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    • 专利摘要:
    PURPOSE: A method of preparing a biomaterial for tissue restoration by treating collagen-based biological tissues obtained from a mammal with a polyepoxy compound, cross-linking the collagen of the collagen-based tissues, decellularizing the tissues and then freeze-drying the cell-free tissue by employing a cryoprotective solution is provided. Therefore, the method is simple and economical as compared to conventional methods. CONSTITUTION: A biomaterial for tissue restoration is prepared by the steps of: obtaining collagen-based biological tissues from a mammal; obtaining biological tissues containing a cross-linked collagen by treating the collagen-based biological tissues with a polyepoxy compound; obtaining cell-free tissues by decellularizing the biological tissues; and immersing the cell-free tissues in a cryoprotective solution containing hyaluronic acid and freeze-drying the tissue. The polyepoxy compound is polyglycerol polyglycidyl ether or polyethylene glycol glycidyl ether.
    公开号:KR20030060767A
    申请号:KR1020027012668
    申请日:2002-09-05
    公开日:2003-07-16
    发明作者:김태운；박성영；황호찬
    申请人:한스바이오메드 주식회사；
    IPC主号:
    专利说明:

    A process for preparing a biomaterial for tissue issue
    [2] In order to treat facial contour deformity, loss and depression of soft tissues due to trauma, dwarfness of existing soft tissues and various urological diseases, various injection materials are used as restoration materials for soft tissues and dermal tissues. Representative restoration materials currently used include liquid silicone, bovine collagen, autologous skin or autofat.
    [3] Liquid silicones were used mainly in the military during World War II, but began to be used in the human body after developing medical grade '360' in the United States in 1963. It was actively used because of its merits. However, their use is discouraged after the occurrence of inflammation, induration, discoloration, ulceration, migration, and formation of silicone granulomas after transplantation. (Klein AW, Rish DC, J. Dermatol. Surg. Oncol., 11: 337-339, 1985; Nosanchuk JS, Arch. Surg., 97: 583-585, 1968; Piechotta FU, Aesthetic Plast. Surg., 3: 347-355, 1979; Spira M., Rosen T., Clin.Plast.Surg., 20: 181-188, 1993).
    [4] Bovine collagen for injection, on the other hand, is known to require a skin sensitivity test of transplant recipients a few weeks before use. In addition, about 3% of the recipients of the transplant were hypersensitivity even after sensitization trials and transplantation (Elson ML, J. Am. Acad. Dermatol., 18: 707-713, 1998). The duration was reported as short, with an average of 3 to 6 months (Gromley DE, Eremia S., J. Dermatol. Surg. Oncol., 16: 1147-1151, 1990; Matti BA, Nicolle FV, Aesthetic Plast. Surg) , 14: 227-234, 1990). In addition, side effects such as transient erythema, swelling, local skin necrosis and abscess formation after transplantation have been reported (Cooperman LS et al., Aesthetic Plast. Surg., 9: 145). -151, 1985; Frank DH et al., Plast.Reconstr. Surg., 87: 1080-1088, 1991; Hanke CW, et al., J. Am.Acad.Drmatol., 25: 319-326, 1991; Matti BA et al., Aesthetic Plast.Surg., 14: 227-234, 1990).
    [5] Next, autologous skin is used in that it has an average duration of 1 to 2 years after transplantation and does not need to be tested for safety and skin sensitization. Complications occur, which takes a long time to cure.
    [6] Finally, autologous fat, which has increased in use with the development of liposuction, is shorter than bovine collagen after transplantation in the human body, so autologous fat should be continuously implanted for the desired level of treatment (Gromley DE, Eremia S). , J. Dermatol.Surg.Oncol., 16: 1147-1151, 1990).
    [7] Although the aforementioned soft tissue restorers each exhibit some of the characteristics of an excellent soft tissue restorer in one or more respects, none of them can meet all of the conditions for an ideal soft tissue restorer.
