JPH09277418A - Medical material and its manufacture - Google Patents

Abstract

PROBLEM TO BE SOLVED: To obtain a medical material having flexibility, liquid shielding properties, extremely little generation of fiber chips from the cut surface and excellent drape. SOLUTION: The medical material is obtained by discharging a thermally melted thermoplastic resin from a spinning hole in a long fiber cloth state, simultaneously orienting it in a fiber state by heating fluid injected from a pore near the hole to form a fiber layer having three-dimensional confounding, then placing a film on the layer and press bonding it by a press bonding roll. In this case, the three-dimension confounded extrafine finer layer is formed as an adhesive layer between the long fiber cloth state and the film.

Description

Detailed Description of the Invention

[0001]

BACKGROUND OF THE INVENTION 1. Field of the Invention The present invention relates to a medical material and a method for producing the same, more specifically, a medical material having a liquid-shielding property, an extremely small amount of fiber waste from a cut surface, and a good texture. Material and manufacturing method.

[0002]

2. Description of the Related Art Conventionally, knitted fabrics, woven fabrics, non-woven fabrics, plastic thin films and the like have been used as medical materials used as drapes (cloths to be put on a patient during surgery) or operating table covers during surgery. . Generally, a woven fabric, a knitted fabric, or a non-woven fabric is soft and has a good texture, but when a large amount of body fluid, moisture, or the like is attached, it penetrates into the inside. That is, when used as a drape, there is a risk that the patient will be contaminated with his or her blood or drugs during surgery, and even when used as a cover for the operating table, blood or drugs will penetrate into the table itself, There was a risk of contaminating everything above.

Further, a cloth made of a woven fabric, a knitted fabric, a non-woven fabric or the like has a problem of generation of fiber waste. That is, during operation, the fiber pieces generated from these fabrics may come loose and contaminate the patient. For example, in the case of a drape, a window for actually performing a surgical operation may be made on site during surgery, but in such a case, the problem of fiber waste is particularly great. In this sense, a knitted fabric or a woven fabric composed of yarn obtained by twisting short fibers is not desirable, and the same problem occurs in the short fiber system even in the case of a non-woven fabric. In this way, minimizing fiber waste and the like is necessary to prevent contamination of the environment of the operating room and the surgical incision site by foreign material pieces.

Therefore, conventionally, in order to solve these problems, a sheet in which a cloth and a film-like material are integrated as a liquid impermeable layer has been used. That is, a soft and good-looking cloth covers the patient or the table, and a film-like material as a liquid impermeable layer prevents various liquids such as blood and washing liquid generated during surgery from diffusing to other parts. I was there.

For example, as an example of a medical material in which a cloth and a liquid impermeable layer are integrated, an extruded film laminated cloth (Japanese Unexamined Patent Publication Nos. 4-203848 and 05-05).
148759). For example, Japanese Patent Laid-Open No. 05-1
In Japanese Patent No. 48759, a nonwoven fabric is subjected to water repellent treatment and extrusion laminated. According to this, the surface fiber of the water repellent non-woven fabric is covered with the extruded liquid impermeable layer, and the non-woven fabric and the impermeable layer are bonded and integrated.

However, in such a structure, pinholes are apt to be generated, the liquid impermeable layer which is present at all cannot serve its purpose, and there is a risk of exposure due to permeation of blood or the like. That is, since the surface of the fabric generally has unevenness,
It is a very difficult technique to form a thin liquid-impermeable layer uniformly on top of this without pinholes. As a measure for eliminating such pinholes, it is possible to increase the thickness of the liquid impermeable layer to be extruded and laminated. In fact,
By increasing the thickness of the liquid impermeable layer, it is possible to prevent the occurrence of pinholes, which was an initial problem. However, if the thickness of the liquid impermeable layer is increased, the thickness of the product itself is increased, and as a result, a medical material that is used as a cover cloth during surgery is hard and the texture is impaired. As described above, a satisfactory extrusion-molded film laminated fabric has not been obtained.

