KR101903132B1 - Splint for Medical Treatment - Google Patents

Abstract

The present invention relates to a medical splint comprising a core material, a bending stabilizing member, an inner skin, and an outer covering, wherein the bending stabilizing member is positioned on the upper and lower portions of the core member, , Preheated at a temperature equal to or higher than the softening point of each material, and molded into a shape suitable for a bent shape of the affected part, thereby providing a medical splint.

Description

{Splint for Medical Treatment}

BACKGROUND OF THE INVENTION 1. Field of the Invention [0001] The present invention relates to a medical splint, and more particularly, to a medical splint with improved wearability of the joint.

In general, gypsum bandages and synthetic bandages have been used to fix body fractures and injured parts of muscles, and in recent years, fixing methods by various methods such as synthetic splints have been developed. An orthopedic splint is one of the medical supplies for fixing a part of the body such as a fracture part of an arm or a leg so as not to move for a predetermined period.

The splint was used for the longest time when a fractured patient occurred. In the early days, the splint was used to manufacture splint. However, the splint is too heavy to apply to the activity. In order to solve the weight of such gypsum, a synthetic splice flow which is made of synthetic fibers and glass fibers as a support and water-soluble synthetic resin as a curing material and impregnated into a support is widely used.

The synthetic brace flow is used by wrapping the support in padding for easy application to the patient while protecting the curing material.

The splint, which has been developed and used so far, has a three-layer structure in which a base layer protecting the skin and a top layer exposed to the outside are joined along both sides and a core is inserted therebetween.

In splintes, the lower and upper layers play a role in protecting the core material therebetween, and when applied to the affected part, the lower layer is a part directly contacting the skin. The underlayer and upper layer are both made of nonwoven fabric, but since the underlayer has direct contact with the skin, a nonwoven fabric having a thickness of about 3 to 4 mm is used, which is soft and bulky. The reason for using spun lace and polyester bonding fabrics in the upper layer is meaningful to use to reduce the overall thickness of the product. However, the resin impregnated in the core material, which is one of the problems caused by thinning of the upper layer, can easily escape to the upper layer, and the resin coming out from the resin may stick to the elastic bandage wound around the sprint product at the end of the procedure. And there is a problem that it is stuck to. Therefore, the polyester fabric is subjected to a water-repellent treatment to protect the resin coming out into the upper layer, and the polypropylene spun lace is used for ultrasonic bonding with the ground layer made of polypropylene.

In the splint, the core inserted between the lower and upper layers is the most important part. The water-curable resin is applied to the core material to absorb water and harden. That is, when the splint is applied to the fracture portion, if the core material is made to absorb water and then applied to the fracture portion, it is hardened to a certain shape.

The core of the splint usually has a width of 2 to 6 inches, and the length is usually 10 to 45 inches, but may be longer than 4 to 5 m. Since the base and upper layers must accommodate the core inside, the width of the core and the core must be larger. Various materials have been developed and used as core materials for splint. Typical examples thereof include glass fiber knitted fabrics and nonwoven fabrics.

In the case of glass fiber knitted fabrics, several layers, usually 8 layers of glass fiber knitted fabrics, have been used as core materials. This glass fiber material has the advantages of good strength and air permeability and good stretchability. The splint is fixed in contact with the skin for a certain period of time, and therefore must have good air permeability and good elasticity because it must be freely cured in a desired shape according to the affected part. However, glass fiber materials are relatively expensive, have a heavy weight, and have a risk of being cut. The splint should be properly cut according to the position and size of the affected part. When the glass fiber knitted fabric is cut, a full glass fiber protrudes, and the protruded glass fiber will damage the skin. Nonwoven fabrics have been developed to overcome these disadvantages of glass fiber materials.

When nonwoven fabric is used as core material, it is lighter than glass fiber, less expensive, and less dangerous when cutting. However, the nonwoven fabric has poor air permeability, poor molding and poor bending, and has a weaker strength than glass fiber.

Other attempts have been made to use synthetic fibers such as polyesters as a core material in which a plurality of layers are laid one on top of another, but in this case, the cutability is poor (visible on the cut surface at the time of cutting). Since the location and the size of the affected part are different, the splint is used after being cut by cutting means such as scissors to fit the affected part.

Therefore, it is required to develop a splint for medical use in which the splitting property is good and the splitting does not occur, since the splint has good cutability so that there is no problem in use.