    [8] In order to overcome the above-mentioned disadvantages, tissue engineering including the field of biomaterials is rapidly developing, and some technologies are commercially available and commercially available. In this trend, there is a perfect restoration material to replace human soft tissues in the near future. It is estimated to be developed. However, since the technologies developed to date cannot overcome all of the above disadvantages, continuous technology development is required. For example, U. S. Patent No. 5,336, 616 discloses a technique for preparing a cell-free dermal layer for transplantation that includes a step of eliminating cells in the matrix that cause an immune response and a freeze protection step of preventing collagen structure damage of the tissue during lyophilization. It has been disclosed that the cell-free dermal layer prepared by this method has gained much attention due to its long-term preservation without causing an immune rejection reaction. However, there are disadvantages in that the processing method is complicated and the economical efficiency is low and the possibility of contamination is high. In addition, since the processing step to protect the collagen tissue is not included in the processing before lyophilization, collagen tissue is likely to be damaged, which is pointed out that the collagen fibers are rapidly degraded after transplantation.
    [9] Therefore, the necessity of developing a new bio-recovery material having a simple processing method and a low damage rate of collagen tissue by effectively processing collagen biological tissues has emerged constantly.
    [1] The present invention relates to a method for producing a biological restorative material. More specifically, the present invention provides a step of crosslinking collagen of collagen tissue obtained from a mammal, removing cells from the tissue cross-linked with electric collagen, and lyophilizing the tissue from which cells have been removed using cryopreservation solution. It relates to a method for producing a bio-restored material comprising a bio-restored material produced by the electrical method.
    [13] 1 is a graph comparing the cross-linking index with temperature change over time.
    [14] 2 is a graph comparing the crosslinking index over time according to the concentration change of polyepoxy.
    [15] Figure 3 is a graph comparing the cross-linking index with time changes.
    [16] 4 is a graph showing the decomposition degree of the dermis layer by collagenase over time.
    [17] Figure 5 is a graph comparing the size of the powder particles according to the grinding method.
    [18] Figure 6 is a graph comparing the duration according to the particle size and injection concentration of the biorecovery material.
    [19] Figure 7a is a photograph of the tissue 1 week has passed after subcutaneous transplantation.
    [20] 7B is a photograph of tissue 1 month after subcutaneous transplantation.
    [21] 7C is a photograph of tissue 12 months after subcutaneous transplantation.
    [22] Detailed description of the invention
    [23] Method for producing a biorecovery material of the present invention comprises the steps of obtaining a collagen biological tissue from a mammal; Treating the previously obtained biological tissue with a polyepoxy compound to obtain a biological tissue including cross-linked collagen; Removing cells from the previously obtained biological tissue to obtain acellular tissue; And immersing the cell-free tissue obtained in the cryopreservation solution containing hyaluronic acid and lyophilizing. At this time, the collagen tissue is not particularly limited, but it is preferable to use a fascia, amnion, placenta, dermis, epidermal layer, etc. of the mammal, and the polyepoxy compound is not particularly limited, polyglycerol polyglycidyl It is preferred to use polyglycerol polyglycidyl ether or polyethylene glycol glycidyl ether or to use a commercially available product. In addition, the treatment conditions of the polyepoxy compound are not particularly limited, but the treatment is preferably performed for 10-20 hours at a concentration of 1-7% (w / v), pH 8-11 and conditions of 30 to 45 ℃. In addition, the physical processing method of the cryopreserved acellular tissue is not particularly limited, but in order to prevent damage to the tissue due to heat generated during the processing, the liquid-filled impact grinding container filled with liquid nitrogen It is preferable to physically process the cells, and more preferably, the lyophilized acellular tissue is lyophilized in a liquid nitrogen-filled impact grinding vessel. In addition, the method may further include pulverizing the electrically lyophilized acellular tissue or rehydrating and cutting the lyophilized acellular tissue.