Another prior art method used in the manufacture of medical materials is to make the fabric itself adhesive, or to make it melt filmable. For example,
As the former cloth having adhesiveness, (a)
In the case of a non-woven fabric using a molten polymer, a low-melting polymer in which the fibers themselves have a sheath core structure and is coordinated to the sheath side is melted (Japanese Utility Model Publication No. 22317/1990, 20384/1992).
No. 8), or (b) a method of mixing two types of polymer fibers having different melting temperatures to melt only fibers from a polymer having a low melting point (Japanese Patent Laid-Open No. 12565547). . In these methods, the low melting point fibers constituting the web are melted by heat to bond other film-like materials to obtain a medical material. However, these bonding methods did not increase the bonding strength, and the resulting molded product was apt to have defects.

Further, in the latter method in which the cloth itself is made to have a film-forming property, two kinds of molten polymers are used, and a low melting point polymer is dissolved and re-solidified to form a film. As in the case of the extruded layer, there is a problem that pinholes are easily generated and the defective rate is high. Also, because the cost of manufacturing the sheath-core structure fiber itself is high,
There was a drawback that the price of the product as a medical material was high.

Further, another structure (Japanese Patent Laid-Open No. 55-3739).
No. 0, Japanese Utility Model Publication No. 62-25534), in order to solve the above-mentioned problems, a flexible film such as vinyl chloride is used and integrated with a fabric through an adhesive. There is something. The types of adhesives include water-based or solvent-based polymer resins, adhesives of a chemical crosslinking method such as ester crosslinking of epoxy resins, and thermoplastic resins typified by polyolefins, polyesters, and polyamides. There is a hot melt agent. Among them, the adhesive by chemical cross-linking has a high adhesive force to a specific material, but due to the solvent or plasticizer contained in the adhesive itself,
There is a risk that the performance of the product may be impaired by volatilization or migration of these.

In addition, the form of the adhesive layer may be a full-surface adhesive in which the adhesive layer covers the entire surface or a partial adhesive in which only a part is adhered. In the case of full surface adhesion, the adhesion is strong. Further, even if the cloth is cut arbitrarily, one side of the cloth is fixed by the adhesive, so that the generation of fiber waste is reduced as compared with the cloth without the film. However, with full-face adhesion, the texture tends to become hard because the cloth and film are completely fixed. As the partial adhesion, streak-like adhesion and dot-like adhesion are known. The texture of these partially bonded samples is softer than that of the fully bonded sample. However, when the cloth is cut, if the unbonded portion is cut, the cloth becomes the same as the cloth without the film, and the effect of reducing the generation of fiber waste cannot be obtained.

As described above, the conventionally used medical materials have not been satisfactory in terms of their performance and safety.

[0012]

DISCLOSURE OF THE INVENTION As a result of studying the problems of the above-mentioned prior art, the inventors of the present invention have found that a fiber layer made of three-dimensionally entangled ultrafine fibers is used as an adhesive layer between a long fiber cloth and a film. It has been found that by using it, a medical material that is flexible, has a liquid blocking property, generates very little fiber waste from the cut surface, and is safe and has a good texture is obtained.

[0013]

That is, the present invention is characterized in that a fiber layer made of three-dimensionally entangled ultrafine fibers is formed as an adhesive layer between a long fiber cloth and a film. It is a material, and a thermoplastic resin that is heated and melted is discharged from a spinning hole onto a long-fiber cloth or a film, and at the same time, it is stretched into a fibrous shape by a heating fluid ejected from pores near the spinning hole to form a three-dimensional shape. The method for producing a medical material is characterized in that after forming a fiber layer having entanglement, a film or a long fiber cloth is placed on the fiber layer and pressure-bonded by a pressure roll.

The present invention will be described in detail below. The long fiber cloth of the present invention is a long fiber woven fabric, a long fiber knitted fabric, or a long fiber non-woven fabric. As the long fiber woven fabric and the long fiber knitted fabric, any known woven or knitted fabric can be used as long as it uses long fibers. In order to obtain a long-fiber nonwoven fabric, any nonwoven fabric made by a known production method can be used, but from the viewpoint of suppressing the generation of fiber waste, which is the object of the present invention,
In particular, it is more preferable to use a long-fiber nonwoven fabric such as a spunbonded nonwoven fabric in which a thermoplastic resin is laminated directly on the upper side of a net with a fiber stretched with an air sucker immediately below a spinning hole and partially thermally bonded or thermocompression bonded. In addition, it is more preferable to use, as the fiber of the cloth, a stretchable yarn or a crimp yarn obtained by a known method or the like for the purpose of improving the feel and the flexibility.

