JP2006231068A - Porus material product - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To provide a porous implant and a manufacturing method of such a porous implant. <P>SOLUTION: A mold material (164) is made of mutually adhering solid particles and formed into a porous network structure. A liquid phase of the final product material is forced into void of the mold (164) and then almost all the liquid material is forced out to form a thin coating. Next, the thin coating is hardened to produce a thin coating of a polymer such as silicone rubber (162). And then, the mold material (164) is dissolved to create a porous structure containing only the hardened polymer. <P>COPYRIGHT: (C)2006,JPO&NCIPI

Description

  The present invention relates to a porous material product, at least a portion of which is porous for use as a prosthetic device, a therapeutic device, and other practical applications.

  In recent years, the application and use of biocompatible synthetic appliances devised for implantation or equipment in or on the human body has increased tremendously. Such appliances and devices include, for example, soft tissue implants, nerve cuffs and skeletons, lymphedema shunts, percutaneous skin and blood for use in, for example, mastogenesis, jaw, nose, ear and other body part reconstruction. Contact / access devices, insulin cell producing implants and other cell osteogenic cage devices, artificial tendons and ligaments and tendons and ligament repair prostheses, artificial heart and vascular prostheses, burn dressings, and drug infusion, release or delivery devices, etc. Is included.

In many cases, these types of devices have failed due to problems at the implant-tissue interface. As early as 1970, Homsey admitted that a “fibrocartilaginous” membrane or capsule would separate the implant from normal tissue if the size of the implant was on the order of centimeters. If the implant is drilled so that the gap (pores and pore interconnects) is on the order of 1 mm or less, the implant will be woven into the tissue instead of being wrapped with a coating as described above ( Homsey, CA, 1970, J. Biomed. Mater. Res., 4: 341-356). Smooth wall silicone breast implants have been developed with various consequences, although they interfere with the gel around the silicone envelope. In a prosthesis using a silicone skin, the polyurethane foam was mechanically secured to the skin with a silicone adhesive. However, the interfacial bond between the foam and the skin was weak and in many cases delamination occurred and sometimes silicone gel leaked into the surrounding tissue. In prostheses that do not use a silicone skin, the gel typically leaked or “leached” through the polyurethane cover and into the surrounding tissue. Such “contamination” of the surrounding tissue with the gel caused local inflammation and migration of the gel to distant organs. Also, a “Chinese finger trap” -like state due to the steric connectivity of the pores in the polyurethane foam, the relatively inelastic nature of the polyurethane and the high proportion of ingrowth structure compared to the amount of material in the foam. (With ingrowth tissue intertwined with the foam) and tissue, which made it very difficult to remove or replace the prosthesis. Furthermore, polyurethanes are biologically unstable and can be chemically degraded, leading to structural collapse and sometimes accompanied by severe inflammation. A recent concern with such chemical degradation is the possibility of the release of toluenediamine (TDA), a chemical known to cause cancer in laboratory animals, even in small quantities.

  Conventional approaches to porous material formation (for implants or other applications) typically involve the use of 40-60% foam, but this thick “fibrocartilage” formed around the implant “Due to the membrane, the implant becomes hard, inelastic and often painful. This fibrous coating also creates other problems generally around the implant because it consists primarily of dense collagen and fibroblasts with little or no vascularity. The result is that the implant, the implant-capsule interface and the coating itself are separated from the cellular advantage of nutrition, metabolism and good blood supply, thereby making the implant site more susceptible to infection, natural resistance mechanisms and / or Or make the infection more difficult to cure by antibodies in the bloodstream.

  Porous devices known under the trade names of Ivalon Sponge (polyvinyl chloride) and Ashley masculinization prosthesis (polyurethane) were made to allow tissue to grow into the pores in the implant. These devices are generally porous, sponge-like devices that do not limit the in-growth of tissue pores or limit the contact / access of implants to body fluids. Or nothing to stop or inhibit liquid access, resulting in poor ingrowth tissue with internal calcification and hardening. Such curing results in an unnatural appearance and function as well as uncomfortable feelings for the recipient.

  In order to solve some of the above-mentioned problems, the following attempts have been made at least with respect to a breast-forming prosthesis. That is, polyurethane foam coated silicone rubber mammary prosthesis (with and without forming technology), sintering of metal or polymer particles into partial fusion, expansion of polymer melt or solution (eg, use for Gortex manufacturing) , Textile processing for the production of woven felt, velour, mesh or woven fabric, and the reproduction or reproduction of the microstructure of carbonized animal skeletal materials. For example, White, RA, Weber, JN and White, EW, “Replanineform: A New Process for Preparing Porous Ceramic, Metal, and Polymer Prosthetic Materials,” Science, Vol. 176, 922-924; US Pat. No. 3,890,107; Leidner , J. et al., “A Novel Process for the Manufacturing of Porous Grafts: Process Description and Product Evaluation,” Journal of Biomedical Materials Research, Vol. 17, 229-247, 1983. A problem in using foaming techniques for the production of porous materials is the difficulty of separately controlling the pore size, pore shape and pore interconnect. Also, the resulting pores typically include sharp edges and ends that promote inflammation and can cause problems and / or discomfort when implanted. Sintering and polymer expansion approaches are typically limited to certain materials, such as sintering metals and polytetrafluoroethylene for polymer expansion, which have the desired flexibility, elasticity, and biological properties. It may not be a material having a physical compatibility. The use of fiber processing is limited to materials that can be made into fibers, and the resulting structure is basically planar. While the reproduction of carbonized skeletal structures is suitable for certain uses, it is necessary to machine the material to the desired size and shape, and again the pore size and shape cannot be adjusted.