    [24] To date, various crosslinking techniques have been studied in connection with tissue transplantation as a method for stabilizing collagen structure in tissues while maintaining the mechanical strength and inherent properties of the tissues. In addition to cross-linking technology, cell removal technology is also being actively researched to reduce the immune response to the graft of the host during transplantation and to develop biomaterials for cell culture and tissue engineering. Although cross-linking agents used for the purpose of enhancing the structural stability of tissues have been mainly studied with respect to glutaraldehyde, research on new cross-linking methods has been actively conducted due to the disadvantage that they show strong toxicity to the living body. It's going on. Among them, newly studied is crosslinking of collagen tissue using a polyepoxy compound.
    [25] Polyepoxy compounds are a group of chemicals having various lengths of backbones and functional groups, and a commercially available product called 'Denacol ™ (Nagase Chemical Company, Japan) is mainly used for crosslinking tissue.
    [26] Polyepoxy compounds differ from glutaraldehyde in the crosslinking mode. That is, glutaraldehyde reacts with the ε amino group of the lysine residue present in the protein, but the epoxy group of the polyepoxy compound reacts with high reactivity with various functional groups such as amino group, carboxy group, hydroxy group, phenol group and alcohol group. In particular, compounds having a medium length main chain composed of 17-25 carbons and 4-5 epoxy groups are known to be effective for crosslinking molecules having a helical polypeptide structure such as collagen.
    [27] In addition, when the polyepoxy compound is treated to a molecule having a helical polypeptide structure such as collagen, the antigenicity or immune response of the tissue is reduced in proportion to the treatment time, and the toxicity to the living body is lower than that of glutaraldehyde. Therefore, it shows relatively good biocompatibility (Lohre JM et al., Artif. Organs, 16: 630-633, 1992; Uematsu M. et al., Artif. Organs, 22: 909-913, 1998).
    [28] Physicochemical and biomechanical properties of collagen tissue are due to the structure of the collagen fibrils that make up it. Collagen molecules contained in the collagen fibrils exist in a kind of twisted state in which three polypeptide chains are spirally wound together, and can be stabilized through covalent crosslinking formed between molecules using chemicals. When using a polyepoxy compound, one molecule of the polyepoxy compound reacts with two or more amino groups of collagen to form a crosslink. The electroformed crosslinks provide suitable tensile strength and biostability for implantable tissue. That is, externally inserted collagen tissue is degraded by protease secreted from the living body, and electrical crosslinking effectively prevents the proteinase from accessing collagen molecules, thereby protecting the inserted collagen tissue.
    [29] Therefore, in the present invention, in order to minimize the damage of collagen, which is a disadvantage pointed out in the conventional method for preparing acellular dermal layer (US Pat. No. 5,336,616), it was improved to add a crosslink formation step of collagen using a polyepoxy compound. That is, before removing the cells, the polyepoxy compound is treated with collagen biological tissues to induce crosslinking within or between the collagen fibers constituting the collagen, thereby strengthening the structure of the tissue.
    [30] On the other hand, the development of cell removal technology for producing cell-free tissue completely removed cells that cause the immune response is also actively progress. At this time, "cell removal technology" refers to a technology that removes only cells while maintaining extracellular matrix components through chemicals, enzymes, and mechanical methods. Transplantation technology is recognized as an important part in the development of biorecovery materials, since transplantation of tissues from which is completely removed results in the remodeling of the implants through vascular remodeling and cell proliferation. In this case, the important point is that after removing the cells, all residues must be removed to prevent the immune response that may occur after transplantation. To this end, various methods may be used, but a method using a surfactant is most preferable, an ionic surfactant such as sodium dodecyl sulfate (SDS), or Triton X-100, Tween 20, Tween 80 , Nonionic surfactants such as NP-10 (nonidet P-10), NP-40 (nonidet P-40) and the like can be used.
