WO2016003204A1

WO2016003204A1 - Method for manufacturing compressed receptor for medical prosthesis, compressed receptor using same, and medical prosthesis

Info

Publication number: WO2016003204A1
Application number: PCT/KR2015/006786
Authority: WO
Inventors: 이훈범
Original assignee: 가톨릭관동대학교산학협력단
Priority date: 2014-07-01
Filing date: 2015-07-01
Publication date: 2016-01-07

Abstract

The present invention relates to a compressed receptor for a medical prosthesis, and a method for manufacturing same, and specifically, to a receptor and a prosthesis, the receptor being accommodated in the medical prosthesis, enabling the improvement of texture and compatibility with the human body, etc., and the prosthesis having compatibility with the human body, and being capable of being used for human body restoration and cosmetic purposes, etc. Provided is a filling member of the medical prosthesis, the filling member enabling the simultaneous improvement of spatial efficiency in the manufacturing/distribution processes, and ease of surgery, etc.

Description

Method of manufacturing compression receptor for medical implant, compression receptor and medical implant using same

The present invention relates to a compression receptor for medical implants and a method for manufacturing the same, and more particularly, to a receptor that can be accommodated in a medical implant and improve touch and human fit, and can be used for the purpose of restoring the human body and cosmetics. It relates to a prosthesis having human compatibility. The present invention relates to a prosthesis having human suitability usable for the purpose of restoring the body, beauty, and the like.

Medical implants are used for the purpose of restoring a damaged human body such as depression due to an accident or disease or to improve the appearance of a woman's breast. For example, it can be used to restore the volume of the chest, which may be necessary after tumor removal, or to aesthetically improve the shape of the chest.

In the case of implants for female breasts, implants in which a liquid, that is, gel-type silicon is injected into a hard type silicone pouch having a thickness of 1 to 2 mm have been developed.

However, in the case of this type of prosthesis, when the silicone pouch is broken and the internal silicone gel is leaked to the human body, the silicone gel may be absorbed into the human tissue and necrotic the tissue.

For this reason, efforts have been made to increase the biocompatibility by making hard-type silicone pouches in two layers to reduce the possibility of breakage or to replace the silicone gel with physiological saline or cohesive gel.

However, when the hard type silicon pouch is doubled, there is a problem that the strength is strong, causing a heterogeneous texture different from the human touch, and there is still a risk of breakage.

In addition, the implants that replaced the silicone gel with physiological saline caused problems such as poor texture and the subjects felt heterogeneity in their daily lives. There was a problem that the deformation of the shape is so strong that it feels heterogeneous unlike the human body.

In this way, the implant for human body should have a similar texture to the human body, high human suitability or stability, and should not be heterogeneous because the deformation of the shape according to daily life is similar to the human body. In addition, the incision site of the human body should be minimized during surgery.

The present invention provides a filling member and a medical implant for medical implants that can simultaneously improve the ease of surgery and spatial efficiency in the manufacturing / distribution process.

In another aspect, the present invention provides a filling member and a medical implant to improve the human fit so that problems do not occur even when the implant is damaged and the contents are leaked to the human body.

In addition, the present invention provides a filling member and a medical implant having improved touch as compared with a implant containing a conventional saline solution or cohesive gel while improving the human fitness.

The compression receptor for medical implants according to the present invention comprises a dry substitute which is compressed and dehydrated condensed at a higher shrinkage rate than the shrinkage rate due to simple dehydration condensation from the hydrogel state.

In addition, the dry substitute may be formed of at least one material of polyvinyl alcohol (PVA) and polyvinyle acetate (PVAc).

In addition, the dry substitute may be formed of a porous material.

In addition, the dry substitute may be formed of a material having biocompatibility.

In addition, the dry substitute may be manufactured to have a volume larger than the maximum compressible volume and the same or smaller than the volume of the object to be accommodated.

In addition, the dry substitute may be formed in the shape of any one of a lump, a strap and a plate.