On the other hand, these splints or sprints are opened in a sealed container, sprinkled or sprayed with water to activate the hardener, which is then molded to the body and attached to the body. However, in this process, as shown in FIG. 1, there is a problem in that the folded part of the joint part, that is, the bent part is not overlapped with the double part or adhered to the excited body, and the affected part is not fixed due to the noncontact part. )

In order to solve such a problem, Korean Patent Laid-Open Publication No. 2001-16562 discloses a splint for covering and protecting a lesion. The splint includes an inner skin and an outer skin which are formed such that a horizontal portion and a vertical portion are formed by bending means, A bending splint having a structure in which the inner surface of the outer skin and the outer peripheral surface of the outer skin are adhered to each other to form an integral body is proposed in which a hardening solution of a moisture-curing polyurethane resin or a gypsum solution is applied and inserted between the inner skin and the outer skin .

However, the bending splint is formed by directly contacting the core for hardening between the inner and outer surfaces, and in the process of actual curing, the bent part is deformed without maintaining the shape of the bending part.

In order to solve the above-mentioned problems, an object of the present invention is to provide a splint for medical use in which the adhesion of a bending portion such as a joint is improved.

Another object of the present invention is to provide a splint for medical use in which there is no visible occurrence even when cutting is performed in order to fit the user, and no layer separation occurs.

Another object of the present invention is to provide a medical splint that has excellent strength and hardly generates heat.

In order to achieve the above object, the present invention provides a medical splint comprising a core, a bending stabilizing member, an inner cover, and an outer covering, wherein the bending stabilizing member is positioned at the upper and lower portions of the core, The medical splint is provided with an inner skin and an outer skin, preheated at a temperature equal to or higher than the softening point of each material, and molded into a shape suitable for the shape of the lesion.

Further, the present invention provides a splint for medical use in which the bending stabilizing member is formed into a hollow cylindrical shape having an inner space, and a core material is inserted into the inner hollow portion.

Further, the present invention provides a medical splint wherein the preheating is performed for 1 to 30 minutes at a temperature range of 10 to 15% or more of the softening point of the material.

Further, the present invention provides a medical splint wherein the molding is formed by inserting the mold into a mold without additional heat supply to the mold, followed by compression and quenching.

Further, the present invention provides a splint for medical use in which the splint is formed integrally with the splint or a band-shaped fixing band formed only by male velcro.

The present invention also relates to a method for producing a polyester fiber filament yarn comprising the steps of: forming a polyester yarn (DTY) and a polyester filament yarn in a weight ratio of 1: 3 to 1: 4 on a ramp, Provide splint.

The present invention also provides a medical splint wherein the polyester DTY (Draw Textured Yarn) yarns are between 300 and 400 denier and the polyester filament yarns are between 900 and 1200 denier.

The present invention also provides a medical splint wherein the knitted fabric comprises 3 to 5 plies.

The present invention also provides a splint for medical use wherein the envelope is a fabric formed of a hydrophilic material and / or a hydrophobic material, but having a loop structure, or a fabric formed of a velcro loop.

The present invention also provides a medical splint, wherein the splint further comprises a film punctured on the surface.

Further, the present invention provides a medical splint formed of a mesh-like structure of the endothelium or formed of a hydrophilic material and / or a hydrophobic material.

The medical splint according to the present invention is advantageous in that the bending portion is brought into close contact with the skin surface to improve the shape stability.

In addition, the medical unit according to the present invention improves the adhesion stability, so that the fractured arm or leg is stably fixed, thereby controlling the pain generated in the fine flow due to the non-contact.

Further, the medical splint according to the present invention is advantageous in that no visibility occurs when the core member is cut, and no layer separation occurs.

In addition, the medical splint according to the present invention is capable of absorbing a hardening agent well, has excellent strength and adhesion, and hardly generates heat.

BRIEF DESCRIPTION OF THE DRAWINGS Fig. 1 is a photograph showing the shape of a bent portion of a conventional splint. Fig.
2 is a developed view of a medical splint according to an embodiment of the present invention;
3 is a perspective development view of a medical splint according to another embodiment of the present invention.
4 is a conceptual view of wearing a medical splint according to an embodiment of the present invention;
Figures 5 and 6 are conceptual views of the wearing of a medical splint according to one embodiment of the present invention.

