, and the higher the glass melting rate. Therefore, in order to increase the elution amount of Ca and promote cell growth, it is advantageous that the value of B/Si is large. However, in order to increase the B/Si value, it is necessary to increase the B ₂ O ₃ content of the glass, and as a result, the elution amount of B increases and an excessive bactericidal effect is exerted, resulting in cell growth. It will be suppressed.

Under these circumstances, the value of B/Si is preferably 0.1 to 20.0, 0.15 to 10.0, 0.2 to 5.0, and particularly 0.4 to 1.0. .. If the value of B/Si is too small, it becomes difficult to obtain the cell growth effect and bactericidal effect required for the wound dressing. On the other hand, when the value of B/Si is too large, an excessive bactericidal effect is exerted and cell growth is suppressed.

Further, components other than the above-mentioned components (SiO ₂ , B ₂ O ₃ , CaO, MgO, Na ₂ O, K ₂ O, P ₂ O ₅ ) may be included. However, it is desirable to adjust the composition so that the total content of the above-mentioned components is 98% or more, particularly 99% or more. The reason is that when the total amount of these components is less than 98%, the dissolution rate of glass into blood or exudate is lowered due to unintentional mixing of different components. As a result, inconveniences such as deterioration of properties as a wound dressing material and deterioration of biocompatibility are likely to occur.

As components other than the above-mentioned components, for example, Cu, Ag, Zn, Sr, Ba, Fe, F, Mo, Au, Mn, Sn, Ce, Cl, La, W, Nb, Y for improving the bactericidal effect. Etc. may be contained up to 2% in total.

Glass fiber has a specific surface area of 0.01 m ² / g or more, 0.05 m ² / g or more, 0.1 m ² / g or more, and particularly preferably 0.2 m ² / g or more. When the specific surface area is less than 0.01 m ² /g, the contact area between the glass fiber member and blood or exudate becomes small, so that the dissolution rate of glass is extremely reduced, and the bactericidal effect required as a wound dressing material is obtained. It gets harder. Furthermore, it becomes difficult to obtain the effect of promoting cell growth.

The glass constituting the glass fiber preferably has the following characteristics. Glass powder of density×0.256 parts by weight classified to a particle size of 300 to 500 μm was used, and the theoretical value of the inorganic ion concentration was 142.0 mM for Na ⁺ , 5.0 mM for K ⁺ , 1.5 mM for Mg ²⁺ , and Ca. It was immersed for 2 days in 60 ml of simulated body fluid adjusted to have ²⁺ of 2.5 mM, Cl ⁻ of 148.8 mM and HPO ^{4 −} of 1.0 mM, and stirred once/day. In the dissolution test, the B concentration in the simulated body fluid is preferably 0.1 to 70 mM and the Ca concentration is preferably 3 to 20 mM. If the B concentration in the simulated body fluid according to this dissolution test is less than 0.1 mM, it becomes difficult to obtain the bactericidal effect required as a wound dressing. On the other hand, when the B concentration is more than 70 mM, the dissolution rate of glass is extremely increased, which requires frequent replacement of the wound dressing. Further, if the Ca concentration is less than 3 mM, it becomes difficult to obtain the effect of promoting cell growth. On the other hand, when the Ca concentration is higher than 20 mM, the dissolution rate of glass is extremely increased, which requires frequent replacement of the wound dressing.

The glass fiber preferably has an average fiber diameter of 100 nm to 10 μm. Here, the "average fiber diameter of the glass fiber" means a secondary electron image or a backscattered electron image of the glass fiber using a scanning electron microscope (HITACHI s-3400N type II), and the length measuring function of the scanning electron microscope. The diameter of 50 glass fibers was measured using, and the average value was determined as the average fiber diameter.

The glass fiber preferably has a liquidus viscosity of 10 ^0.3 dPa·s or more, 10 ^0.4 dPa·s or more, 10 ^0.5 dPa·s or more, and particularly 10 ^1.0 dPa·s or more. If the liquidus viscosity is too low, the amount of glass beads, glass flakes, etc. mixed in when the molten glass is made into fibers becomes large. Here, the "liquidus viscosity" refers to the viscosity derived from the viscosity curve by the method of measuring the viscosity at the crystal precipitation temperature (liquidus temperature).