  Two recently published patents Nos. 4,859,712 and 4,889,744 disclose the use of soluble particles, which first cure the particles on the uncured silicone and then dissolve the particles. To create a silicone product having a so-called continuous cell porous surface. The particles described in both patents as preferred solid soluble particles are crystalline sodium chloride (salts) and no specific examples of other particles are given. There are a number of problems or difficulties with the methods disclosed in the two patents. For example, it is difficult to obtain a complete open cell structure because the salt particles are simply cured after the salt particles are simply placed on the uncured implant surface and the salt particles are dissolved. Since many particles will not contact, a cell portion is created that is mostly closed except for the surface layer. With this technique (since the salt particles are not held together and therefore are not shaped), it is also very difficult, if possible, to form solid particles into a predetermined desired shape (salt crystals) Can not adjust the depth of the porous part, the size and shape of the structural connections surrounding individual continuous cells) .

  Since the only possible treatment with the approaches disclosed in the above two patents is the surface, not the true steric orientation, the thickness and density of the fibrous coating that occurs after implantation is substantially the same as for smooth surface implants. Are the same. A true steric single porous silicone rubber prosthesis did not exist until the technology of the present invention was developed.

(Object of invention)
The object of the present invention is to obtain a porous material product which improves the above-mentioned drawbacks.
The invention further relates to a method for producing such a porous material product in which the ratio of the porous and non-porous parts of the product can be individually controlled.

In performing the porous or partially porous product composition process according to the present invention, the first step is used to form a selectively removable continuous cell porous mold (SRO-CPMF) from which the final product is molded. Simply selecting the molding material to do. Such molding materials are advantageously readily available, inexpensive, and resistant to dissolution by liquid form (or dissolved or dispersed form) of the final product material.
Also, the molding material must be available in particles of a selective size and shape so that they easily adhere (or are made to adhere), thereby removing or dissolving the molding material. When removed, a continuous all-continuous cell product is established. Finally, when the molding material is in the mold, it must be easily removable without significantly changing the final product (or product material). This removal can be done by dissolving the final product material with a solvent that does not significantly dissolve. Alternatively, the molding material may be melted (or burned) away from the molded product material if the melting point (or burning point) of the molding material is lower than that of the final product material.
Similarly, the final product material is selected to have the desired properties, for example, silicone rubber is selected when flexibility and elasticity are required, and polyester resin, epoxy resin, when rigidity is required. Metals or metal alloys or ceramics can be selected.

  The first example considered describes a partially porous device and a method for adjusting the position of porous and non-porous portions. In this specific embodiment, sugar is selected as the molding material or SRO-CPMF and silicone rubber is selected as the final product material.

  The sugar has a moderately uniform particle size and crystal form with facets, but when a more uniform size is required, the particle size can be selected using standard sieve size classification techniques.

  Once the desired particle size and size distribution for the sugar molding material is obtained, the sugar particles are mixed with deionized or purified water in a volume ratio of 1 part water to 8-25 parts sugar. If a higher percentage of porous end product is desired, more water can be added to this mixture to increase surface contact and sugar particle fusion, resulting in a larger number of large pore connections. Let A lower percentage of the final product is obtained by using less water and, consequently, less contact and more space between the SRO-CPMF particles. If a larger pore size is desired in the final product, a larger particle size is selected. Conversely, if a smaller pore size is desired in the final product, a smaller particle size is selected.

  The sugar and water are mixed well until the total sugar particles are in contact with water and until some partial dissolution in a saturated (no further dissolution) sugar solution. When the desired firmness is reached and the mixture is stable, the resulting wet semi-solid mass (molding mass) can be placed in a pre-shaped mold and molded into a mold. That is, the water in the mold is evaporated and the sugar solution is recrystallized to precipitate on or between the sugar particles. FIG. 1 is a cross-sectional view of a conventional cylindrical container 4 in which a wet sugar lump 8 is precipitated. The sugar lump portion 12 represents an enlarged portion of the sugar particle 20 and the gap 16 between the particles.

  Solidification of the molding mass to SRO-CPMF can be facilitated, for example, by supplying dry air (which may be heated) to the mass. Freezing, lyophilization or heating or non-heating vacuum drying is also used to solidify the mass. The enlarged view 12 of the SRO-CPMF represents a sugar granule or particle 20 fused leaving a void 16 between the particles.

  After solidification, depending on the desired end product properties, the sugar mold can be left in its original position in the container 4 (FIG. 1) or removed from the container 4 (in the case of FIG. 3 described below). For example, by leaving a sugar mold in the container 4, the mass is maintained in contact with and attached to the container wall 24 (FIG. 2A). That is, as a result of the injection of the final product material into the mold (described below), a porous surface 28 is obtained in the final product (FIG. 2B) and the surface pores 30 in contact with the container wall 24 are the sugar particles of the mold. 26 (FIG. 2A). On the other hand, when the sugar mold 8 is removed from the container (or the adhered surface of the container wall is removed) and the final product is fed into the mass, for example, as it is held in a larger container 38 (FIG. 3A). ), The exterior surface 40 (FIG. 3B) of the final product (covering the sugar mold) will not have pores. FIG. 3B shows this non-porous surface region and portion 40 and porous cross-section 42, the thickness of this non-porous cross-section 40 depending on the amount of final product material applied to the outside of the mold.

  In another specific method for forming SRO-CPMF, pure sugar particles of a desired size are placed in a metal container, and then the particles are gradually heated at or slightly below the melting point of the sugar. During this process, the sugar particles are compressed and forced into contact with each other, and then the mass is allowed to cool. The more sugar particles that are compressed, the larger the size and number of particle linkages, the denser the SRO-CPMF, and the greater the percentage of porosity in the porous portion of the final product. When the number of sugar particles is small, all are reversed. After cooling, the mold may be removed from the container or left in the container in contact with the container as described above.