On the other hand, the compressed receptor manufacturing method for medical implants according to the present invention provides a step of providing a water-soluble synthetic resin; A softening step of softening the water-soluble synthetic resin through hydrolysis; Compressing the softened water-soluble synthetic resin; And a dehydration condensation step of dehydrating or drying the compressed water-soluble synthetic resin.

In addition, the providing step may further comprise the step of preparing a PVA sponge from PVA or PVAc.

In addition, the PVA sponge manufacturing step, to obtain a PVA aqueous solution by mixing PVA and water; Adding and stirring a pore-forming agent to the PVA aqueous solution; And acetalizing by heating after the stirring step.

In addition, the PVA sponge manufacturing step, to obtain a PVA aqueous solution by hydrolyzing PVAc; Adding and stirring a pore-forming agent to the PVA aqueous solution; And acetalizing by heating after the stirring step.

In the compressing step, the softened water-soluble synthetic resin may be compressed by any one of rolling up, folding and pressing or a combination of two or more methods.

Medical implants according to the present invention is a pouch; Physiological saline provided in the pouch; And a receptor formed of at least one of polyvinyl alcohol (PVA) and polyvinyle acetate (PVAc) and provided in a softened state by the saline solution in the pouch.

In addition, the pouch may be formed of at least one material of silicon and polyurethane.

In addition, the receptor may be provided in a state in which at least one xerogel of PVA and PVAc is swollen by the saline solution.

In addition, the dry substitute may be formed of a porous material.

In addition, the dry substitute may be prepared in a compressed state to have a smaller volume than the volume contracted by dehydration of the hydrogel.

In addition, the dry substitute may be formed to have a size less than the volume of the pouch.

In addition, the dry substitute may be formed of at least two separated solids.

In addition, the size of the sponge may be formed by a combination of two or more types of sizes.

In addition, the inner surface of the pouch may be attached to at least a portion of the receptor.

In addition, the receptor attached to the inside of the pouch may be attached by a medical silicone adhesive.

On the other hand, medical implants according to the present invention is a pouch; An inlet provided in the pouch and into which the fluid is introduced into the pouch; And a receptor provided as a dry substitute according to dehydration condensation of the water-soluble plastic in the pouch and softened by hydrolysis of the fluid flowing into the pouch.

In addition, the receptor may be formed of a material having biocompatibility.

In addition, the receptor may be formed of at least one material of polyvinyl alcohol (PVA) and polyvinyle acetate (PVAc).

In addition, the dry substitute may be formed of a porous material.

In addition, the dry substitute may be formed to have a size of more than the maximum compressible volume and less than the volume of the pouch.

In addition, the dry substitute may be formed of at least two separated solids.

In addition, the dry body may be attached to at least a portion of the inner surface of the pouch.

In addition, the dry substitute attached to the inside of the pouch may be attached by a medical silicone adhesive.

According to the invention there is an effect to minimize the incision site of the patient during surgery by artificially adding a compression process before the manufacture of dry substitute.

According to the present invention, by including physiological saline that is harmless to the human body and synthetic resin having high human compatibility, there is an effect of preventing problems such as necrosis of tissues of the human body even when the pouch is broken and the contents leak into the human body.

In addition, according to the present invention by including the PVA and PVAc in the form of a hydrogel can improve the human compatibility and at the same time can feel the texture similar to the human body compared to the case where only physiological saline is accommodated or strong cohesive gel is received.

In addition, according to the present invention it is possible to minimize the natural and heterogeneous feeling of shape deformation in everyday life as compared to weak viscous saline or viscous strong cohesive gel.

Further, according to the present invention, the injection of physiological saline is performed after insertion of the pouch and the receptor into the human body, and the expansion of the receptor is performed according to the injection of the physiological saline, thereby minimizing the size of the human incision during surgery.

1 is a schematic view showing a state in which a medical implant is applied according to an embodiment of the present invention.

Figure 2 is a block diagram showing a method of manufacturing a water-soluble synthetic resin and dry replacement for medical implants according to an embodiment.

3 is a schematic diagram showing a method of manufacturing and using a dry replacement for a medical implant according to an embodiment.

4 is a cross-sectional view showing a medical implant according to an embodiment.