    [31] Lyophilization or freeze drying is done to preserve the cells or tissue structure without damaging the tissue when it is frozen. The cryopreservation solution, which is used in advance for tissue protection before lyophilization, is a buffer solution that maintains the ionic strength and osmotic pressure of the solution, and lyophilization that prevents physical and chemical damage to the tissue and freezes and dries the tissue It consists of a cryo-dryprotectant. In this case, the freeze-drying protector increases the glass transition temperature to prevent tissue collapse caused by recrystallization of the ice particles during the freeze-drying process and enhances the stability of the tissue. That is, if the temperature of the tissue during drying is higher than the glass transition temperature, recrystallization of the ice particles occurs, and the recrystallized ice particles become larger and the tissue is damaged. Therefore, if the glass transition temperature is increased by using a lyophilizer, the tissue is less than hexagonal ice. The higher specific gravity of the glass ice or square ice, which is stable and small in size of ice crystals, can cause less damage to the tissue and speed up drying.
    [32] Currently, commonly used lyophilizers are dimethylsulfoxide, dextran, sucrose, propylene glycol, glycerol, mannitol, sorbitol, and fructose (DMSO). fructose, trehalose, raffinose, raffinose, butanediol (2,3-butanediol), hydroxyethyl starch (HES), polyethylene glycol (PEG), polyvinyl pyrrolidone (PVP), proline, hetastarch (hetastarch) ), Serum albumin, etc. are combined according to the purpose, but their biosafety has already been verified, but since the mixing conditions are difficult according to the purpose, the manufacturing method is complicated and costs are high in manufacturing. There is this.
    [33] In the present invention, hyaluronic acid was used as a cryoprotectant in order to improve the cryoprotection of the acellular tissue for transplantation and the biocompatibility in the transplanted tissue. Hyaluronic acid, a polysaccharide that has a very high reactivity with water, is an unbranched polysaccharide in which glucuronic acid / N-acetyl-D-glucosamine disaccharide unit is continuously linked. polysaccharide) is a substance widely present in the extracellular matrix of various tissues such as skin or cartilage.
    [34] The main functions of hyaluronic acid are known as space-filling, structure-stabilizing, cell-coating, and cell-protecting. In addition, the formation of an integrated system with fibrous proteins in the extracellular space structurally provides a substrate with elasticity, viscosity, protection, lubrication and stabilization. In addition, the high fluidity possessed by hyaluronic acid plays a pivotal role in hydration of the extracellular matrix, and confers a property that metabolites can easily move through diffusion even at relatively small concentrations.
    [35] When hyaluronic acid is used as a cryoprotectant in the present invention, it is possible to play a role as a cryoprotectant due to the basic polysaccharide structure, and can improve biocompatibility in the body in which acellular tissue is transplanted by the original function of hyaluronic acid. Could know.
    [36] Hereinafter, the present invention will be described in more detail with reference to Examples. These examples are only for illustrating the present invention in more detail, it will be apparent to those skilled in the art that the scope of the present invention is not limited by these examples in accordance with the gist of the present invention. .
    [37] Example 1 Establishment of Polyepoxy Treatment Conditions
    [38] Skin from pigs was placed in RPMI-1640 (13200-076, Gibco-BRL, USA) medium containing 50 ng / ml amphotericin-r (A-9528, Sigma, USA), 1 mM EDTA, and 4 ° C. The following temperature was maintained. Then, the skin tissue was taken out and cut into a size of 1 x 2 cm 2 to prepare a sample. The 330 mM EDTA solution was treated for 2 hours, the epidermal layer of the sample was removed and washed with PBS.
    [39] Thereafter, each sample was treated with Denacol ™ EX-512 (Nagase Chemical Company, Japan) at different temperatures, concentrations or pHs, and the crosslinking indices were measured and compared with each other.