As the thermoplastic resin constituting the long fiber cloth of the present invention, nylon 6, nylon 66 and nylon 12 are used.
Polyamide resin such as, polyolefin resin containing a monoolefin polymer such as ethylene, propylene and butene and copolymers thereof as a main component, polyester resin such as polyethylene terephthalate and polybutylene terephthalate, acrylic resin and the like are used. It The fibers constituting these long-fiber non-woven fabrics may be a single component or a mixed component. That is, the resin described above may be used alone,
For example, it may be a composite fiber obtained by mixing polyethylene / polypropylene, polyethylene or polypropylene / polyester. However, when considering the soft texture, polyamide fibers, particularly preferably nylon 6
A fabric made of fibers is more preferable. Further, as the long fiber non-woven fabric, a cellulosic long fiber non-woven fabric obtained by wet coagulation from a cellulose copper ammonia solution is also used. Since this non-woven fabric itself has liquid absorbability, there is no need for processing such as liquid absorption treatment and it is excellent in biocompatibility, which is preferable.

The long fiber fabric of the present invention has a basis weight of 20 g / m.
^{2 to} 80 g / m ² is preferable. The basis weight of the non-woven fabric layer is 20g
If it is less than / m ^2, it is too thin to have sufficient strength and lacks in texture as a medical material. On the other hand, if it exceeds 80 g / m ² , the texture becomes hard, which is not preferable as a medical material. The fiber diameter of the long-fiber cloth of the present invention is not particularly limited as long as the texture of the cloth and the laminate is not impaired, but is 0.5 to
6 denier is preferable, and 1.0 to 3 denier is more preferable, because strength and texture are balanced.

In order to impart water-absorbing performance to the medical material of the present invention, it is preferable to apply a known water-absorbing agent such as hydrophilic surfactant to the nonwoven fabric before use. A known film can be used as the film used in the present invention. That is,
Examples thereof include polyolefin polymer films such as polyethylene polymers and polypropylene polymers, polyvinyl chloride films, polyvinylidene chloride films, polytetrafluoroethylene films, and films made of ethylene vinyl acetate copolymer. These polymers alone,
Alternatively, they may be mixed and used, or films of different polymers may be laminated and used. Among them, from the viewpoint of flexibility, adhesiveness, flammability, and price, a polyolefin polymer film such as polyethylene polymer, polypropylene polymer, amorphous polypropylene, or a film obtained by mixing or laminating a polyolefin polymer and an ethylene vinyl acetate copolymer. preferable.

The thickness of the film of the present invention is 5 μm to 35 μm.
μm is good. If the thickness of the film is less than 5 μm, pinholes are likely to occur in the product, and the reliability of the product may be reduced. On the other hand, when the thickness of the film exceeds 35 μm, the softness of the product is lowered and it becomes difficult to use. In this sense, the thickness of the film of the present invention is preferably 5 μm to 35 μm, more preferably 15 μm to 25 μm.

In the production of the medical laminated material of the present invention, the thermoplastic resin heated and melted was discharged from the spinning hole onto the long fiber cloth, and the discharged thermoplastic resin was provided in the vicinity of the spinning hole. Stretching by heating fluid ejected from the pores to form ultrafine fibers, the ultrafine fibers are formed as a fiber layer having three-dimensional entanglement on a long fiber cloth, a so-called microweb, and then a film is placed on the fiber layer. Crimp with a crimp roll,
A method of integrating a laminate comprising a long fiber cloth, a fiber layer and a film is adopted. As in this method, after the fiber layer is formed on the long-fiber fabric, the film may be subsequently placed on the fiber layer and pressure-bonded by a pressure roll to integrate the laminate, but on the contrary, on the film. It is also possible to form a fiber layer on the above, and subsequently place a long fiber cloth on the fiber layer and press it with a press roll to integrate the laminate.

For the production of the ultrafine fibers having the above-mentioned three-dimensional entanglement, for example, a curtain spray made by Santool can be used. This device has a slit-shaped spinning hole, and is provided with a slit-shaped ejection port for heating fluid in the vicinity of this spinning hole. Immediately below the slit-shaped spinning hole, there is a comb-teeth-shaped separating material, and the thermoplastic resin spun in paper is ejected from the slit-shaped heating fluid ejection hole in the vicinity (usually heating Air and hot air), and at the same time, it is divided into fine fibers by the splitting body,
It is formed as a fiber layer on a long fiber fabric or film.