  After the sugar mold is completed, the medical grade silicone rubber is catalyzed, mixed in a conventional manner, degassed to a liquid state, followed by polymerization, ie, from liquid to solid Silicone rubber is prepared. The prepared and catalyzed silicone rubber is then applied to the sugar mold gap, i.e., by pressurizing the silicone rubber, applying vacuum to the mold, gravity flow, mechanical agitation or a combination of these techniques. Push into the pores. The thickness of the porous portion of the final product can be the same as or thinner than SRO-CPMF. This can be specifically adjusted by adjusting the penetration depth of the final product material into the liquid SRO-CPMF. If the liquid is forced to penetrate completely through the mold, the specific thickness of the SRO-CPMF itself can be used to adjust the thickness of the porous portion of the device.

  After feeding the liquid silicone rubber to the mold, the silicone rubber is allowed to polymerize (or in some way), after which the sugar mold is dissolved by a suitable solvent (in this case deionized water) and stirring. What is left after this step is the desired finished silicone rubber product. Although multiple washings are necessary to completely remove all residual sugar, an ultrasonic water bath or other agitation is particularly effective for this purpose. It is also possible to use hot deionized water or steam rinse, after which the final product is dried.

  When the combined structure of SRO-CPMF and final product material is created by removing the mold from the container before applying the final product material to the mold (FIG. 3A), the coating of the final product material surrounds the mold. As a result, a non-porous coating 40 is formed, preventing the solvent from reaching the mold 8 and dissolving (FIG. 3A). In this case, if a small portion of the final product material is removed at the surface, the aqueous solution can be put inside. Instead, needle penetration of the solid product material 40 allows the desired access of the aqueous solution and removal of dissolved sugar.

  The thickness and shape of the non-porous surface portion of the final product can be selected by selecting a container of the appropriate size and shape for containing the mold, and then placing the mold in it and filling the container or mold with non-polymerized silicone rubber It can be easily adjusted by standard molding or injection molding die techniques. If SRO-CPMF occupies a very small volume of the container, the thickness of the non-porous portion of the final product will increase. The size and shape of the non-porous portion of the final product is determined as the difference between the size and shape of the container that contains the mold and the size and shape of the mold that is placed in the container.

The shape and amount of the porous portion of the final product depends on the shape and portion of the mold filled with the final product material. The portion of the mold that is not filled with the final product material becomes the void 142 of the final product (see FIGS. 8C and 8D). The position of the porous part of the final product relative to the non-porous part depends on the position of the mold in the mold.
Except as described below (when gas is forced through the mold), a portion of the surface of the final product material becomes non-porous. This portion corresponds to a position where the liquid final product material is introduced into the mold. Adjusting the mold attachment to the container or mold surface adjusts the integrity of the penetration of the liquid mold into the mold and adjusts the surface area and size of the liquid mold final product material introduced into the mold. Thus, the position of the continuous cell surface and the position of the non-porous surface can be adjusted. For example, a product manufactured as a sheet can be completely porous on the lower surface and non-porous on the upper surface. In the example of using the adhesive container wall 4 to the mold 8 in FIG. 1, this introduces the final product material so that it completely penetrates the mold 8 at its entire upper surface, and the lower surface of the mold is This is done by adhering to and holding the container wall.
Alternatively, the final product material can be poured to penetrate partway through the mold.
Either example results in a partially porous end product having a non-porous top surface 32 and a porous portion 34 with the porous surfaces on the sides and bottom of the porous portion 34 (FIG. 2C). . However, if the final product material is introduced from the side using adhesive molds (otherwise to the entire container wall) in the rest of the mold, not only the side where no liquid is injected, but also the top and bottom of the sheet The surface becomes porous. In this way, the ratio between the surface of the porous part and the non-porous surface part of the device can be adjusted.

  A silicone rubber end product that is at least partially porous is cured (polymerized), for example, with a particular silicone rubber used, in a drying oven for 15 minutes to 1 hour at a temperature in the range of 275 to 425 degrees Fahrenheit. . The final product can be further shaped or engraved by cutting, adding to the product, or bonding other solid or porous silicone rubber parts or materials. However, an advantage of the method of the present invention is that there is little need for cutting, gluing, engraving or adding to the final product because the variables of the porous and non-porous parts can be adjusted separately. Cutting, bonding, engraving, etc. also leads to interfaces, irregularities, distortions and external defects. In the method of the present invention, the porous and non-porous portions of the device can be united without having interfaces, defects or irregularities. Standard packaging and sterilization steps can then be performed if desired.

  Complex shapes, molds and sizes can be easily fabricated using the continuous cell porous product molding process described above. Moreover, there is no restriction | limiting which exists in the conventional method regarding the position of the porous part of a product.

In the second embodiment of the invention described below, the pore size of the porous portion of the final product varies. First, small particles of sugar (eg 50-75μ) are placed in a container, for example 0.2 mm deep. Then another size range of sugar particles (e.g. 100-150 [mu]) is placed on the first layer at a separately defined depth, e.g. This is continued until the final layer, for example, 200-300μ particle size is added to a depth of 0.6 mm. The SRO-CPMF particles in the container are then added to the total particles after adding the sugar-saturated solution, and then it is evacuated from the bottom, or the container and the step-sized particles are brought to approximately 100% humidity. The SRO-CPMF is left to dry (cured) after being exposed for 15 minutes to 4 hours, thereby being adhered to each other.
Alternatively, as described above, the particles may be heated to the melting point, packed tightly and then cooled. The SRO-CPMF is then filled with a liquid type final product material (here silicone rubber) as described above. The resulting product is a partially porous device such that the porosity can be selectively or continuously varied by region as desired. This is shown in FIG. 3B where the pore size changes from small to large in the direction away from the non-porous portion 40.