    [40] Example 1-1 : Measurement of Crosslinking Index According to Temperature Change
    [41] Electrical samples were immersed in 50 ml of 4% (w / v) Denacol ™ EX-512 at pH 9.5 at 25 ° C. and 37 ° C., respectively, and shaken at 30 ± 5 rpm, 3, 6, 9, 12, 15, 18, 24 After a period of time, unreacted amino acids were measured using a ninhydrin assay. Ninhydrin reacts with the amino acids of collagen to develop a bluish purple color. At this time, the sample which was not crosslinked was used as a control.
    [42] First, samples were obtained for each time period, and each sample was reacted with a ninhydrin reagent at 100 ° C. for 20 minutes, and then the color development results were measured at 570 nm with a spectrophotometer (Byrophotometer, Biomate 3, Thermo Spectronix). In this case, various concentrations of commercially available N-δ-acetyl lysine are used as a reference, and the concentration of the unreacted amine (mole) to the concentration of the collagen (mole) of the sample is regarded as an unreacted amino group. It was. The crosslinking index was measured by substituting the measured values of each experimental group and the control group into the following equations (see FIG.
    [43] Crosslinking index = 100 × {1- (ninhydrin measured value) experimental group ÷ (ninhydrin measured value) control group }
    [44] 1 is a graph comparing the crosslinking index according to the temperature change. As shown in FIG. 1, the crosslinking index increased proportionally with time, and showed a very small increase rate from 9 hours after treatment, and after 15 hours, a constant crosslinking was formed. This increase was found.
    [45] Example 1-2 measurement of crosslinking index according to the change of concentration of polyepoxy
    [46] The crosslinking index was measured in the same manner as in Example 1-1, except that the electrical samples were immersed in 50 ml of 0.5, 1 or 4% (w / v) Denacol ™ EX-512 at pH 9.5, respectively, at 37 ° C. (See FIG. 2). Figure 2 is a graph comparing the crosslinking index according to the change in the concentration of polyepoxy. As shown in Figure 2, it was found that the crosslinking index increases as the concentration of polyepoxy increases.
    [47] Example 1-3 Measurement of Crosslinking Index According to pH Change
    [48] The crosslinking index was measured in the same manner as in Example 1-1, except that the electrical samples were immersed in 50 ml of 4% (w / v) Denacol ™ EX-512 at pH 8.5, 9.5 or 10.5, respectively, at 37 ° C. (See FIG. 3). 3 is a graph comparing the crosslinking index according to the pH change. As shown in Figure 3, it was found that the crosslinking index increases as the pH value increases.
    [49] Therefore, the results were summarized, and it was confirmed that treatment of polyepoxy at a concentration of 4% (w / v) at a pH of 9.5 and 37 ° C. for an effective crosslinking of the samples was optimal.
    [50] Example 2 Damage Inhibition Effect of Collagen Tissue by Polyepoxy Compound and Hyaluronic Acid Treatment
    [51] Skin from pigs was placed in RPMI-1640 medium containing 5 μg / ml gentamycin (G-1397, Sigma, USA), 50 ng / ml amphotericin-r, 1 mM EDTA, and the temperature was below 4 ° C. Was maintained. Subsequently, the skin tissue was taken out and the dermis layer faced down, spread out on a 24.5 x 24.5 cm 2 bioassay plate, and a sterile blade was scratched at one corner to distinguish the epidermal and dermal layers. The unfolded skin is cut into rectangles of 6 x 10 cm 2, placed into three aseptic containers, and then 50 ml of 0.5% (v / v) protamine solution containing 330 mM EDTA is dispensed, respectively. It was shaken for 2 hours at a speed of 45 ± 5rpm at room temperature. The epidermal and dermal layers were separated using tweezers, and the dermal layer was obtained and washed with PBS. The obtained dermal layer was divided into three experimental groups as follows.