In addition, by a method other than this, the thermoplastic resin is discharged from the spinning hole, and the thermoplastic resin is drawn by the heating fluid discharged from the pores provided in the vicinity of the spinning hole to form ultrafine fibers. A so-called melt-blowing method, which is known as a method for manufacturing a non-woven fabric, may be used. Therefore, the ultrafine fibers constituting the fiber layer of the present invention are extremely fine fibers having a denier of 1 denier or less, more preferably 0.01 denier or less, and when used as an adhesive layer for adhering a long fiber fabric and a film, the three-dimensional entanglement thereof. Combined with the structure, it is a very flexible integrated laminate.

The fiber layer thus obtained is formed as a fiber layer having three-dimensional entanglement on a long fiber cloth (or film), and then the film (or,
A long fiber cloth) is placed and pressure-bonded by a pressure-bonding roll to obtain an integrated laminate, that is, a medical material. Here, if the pressure roll is used so that the long fiber cloth side is in contact with the rubber roll and the film side is in contact with the metal roll, it is effective in enhancing the adhesive effect.

Further, the temperature of the pressure-bonding roll needs to be adjusted depending on the time from the formation of the fiber layer to the pressure-bonding with the pressure-bonding roll. The reason is that while the molten thermoplastic resin fiber discharged from the spinning hole is not sufficiently solidified, the long fiber cloth and the film are bonded by a cold roll at a temperature of about room temperature,
After the time has elapsed and the fibers have solidified, the long-fiber cloth and the film are not bonded unless they are pressure-bonded with a heat roll whose surface temperature is kept near the melting point of the fibers.

In the present invention, either the cold roll or the hot roll described above can be used. However, in order to make the long fiber cloth and the film flexible and to bond them by the fiber layer, the roll surface temperature is 10
The time from the formation of the fiber layer to the pressure bonding with the pressure bonding roll using a cold roll at -30 ° C depends on the type of the thermoplastic resin and the temperature of the heating fluid, but is preferably within 2 seconds. Further, when using a hot roll, it is preferably carried out at 80 to 200 ° C., though it depends on the kind of the thermoplastic resin used.

The pressure-bonded and integrated laminate of the present invention thus obtained is such that a fiber layer having a three-dimensional entangled structure has an adhesive function between the long-fiber cloth and the film and has a uniform thickness. Therefore, it is flexible and generates less fiber waste.
The fiber layer of the thermoplastic resin interposed between the long fiber cloth and the film has a three-dimensional entangled structure, a uniform thickness, and is dispersed in an unspecified direction. Fiber layer of uniform thickness, the basis weight is required ^{2g / m 2 ~15g / m 2} , preferably ^{3g / m 2 ~10g / m 2} . If it is less than 2 g / m ² , the adhesive strength is insufficient and the effect of preventing the generation of fiber waste is lost, and if it exceeds 30 g / m ² , the flexibility is lost, which is not preferable as a medical material.

The thermoplastic resin used for the fibers constituting the fiber layer includes polymers of olefins such as ethylene, propylene and butene, or copolymers of these olefins, copolymers of olefins and vinyl acetate, acrylic acid, methacrylic acid and the like. Combined, dimer acid as a dicarboxylic acid component, adipic acid,
Polyamide resin using azelaic acid, sebacic acid, etc. as diamine, ethylenediamine, hexamethylenediamine, xylylenediamine, PP′-methylenediamine, alkanolamine, etc., the above-mentioned dicarboxylic acid component, and glycol etc. as diol component. A thermoplastic elastomer resin such as a polyester resin, a styrene / butadiene block polymerized elastomer, a styrene / isoprene block polymerized elastomer, or a styrene / ethylene / propylene / styrene block polymerized elastomer is used.

Among these thermoplastic resins, styrene
A thermoplastic elastomer resin such as a butadiene block polymerized elastomer, a styrene / isoprene block polymerized elastomer, or a styrene / ethylene / propylene / styrene block polymerized elastomer is particularly preferably styrene-isoprene-styrene (SIS) or styrene-butadiene-styrene. When (SBS) or styrene-ethylene-butadiene-styrene (SEBS) is used alone or by blending with other resin, the adhesion between the cloth and the film can be further improved.