5 is a cross-sectional view showing a medical implant according to another embodiment.

6 and 7 are cross-sectional views showing a medical implant according to another embodiment.

8 is a cross-sectional view showing a medical implant according to another embodiment.

9 and 10 are perspective views schematically showing a state of the conventional medical implant and the medical implant of Figure 8, respectively.

11 and 12 are cross-sectional views illustrating embodiments that can be combined.

13 is a cross-sectional view showing a medical implant according to another embodiment.

Hereinafter, embodiments of the present invention will be described with reference to the accompanying drawings. Unless otherwise defined or mentioned, terms indicating directions used in the present description are based on the states shown in the drawings. In addition, the same reference numerals throughout the embodiments indicate the same member. On the other hand, each of the components shown in the drawings may be exaggerated in thickness or dimensions for the convenience of description, and does not mean that actually should be configured by the ratio between the dimensions or configurations.

A medical implant according to an embodiment of the present invention will be described with reference to FIG. 1. 1 is a schematic view showing a state in which a medical implant is applied according to an embodiment of the present invention.

As shown in FIG. 1, the medical implant 100 according to the present embodiment may be inserted into the human body B, particularly in the female breast region. 1 and related descriptions are provided for convenience of description and are not limited to surgery of a woman's chest of the medical implant 100. That is, the medical implant may be applied to various parts of the human body through changes in size and shape in addition to the use for women's chest surgery. For example, it is possible to use the skin recessed portion and wrinkles, etc., and furthermore, it is possible to use for improving the volume sense of cosmetic purposes.

Medical implant 100 according to the present embodiment includes a pouch 110, physiological saline (W) and the receptor (filler member 120). The pouch 110 is formed of a hard type silicon material to form an outer shape of the implant 100, and may have some elasticity or no elasticity according to the purpose. Physiological saline (W) and the receptor 120 is accommodated inside the pouch (110). Receptor 120 inside the pouch 110 is provided in a softened state by physiological saline (W).

The receptor 120 may be formed of a water-soluble synthetic resin and hydrolyzed by physiological saline (W) to be provided inside the pouch 110 in a softened state. In this case, PVA (polyvinyl alcohol) and / or PVAc (polyvinyle acetate) may be used as the water-soluble synthetic resin.

The receptor 120 is made of xerogel and then reacts with physiological saline (W) in the pouch 110 to exist as a hydrogel.

Hydrogel refers to a state in which when a substance is placed in a larger amount of water, the substance can swell quickly and maintain a large amount of water in the swollen structure. Substances present in the hydrogel state retain a three-dimensional structure rather than dissolve in water. Gels formed on such aqueous solutions are called hydrogels. Hydrogels are usually made of hydrophilic polymer resins that are crosslinked by other bonding forces such as chemical bonds, ionic interactions, hydrogen bonding or hydrophobic action.

The term hydrogel is applied when the material is already swollen in water. Dried gels are called xerogels or dry gels. During the drying process, moisture evaporates from the gel, and the surface tension causes the gel to crush itself. Thus the gel shrinks to a very small fraction of swollen size. If moisture is removed without disruption of the polymer structure by lyophilization or extraction with organic solvents, then the remaining material has an extremely light weight with high porosity. Such dehydrogenated hydrogels are called xerogels or sponges.

Hereinafter, for convenience of explanation, a receptor dried in a manufacturing step or in a physiological saline solution is called a dry substitute, and a receptor in a physiological saline solution is particularly called a hydrogel.

Meanwhile, polyvinyl alcohol (hereinafter referred to as PVA) is a hydrophilic polymer synthetic resin obtained through hydrolysis of polyvinyl acetate (hereinafter referred to as PVAc). Crosslinking of PVA occurs through chemical and physical methods. In chemical crosslinking, an acidic crosslinking agent binds to a hydroxyl group and an aldehyde solution of PVA to form a gel. Representative methods of physical crosslinking are freeze-thawing. Hydrogels prepared by the freeze thawing method have little toxicity, contain no impurities, and contain about 80 to 90% water. In addition, since it does not use a crosslinking agent, it can be used as an attractive biomedical hydrogel.