    [52] The first group (PE + HA) was immersed in 50 ml of 4% (w / v) Denacol ™ EX-512 containing 1% (w / v) Tween20, shaken at 37 ° C. for 15 hours, and then PBS Washed with. Subsequently, it was immersed in 0.5% (w / v) hyaluronic acid solution and shaken for 1 hour at 37 ℃, the hyaluronic acid solution was removed, washed with PBS, and then again in 0.5% (w / v) hyaluronic acid solution Dipping and shaking at 37 ° C. for 1 hour.
    [53] The second group (PE) was treated the same as the first group except that no hyaluronic acid was treated.
    [54] The third group (None) was soaked in the dermal layer in 0.5% (w / v) SDS solution, shaken for 12 hours at room temperature, and then washed with PBS. Subsequently, it was immersed in 10% (v / v) glycerol solution, and shaken for 2 hours at room temperature.
    [55] Each dermal layer treated in each experimental group was spread well on the floor with the dermis side up on the bioanalytical dish, and the bioanalytical dish was frozen with a minimum shelf temperature of -50 ° C and a minimum condenser temperature range of -60 ° C. Placed in a dryer (Ultra35 super LE, Virtis, USA). Subsequently, the temperature was lowered at a rate of −2.5 ° C. per minute to freeze at a high rate up to −40 ° C., and the temperature was maintained for 10 minutes when the temperature of the dermal layer reached −40 ° C. Then, the conditions are set so that the residual moisture content is within 5% (w / w), and the temperature of the dryer is gradually raised to 30 ° C by 10 ° C, and the vacuum is removed to remove water in the dermis layer for 30 to 40 hours. The dermal layer was dried using. Once completely dried, the bioanalytical dish with the dermal layer spread out was transferred to a sterile workbench, and then vacuum-packed in a short time so as not to absorb moisture from the dried dermal layer, and refrigerated at 4 ° C.
    [56] Samples of each lyophilized group were cut into 1 × 3 cm 2 , immersed in a 1U / ml collagenase solution containing 10 mM CaCl 2 , shaken at 37 ° C. for 25 hours, and each time period. Samples were obtained. The weight of each sample obtained was measured, and the weight ratio to the weight before the treatment was measured to compare the degree of decomposition of the dermal layer over time (see Fig. 4). 4 is a graph showing the degree of decomposition of the dermal layer by collagenase. As shown in FIG. 4, the experimental group treated with polyepoxy reduced the degree of degradation by collagenase compared to the experimental group not treated with polyepoxy. In addition, it was found that the degree of degradation by collagenase was reduced in the experimental group treated with hyaluronic acid than the untreated experimental group.
    [57] Accordingly, it was confirmed that the dermal layer treated with the polyepoxy and hyaluronic acid of the present invention contained a more stable collagen structure than the dermal layer prepared by a known cell-free dermal layer manufacturing method.
    [58] Example 3 Preparation of Biological Restorative Material Based on Placenta of Bovine
    [59] Placenta from cows was placed in RPMI-1640 medium containing 5 µg / ml gentamycin, 50 ng / ml amphotericin-r, 1 mM EDTA, and iced to maintain a temperature below 4 ° C. The iceboxes were filled and transferred to a clean bench. The transferred placental tissue was immersed in Dulbecco's phosphate buffer solution (21600-010, Gibco-BRL, USA) containing 5 μg / ml of gentamycin, removing placental blood and foreign material, and then separating the amnion from the placenta. It was. The separated amniotic membrane is placed on a 24.5 x 24.5 cm 2 bioassay dish (Nalgen Nunc, USA) with the substrate side facing down, and a sterile blade is scratched at one corner to distinguish the epidermal and dermal layers. It was made. The unfolded skin is cut into 6 x 10 cm 2 rectangles, and 3 pieces per sterile container are dispensed, and 50 ml of 0.5% (v / v) protamine solution is dispensed, respectively. Shake for hours. Subsequently, it was immersed in 50 ml of 4% (w / v) Denacol ™ EX-512 (Nagase Chemical Co., Japan) containing 0.5% (w / v) SDS and shaken at 37 ° C. for 30 hours at 30 ± 5 rpm. Then washed again with PBS. It was then immersed in 0.5% (w / v) hyaluronic acid solution, shaken at 37 ° C. at 30 ± 5 rpm for 1 hour and then washed with PBS. 0.5% hyaluronic acid solution was then added back to the vessel and shaken at 37 ° C. at 30 ± 5 rpm for 1 hour. The electrotreated dermal layer was spread on the floor with the dermis face up in a bioassay dish on a sterile workbench and lyophilized in the same manner as in Example 2.