Further, a copolymer of an olefin and vinyl acetate, acrylic acid, methacrylic acid or the like, and a typical example thereof is ethylene vinyl acetate (EVA) resin can be preferably used. The medical material of the present invention thus obtained is flexible, has a small amount of lint such as fiber waste, and is a flexible sheet having a liquid-shielding property. It is also suitable as a medical-related sheet such as a surgical gown, a hat, a mask or a care sheet, an incontinence pad, and pants.

[0029]

BEST MODE FOR CARRYING OUT THE INVENTION Hereinafter, the present invention will be described in more detail with reference to Examples. In the example obtained in the present invention, each item was evaluated by the following evaluation methods. (1) Evaluation Method of Integration The non-woven fabric and the film were integrated and evaluated by the adhesive strength of the non-woven fabric and the film. The evaluation method is JIS-L
According to -1086. That is, length 15 cm, width 5 cm
5 samples were taken for each of the length and the weft, and the cloth tape No. manufactured by Nichiban Co., Ltd. was attached to the film side. 102 (width 50 mm) is stuck, 5 cm from the end is accurately peeled between the nonwoven fabric and the film in the length direction of the sample piece, and it is held in the tensile tester and the gap 5
Attached at cm, peeling length 5 at pulling speed 100 mm / min
cm is T-type peeled, and the maximum peel strength is 3 from the chart.
An average value of 6 points was calculated by taking the points and 3 local minimum values.

(2) Method of measuring liquid shielding property The liquid shielding property was evaluated by the water resistance test method (hydrostatic pressure method) of JIS-L-1092. Also, check the presence or absence of pinholes on the film by checking the film side of the sample to 20 x 20 cm.
2 ml of IPA (2-propanol) colored with a red ink was applied to the range of, and wiped off for observation.

(3) Measurement of dusting property The dusting property was measured according to (2) Light scattering type particle counter method of JIS-B-9923. A tumbling method was used for the dust generating device. Flow rate of light scattering type particle counter is 500ml /
Minutes, the number of particles in 0.01 cubic feet, or 3
The number of particles measured in 4 seconds was measured 12 times, and the number of particles generated in 1 second from the sample was calculated from the average of 10 times excluding the maximum value and the minimum value.

As a sample, a sample having a length of 50 cm and a weft of 100 cm was prepared as a blank, and the edges were wrapped with cellophane tape,
Prevented lint from being generated from the cut surface. As a measurement sample, 20 pieces of wefts and 20 pieces of wefts having a length of 30 cm were put in the same cloth as the blank. The calculation was by subtracting the number of particles from the blank from the number of particles from the scored fabric.

(4) Measurement of bending resistance In order to evaluate the flexibility, the bending resistance of the sample (gf / cm ² /
cm) to KES (Kawabata's Evalua
It was measured by the bending characteristics of the Tion System method. (5) Evaluation of texture The texture was evaluated by a sensory test by touching the sample with hands. The evaluations are indicated by ◯, Δ, and x, soft ones were ◯, hard ones were x, and the middle was Δ.

[0034]

Example 1 As a long fiber cloth, a commercially available spunbonded non-woven fabric (weight per unit area: 50 g / m ² ) made of nylon 6 fiber was used. This nonwoven fabric was subjected to water absorption processing. That is, Nopco Wet SN20-T manufactured by San Nopco Co., Ltd. was diluted with water so as to have a concentration of 1 g / m ² , impregnated, and then dried. As the film, a multilayer film having a total thickness of 25 μm, which is composed of an ethylene-vinyl acetate copolymer film having a thickness of 14 μm, a special low-density polyethylene film having a thickness of 8 μm, and a mixture film of a low-density polyethylene polymer and a polypropylene polymer having a thickness of 3 μm, is used. Using.

The above-mentioned non-woven fabric was placed on a traveling conveyor, and a curtain spray made by Suntool was used to discharge the melted ethylene vinyl acetate (EVA) resin having a melt viscosity of 2000 cps at a pressure of 0.6 Kg / cm ^2. ,
The fiber was stretched with hot air at a temperature of 160 ° C. to form a fiber, and a fiber layer of uniform thickness having a three-dimensional entanglement with a basis weight of 7 g / cm ² was formed on the nonwoven fabric.