Hereinafter, preferred embodiments of the present invention will be described in detail with reference to the accompanying drawings. First, it should be noted that, in the drawings, the same components or parts have the same reference numerals as much as possible. In the following description of the present invention, a detailed description of known functions and configurations incorporated herein will be omitted so as to avoid obscuring the subject matter of the present invention.

The terms " about ", " substantially ", etc. used to the extent that they are used herein are intended to be taken to mean an approximation of, or approximation to, the numerical values of manufacturing and material tolerances inherent in the meanings mentioned, Accurate or absolute numbers are used to help prevent unauthorized exploitation by unauthorized intruders of the referenced disclosure.

The present invention relates to a medical splint, and more particularly, to a medical splint, which may include a core 110, a bending stabilizer 130, an inner skin 150, and a skin 170. The bending stabilizing member 130 may be positioned at the upper and lower portions of the core 110, and may be formed into a hollow cylindrical shape, and the core 110 may be inserted into the hollow portion. An inner skin 150 and an outer skin 170 may be formed on the upper and lower portions of the bending stability member 130, respectively. In a cross-sectional view, the outer cover 170, the bending stability member 130, the core member 110, the flexural stability member 130, and the inner skin member 150 may be formed from the outside.

The splint assembled in the laminated structure is formed in a pre-designed shape, and the shape thereof may be formed into a shape in which the bent portion is formed in advance as shown in FIGS. The molding process may be performed by preheating the spliced joint. The preheating temperature may be at a temperature above the softening point of the material, and may be at a temperature above the softening point, which is demonstrated empirically according to various materials of the present invention. For example, in the case of a polyester-based material, since the temperature is about 240 degrees Celsius (softening point), it can be preheated for about 1 to 30 minutes in a temperature range of about 10 to 15% or more. Preheating at a temperature above the softening point is to form crystalline or oriented state of a polymer molecular chain formed at a glass transition temperature or lower and amorphous state to achieve morphological transformation through rearrangement of molecular chains. By inserting the splint formed into the amorphous state by the preheating process into the molding for forming the shape as shown in FIG. 2 and FIG. 3, and then rapidly cooling the same by pressing, the amorphous region is crystallized to complete the splint having the smooth bent portion. Thereafter, the molded splint is coated with a curing solution and packaged.

In the case of splint having a conventional bent portion, the core is integrally adhered in a state in which the hardening solution is coated in advance, and the core is integrally adhered. In the process of joining the core and the envelope-endothelium already coated with the hardening solution, The advantages of the present invention are also remarkable in that there is a disadvantage that the productivity is high and the fairness is low.

On the other hand, the quenching may be performed by molding the molding apparatus without additional heat supply. That is, it can be performed at room temperature. Although the room temperature environment may be changed according to the environmental change, since the room temperature condition is usually lower than the glass transition temperature, it is considered that the room temperature environment change does not have a great influence. However, since the closing edge of the splice should be sealed, sealing (or sealing) may be performed separately through heat supply only to the edge of the molding.

FIG. 4 is a view showing a state of wearing splints according to the present invention. In the example of a leg fracture, it is advantageous that a leg is inserted into a shape in which a bent part is formed in advance and a stable and close state is maintained.

5 and 6 show another example of the present invention. In the case of a conventional splint, a bandage is wound around the splint to fix the splint to the affected part. In this case, as the tension of the bandage is loosened, there is a problem that the fixability is weakened and the breathability is lowered, and the discomfort is increased. There have been proposals to fix this problem by attaching connecting means such as Velcro to the splint in advance, but problems such as the bulky shape have been raised because it is fixed in the splint in advance.

In the present invention, it is possible to additionally form the fixed velcro, but it is formed integrally with the splint. However, the velcro may be formed of only the male velcro. In other words, the envelope itself acts as an arm velcro and the non-integral velcro can fix the splint to the desired clamping force. On the other hand, the non-integral type velcro may be formed in a band shape or a male velcro may be formed in both end portions.

Characteristics of the respective elements constituting the splint of the present invention will be described. The core material may be composed of a polyester DTY (Draw Textured Yarn) yarn and a polyester filament yarn in a weight ratio of 1: 3 to 1: 4 in an inclined manner, and the polyester filament yarn is made of a woven fabric composed of weft yarns.