That is, in the case of the silicone gel, when the outermost pouch is broken, there is a concern that it may flow to the outside and be absorbed into the biological tissue, causing necrosis, whereas in the case of the PVA hydrogel as in this embodiment, the outermost pouch is broken. Even if it is kept in a certain form is less likely to leak to the outside, even if spilled biocompatibility is high, there is no fear of necrotic tissue.

Referring to Figures 2 and 3 will be described in the receptor and its manufacturing method according to an embodiment. FIG. 2 is a block diagram illustrating a method of manufacturing a water-soluble synthetic resin and a dry replacement for a medical implant according to an embodiment, and FIG. 3 is a schematic view showing a method of manufacturing and using a dry replacement for a medical implant according to an embodiment.

PVA dry substitutes are characterized by excellent elasticity and very softness in wet conditions and hardness in dried conditions, which are not only used for cleaning rollers for semiconductor wafers, glass for TFT LCDs, and for manufacturing rollers. It is also used as a material for medical gauze, beauty towels, sports towels, kitchen scaffolding mats, and microbial tins.

PVA, a raw material of PVA dry substitute, is a white powder that is insoluble in ordinary organic solvents other than water, and remains stable up to about 140 degrees Celsius. It is used as a paste for textiles, sizing of paper or an emulsifying stabilizer. PVA dry substitute is manufactured from the PVA as a raw material (S10). After mixing PVA and water in a certain ratio, the mixture was heated to obtain a PVA aqueous solution, followed by adding corn starch as a pore-forming agent, adding formalin and stirring, and then adding sulfuric acid (H 2 SO 4) as a catalyst. Then, it is injected into a mold prepared in advance, heated and acetalized to form a PVA dry substitute. The acetalized PVA dry substitute is extracted from the mold and thoroughly washed, and then cut and processed according to specifications to produce a product.

The PVA sponge manufacturing method has a problem in that even though the use regulation of harmful substances is spread, formalin or paraformaldehyde, which is a use restriction substance, must be used.

It is also possible to manufacture PVA dry substitutes using the following methods to avoid the use of environmentally regulated materials and to improve the environment of the manufacturing workplace.

First, the PVA resin of 16-21% of the water weight is weighed and mixed with water, and then heated to a temperature of 30 degrees Celsius or more to obtain an aqueous PVA solution, and to the ratio of pores to form corn starch as a pore-forming agent in the PVA aqueous solution. Accordingly 25 to 45% of the PVA aqueous solution. Separately, hexamethylene tetramine of 28 to 35% of the weight of water is added to water and heated to a temperature of 40 degrees Celsius or more to obtain an aqueous solution of hexamethylene tetramine.

12 to 18% hexamethylene tetramine aqueous solution of PVA aqueous solution was added to the PVA aqueous solution, followed by stirring to obtain an aqueous PVA and hexamethylene tetramine aqueous solution. Then, an acid-based catalyst such as an aqueous sulfuric acid solution having a dilution concentration of about 50% was added to the aqueous solution. 19-21% After that, it is injected into a mold prepared in advance, placed in an oven, and heated (aged) for 29 to 34 hours at a temperature of 62 to 80 degrees Celsius to be acetalized. The acetalized PVA sponge is extracted from the mold and thoroughly washed, and then cut and processed according to the specifications to produce a product.

The manufactured dry substitute is softened again for compression. (S20) However, the softening step of the present dry substitute is simply necessary to perform a subsequent compression (S30) step, and the same step as that of providing a water-soluble synthetic resin (S10). It is also possible to be carried out in, and is not necessarily to be performed in a separate step from the water-soluble synthetic resin providing step (S10).

On the other hand, in the case of drying by dehydrating condensation of the hydrogel receptor as described above, as the water escapes, a certain volume decreases and becomes a solid state. However, simply dehydrating condensate receptors in the hydrogel state results in insignificant volume reduction. Therefore, in the present embodiment, a compression process is further performed before drying or dehydrating the hydrogel receptor. In the compression step S30 according to the present embodiment, the compression process is performed by one or two or more combinations of rolling up, folding, twisting, pressing, and the like in a hydrogel state. It is possible to do

Thereafter, by drying or dehydrating the compressed receptor, it may be made into a dry state (S40).