The glass beads may be mixed with glass beads. However, if the amount of glass beads mixed in is large, the specific surface area of the glass fibers will be small, and the dissolution rate of glass will decrease, making it difficult to adequately provide Ca or B to blood or exudate, thus making it difficult to cover wounds. The characteristics of the material are degraded. Furthermore, when forming into a non-woven fabric, the glass beads are crushed and fall off in the compression process, thereby forming a through hole in the non-woven fabric. Therefore, the smaller the amount of glass beads mixed, the more preferable. To reduce the amount of glass beads mixed in, the viscosity of the glass during molding may be adjusted.

In addition to glass beads, the glass fibers may include glass bodies having various shapes such as powder and flakes. It is also possible to add and impregnate various chemicals.

(3) pH adjusting fiber layer The binding force between hemoglobin and oxygen in blood decreases as the pH decreases. This phenomenon is called the Bohr effect. The more easily hemoglobin dissociates oxygen, the higher the oxygen concentration in blood, and the more oxygen is supplied to the fibroblasts, the more proliferative and migration of fibroblasts become. Furthermore, the low pH suppresses the growth of bacteria harmful to the human body including Staphylococcus aureus. Therefore, from the viewpoint of promoting wound healing, it is said that the pH of the wound surface should be kept weakly acidic.

Therefore, the wound dressing of the present invention can be provided with a pH-adjusting fiber layer containing water-soluble or hydrophilic organic fibers containing organic acid or acidic polysaccharide (hereinafter, simply referred to as pH-adjusting organic fibers). More specifically, it is preferable to include a pH adjusting fiber layer composed of a nonwoven fabric of pH adjusting organic fibers. The “water-soluble or hydrophilic organic fiber” refers to an organic compound having a property of absorbing blood or exudate flowing out from the wound surface, swelling, and gelling. The “organic acid” refers to an organic compound having a functional group such as a carboxyl group, a sulfo group and a hydroxy group and having an action of making the pH of an aqueous solution acidic. The “acidic polysaccharide” refers to a carbohydrate that has a structure in which monosaccharides such as glucose and mannose are connected, absorbs water, gels, and exhibits acidity. All of these organic compounds have a function as a so-called pH adjusting agent that suppresses a pH increase due to alkali metal or alkaline earth metal ions eluted from glass.

The pH-adjusted organic fiber gels when contacted with blood or exudate and contributes to the construction of a moist environment on the wound surface. The pH-adjusted organic fiber can also form a crosslinked structure under specific conditions such as sugar concentration, pH, and metal ion concentration, or can construct a strong crosslinked structure via ions eluted from the glass fiber. When such a strong crosslinked structure is formed, the fiber structure can be maintained even when exposed to a wet environment for a long time, and a stable wet environment can be provided.

The pH-adjusted organic fiber contains various organic acids and acidic polysaccharides. Organic acids and acidic polysaccharides are widely used as pH adjusters and gelling agents for foods, cosmetics, toiletries, oral care, medicines, medical products, etc., and are highly safe for the human body. Such an organic acid or acidic polysaccharide has a function as a pH adjuster for lowering the pH of the wound surface, and suppresses an increase in pH due to alkali metal ions or alkaline earth metal ions eluted from the glass fiber.

The pH-adjusting organic fiber preferably contains an organic acid or acidic polysaccharide having at least one functional group selected from the group consisting of a carboxyl group, a sulfo group and a hydroxy group. Organic acids having such a functional group include carboxylic acid, sulfonic acid, and hydroxy acid, which are acidic when dissolved in water. Further, the above-mentioned polysaccharides having a functional group include natural polymers derived from plants (seed, sap, fruit, etc.), seaweed, and microorganisms, which absorb water to form gels, and their surface pH is weak. Shows acidity. By adopting these polymers, it is easy to achieve both the establishment of a moist environment on the wound surface and the suppression of pH rise.

pH-adjusting organic fibers include pectin, karaya gum, gum arabic, xanthan gum, gellan gum, agar, tragacanth gum, citric acid, malic acid, succinic acid, glycolic acid, tartaric acid, phosphoric acid, polylactic acid, polyglycolic acid, sulfonic acid, hyaluronic acid. It is preferable to contain at least one selected from the group consisting of methacrylic acid, maleic acid, phthalic acid and adipic acid.