  Using the method described above, many useful devices such as vascular graft prostheses were produced from medical grade silicone rubber, Biomer and Biolon (medical grade polyurethane). The blood contact surface of the vascular device is made as described above with pore sizes of 25μ, 50μ, 75μ and 100μ. The pore size of the remaining part of the product is in the range of 30 μ-300 μ and the wall thickness is 0.5-2 mm. Endothelial and smooth muscle cell cultures were grown on the blood contacting surface of the device. Here, the porous aids attachment, so during transplantation the porous adds nutrients to these cells during and after tissue and neovascular ingrowth.

  In order to obtain a larger pore size (50 to 100 cm) at the blood contact surface of a vascular transplant, it is necessary to coagulate the implant in advance. After tissue ingrowth, the neovasculature can support neointimal cell regeneration of the blood contact surface of the device with or without cell culture inoculation.

  The vascular prosthesis described above can be implanted subcutaneously or intramuscularly. After the prosthetic wall is filled with tissue [depending on the type of tissue desired, after several minutes (pre-coagulated), several days (cell inoculation), several weeks (tissue ingrowth)], It can be removed from that location and implanted as a combined implant (consisting of two types of materials, tissue and polymer), into the receiving site (in this case a blood vessel). In this way, a vascular graft made of tissue (and polymer) can be used as a living autogenous graft without creating a pathological condition on the recipient side that sacrifices blood vessels. Similarly, many types of tissue can be transplanted, including bone marrow, liver, pancreas, collagen or neovasculature, or tissue or cell cultures that are enabled to grow into the porosity of the implant.

  A third embodiment of the present invention involves the use of fibers that are distributed into or extend from the porous portion of the final product, which is intended to enhance or change the porous nature of the final product. It is. The construction of such a final product is as follows.

  After mixing the sugar molding lump, as in the first embodiment (see FIG. 1), a commercially available fiberglass or carbon graphite fiber is cut to a desired length, for example 1 cm, to form the molding lump. Mix at random. The molding mass is then placed in a container as described above and solidified to form SRO-CPMF. In any fiber, some of the fiber is in the sugar and is partly dissolved and then on a particle such that some additional sugar is deposited or recrystallized on its surface, or the particle surface and / or Deposited or solidified by particle connection. Furthermore, in any fiber, a portion of the fiber does not come into contact with the sugar and simply extends into the SRO-CPMF voids. If a soft reinforced porous portion is desired in the final product, a final product material such as silicone rubber is selected. If a hard end product is desired, a polyester or epoxy resin is introduced into the SRO-CPMF voids as described above. The portion of the fiber that is exposed in the void is coated and incorporated into the matrix of the final product material. Next, the sugar of SRO-CPMF is dissolved, and the portion of the fiber 41 in the sugar (FIG. 4) is exposed in the gap 43 of the final device 45. These exposed fibers can be grown and fixed in the tissue after implantation.

The proportion of fibers mixed into the SRO-CPMF can vary greatly depending on the stickiness (inherently or by the binding medium used) the particles in the SRO-CPMF, the wettability of the fibers themselves, the diameter and the stiffness. If the ratio of fibers and molding lump particles becomes too large, the molding lump particles become non-adhesive to each other, and the characteristics of SRO-CPMF connectivity continuous cells are impaired and no longer function as a porous mold. do not do.
The length of the fiber used can also vary greatly. The fibers are arranged, pre-stretched, pre-woven and placed in a container prior to the introduction of the molding mass to determine the directional position within the SRO-CPMF and the final product. The fibers can also be placed out of the SRO-CPMF and out of the void of the final product and outside the non-porous portion or the final product itself.

  Similarly, a medical grade Dacron mesh (pore size about 1 mm) can be formed into a cylinder having a diameter that is about 2 mm smaller than the diameter of the inner wall of the container in which it is placed, for example. After being put in the container, the molding lump is put in the container around and inside the mesh cylinder, packed tightly and solidified. As a result, a mesh is formed 1 mm away from the container wall and around it and in the SRO-CPMF. Sugar particles and sugar particle connections are continuous through each side and mesh. The SRO-CPMF is then removed and placed in another container, for example, about 1 mm larger in diameter than SRO-CPMF. The final product material, such as catalyzed liquid silicone rubber, is then allowed to solidify (polymerize) by pushing it around and into the SRO-CPMF, for example to a depth of 2 mm. The SRO-CPMF is then dissolved as described above and the end of the tube is cut. The resulting prosthesis is inverted (inside out) to obtain a device with a homogeneous, non-porous portion at the inside at a depth of 0.5 mm and a porous portion at the outside at a depth of 2 mm. The central part of the porous part is reinforced by the Dacron mesh, but the porous part is located on both sides and is continuous through the mesh.

  The devices described above have been used as percutaneous cuff prostheses for artificial heart power transmission pathways. This is slid through the skin at their exit point and adhered to the system, thereby allowing tissue ingrowth and skin and subcutaneous fixation. Similar reinforcing and fiber modified porous prostheses were made from medical grade blood compatible polyurethane as vascular prostheses.

  In the previous example where the sugar SRO-CPMF molding material was removed from the container before injecting the liquid silicone rubber, one of the final product choices was to make one side porous and the other non-porous. (FIGS. 3A and 3B). However, in the use of many biological materials, it is desirable to have the porous portion on the outside and the non-porous portion on the inside in various shapes and proportions. An example use for such a final product is a dorsal nasal augmentation implant, and how to make such a final product (and similar final product) is as follows.

The first step in the process is to create a real image model in the exact size and shape of the desired final implant. Any material can be used, but the clay-like thermoplastic material known as Sculpey Modeling Compound has proven to be the best. Such a material is formed and engraved into the desired shape using hand or molding tools, and then the material is solidified by heating at 300 degrees Fahrenheit for about 15-20 minutes. A single real image model can be used to fabricate multiple SRO-CPMF moldings, thus adjusting the number of final products and the thickness, position and shape of the porous versus non-porous portion.