Referring to FIG. 3, the receptor (HG) in the softened state was made into dry substitutes (XG) through compression (II) and dehydration condensation (III) before drying, and then induced hydrolysis when used in the implant. It is converted to the hydrogel (HG) state (IV).

Hereinafter, medical implants according to various embodiments will be described. In addition, in the following embodiments it is preferable to manufacture the implant using the compressed dry substitute described above. By manufacturing a medical implant using a compressed dry substitute, it is possible to minimize the incision site of the patient during surgery or to improve spatial efficiency such as storage and transport at the manufacturing stage.

First, a medical implant according to an embodiment will be described with reference to FIG. 4. 4 is a cross-sectional view showing a medical implant according to an embodiment.

Medical implant 100 according to the present embodiment is characterized in that the receptor 120 provided inside the pouch 110 is formed of a single solid.

Specifically, the pouch 110 forms the outer shape of the medical implant 100. The pouch 110 is preformed to have a volume and shape according to the desired volume and shape. The pouch 110 may be manufactured using a hard type silicon that is used for medical purposes.

The inside of the pouch 110 is provided with a physiological saline (W) similar to the body composition, the physiological saline (W) is provided with a receptor 120 as a single solid.

The receptor 120 may be formed in various sizes and shapes according to the volume and elasticity of the desired medical implant 100. In the case of using a compressed dry replacer, the dry replacer is prepared in consideration of the volume to be expanded when the dry replacer is converted into a hydrogel state. At this time, in order to increase or decrease the elasticity of the manufactured medical implant 100, it is possible to control such as forming a larger or smaller volume of the dry body. However, in consideration of the expansion of the dry replacement, it is preferable that the size of the dry replacement itself is manufactured so as not to exceed the volume of the pouch 110.

On the other hand, as described above, the dry substitute is preferably manufactured in the form of a porous material, sponge in order to further improve the expansion and shrinkage of the volume.

The medical implant 100 prepared as described above has a tactile feeling enhanced by PVA and / or PVAc accommodated in a hydrogel state, unlike a medical implant containing only physiological saline, and even when the pouch 110 is damaged. Since only saline is leaked, it is harmless to the human body, and even when PVA or PVAc hydrogels are leaked, high biocompatibility does not cause problems such as tissue necrosis.

A medical implant according to another embodiment will be described with reference to FIG. 5. 5 is a cross-sectional view showing a medical implant according to another embodiment.

This embodiment is different from the embodiment of FIG. 4 described above in that the receptor 120a included therein is divided into a plurality of solids.

That is, the receptor 120a may be accommodated in the pouch 110 as a small mass having a predetermined size instead of being included as a single solid body. In this case, as compared with the above-described embodiment, securing the position of the receptor 120a in the pouch 110 may be more easily performed in the process of expanding the receptor 120a.

Other conditions such as the state of the receptor (120a) is not significantly different from the above-described embodiment.

A medical implant according to another embodiment will be described with reference to FIGS. 6 and 7. 6 and 7 are cross-sectional views showing a medical implant according to another embodiment.

This embodiment is different from the above-described embodiment in that it has a configuration and structure to maximize the ease of surgery.

Medical implant 100b according to the present embodiment does not include physiological saline at the manufacturing stage.

Specifically, in the manufacturing step, as shown in FIG. 6, the pouch 110 is manufactured in a state where a dry substitute, preferably a compressed dry substitute, of the receptor 120b is accommodated. However, the inlet 112 is provided on one side of the pouch 110. The inlet 112 serves as a valve through which the fluid can be introduced, and it is preferable to use a one-way valve to facilitate the injection of the fluid and to prevent the inflowed fluid from flowing out.