    [60] Example 4 Comparative Analysis of Particle Size Distribution of Powders According to Grinding Method of Lyophilized Amniotic Membranes
    [61] In order to refine the biorecovery material prepared in Example 3 to a size that can be injected, it was divided into two methods and ground. The first method is to grind 5 g of lyophilized biorestore material through the rotation of a saw blade in a grinding chamber filled with liquid nitrogen, using a mechanical stirrer with a tooth, and the second method is 5 g of lyophilized biorestore material. It is put in an airtight pulverization container with an impact rod, mounted in a freezer mill (Freezer mill 6850, Spex CertiPrep, USA), and injected with liquid nitrogen into the crusher so that the pulverization container is completely submerged in liquid nitrogen, and then pulverized by impact. The size of the powder particles obtained when the two powders were pulverized was compared (see FIG. 5). Figure 5 is a graph comparing the size of the powder particles according to the grinding method. As shown in Figure 5, when pulverizing the lyophilized amniotic membrane with a mechanical stirrer, it is impossible to control the size of the powder particles according to the rotational speed of the stirrer saw blade, 60% or more was pulverized into a powder having a size of 500㎛ or more, freeze crusher In the case of using, since the impact number of the impact rod can be adjusted during freezing, it is possible to obtain 70% or more of a powder having a particle size of 100-500 µm.
    [62] Example 5 Determination of Optimal Use Concentration of Biological Restoration Material
    [63] Subcutaneous injection experiments were performed using male mice (central laboratory animals, Korea), 8 weeks old, to determine the optimal amount of implantation of the biorecovery material prepared in Example 3 above.
    [64] Mice were anesthetized using ethyl ether in a sterile workbench, and injected into the subcutaneous part of the experiment by dividing the experimental groups by powder particle size and injection concentration. At this time, the powder particle size was divided into three groups of 100 µm or less, 100-500 µm and 500 µm or more, respectively, and the injection concentration was divided into three groups of 250 µg / ml, 350 µg / ml and 450 µg / ml, respectively.
    [65] For each powder particle size and injection concentration, a leur-lok syringe containing powdered reconstituted material and a luerlock syringe containing 1 ml of PBS were connected to each other using an adapter. The contents contained in the syringe were mixed to prepare an injection material for injection. The previously prepared reconstituted injections were each injected by subcutaneous injection using a 26 gauge needle for 0.5 ml each. At the 1, 2, 4, 8, 12, 16, 20, and 24 weeks after transplantation, the duration of each restoration in the subcutaneous tissue at the site of implantation of the injection (See FIG. 6). Figure 6 is a graph comparing the duration according to the particle size and injection concentration of the biorecovery material. As shown in FIG. 6, the injection concentration showed the longest duration at 450 μg / ml irrespective of the powder particle size, and the reconstructed material of 100-500 μm lasted the longest in the tissue.
    [66] Therefore, it could be confirmed that the optimal powder particle size and injection concentration were 100-500 μm and 450 μg / ml to maximize the transplant effect by prolonging the duration.