In addition, in the wound dressing of the present invention, the pH-adjusting organic fiber may contain, by mass%, 20 to 80% pectin, 1 to 50% polyvinyl alcohol, and 0 to 18% carboxymethylcellulose. preferable.

Pectin is a natural polysaccharide derived from citrus or apple, and has a structure in which galacturonic acid having a carboxyl group and galacturonic acid methyl ester in which the carboxyl group is methyl ester are linearly bonded. Pectin absorbs water and gels, and has a function of constructing a moist environment on the wound surface. Further, since the surface pH of the gel is weakly acidic, it has a function of lowering the pH for a long period of time. The more preferable content of pectin is 22 to 68%, 28 to 57%, 32 to 50%, and particularly 35 to 45% by mass%. When the content of pectin is too large, the viscosity of the aqueous solution becomes too high, which makes it difficult to form a fiber by the dry spinning method. If the content of pectin is too small, a stable gel will not be formed and it will be difficult to construct a wet environment.

Polyvinyl alcohol is an organic compound having a hydroxy group in the molecule, and is used in a wide range of fields as a binder, a surfactant, and an emulsifier. In addition, it is an organic compound that is highly safe for the human body. Polyvinyl alcohol has a function as a so-called thickener for adjusting the viscosity of an aqueous solution of an organic compound to a spinnable viscosity when producing an organic fiber by a dry spinning method. The more preferable content of polyvinyl alcohol is 5 to 47%, 8 to 42%, 16 to 35%, and particularly 20 to 30% by mass%. When the content of polyvinyl alcohol is too large, the stability of the gel formed on the wound surface is lowered, and the gel is dissolved at an early stage, making it difficult to maintain a moist environment. When the content of polyvinyl alcohol is too small, the viscosity of the organic compound aqueous solution is lowered, and it becomes difficult to fibrillate when producing the organic fiber by the dry spinning method.

Carboxymethyl cellulose is an organic compound in which the hydroxyl group of cellulose is replaced with a sodium carboxymethyl group, and is used as a thickener in cosmetics and pharmaceuticals. It also has the function of building a crosslinked structure with polyvalent metal ions to form a stable gel. Therefore, by adding carboxymethyl cellulose, it is possible to improve the stability of the gel formed on the wound surface and maintain the moist environment for a long time. The more preferable content of carboxymethyl cellulose is 0.5 to 15% by mass%, 1 to 12%, and particularly 2 to 9%. When the content of carboxymethyl cellulose is too large, the viscosity of the aqueous solution of the organic compound is lowered, and it becomes difficult to fibrillate when producing the organic fiber by the dry spinning method.

As for the pH-adjusted organic fiber, 1 g of the organic fiber has a theoretical value of inorganic ion concentration of 142.0 mM for Na ⁺ , 5.0 mM for K ⁺ , 1.5 mM for Mg ²⁺ , 2.5 mM for Ca ²⁺ , and Cl ^−. Is 148.8 mM and HPO ^4- is 1.0 mM, the pH of the aqueous solution is preferably 7.0 or less when immersed in 50 ml of simulated body fluid at 37°C for 16 hours. When the pH of the aqueous solution is higher than 7.0, it is difficult to suppress the pH increase due to the alkali metal ions or alkaline earth metal ions eluted from the glass fiber.

Further, the pH-adjusted organic fiber may contain a small amount of a pharmacologically active ingredient for promoting wound healing. For example, growth factors (eg, TGF, bFGF, PDGF, EGF), antibiotics (eg, chlorhexidine gluconate, benzalkonium chloride, benzenitium chloride, sulfa drugs), antiseptics (eg, povidone, iodine), anti-inflammatory agents (eg, hydrocortisone, triamcinolone). -Acetonide), a skin protective material (for example, zinc oxide), etc. can be blended. (4) Fiber laminate The fiber laminate has a hydrogel fiber layer 1 on the wound side and a glass fiber layer 2. The fiber laminate has a first surface X on the wound surface side and a second surface Y on the opposite side to the wound surface.

The fiber laminate may have a plurality of glass fiber layers. Further, the fiber laminate may further have one or more hydrogel fiber layers in addition to the hydrogel fiber layer provided closest to the wound surface side.