Surgery may be performed using the medical implant 100b manufactured as described above. For example, physiological saline may be injected through the inlet 112 after inserting the medical implant shown in FIG. 6 through the incision site during surgery of the patient. In this case, as shown in FIG. 7, the receptor 120b is swelled by the physiological saline W introduced thereto, and is restored to the volume and shape before compression. As the saline solution is introduced into the pouch 110 and the receptor 120b is expanded, the medical implant 100b has an intended volume, shape, and elasticity in the patient's body.

As such, during surgery, the volume is inserted into the patient's body in a state capable of being transformed into a minimized volume and an easy-to-insert shape, whereas after being inserted into the body, physiological saline is injected into the implant. Since the same effect as the above-described embodiments can be obtained by restoring the shape, the incision site of the patient can be minimized.

A medical implant according to another embodiment will be described with reference to FIGS. 8 to 12. 8 is a cross-sectional view illustrating a medical implant according to still another embodiment, and FIGS. 9 and 10 are perspective views schematically illustrating a conventional medical implant and a medical implant of FIG. 8, respectively, and FIGS. 11 and 12 may be combined. Sectional drawing showing embodiments.

The medical implant 100c according to the present embodiment has a difference in that a receptor 120c is formed on an inner wall of the pouch 110 as illustrated in FIG. 8. In this case, the receptor 120c may be attached to the entire inner wall of the pouch 110, or may be attached only to a part of the inner wall of the pouch 110 where wrinkles are easily formed. In this case, the receptor 120c may be formed in the shape of a strap, a plate, or the like.

In the case of a conventional implant using a single silicon pouch, as shown in FIG. 9, wrinkles are formed in the implant according to the use state, and these wrinkles are reflected in the appearance of the human body, causing problems in appearance. . In order to compensate for this, when using two or more layers of silicon pouches, problems such as touch and shape may occur as described above.

However, in the case of forming a separate layer by attaching a receptor to the inner wall of the silicon pouch as shown in the present embodiment, since the receptor is present as a hydrogel in physiological saline, it satisfies the criteria in terms of touch and compensates for the thickness of the pouch. Since the effect can be obtained, as shown in FIG. 10, wrinkles can be prevented as much as possible.

As such, forming a layer using a separate receptor inside the pouch may be implemented with the above-described embodiments. For example, it is possible to have another receptor 120 formed of a single solid body inside the receptor 120c forming a separate layer, as shown in FIG. 11, and as shown in FIG. 12. It is also possible to have further receptors 120a formed of a plurality of solids inside the receptor 120c forming the same.

A medical implant according to another embodiment will be described with reference to FIG. 13. 13 is a cross-sectional view showing a medical implant according to another embodiment.

Medical implant 100f according to the present embodiment has a unique effect in that it employs two pouches (110a, 110b) to more effectively prevent damage to the pouch (110).

Specifically, as illustrated in FIG. 13, the pouch 110 may be configured as two layers of the inner pouch 110b and the outer pouch 110a. The inner pouch 110b and the outer pouch 110a may be formed of the same component, respectively, and may be filled with the silicon gel 115 between the inner pouch 110b and the outer pouch 110a.

However, it is also possible to replace with PVA hydrogel instead of the silicone gel 115 to improve the feel.

Other inner configurations are not different from the above-described embodiments, and each embodiment may be applied or implemented by a combination of the embodiments.

Although the preferred embodiment of the present invention has been described above, the technical idea of the present invention is not limited to the above-described preferred embodiment, and may be variously implemented in a range without departing from the technical idea of the present invention specified in the claims. have.