The real image model is then placed in a hinged polyethylene rectangular container 44 (FIG. 5A) and a molding material 48 for SRO-CPMF such as a sugar molding mass is placed on one side thereof. Next, the real image model 52 (in this case, a nasal implant) is pushed in part of the molding material 48 so that only the top (concave) surface is exposed.
A thin layer 56 of polyurethane sheet or similar non-adhesive material is then placed over the molding material 48 and the real image model 52. Next, after filling (or overfilling) the other half of the hinged container with the sugar molding lump 60, the container is closed as shown in FIG. 5B. As a result, the molding block 60 is put on the sheet 56 and pressed strongly along the shape of the exposed surface of the real image model 52. The molding materials 48 and 60 are then dried (cured) and both halves of the hinged container 44 are reopened to remove the sheet 56 and the real image model 52, leaving the SRO-CPMF 48 and 60 in the container. Alternatively, hinged container 144 can be first carefully opened to remove sheet 56 and model 52 and the molding mass can be dried in SRO-CPMF.

  A medical grade elastomer such as RTV silicone rubber is then pressed into molds 48 and 60 to the same depth as the desired thickness of the porous surface area of the final product. Silicone rubber is also placed in the voids in the molding materials 48 and 60 left in the real image model 52 to close the container 44 again as shown in FIG. 5C. Silicone rubber is polymerized in molds 48 and 60 as in FIG. 5C, then container 44 is opened, the mold is dissolved, and the final product implant is removed to produce solid interior 64 and porous as shown in FIG. 5D. A silicone rubber nasal implant is formed having a conductive outer surface region 68.

In addition to the above methods for the formation of nasal implants or similar end products, conventional injection molding methods, i.e. models that use sugar and other removable materials to create the desired voids or voids using heat and pressure A die having a desired shape and a method of baking to a mold are also effective for molding using SRO-CPMF. The final product material, ie silicone rubber, is then pressure injected into the gap and mold to the desired thickness using the same mold or die used to form the mold or, if necessary, another die or mold. To do. The device obtained by any of the above methods is a partially porous end product in which the position and thickness of the porous part and solid non-porous core and / or gap are effectively adjusted. A more viscous mass is obtained by using corn syrup instead of water as the sugar bond dissolution medium, which provides greater particle contact in the mold and thus greater pore interconnectivity in the final product. The viscosity of the final product material also affects the porosity of the final product when solidified. Non-polymerized silicone rubber with higher viscosity will contact in less surface area of SRO-CPMF particles and surface molding will be incomplete, so when high viscosity silicone rubber solution is used in final silicone rubber product Larger pores are formed. Furthermore, the pores and the pore connecting portions are smoother and rounder.

  A dual porous membrane (porous on both sides but separated by a non-permeable membrane) can be formed in a similar manner as described above for the nasal implant. Here, the process is substantially the same except that the real image model 52 (FIGS. 5A and 5B) is removed. Both halves of the hinged container are closed over the non-adhesive sheet 56 so that the two opposing surfaces of the molding mass materials 48 and 60 (separated by the sheet 56) are brought together. The hinged container 44 is then opened and the sheet 56 is removed to allow the molding materials 48 and 60 to solidify. The final product material is then positioned between the two molding materials 48 and 60 and then pushed into it to the desired depth. Curing results in a final product as in FIG. 6 having a non-porous membrane 65 and two porous surfaces 67 and 69. The thickness of the non-porous membrane 65 can be adjusted by adjusting the thickness of the non-adhesive sheet 56 and the degree of bonding force between the two opposing surfaces of SRO-CPMF. Complex shapes and tools, such as tubes and external facing materials used for artificial hearts and blood vessels with one or both sides porous, were made in the same way using silicone and biocompatible polyurethane.

Another example of a partially porous device according to the present invention is a breast (mammogenesis) implant. For example, a solid real image model having the desired curves and dimensions is first created by machine or other suitable molding technique using polymethyl methacrylate, etc., and polished and cleaned to prevent contamination. The sides of a hinged rectangular container 74 (FIG. 7A), somewhat larger than the real image model 82, are then filled with sugar molding lumps 78 and 80, similar to the formation of a nasal bridge implant. The polymethyl methacrylate breast implant model 82 is then pushed halfway into the molding mass 78 on one side of the container so that the upper recessed surface of the model is exposed. The thin layer polyethylene sheet 86 or other non-adhesive thin sheet material is then placed over the strip and the container 74 is tightly closed over the polyethylene sheet. Next, after the molding lumps 78 and 80 are cured as in the above example, the container 74 is opened and the model 82 and the sheet 86 are removed. The medical grade elastomer 90 (FIG. 7B) is then SRO− to the same depth as the desired thickness of the resulting porous coating of the final product (excess flow out depending on the desired thickness of the non-porous portion). After pushing into CPMF 78 and 80, container 74 is closed again and the elastomer is polymerized.
An additional coating of polymer can be applied to the interior of the SRO-CPMF to give the final product non-porous skin thickness according to the desired specifications. (As described below, if additional liquid mold end product material needs to be introduced into and onto and in the voids of the molds 78 and 80 created by the model 82, small holes are present anywhere. The layer can be added prior to final polymerization so that there is no interface between the porous and non-porous parts of the device or between the non-porous parts of the device.