The fiber laminate may have a structure composed of only a hydrogel fiber layer and a glass fiber layer, but may include other layers, for example, the pH-adjusting fiber layer described above.

When the fiber laminate includes a pH adjusting fiber layer, it can be provided between the hydrogel fiber layer and the glass fiber layer and/or on the non-wound surface side of the glass fiber layer. Further, glass fiber layers and pH adjusting fiber layers may be provided alternately. In this case, the number of laminated glass fiber layers and pH adjusting fiber layers is not particularly limited, but the total number is preferably 3 to 41 layers, 3 to 31 layers, and particularly 5 to 21 layers. As the number of layers increases, the layer thickness per layer becomes smaller, making it easier to balance the elution amount of alkali metal ions and alkaline earth metal ions (and the pH increasing effect) with the pH decreasing effect of the organic fiber layer. Become. However, if the number of laminated layers is too large, the layer thickness per layer becomes too thin, and the pH adjusting fiber layer may disappear.

(5) Moisture Non-Absorbing Member The wound dressing of the present invention is preferably provided with a moisture non-absorbing member on the second surface Y of the fiber laminate.

The moisture non-absorbing member is made of a material that is waterproof and does not easily deteriorate due to moisture. Therefore, it is possible to prevent the fiber laminate from being dissolved early due to the invasion of moisture from the outside. Further, it can prevent the invasion of bacteria and reduce the risk of bacterial infection.

Further, it is desirable that the moisture non-absorbing member is provided so that the peripheral portion thereof protrudes from the fiber laminate. Since the non-moisture absorbing member can adhere to the skin, the fiber laminate can be fixed to the wound surface by providing the protruding portion. Further, by adhering to the normal skin around the wound surface, blood or exudate containing various ions eluted from the glass can be retained on the wound surface.

The thickness of the moisture non-absorbing member is preferably 5 to 100 μm, 7 to 80 μm, 10 to 60 μm, and particularly 18 to 34 μm. If the thickness of the moisture non-absorptive member is too thin, the moisture non-absorptive member is likely to be broken, and the wound surface cannot be protected from physical irritation from the outside. When the thickness of the moisture non-absorptive member is too thick, the flexibility of the moisture non-absorptive member is extremely reduced, and a feeling of strangeness is likely to occur when the moisture non-absorptive member is attached to a flexion site such as a heel or a knee. In addition, as a result of the increased thickness of the wound dressing, it is difficult to adhere along the skin surface having fine irregularities, the adhered state tends to be conspicuous, and discomfort tends to increase.

The moisture non-absorptive member may be a so-called self-adhesive type material in which the material itself has tackiness, but it is preferably a polymer film including an adhesive layer and a support layer.

When composed of a polymer film, the support layer is preferably made of at least one selected from the group consisting of polyurethane, polypropylene, polyisobutylene, polyisoprene, polystyrene, and polybutylene terephthalate, and the adhesive layer is an acrylic adhesive, a urethane adhesive. It is preferable that at least one selected from the group consisting of adhesives and silicone-based adhesives is used. There is no limitation on the preferable combination of the support layer and the pressure-sensitive adhesive layer, but a combination of polyurethane and an acrylic pressure-sensitive adhesive is particularly preferable.

The moisture non-absorptive member preferably has a water vapor permeability per 24 hours of 50 g/m ² or more, 100 g/m ² or more, and particularly 400 g/m ² or more. Here, the “moisture permeability” is a value obtained under the B condition (temperature 40° C., relative humidity 90%) defined in JIS Z0208. If the moisture vapor transmission rate is too low, when the wound dressing is applied to the skin, perspiration tends to accumulate on normal skin and stuffiness tends to occur.

(6) Wound dressing The wound dressing of the present invention preferably has the following properties.

The theoretical value of inorganic ion concentration for a sample of 230 mg was 142.0 mM for Na ⁺ , 5.0 mM for K ⁺ , 1.5 mM for Mg ²⁺ , 2.5 mM for Ca ²⁺ , 148.8 mM for Cl ⁻ , and HPO ^{4. In} an elution test in which the simulated body fluid was immersed in 43 ml of the simulated body fluid for 16 hours at 37° C. adjusted so that ⁻ was 1.0 mM, the B concentration in the simulated body fluid was 0.1 to 70 mM and the Ca concentration was 3 to 20 mM. It is preferable.