Two seconds after the formation of this fiber layer, the ethylene vinyl acetate copolymer film in the above-mentioned multi-layer film was superposed on this fiber layer so as to be in contact with the fiber layer side, and the non-woven fabric side was covered with a rubber roll and a film. It was passed between a rubber roll having a surface temperature of 21 ° C. and a metal roll so that the metal roll was in contact with the side. Rubber roll is JIS-K
The rubber hardness determined by −6301 was 75 degrees, and the roll was pressed at a roll pressure of 5 kg / cm ² . As a result, the nonwoven fabric and the film were integrated with each other, and the resulting medical material had flexibility, had very little generation of fiber waste from the cut surface, had liquid shielding properties, and had a good texture. The results are shown in Table 1.

[0037]

[Example 2] As the cloth, a spunbonded non-woven fabric made of nylon 6 fiber (weight per unit area: 30 g / m ² ) was used, and the film was
A 20 μm film of low density polyethylene polymer was used. In the same manner as in Example 1, a fiber layer having a three-dimensional entanglement and having a uniform thickness was interposed between the nonwoven fabric and the film, and they were pressure-bonded with a roll to be integrated. From now on,
The generation of fiber waste from the cut surface was extremely small, the liquid shielding property was obtained, and a medical material having a good texture was obtained.
The results are shown in Table 1.

[0038]

[Example 3] A fabric is a long-fiber non-woven fabric composed of cellulose long fibers obtained by wet coagulation from copper ammonia (Basis weight 3
0 g / m ² ), and the film used was a low-density polyethylene polymer 20 μm film. In the same manner as in Example 1, a fiber layer having a three-dimensional entanglement and having a uniform thickness was interposed between the nonwoven fabric and the film, and they were pressure-bonded with a roll to be integrated. From this, it was possible to obtain a medical material having flexibility, generation of fiber debris from the cut surface being extremely small, liquid shielding property, and good texture. The results are shown in Table 1.

[0039]

Example 4 A long-fiber woven fabric (plain weave, basis weight 40 g / m ² ) made of nylon 66 fibers was used as the cloth, and a low-density polyethylene polymer 20 μm film was used as the film. Example 1 between the long fiber fabric and the film
In the same manner as described above, a fiber layer of uniform thickness having three-dimensional entanglement was interposed, and the layers were pressure-bonded with a roll to be integrated. From this, it was possible to obtain a medical material having flexibility, generation of fiber debris from the cut surface being extremely small, liquid shielding property, and good texture. The results are shown in Table 1.

[0040]

[Comparative Example 1] As the nonwoven fabric, a spunbonded nonwoven fabric made of nylon 6 fiber (unit weight: 100 g / m ² ) was used, and as the film, the same multilayer film as in Example 1 was used. In the same manner as in Example 1, a fiber layer having a three-dimensional entanglement and having a uniform thickness was interposed between the non-woven fabric and the multilayer film, and they were pressure-bonded with a roll to be integrated. Although this laminate had a liquid blocking property, it was not preferable as a medical material because it was not flexible and had a poor texture because the nonwoven fabric was thick. The results are shown in Table 1.

[0041]

[Comparative Example 2] As the non-woven fabric, a short fiber non-woven fabric by a needle punching method (unit weight: 40 g / m ² ) was used, and as the film, the same multilayer film as in Example 1 was used. A fiber layer having a three-dimensional entanglement and having a uniform thickness was interposed between the short fiber non-woven fabric and the multilayer film, and they were pressure-bonded with a roll to be integrated. The obtained laminate had flexibility and had a good texture, but generation of fiber scraps from the cut surface was observed. The results are shown in Table 1.

[0042]

[Comparative Example 3] The same non-woven fabric and film as in Example 1 were used. Ethylene vinyl acetate (E used in Example 1
The VA) resin was extruded and extruded by a laminating device to be applied on a non-woven fabric, and a film was immediately overlaid thereon to integrate the non-woven fabric and the film. Although the liquid shielding property of the obtained laminate was obtained, it was not flexible and the texture became hard, which was not preferable as a medical material. The results are shown in Table 1.

[0043]

Comparative Example 4 The same non-woven fabric and film as in Example 1 were used. In the same manner as in Comparative Example 3, an ethylene vinyl acetate (EVA) resin was extruded in a dot shape from a slit and applied on a nonwoven fabric, and a film was immediately overlaid on the nonwoven fabric to integrate the nonwoven fabric and the film. Although the liquid-shielding property of the obtained laminate was obtained, the dots were partially inferior in flexibility at each dot, the texture was hard, and the generation of fiber waste from the cut surface was observed. The results are shown in Table 1.