Since the knitted fabric is suitably arranged with the yarn drawn polyester yarn DTY (Draw Textured Yarn) and the polyester filament yarn, the knitted fabric does not show a cut surface at the time of cutting and does not generate heat.

The inclusion of the knitted polyester yarn DTY (Draw Textured Yarn) enables the curing agent contained in the core material to be easily absorbed. Therefore, even if the knitted fabric is coated with a curing agent, the curing agent can be easily absorbed by the polyester DTY (Draw Textured Yarn) yarn, so that the curing agent hardly appears.

The polyester DTY (Draw Textured Yarn) yarn is preferably 300 to 400 denier. The thickness of DTY is related to the amount of resin impregnation. Generally, the higher the denier, the greater the amount of resin impregnation. When the polyester DTY is less than 300 denier, there is a problem that the resin impregnation amount is decreased and the strength is lowered. If the polyester DTY is more than 400 denier, the resin impregnation amount is increased and the strength can be improved. However, since the resin hardens and heat is generated, There is a problem that can wear.

If the core material is not a single layer but multiple layers, a sufficient resin must be impregnated so that the multiple layers are cured together and sufficient strength can be exhibited. In the case of DTY, there is a large amount of resin that can be impregnated. Therefore, when the resin is impregnated with a small amount of water, the DTY absorbs the resin and does not come out. On the other hand, when a large amount of resin is impregnated so as not to spread the core material, the core material can be cured in a state where the core material does not fall off from each other, but there is a problem in that heat generation during curing may be increased.

The polyester filament yarn is preferably 900 to 1200 denier.

When the polyester filament yarn is less than 900 denier, there is a problem that the strength becomes weak. When the polyester filament yarn is more than 1200 denier, the core material becomes stiff and the product molding property is deteriorated.

Further, it is preferable that the knitted fabric of the core material is three to five layers.

When the knitted fabric of the core material is 3 to 5 layers, the wound is protected well, the strength is excellent, the cut surface is hardly visible, and the layer separation does not occur.

In order for the core to exert its strength, polyester DTY (Draw Textured Yarn) must be stuck together to exert its strength. In other words, polyester DTY (Draw Textured Yarn) uses a hardener to stick to each other. When too much hardener is used, heat is generated. If too little polyester DTY (Draw Textured Yarn) is adhered to each other, the strength is weakened, so that the knitted fabric of the core becomes 3 to 5 layers, and the hardening agent can be used to prevent the occurrence of the strength and heat generation.

If the thickness is less than 3, there is a problem that the strength is lowered. If the thickness is more than 5, the thickness of the product is too thick to be molded, and the weight of the product is too heavy.

Referring to FIG. 3, the warp polyester DTY (Draw Textured Yarn) yarn and the polyester filament yarn are arranged in the same number and can be woven. That is, a polyester DTY (Draw Textured Yarn) yarn and a polyester filament yarn are provided side by side and weaving.

By supplying DTY (Draw Textured Yarn) yarn, the polyester DTY (Draw Textured Yarn) is firmly adhered to each other, resulting in excellent strength and virtually no visible generation during cutting.

Also, the knitted fabric of the core material has improved durability of the core material by coating the hardener, and it is possible to minimize the occurrence of visible or the like at the time of cutting.

There is no particular limitation on the method of coating the hardener, and the core material can be coated by immersing the core material in a liquid coating liquid or by repeatedly applying a liquid resin on the surface of the core material.

The curing agent component for the core coating may be comprised of a polyurethane prepolymer, a stabilizer, a catalyst, and a defoamer.

The composition ratio of the curing agent is preferably 96 to 99.1% by weight of the polyurethane prepolymer, 0.1 to 1.0% by weight of the stabilizer, 0.7 to 1.5% by weight of the catalyst, and 0.1 to 1.5% by weight of the defoamer.

The polyurethane prepolymer is a water-curable resin that reacts well with water and can be coated with the core material.

The stabilizer is used to prevent premature hardening of the coating, and it is preferable to use triethyl phospate or tributyl phosphate as the stabilizer.

Further, any one of amine-based, metal-based and morpholine-based catalysts can be used, and it is preferable to use dimorpholinoethyl ether (DMDEE) as a morpholine system.

The antifoaming agent functions to suppress foaming and to bubble during operation, and it is preferable to use a silicone antifoaming agent.