If the B concentration in the simulated body fluid according to this dissolution test is less than 0.1 mM, it becomes difficult to obtain the bactericidal effect required as a wound dressing. On the other hand, when the B concentration is more than 70 mM, the dissolution rate of glass is extremely increased, which requires frequent replacement of the wound dressing. Further, if the Ca concentration is less than 3 mM, it becomes difficult to obtain the effect of promoting cell growth. On the other hand, when the Ca concentration is higher than 20 mM, the dissolution rate of glass is extremely increased, which requires frequent replacement of the wound dressing.

When the pH adjustment fiber layer is included, the theoretical value of the inorganic ion concentration in the sample of 78 mg is 142.0 mM for Na ⁺ , 5.0 mM for K ⁺ , 1.5 mM for Mg ²⁺ , and 2.5 mM for Ca ²⁺ , Cl ⁻ was adjusted to 148.8 mM, HPO ^{4 −} was adjusted to 1.0 mM, 37° C., 0.4 ml of simulated body fluid was added dropwise, and impregnated for 16 hours. In the dissolution test, the surface pH of the sample was 8. It is preferably 7 or less.

When the surface pH of the sample according to this elution test is higher than 8.7, the oxygen supply amount to the cells is extremely reduced, and the cells are hard to grow. In addition, bacteria harmful to the human body such as Staphylococcus aureus easily grow.

In both of the above tests, the fiber laminate is used as a sample.

(7) Method for manufacturing wound dressing First, cotton-like hydrogel fibers, cotton-like glass fibers, and other fibers (for example, pH-adjusting organic fibers) as needed are prepared. Next, these are laminated so that the hydrogel fibers are located on at least one outermost layer. The order and number of layers of each fiber are not particularly limited, except for the hydrogel fiber located in the outermost layer. The cotton-like fiber laminate thus prepared is set in a press and pressed to a desired thickness. Further, the shape of the outer peripheral portion is adjusted to be circular using tweezers. In this way, a fiber laminate in which non-woven fibers are laminated can be obtained.

Further, if necessary, the moisture non-absorbing member may be provided on the surface (second surface) of the fiber laminate opposite to the hydrogel fiber layer. When providing the moisture non-absorptive member, a moisture non-absorptive member having a size larger than that of the fiber laminated body, that is, a size capable of completely covering the fiber laminated body is prepared. Then, the moisture non-absorbing member may be adhered to the fiber laminate so that the pressure-sensitive adhesive layer of the moisture non-absorbing member contacts one surface of the fiber laminate.

The wound dressing of the present invention produced by the above steps provides a moist environment necessary for cell migration and proliferation, and promotes the wound healing process by supplying ions such as calcium and boron to the wound surface, It is possible to prevent the critical colonization of bacteria on the wound surface and infection. Further, when the pH adjusting fiber layer is included, it is possible to further suppress the increase in pH of the wound surface due to the alkali metal ions or alkaline earth metal ions eluted from the glass.

Hereinafter, the present invention will be described in detail based on examples.

(1) Preparation of hydrogel fiber and pH-adjusted organic fiber Hereinafter, a method for preparing the hydrogel fiber and the pH-adjusted organic fiber used in the wound dressing of the present invention will be described.

The hydrogel fiber was produced as follows. First, 15 g of ion-exchanged water was added to 3 g of polyvinyl alcohol (Wako Pure Chemical Industries, Ltd.) having an average polymerization degree of 1500 to 1800 and a saponification degree of 78 to 82%, and well stirred to prepare a hydrogel aqueous solution. Then, a hydrogel fiber was produced by the same method as the organic fiber.

The pH-adjusted organic fiber was produced as follows. First, 0.8 g of polyvinyl alcohol (Wako Pure Chemical Industries, Ltd.) having an average polymerization degree of 1500 to 1800 and a saponification degree of 78 to 82%, 2 g of HM pectin (Kanto Kagaku), and 0.2 g of carboxymethyl cellulose were added 15 g of ion-exchanged water. After stirring well, an aqueous solution of an organic compound was prepared. Subsequently, an aqueous solution of an organic compound was filled in a syringe (capacity: 25 mL), and an air nozzle and a gas burner (Kinoshita blue burner) were installed near the syringe nozzle. The solution discharged from the syringe nozzle was blown off with high-pressure air, and the moisture was evaporated by a burner flame on the extension line to form a cotton-like short fiber. Further, it was dried at 80° C. overnight to remove water. In this way, an organic fiber was produced.