  The container 74 is opened again, and the molds 78 and 80 are dissolved from the elastomer 90 by washing a plurality of times. The resulting chest implant device shown in FIG. 7C is partially porous and has a predetermined thickness of porous, next inner layer of non-porous elastomer 98 and internal voids 102 on the entire outer surface 94. The void is left intact or later filled with some material to provide a chest implant with the desired feel, conformability and function. For example, the void 102 can be filled with normal saline to make a saline-filled chest prosthesis. Alternatively, the void 102 can be filled or partially filled with a semi-solid such as a partially crosslinked silicone elastomer to make a silicone gel filled implant. Finally, the void 102 can be filled with a catalyzed non-polymerized elastomer, polymerized and fully crosslinked to create a rubber-like non-porous mold with a porous coating. Depending on the application, it may be necessary to leave the gap or fill it with a gas such as air.

  In another specific embodiment of the method of the present invention for chest implant fabrication, a two-part polyethylene mold 114 (FIG. 8A) is defined that defines a space 118 having an elliptical cross-section into which a sugar molding mass 122 is placed. Used. Also disposed is a handle 126 made of stainless steel or other stable corrosion resistant material that extends from the mold 122 to the opening of the mold 114. After the formation, the SRO-CPMF 122 with the handle 126 is taken out from the mold 114.

  Instead, to create the SRO-CPMF 122 of FIGS. 8A and 2B, a stainless steel handle 126 is attached to the polymethyl methacrylate model 82 of FIG. 7A as in FIG. Adhesion is enhanced by coating the mold surface with syrup, then spraying specific size sugar particles on the surface under air pressure and mixing well with a small amount of deionized water (similar to mixing ganite cement). Can be used. When the surface wetted sugar particles strike the model surface 82, they adhere to the model and to each other. The particle layer thickness can be adjusted to create a sugar SRO-CPMF skin of the desired thickness outside the model 82. The sugar envelope can then be dried to form SRO-CPMF as previously described in FIGS. 8A and 8B.

  In any of the above examples, the handle 126 is held by hand and the mold is immersed in the medical grade silicone dispersion. By vacuuming the mold 122 during or immediately after immersion, the penetration depth of the silicone dispersion can be increased to remove bubbles and coating non-uniformities within the mold. The mold can be re-immersed 2-6 times after drying in the silicone dispersion, depending on the desired thickness of the silicone skin to be formed. For the first one or two times, the mold 122 is immersed in the dispersion and the silicone flows into the mold cavity to form what will eventually become the porous portion of the device 138 (FIGS. 8C and 8C). 8D). Subsequent immersion of the mold 122 simply adds a non-porous layer 134 around the mold (FIGS. 8C and 8D). The thickness of the porous portion of the first example can be adjusted by adjusting the viscosity of the silicone dispersion and the time and pressure or vacuum treatment during or immediately after the initial coating, which is also the mold The degree of penetration of the dispersion into 122 is determined. In the second example, it can be adjusted by adjusting the thickness of the SRO-CPMF skin on the polymethyl methacrylate model 82.

  After completion of the dipping step, the silicone dispersion is vulcanized in an oven, for example, at 275 degrees Fahrenheit for about 1 hour. A small hole 130 (1.5-2 cm) (FIG. 8B) was then cut into the non-porous silicone covering the dip pattern and then deionized hot water was put into the hole to reach the SRO-CPMF material 122. Allow to dissolve. Multiple washings may be required for this. The resulting silicone device consists of a skin where the outer surface 134 (FIG. 8C) is non-porous and the inner surface 138 is porous. However, the device is inverted through holes 130 (FIG. 8D) formed to contain hot water to dissolve the mold 122, thereby reversing the position of the non-porous and porous surfaces, thereby making the device porous. The porous portion 138 (FIG. 8D) is on the outside and the non-porous portion 134 (FIG. 8D) is on the inside. Of course, the hollow or void 142 is present in any device as shown in FIG. 8C or 8D.

To close the hole or opening 130, a small solid silicone piece 146 is glued with a medical grade silicone adhesive (or vulcanized unvulcanized silicone rubber piece) to close the opening. Of course, the outer piece surface 146 can be porous or non-porous as desired. Also, a conventional self-sealing valve can be included in the segment 146 so that the materials described above can be inserted into the gap 142 at any time.
In another embodiment of the use of the present invention, the SRO-CPMF particles in the final product material 152 are left in the final product material 152 by leaving at least some SRO-CPMF material in the final product to dissolve over time after the product is implanted into the body. 150 (FIG. 9) is used.
Indeed, the device becomes a drug release system for implantation, and the SRO-CPMF material consists of or includes a drug released in or on the human body. Examples of such agents that can be included in the device during fabrication include gentamicin, tetracycline, or cephalosporin crystals, but many other available agents or agents that can be in crystalline form can be used. Many drugs, such as antibiotics normally used as powders, dissolve and recrystallize into larger crystals. The crystals are then partially dissolved and mixed, depending on the inherent stickiness and thermal stability, to form as a molding mass or heated to close packing and SRO as described for sugars. -Use as CPMF. (If necessary, a packing medium such as glucose crystals can be mixed with the drug to obtain a lower concentration of drug.) Instead, the crystals are neutral, non-drug-interacting biocompatible bonds. Along with a medium, for example a concentrated glucose solution, it can be combined in a proportion of 1 part saturated glucose solution and 4-40 parts drug crystals. In a further alternative, the powdered drug particles are dissolved or suspended in a glucose solution and then this solution is used to coat other particles such as other drugs or glucose crystals to surface the precipitated glucose and drug particles. SRO-CPMF is formed. As in the sugar SRO-CPMF example described above, drugs dissolved or suspended in a glucose solution can also be recrystallized, sized and made into SRO-CPMF itself. That is, examples of such combinations include dissolution, recrystallization of gentamicin crystals in a pharmaceutically pure saturated glucose (sugar) solution, and shaping of these particles into SRO-CPMF, which is then followed by silicone. Or other end product material is located.