When the core material is coated, the mixing ratio of the knitted fabric and the coating solution is preferably 35:65 to 45:55 by weight. When the coating is carried out at the above mixing ratio, the coating liquid is appropriately blended in the knitted fabric, and durability is improved.

On the other hand, another structure of the core material may be a nonwoven fabric composed of one of polyethylene, polypropylene and polyester. The thickness is preferably 2 mm to 10 mm, and the density is preferably 300 to 1000 g / m ³ .

The yarn type may be selected from among polyester, polypropylene, and nylon, and a stretchable yarn may be used for the stretchability of the splint stabilizing member according to one embodiment of the present invention. The elastic yarn can be selected from rubber yarn, spandex yarn, and covering yarn. . The thickness may be 0.5 mm to 2 mm, the yarn fineness may be 300 D to 1500 D, and the fineness of the stretchable yarn may be 100 D to 500 D.

In the meantime, the present invention can be formed of a nonwoven fabric of an inner skin and an outer skin, and can be composed of any one of polyethylene, polypropylene and polyester, and has a thickness of 10 mm to 30 mm. The density of the nonwoven fabric is preferably 100 to 500 g / m ³ .

In the case of the outer sheath, a band-shaped fixing band formed by only a male velcro integrally or integrally with a splint may be further formed on the splint. In this case, in the case of a jacket, Structure of the structure) or may be in the form of a combination of velcro loops. In order to allow water to penetrate inward in order to harden the splint, the shell is preferably hydrophilic or water permeable. In addition, the curing agent coated on the core material can be thickly coated or punched film so that the curing agent does not leak to the outside. Further, since the purpose is to improve the wrinkles of the folded portion when the folded portion is used in the curved region, it can be a material that can be formed. Nevertheless, hydrophobic materials may be used as needed.

In the case of the endothelium, a portion of the endothelium that touches the affected part is required to function as a cushion with sufficient thickness so that the hardened core material does not contact the affected part to cause pain. And may be formed to have a suitable thickness so as not to allow the affected part to feel the heat generated during curing as much as possible. Further, it may be a material that can be formed to improve the wrinkles in the folded portion when used in the bent portion. Furthermore, the endothelium may be constituted to be hydrophobic so as not to reach the affected part as much as possible. The endothelium may be formed into a mesh shape to exhibit the above-mentioned characteristics. The endothelium may be formed into a mesh shape. Since it has excellent moisture release and ventilation properties, it may not feel a sense of heterogeneity in the affected part. It may be desirable to increase the density of the endothelium in order to impart a cushion, which may result in stiffness and roughness of the surface. As another example, a hydrophilic non-woven fabric and a hydrophobic spun lace structure may be used. The hydrophilic non-woven fabric and the hydrophobic spun lace structure may be combined with each other. There is a characteristic that comfort can be realized. Nevertheless, a hydrophilic material may be used if necessary.

Hereinafter, embodiments of the present invention will be described in detail.

Example 1

Polyester DTY (Draw Textured Yarn) and polyester filament yarns were formed in a weight ratio of 1: 3 for the production of core material, polyester DTY (Draw Textured Yarn) 300 denier, and polyester filament yarn 900 denier The number of DTY (Draw Textured Yarn) yarns and polyester filament yarns were alternately arranged in a line. The polyester filament yarn was supplied as a weft yarn to produce a knitted fabric. .

The flexural stability member was made of polyester 900 denier and 300 denier of spandex in a 1: 1 ratio, 1 mm thick, cylindrical knitted fabric.

The inner and outer sheaths were made of nonwoven fabric using polypropylene staple fibers. The upper layer was made of two layers, one layer was made of polypropylene spun lace and the other layer was made of polyester fabric.

After inserting the core material between the bending stabilizing members, the inner film and the outer film were laminated, respectively, preheated at a temperature of about 280 DEG C for 10 minutes, and then inserted into a mold.

Example 2

The procedure of Example 1 was repeated,

The core woven fabric was coated with a curing agent,

A polyurethane prepolymer of 96% by weight, a stabilizer of 1.0% by weight, a catalyst of 1.5% by weight and an antifoaming agent of 1.5% by weight. Triethylphosphate was used as the stabilizer and dimorpholinoethyl ether (DMDEE) as a defoaming agent, and a silicone defoaming agent as a defoaming agent.