(2) Production of bulk glass Table 1 shows composition examples (Nos. 1 to 5) of bulk glass used for producing the glass fiber of the present invention, density, and B and Ca concentrations in the simulated body fluid.

Hereinafter, a method for manufacturing bulk glass will be described.

First, various glass raw materials such as natural raw materials and chemical conversion raw materials were weighed and mixed so that the glass compositions shown in Table 1 were obtained, to prepare glass batches. Next, this glass batch was put into a platinum-rhodium alloy crucible and then heated at 1200 to 1550° C. for 4 hours in an indirect heating electric furnace to obtain a molten glass. In addition, in order to obtain a homogeneous molten glass, the molten glass was stirred a plurality of times using a heat-resistant stirring rod during heating. Then, the obtained molten glass was poured into a refractory mold and allowed to cool in air to obtain a bulk glass sample.

Subsequently, the density measurement of the obtained bulk glass and the amounts of B and Ca eluted in the simulated body fluid were evaluated (In vitro Test). The results are shown in Table 1.

The density was measured by the Archimedes method.

The amounts of B and Ca eluted in the simulated body fluid were evaluated as follows.

First, an agglomerated glass sample is crushed, glass having a particle size of 300 to 500 μm is precisely weighed by a density of 0.256 weight, and then 60 ml of simulated body fluid is put into a polypropylene container (PP container) having a capacity of 100 ml. The sample was dipped and an elution test was performed under the conditions of 37° C. and 2 days. At that time, stirring was performed once/day. The stirring was performed by shaking the PP container several times by hand. After the elution test, the test solution was filtered, and the concentrations of B and Ca in the eluate were quantified using ICP-OES.

The simulated body fluid was prepared as follows. First, a beaker containing 100 ml of distilled water was set on a stirrer. Next, each reagent (7.995 g/L NaCl, 0.353 g/L NaHCO ₃ , 0.224 g/L KCl, 0.174 g/L K ₂ HPO ₄ , 0.305 g/L MgCl ₂ ·. 6H ₂ O, 0.368 g/L CaCl ₂ ·2H ₂ O, 0.071 g/L Na ₂ SO ₄ ) were weighed, and after the respective reagents were completely dissolved, the next reagents were added to distilled water in order. And melted to form a solution. The reagent attached to the medicine packing paper was dissolved in the solution by pouring distilled water. Next, 90 ml of distilled water was added to 10 ml of 35% hydrochloric acid to prepare diluted hydrochloric acid, and this was added little by little to the solution until the turbidity disappeared. Next, the solution was transferred to a 2 L beaker, 825 ml of distilled water was added, and the mixture was stirred with a hot stirrer. Next, a pH meter was prepared, and diluted hydrochloric acid was gradually added with a dropper to dissolve the diluted hydrochloric acid to pH 2. Subsequently, 6.057 (g/L) of trishydroxymethylaminomethane (Tris buffer) was added to the solution to dissolve it, and after adjusting the pH to 8, diluted hydrochloric acid was gradually added while heating with a hot stirrer, and finally the liquid temperature. The solution was brought to pH 7.25 at 37°C. This solution was transferred to a graduated cylinder with a stopper, distilled water was added to make 1 L, and the solution was shaken well so as to be mixed. The solution thus obtained was transferred to polyvin and then stored in a refrigerator for 1 day or more to obtain a simulated body fluid used in the experiment.

The theoretical values of the inorganic ion concentration in the simulated body fluid are as follows: Na ⁺ 142.0, K ⁺ 5.0, Mg ²⁺ 1.5, Ca ²⁺ 2.5, Cl ⁻ 148.8, HPO ^{4. -} it is 1.0. (All units are mM).

(3) Production of glass fiber Table 2 shows the average fiber diameter and the specific surface area of the glass fiber.

Hereinafter, a method for producing glass fibers used in the wound dressing of the present invention will be described.