[0044]

Example 5 As the long fiber cloth, a commercially available spunbonded non-woven fabric made of nylon 6 fiber (unit weight: 50 g / m ² ) was used. This nonwoven fabric was subjected to water absorption processing. That is, Nopco Wet SN20-T manufactured by San Nopco Co., Ltd. was diluted with water so as to have a concentration of 1 g / m ² , impregnated, and then dried. As the film, a multilayer film having a total thickness of 25 μm, which is composed of an ethylene-vinyl acetate copolymer film having a thickness of 14 μm, a special low-density polyethylene film having a thickness of 8 μm, and a mixture film of a low-density polyethylene polymer and a polypropylene polymer having a thickness of 3 μm, is used. Using.

The above non-woven fabric was placed on a traveling conveyor, and styrene-isoprene-styrene (SIS) was heated and melted using a curtain spray made by Suntool.
Discharge resin, pressure 0.6Kg / cm ² , temperature 160 ℃
Stretched with hot air to fiberize and have a basis weight of 7 g / c
A fibrous layer of uniform thickness having a three-dimensional entanglement of m ² was formed on the non-woven fabric.

Two seconds after the formation of this fiber layer, the ethylene vinyl acetate copolymer polymer film in the above-mentioned multilayer film was superposed on this fiber layer so as to be in contact with the fiber layer side, and the non-woven fabric side was covered with a rubber roll and a film. It was passed between a rubber roll having a surface temperature of 21 ° C. and a metal roll so that the metal roll was in contact with the side. Rubber roll is JIS-K
The rubber hardness determined by −6301 was 75 degrees, and the roll was pressed at a roll pressure of 5 kg / cm ² . As a result, the nonwoven fabric and the film were integrated with each other, and the resulting medical material had flexibility, had very little generation of fiber waste from the cut surface, had liquid shielding properties, and had a good texture. The results are shown in Table 1.

[0047]

Example 6 As the long fiber cloth, a commercially available spunbonded non-woven fabric made of nylon 6 fiber (weight per unit area: 50 g / m ² ) was used. This nonwoven fabric was subjected to water absorption processing. That is, Nopco Wet SN20-T manufactured by San Nopco Co., Ltd. was diluted with water so as to have a concentration of 1 g / m ² , impregnated, and then dried. As the film, a multilayer film having a total thickness of 25 μm, which is composed of an ethylene-vinyl acetate copolymer film having a thickness of 14 μm, a special low-density polyethylene film having a thickness of 8 μm, and a mixture film of a low-density polyethylene polymer and a polypropylene polymer having a thickness of 3 μm, is used. Using.

The above-mentioned non-woven fabric was placed on a traveling conveyor, and a curtain spray made by Suntool was used to discharge an ethylene vinyl acetate (EVA) resin having a melt viscosity of 2000 cps, which was heated and melted, at a pressure of 0.6 Kg / cm ^2. ,
The fiber was stretched with hot air at a temperature of 160 ° C. to form a fiber, and a fiber layer of uniform thickness having a three-dimensional entanglement with a basis weight of 7 g / cm ² was formed on the nonwoven fabric.

After 60 seconds, the ethylene-vinyl acetate copolymer film in the above-mentioned multi-layer film was superposed on this fiber layer so that it was in contact with the fiber layer side, and the non-woven fabric side was in contact with the rubber roll and the film side was in contact with the metal roll. It was passed between a rubber roll and a metal roll each having a surface temperature of 115 ° C. The rubber roll has a rubber hardness of 75 degrees defined by JIS-K-6301 and is pressure-bonded at a roll pressure of 5 kg / cm ² . As a result, the non-woven fabric and film are integrated, and they have flexibility, and the generation of fiber waste from the cut surface is extremely small,
Further, a medical material having a liquid-shielding property and a good texture was obtained. The results are shown in Table 1.

[0050]

Example 7 A commercially available spunbonded non-woven fabric (weight per unit area: 50 g / m ² ) made of nylon 6 fiber was used as the long fiber cloth. This nonwoven fabric was subjected to water absorption processing. That is, Nopco Wet SN20-T manufactured by San Nopco Co., Ltd. was diluted with water so as to have a concentration of 1 g / m ² , impregnated, and then dried. As the film, a multilayer film having a total thickness of 25 μm, which is composed of an ethylene-vinyl acetate copolymer film having a thickness of 14 μm, a special low-density polyethylene film having a thickness of 8 μm, and a mixture film of a low-density polyethylene polymer and a polypropylene polymer having a thickness of 3 μm, is used. Using.