  Different drug concentrations in different layers (similar to using graded sized particles as in FIG. 3B to make SRO-CPMF) or SRO-CPMF molding material so that different drugs are placed in different layers Manufactures, whereby different concentrations of drugs or different drugs are released as ingrowth proceeds, depending on the mechanism used by the organism for removal of the selected SRO-CPMF.

  As noted above, the drug or drug filtered mass can be used as a molding mass for SRO-CPMF and a biocompatible material such as medical grade silicone rubber can be used as the final product material. RTV (room temperature vulcanization) silicone is a preferred final product material because it does not require the heat treatment required for other types of silicones. Such heat polymerization modifies or changes the active form of the drug. Alternatively, the use of polyvinyl alcohol or polyglycolic acid or polylactic acid or other absorbent end product material is also possible. To ensure sterility, SRO-CPMF is manufactured under sterile conditions (all materials and fabrication tool equipment are sterilized, drugs are sterilized) or alternatively the device is in “clean room” conditions Produced below and sterilized by techniques found to not alter the biological activity of the drug. The device is then implanted into the human body or placed on the human body or in a body cavity to allow tissue ingrowth or penetration of the liquid and by passive and / or active dissolution of SRO-CPMF by the body. Release the drug. Here again, the features that can be created in the porous part of the device by the above method of preventing thick film formation and non-separation of the vasculature from the implant are recognized, which is important for the success of the device thus implanted. Key. Implant size, amount of porous surface area exposed for passive dissolution or tissue ingrowth, pore size, pore interconnect size, drug concentration in SRO-CPMF, drug water soluble type pair By adjusting the proportion of fat-soluble form and the site of implantation, pharmacokinetics can be adjusted. Also, a combination device that incorporates the drug into both SRO-CPMF and the final product material to make it a bilayer absorption type would either physically mix the drug particles or use a concentrated drug solution and then mix with the final product material. And can be manufactured by processing them as described above.

  Another use embodiment of the present invention relates to the manufacture of a porous metal or metal alloy device 154 (FIG. 10), which device is non-porous used as an electrode or battery plate, etc. in vivo or on a living body. A portion 156 and a porous portion 158 are included. In order to fabricate a metal partial porosity device, the sugar SRO-CPMF is first vacuum impregnated with wax. The SRO-CPMF is then removed by dissolution and dried. A conventional ceramic refractory material is then vacuum impregnated in wax instead of SRO-CPMF. The silver, gold, Vitallum or other castable metal is then heated to their molten phase and replaced with SRO-CPMF negative wax made of a ceramic refractory material in place of the wax using standard centrifugal casting techniques. Cast in replica. This produces the same porous mold that is obtained when silicone rubber is introduced into the SRO-CPMF as already described, although in this case from metal.

To create a ceramic partially porous device, SRO-CPMF is vacuum impregnated with wax as described above to dissolve the SRO-CPMF and dry the wax.
The ceramic is then dried by vibrating a concentrated suspension of fine particle size (5 mm) ceramic, such as α-alumina, into the pores of a wax continuous cell porous mold. The wax mold and ceramic combination is then heated to about 400 ° C. to melt and / or fade the wax. The ceramic is then sintered at 1650-1700 ° C. The porous body at this time is a negative replica of SRO-CPMF, and the sintered ceramic essentially becomes a replica of SRO-CPMF. A positive or negative copy of SRO-CPMF by a construction technique of the type described above using sugars, waxes, heat resistant substances and other selectively removable materials as SRO-CPMF or as a filling of the space between SRO-CPMF. Can be created. All other adjustment techniques described above with respect to porous and non-porous portions, continuous cell surface area size and position, etc. are applicable to the manufacture of the described metal or ceramic devices. As already mentioned, these devices can be used in a variety of situations where a large surface area exposure of the device is required.

  Another use embodiment of the method of the present invention is similar to the construction of the device of the above embodiment, but relates to the application as a dialysis device or a device for feeding oxygen into the blood (blood oxygenation). These devices utilize a double porous membrane as shown in FIG. Mold material 164 is produced by any of the methods described above. The liquid phase end product material (eg, RTV silicone rubber) is then pushed into the cavity of the mold 164. Next, most of the silicone rubber is extruded from the voids of the mold 164 with a gas such as liquid or compressed nitrogen gas to obtain a mold having a very thin coating of the silicone rubber 162. This reconstructs a continuous cell structure on the silicone rubber coating or membrane side opposite the mold material location, forming a secondary porous 160 (FIG. 11). The next step in the process is to cure or polymerize the silicone rubber 162 as previously described to dissolve the mold material 164 and create the primary porous (where the mold material was). The silicone rubber itself, which may close the porous material created in this way, using certain surfactants, such as thin soap solutions, both in the mold material solution and on the secondary porous side It is useful to prevent adhesion to.

When dissolution of the mold material is completed, a double-porous silicone rubber film 162 is left unconnected between the two porosities. The primary porous 164 on one side of the membrane 162 (made visible without mold material) has its own porosity created by the mold, while the secondary porous 160 on the other side of the membrane is molded. It has its porosity created by removing most of the silicone rubber in the mold gap. This side of the membrane is then separated by standard molding or construction techniques, and a gas such as oxygen or a liquid such as kidney dialysis solution is circulated through this secondary porosity without cross-circulating into the primary porosity. Can do. Such a device can then be implanted so that the primary porous 164 is completely filled with new blood vessels and free connective tissue.
This device was found to be very tissue compatible, without fiber formation in the primary part, and the capillaries and blood vessels were in fact very close to the silicone rubber membrane.