The composition No. of bulk glass was added to a noble metal pot equipped with a glass discharge nozzle. 1 was charged and the glass sample was remelted by electric heating. After that, high-speed air was blown onto the glass flowing down from the discharge nozzle, and the molten glass was drawn into fibers to obtain cotton-like glass fibers.

The average fiber diameter of the glass fibers was measured as follows. First, a secondary electron image or a backscattered electron image of glass fiber is taken using a scanning electron microscope (HITACHI s-3400N type II). Next, the diameter of 50 glass fibers was measured using the length measuring function of the scanning electron microscope, and the average value was used as the average fiber diameter of the glass fibers.

The specific surface area was measured as follows. First, glass fiber was filled in a sample cell whose weight was measured in advance, and after performing a drying treatment at 0.050 Torr or less at a temperature of 300° C. for 3 hours using a sample pretreatment device (Flo Vac Degasser), The total weight of the sample cell and glass fiber was measured. Next, the sample cell was set in an automatic specific surface area/pore size distribution measuring apparatus main body (QUADRASORB SI), the adsorption isotherm of nitrogen gas was measured, and the sample surface area was determined by the BET method (multipoint method). Then, the surface area of the sample per weight was calculated from the weight of the glass fiber.

(4) Production of Fiber Laminate A fibrous laminate was produced using the cotton-like hydrogel fiber, pH-adjusted organic fiber and glass fiber produced as described above.

Table 3 shows the compounding amount and compounding ratio of each fiber of the fiber laminate, and the number of layers.

First, the glass fiber and the organic fiber having the compounding amounts shown in Table 3 were taken out, and this was evenly divided by the number of laminated layers shown in Table 3. Next, two release films were prepared, and one layer of organic fiber was placed on one release film. Subsequently, one layer of glass fiber was laminated on the organic fiber, the organic fiber and the glass fiber were repeatedly laminated in this order, and finally the organic fiber was laminated (21st layer). Subsequently, one layer of cotton-like hydrogel fiber (5 mg) was laminated, and finally another release film was placed.

Next, the cotton-like fiber laminate sandwiched between two release films was set in a press and pressed to a thickness of 3 mm. Further, the shape was adjusted by using tweezers so that the size became φ15 mm.

The prepared laminated sample was packed in a nylon pack with a zipper, and then sterilized with gamma rays to prepare Sample A (Example 1) for animal experiments. The dose of gamma ray sterilization was 25 kilogray. In this way, a fiber laminate (hereinafter, simply referred to as a fiber laminate sample) was obtained.

Next, using the produced fiber laminate sample, the concentrations of B and Ca eluted in the simulated body fluid and the pH of the sample surface were measured. The results are shown in Table 4.

The amounts of B and Ca eluted in the simulated body fluid were evaluated as follows.

First, three prepared fiber laminate samples were prepared, 42.5 ml of simulated body fluid was placed in a polypropylene container (PP container) having a capacity of 100 ml, and the fiber laminate was immersed in the polypropylene container (PP container) at 37° C. for 16 hours. A dissolution test was performed. After the elution test, the test solution was filtered, and the concentrations of B and Ca in the eluate were quantified using ICP-OES.

The surface pH of the sample in the simulated body fluid was evaluated as follows.

First, one fiber laminated body sample was prepared, 0.4 ml of simulated body fluid was put into an ointment container having a capacity of 5 ml, and the fiber laminated body sample was impregnated with it, and an elution test was performed at 37° C. for 16 hours. After the elution test, the fiber laminate sample was sampled with tweezers, and the surface pH on the wound side was measured using a flat pH electrode (HORIBA ISFET 0040-10D) and a pH meter (HORIBA F-71).

The simulated body fluid used for the evaluation is the same as that used for the evaluation of the bulk glass.

(5) Preparation of wound dressing A wound dressing was prepared using the fiber laminate sample prepared and sterilized as described above.

First, as a moisture non-absorbing member, a medical film (thickness 25 μm, 50 mm×50 mm) having a polyurethane support layer coated with an acrylic adhesive was prepared. Then, the adhesive film side of this medical film was attached so that one surface of the fiber laminate sample was in contact.

The wound dressing thus obtained was in a state in which the medical film protruded from the fiber laminate by 15 to 30 mm over the entire circumference.