The above-mentioned multilayer film was placed on a traveling conveyor so that the ethylene-vinyl acetate copolymer film in the multilayer film was on top, and the melt viscosity was heated and melted by using a curtain spray made by Suntool on it.
Discharge 000 cps ethylene vinyl acetate (EVA) resin, draw with a pressure of 0.6 Kg / cm ² and hot air at a temperature of 160 ° C. to form fibers, and have a basis weight of 7 g / cm ² .
A uniform thickness fiber layer with dimensional entanglement was formed on the non-woven fabric.

Two seconds after the formation of this fiber layer, the above spunbonded non-woven fabric was superposed on this fiber layer, and the surface temperature was 20 ° C. so that the non-woven fabric side was in contact with the rubber roll and the film side was in contact with the metal roll. It was passed between a rubber roll and a metal roll. The rubber roll has a rubber hardness of 75 degrees defined by JIS-K-6301 and a roll pressure of 5 kg / c.
It was crimped with m ² . As a result, the nonwoven fabric and the film were integrated with each other, and the resulting medical material had flexibility, had very little generation of fiber waste from the cut surface, had liquid shielding properties, and had a good texture. The results are shown in Table 1.

[0053]

[Comparative Example 5] As a long fiber cloth, a commercially available spunbonded non-woven fabric made of nylon 6 fiber (unit weight: 50 g / m ² ) was used. This nonwoven fabric was subjected to water absorption processing. That is, Nopco Wet SN20-T manufactured by San Nopco Co., Ltd. was diluted with water so as to have a concentration of 1 g / m ² , impregnated, and then dried. As the film, a multilayer film having a total thickness of 25 μm, which is composed of an ethylene-vinyl acetate copolymer film having a thickness of 14 μm, a special low-density polyethylene film having a thickness of 8 μm, and a mixture film of a low-density polyethylene polymer and a polypropylene polymer having a thickness of 3 μm, is used. Using.

The above non-woven fabric was placed on a traveling conveyor, and a curtain spray made by Suntool was used to discharge ethylene vinyl acetate (EVA) resin having a melt viscosity of 2000 cps, which was heated and melted, to 0.6 Kg / cm ² , 16
Stretched with 0 ° C hot air to form fibers and have a basis weight of 35
A fibrous layer of uniform thickness having a three-dimensional entanglement of g / cm ² was formed on the nonwoven fabric.

Two seconds after forming the fiber layer, the ethylene vinyl acetate copolymer film in the above-mentioned multi-layer film was superposed on the fiber layer so as to contact the fiber layer side, and the non-woven fabric side was placed on the rubber roll and the film side. It was passed between a rubber roll having a surface temperature of 21 ° C. and a metal roll so that the metal roll was in contact with each other. The rubber roll has a rubber hardness of 75 degrees defined by JIS-K-6301 and a roll pressure of 5 kg / c.
It was crimped with m ² . As a result, the non-woven fabric and the film were integrated with each other, the generation of fiber waste from the cut surface was small, and the liquid-shielding property was exhibited, but the flexibility was poor and the texture was not good. The results are shown in Table 1.

[0056]

[Table 1]

[0057]

According to the present invention, it is possible to obtain a medical material which is flexible, has a liquid-shielding property, has very little generation of fiber waste from the cut surface, and has a good texture.

Claims (3)

[Claims] 1. A medical material comprising a long fiber cloth and a film, and a fiber layer formed of three-dimensionally entangled ultrafine fibers as an adhesive layer. 2. The medical material according to claim 1, wherein the basis weight of the fiber layer made of three-dimensionally entangled ultrafine fibers is ² to 15 g / cm ² . 3. A three-dimensional entanglement in which a thermoplastic resin which is heated and melted is discharged from a spinning hole onto a long fiber cloth or a film, and at the same time, it is drawn into a fibrous shape by a heating fluid ejected from pores near the spinning hole. A method for producing a medical material, comprising forming a fiber layer having the following features, placing a film or a long fiber cloth on the fiber layer, and pressing the film or the long fiber cloth with a pressure bonding roll.