  In the prosthesis used as the dialysis machine, the standard dialysis solution circulates through the secondary porous 160. The membrane 162 between the porous 160 and 164 acts like a dialysis membrane in a standard artificial kidney, removing unwanted urea, nitrogen compounds and ions based on standard diffusion principles. The large surface area of the primary porosity and the fact that no coating is formed between the neovasculature and the silicone rubber membrane makes an implantable dialysis device practical here.

  Similarly, a similar device can be constructed for blood oxygenation. The device is implanted and a specific oxygen concentration is circulated through the secondary porous 160. In this case, the thin silicone rubber film 162 acts as a gas transfer film, oxygen moves into capillaries and blood vessels grown in the primary multi-quality 164, and carbon dioxide gas circulates from the vessel to the secondary porous 160. Removed in oxygen. Next, the carbon dioxide gas is removed. Using the previous example, a final product as shown in FIG. 12 with a layered film or layer coating can be made as follows. After applying a thin film of the final product of silicone rubber 170 to the mold and curing as in the previous example, but before removing the mold, a liquid type secondary material such as Biomer polyurethane solution 174 is applied. Then, vacuum impregnation treatment is performed in the secondary porous material. This may be either partially ejected as previously described with respect to the formation of the membrane of the previous example, or vacuum impregnated with a thin (ie 10-15%) solution of Biomer and dried in an oven at 50 ° C. for 2 hours. (Resulting in 85-90% solvent removal). This provides a double layer interlocking membrane with separate porosity on each side as shown in FIG.

Similarly, physical intermingling of two materials processed as described above can be advantageously used to join two different materials (not easily attached).
This can leave a double porosity as shown in the embodiment of FIG. The other two methods can also be used to join the two materials so that one side is a porous or non-porous surface. Using the embodiment described above with reference to FIG. 11, a thin silicone rubber film can be applied to the mold and cured, but the mold is held in place. For example, the following material such as a polyester resin treated with a catalyst is vacuum-impregnated into the secondary porous material and polymerized. The mold is removed to obtain a polyester connection structure in direct contact with the non-porous polyester surface and the thin silicon film, the porous being on the membrane side away from the polyester resin.

  Similarly, two sheets or structures can be joined using a porous material. This is done by making a partially porous sheet of silicone rubber having a non-porous portion 186 (FIG. 13) and a porous portion 184 as described in the embodiment shown in FIG. After drying, the catalyst-treated polyester resin is vacuum impregnated into the porous silicone rubber. After polymerization, the resulting structure has two non-porous surfaces for the silicone rubber 186 and the polyester resin 180, and the associated porous 184 and 182 each physically contact directly and interact with the two materials. It is connected.

  It will be understood that the above combinations and constructions are merely illustrative of the application of the principles of the present invention. While many modifications and variations of combinations and constructions can be devised by those skilled in the art without departing from the spirit and scope of the present teachings, the appended claims are intended to cover all such modifications, combinations, and constructions.

1 is a side cross-sectional view of a container in which a sugar molding material is deposited for the production of a porous material product according to the principles of the present invention, with an enlarged view showing a portion of a solidified sugar lump. A, B and C are respectively a partial view, a cross-sectional view of the sugar lump in the container, and a diagram representing the final porous product obtained. A and B are an elevational sectional view of a container containing a sugar molding material and a final product material, respectively, and an elevational sectional partial view of the final product. It is an expanded sectional fragmentary view of the final product material containing the fiber fragment concerning this invention. A, B, C, and D are elevational cross-sectional views of a molded container open, two closed, and the final product, respectively, suitable for use with the method of the present invention. FIG. 4 is a side cross-sectional view of a product having a top and bottom porous portion and an intermediate non-porous portion. A, B and C are cross-sectional views of a molded container containing an implant model, a molded container filled with the final product material, and the resulting final product implant, respectively. A, B, C, and D are elevational cross-sectional views, respectively, of a forming container for forming a forming die, a forming die including an applied final product material, and two types of final prosthetic devices according to the present invention. . 1 is an elevational cross-sectional partial view of a prosthesis for use as a drug delivery implant. FIG. 1 is a cross-sectional side view of a porous metal alloy product made in accordance with the present invention. 1 is a cross-sectional partial view of a double porous prosthesis with a mold made in accordance with the present invention still in place. 1 is a partial cross-sectional view of a final porous product made according to the principles of the present invention with a material coated on the pore surface. FIG. 2 is a partial cross-sectional side view of two connecting materials made in accordance with the present invention.

Claims (2)

A porous material product comprising one or more porous portions, wherein the porous portions have an effective effect in promoting angiogenesis and vascularized tissue ingrowth; and These porous parts have the following configuration:
Tissue contact means for promoting angiogenesis and vascularized tissue ingrowth, the tissue contact means minimizing the formation of fibrous, scar or capsule tissue, and the tissue contact means Is
(A) a large number of pores distributed substantially throughout the porous portion;
(B) a large number of pore interconnectors,
(C) the pores each connected to at least one adjacent pore;
(D) Substantially having the pores forming a continuous cell structure by continuously interconnecting each other, and the pores and the interconnected portions of the pores have almost no sharp edges or edges. Porous material product characterized by having a surface that does not contain much. A dual porous material product for promoting angiogenesis and vascularized tissue ingrowth, the porous material product comprising:
The first and second porous portions have a first porous portion and a second porous portion separated by a membrane, and at least one of the porous portions is
Including tissue contacting means for promoting non-vascularization and vascular tissue ingrowth and for minimizing the formation of fibrous, scar or capsule tissue;
The tissue contacting means comprises
(A) a number of pores distributed substantially throughout the at least one porous portion;
(B) a large number of pore interconnectors,
(C) the pores each connected to at least one adjacent pore;
(D) substantially having the pores forming a continuous cell structure by continuously interconnecting each other, and the pores and pore interconnecting portions have sharp edges or edges Porous material product characterized by having a surface containing almost no part.

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