Example 3

The procedure of Example 2 was repeated,

The composition of the curing agent was 97.5% by weight of a polyurethane prepolymer, 0.5% by weight of a stabilizer, 1.0% by weight of a catalyst and 1.0% by weight of a defoaming agent.

Example 4

The procedure of Example 2 was repeated,

The composition of the curing agent was 99.1% by weight of a polyurethane prepolymer, 0.1% by weight of a stabilizer, 1.7% by weight of a catalyst and 0.1% by weight of an antifoaming agent.

Comparative Example 1

The procedure of Example 1 was repeated,

The knitted fabric was produced by providing warp and weft with only polyester filament yarn.

Comparative Example 2

The procedure of Example 2 was repeated,

Polyester DTY (Draw Textured Yarn) was used to produce warp and weft yarns.

The heating state, strength, breakage visibility and layer separation state of Examples 1 to 4 and Comparative Examples 1 to 2 were measured, and the measurement results are shown in Table 1 below.

Heating temperature (℃) burglar Cross-section visibility Layer separation Example 1 35 6 none none Example 2 37 6 none none Example 3 36 7 none none Example 4 40 7 none none Comparative Example 1 37 4 has exist has exist Comparative Example 2 43 5 none has exist

※ How to measure

1. Measurement of heat temperature

The heating temperature is measured in the state of the nonwoven fabric of the upper layer and the lower layer. The splint cut at a certain length is immersed in water for 10 seconds, the water is removed, the cotton band wound about 5 cm in diameter is wrapped with a cotton band, Raise the splint. Keep the condition and wrap it with elastic bandage, and measure the maximum temperature on the thermometer.

2. Strength measurement

It is measured in flat state with splint. It is cut into a certain length, soaked in water, removed water, and rolls back and forth several times in a certain weight roll to mold the splint. Measure strength with UTM device at 1 hour after immersion in water. The measurement method is 3 point bending method.

3. Measurement of cross-sectional visible and layer separation

Visually inspect whether the product is cut and whether the product is cured in order to measure the strength during splint testing.

The layer separation is to confirm that the multiple layers of core material are attached to each other when they are held together with the upper and lower layers in the product state.

It will be apparent to those skilled in the art that various modifications and variations can be made in the present invention without departing from the spirit or scope of the inventions. It will be clear to those who have knowledge of.

Claims (11)

In medical splints,
Core member, bending stabilizing member, endothelium, and sheath,
The bending stabilizer is located at the top and bottom of the core
The upper and lower portions of the bending stabilizing member are respectively bundled into an inner skin and an outer skin,
After preheating at a temperature equal to or higher than the softening point of each material, the material is formed into a curved shape of the affected part to form a curved part,
Wherein the molding is inserted into a molding and then quenched at the same time as the compression, thereby crystallizing the amorphous region of the material so that the bent portion can be formed smoothly. The method according to claim 1,
Wherein the bending stabilizing member is formed into a hollow cylindrical shape with an inner hollow portion, and a core member is inserted into the inner hollow portion. The method according to claim 1,
Wherein the preheating is performed for 1 to 30 minutes in a temperature range 10 to 15% higher than the softening point of the material. The method according to claim 1,
Wherein the molding is manufactured by inserting the mold into a mold without additional heat supply and then quenching the mold together with compression. The method according to claim 1,
Wherein the splint further comprises a band-shaped fixing band formed by only a male velcro integrally or non-integrally with the splint. The method according to claim 1,
Wherein the core material is made of a knitted fabric in which a polyester DTY (Draw Textured Yarn) yarn and a polyester filament yarn are formed at a weight ratio of 1: 3 to 1: 4 on a ramp, and the polyester filament yarn is composed of weft yarns. The method according to claim 1,
Polyester DTY (Draw Textured Yarn) yarns are between 300 and 400 denier and polyester filament yarns are between 900 and 1200 denier. The method according to claim 6,
Wherein the knitted fabric comprises 3 to 5 layers. The method according to claim 1,
Wherein the sheath is a fabric formed of a hydrophilic material or a hydrophobic material, the fabric having a loop structure or a fabric having a velcro loop. 10. The method of claim 9,
Wherein the shell further comprises a surface punctured film. The method according to claim 1,
Wherein the endothelium is formed of a mesh-like tissue or formed of a hydrophilic material or a hydrophobic material.

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