1 Hydrogel Fiber 2 Glass Fiber X First Surface Y Second Surface

Claims (16)

A hydrogel fiber layer comprising a hydrogel fiber layer containing an organic fiber capable of forming a hydrogel, and a glass fiber layer containing a glass fiber containing B ₂ O ₃ and CaO as glass constituents. Is located on the wound surface side. The wound dressing material according to claim 1, wherein the organic fiber capable of forming a hydrogel contains at least one selected from the group consisting of synthetic resins, proteins, and saccharides. At least one organic fiber capable of forming a hydrogel is selected from the group consisting of polyvinyl alcohol, polyvinylpyrrolidone, polyethylene oxide, polyethylene glycol, carboxymethyl cellulose, gelatin, collagen, tamarind seed gum, guar gum, locust bean gum, starch and pullulan. The wound dressing according to claim 1 or 2, further comprising: The wound dressing material according to any one of claims 1 to 3, wherein the organic fiber capable of forming a hydrogel contains 80% or more by mass of polyvinyl alcohol. Glass fibers, in mass% of oxide _{equivalent, SiO 2 5~70%, B 2} O 3 5~40%, of claims 1 to 4, characterized in that it consists of a glass containing 1 to 50% CaO The wound dressing according to any one of claims. The glass fiber is made of glass containing MgO 0 to 20%, Na ₂ O 0 to 20%, K ₂ O 0 to 40%, and P ₂ O ₅ 0 to 20% by mass% in terms of oxide. The wound dressing material according to any one of claims 1 to 5. The wound dressing material according to claim 1, wherein the glass fiber has a specific surface area of 0.01 m ² /g or more. Glass fibers were classified into a particle size of 300 to 500 μm to obtain a density of 0.256 parts by weight of glass powder, and the theoretical value of the inorganic ion concentration of Na ⁺ was 142.0 mM, K ⁺ was 5.0 mM, and Mg ²⁺ was 1. 0.5 mM, Ca ²⁺ is 2.5 mM, Cl ⁻ is 148.8 mM, and HPO ^{4 −} is 1.0 mM. The wound dressing material according to any one of claims 1 to 7, wherein the concentration of B in the simulated body fluid is 0.1 to 70 mM and the concentration of Ca is 3 to 20 mM in the dissolution test with stirring. The wound dressing material according to any one of claims 1 to 8, wherein the average fiber diameter of the glass fibers is 100 nm to 10 µm. The theoretical value of inorganic ion concentration for a sample of 230 mg was 142.0 mM for Na ⁺ , 5.0 mM for K ⁺ , 1.5 mM for Mg ²⁺ , 2.5 mM for Ca ²⁺ , 148.8 mM for Cl ⁻ , and HPO ^{4. In} an elution test in which the simulated body fluid was soaked in 43 ml of the simulated body fluid at 37° C. and adjusted to −1.0 mM for 16 hours, the B concentration in the simulated body fluid was 0.1 to 70 mM and the Ca concentration was 3.0 to 20 mM. The wound dressing according to any one of claims 1 to 9, wherein The fiber laminate has a first surface on the wound surface side and a second surface on the opposite side to the wound surface, and a moisture non-absorbing member is provided on the second surface of the fiber laminate. The wound dressing according to any one of claims 1 to 10, which is characterized in that. The wound dressing according to claim 11, wherein the moisture non-absorbing member is provided on the second surface of the fiber laminate so that the peripheral edge of the moisture non-absorbing member protrudes from the fiber laminate. .. The wound dressing material according to claim 11 or 12, wherein the moisture non-absorbing member comprises a polymer film including an adhesive layer and a support layer. Polymer film, at least one support layer selected from the group consisting of polyurethane, polypropylene, polyisobutylene, polyisoprene, polystyrene, polybutylene terephthalate, and from the group consisting of acrylic adhesive, urethane adhesive, silicone adhesive The wound dressing according to claim 13, which is composed of at least one kind of adhesive layer selected. It is characterized by comprising a step of laminating organic fibers capable of forming a hydrogel and glass fibers containing B ₂ O ₃ and CaO as glass constituent components, compressing them, and molding into a non-woven fiber laminate. Method for manufacturing wound dressing. The method for producing a wound dressing according to claim 15, wherein a non-moisture absorbing member is further laminated on the surface of the fiber laminate opposite to the wound surface.