Claims

A compression receptor for a medical implant comprising a dry substitute which is compressed and dehydrated condensed at a greater shrinkage rate than a shrinkage rate due to simple dehydration condensation from a hydrogel state.
The method of claim 1,

The dry substitute is a compression receptor for medical implants formed of at least one of polyvinyl alcohol (PVA) and polyvinyle acetate (PVAc).
The method of claim 1,

The dry substitute is a compression receptor for medical implants formed of a porous material.
The method of claim 1,

The dry substitute is a compression receptor for a medical implant is formed of a material having biocompatibility.
The method of claim 1,

Wherein said dry replacement is made to have a volume greater than the maximum compressible volume and having a volume equal to or less than the volume of the object to be accommodated.
The method of claim 1,

The dry substitute is a compression receptor for a medical implant is formed in the shape of any one of a lump, strap and plate.
Providing a water-soluble synthetic resin;

A softening step of softening the water-soluble synthetic resin through hydrolysis;

Compressing the softened water-soluble synthetic resin; And

Dehydration or condensation step of dehydrating or drying the compressed water-soluble synthetic resin; Compression receptor manufacturing method for medical implants comprising a.
The method of claim 7, wherein

Said providing step further comprises the step of preparing a PVA sponge from PVA or PVAc.
The method of claim 8,

The PVA sponge manufacturing step,

Mixing PVA and water to obtain an aqueous PVA solution;

Adding and stirring a pore-forming agent to the PVA aqueous solution;

Acetalization by heating after the stirring step; Compression receptor manufacturing method for a medical implant comprising a.
The method of claim 9,

The PVA sponge manufacturing step,

Hydrolyzing PVAc to obtain an aqueous PVA solution;

Adding and stirring a pore-forming agent to the PVA aqueous solution;

Acetalization by heating after the stirring step; Compression receptor manufacturing method for a medical implant comprising a.
The method of claim 7, wherein

In the compressing step, a method for producing a compression receptor for medical implants which compresses the softened water-soluble synthetic resin by any one of rolling up, folding and pressing or a combination of two or more methods.
pouch;

Physiological saline provided in the pouch; And

A medical implant comprising: a receptor formed from at least one of polyvinyl alcohol (PVA) and polyvinyle acetate (PVAc), and being provided in a softened state by the saline solution in the pouch.
The method of claim 1,

The pouch is medical implants formed of at least one material of silicone and polyurethane.
The method of claim 12,

The receptor is a medical implant that is provided with at least one of the xerogel (Serogel) swelled by the physiological saline of PVA and PVAc.
The method of claim 14,

The dry replacement is a medical implant formed of a porous material.
The method of claim 14,

The dry replacement is a medical implant is manufactured in a compressed state to have a volume smaller than the volume shrinked by the dehydration of the hydrogel.
The method of claim 14,

The dry replacement is a medical implant is formed to have a size less than the volume of the pouch.
The method of claim 14,

The dry replacement is a medical implant formed of at least two separated solids.
The method of claim 18,

The size of the sponge is a medical implant formed by a combination of two or more types of sizes.
The method of claim 12,

Medical implant to which the receptor is attached to at least a portion on the inner side of the pouch.
The method of claim 20,

Receptacle attached to the inside of the pouch is a medical implant attached by a medical silicone adhesive.
pouch;

An inlet provided in the pouch and into which the fluid is introduced into the pouch; And

And a receptor provided as a dry substitute according to dehydration condensation of the water-soluble plastic in the pouch and softened by hydrolysis of the fluid flowing into the pouch.
The method of claim 22,

The receptor is a medical implant formed of a material having biocompatibility.
The method of claim 23,

The receptor is a medical implant formed from at least one material of polyvinyl alcohol (PVA), polyvinyle acetate (PVAc).
The method of claim 22,

The pouch is medical implants formed of at least one material of silicone and polyurethane.
The method of claim 22,

The dry replacement is a medical implant formed of a porous material.
The method of claim 22,

The dry replacement is a medical implant is manufactured in a compressed state to have a volume smaller than the volume shrinked by the dehydration of the hydrogel.
The method of claim 22,

The dry replaceable body is formed to have a size that is greater than the maximum compressible volume and less than the volume of the pouch.
The method of claim 22,

The dry replacement is a medical implant formed of at least two separated solids.
The method of claim 29,

The size of the sponge is a medical implant formed by a combination of two or more types of sizes.
The method of claim 22,

Medical implant to which the dry substitute is attached to at least a portion on the inner surface of the pouch.
The method of claim 31, wherein

Medical replacement is attached to the inside of the pouch is a medical implant attached by a medical silicone adhesive.