    [67] Example 6 Preparation and Transplantation of Biological Restorative Material Based on Pig Skin
    [68] Skin from pigs was placed in RPMI-1640 medium containing 5 μg / ml gentamycin, 50 ng / ml amphotericin-ratio and 1 mM EDTA, and maintained at 4 ° C. or lower. Subsequently, the skin tissue was taken out and the dermis layer faced down, spread out on a 24.5 x 24.5 cm 2 bioassay plate, and a sterile blade was scratched at one corner to distinguish the epidermal and dermal layers. The unfolded skin is cut into 6 x 10 cm 2 rectangles, 3 pieces per aseptic container, 50 ml of 0.5% (v / v) protamine solution containing 330 mM EDTA, and 45 ± at room temperature. It was shaken for 2 hours at 5 rpm. The epidermal layer was removed from the dermal layer using tweezers and washed with PBS. Subsequently, it was immersed in 50 ml of 4% (w / v) Denacol ™ EX-512 containing 1% (w / v) of Tween 20, shaken at 37 ° C for 30 hours at 30 ± 5 rpm, and then washed again with PBS. It was. It was then immersed in 0.5% (w / v) hyaluronic acid solution, shaken at 37 ° C. at 30 ± 5 rpm for 1 hour, washed with PBS, and the 0.5% (w / v) hyaluronic acid solution was returned to the vessel. It was added and shaken at 37 ° C. at 30 ± 5 rpm for 1 hour. The electrotreated dermal layer was lyophilized in the same manner as in Example 2 above. Subsequently, 4 g of the lyophilized biorestore material was used, and a powder having a size of 400 μm was obtained by using a freeze mill in the same manner as in Example 4, and 1.5 cc of 1% (v / v) lidocaine solution was used instead of PBS. Except for the use, the restorative for injection was prepared in the same manner as in Example 5.
    [69] Hematoxylin and eosin were harvested by subcutaneous tissue from the transplanted area, which was implanted in the same manner as in Example 5, in the same manner as in Example 5, and after 1 week, 1 month and 12 months. A biopsy was performed by (hematoxylin and eosine, H & E) staining (see FIGS. 7A, 7B and 7C). Figure 7a is a picture of the tissue 1 week has passed after the subcutaneous transplant, Figure 7b is a picture of the tissue 1 month has passed after the subcutaneous transplant, Figure 7c is a picture of the tissue 12 months after the subcutaneous transplantation. . As shown in Figures 7a, 7b and 7c, a week after the implantation of the restoration material, many mouse autologous cells are infiltrating and proliferating around the border of the transplanted portion, and some cells are also proliferating in the center of the transplanted portion. After 1 month, the boundary between the transplanted part and the autologous tissue was clearly present as in 1 week after transplantation, but the cell proliferation was active to the center of the transplanted site and gradually self-organized. In addition, after 12 months, all the restoratives self-organized without boundary between the transplanted restorative tissue and the autologous tissue, and confirmed that the cells were filled in the tissue.
    [70] As described in detail above, the present invention comprises the steps of crosslinking the collagen of collagen tissue obtained from a mammal, removing cells from the cross-linked tissue collagen, and lyophilizing the tissue from which cells have been removed using cryopreservation solution. It provides a method for producing a bio-restored material comprising a bio-restored material produced by the electrical method. Method for producing a biorecovery material of the present invention comprises the steps of obtaining a collagen biological tissue from a mammal; Treating the previously obtained biological tissue with a polyepoxy compound to obtain a biological tissue including cross-linked collagen; Removing cells from the previously obtained biological tissue to obtain acellular tissue; And immersing the cell-free tissue obtained in the cryopreservation solution containing hyaluronic acid and lyophilizing. According to the present invention, compared to the conventional bio-restore material, since the bio-restore material containing a stable collagen structure can be prepared by a simpler method, it can be widely used for the economic production of various bio-restore materials.
    [10] Accordingly, the present inventors have worked hard to develop a new biorecoverable material that effectively processes collagen biological tissues, has a simple processing method, and has a low damage rate of collagen tissues. By strengthening the binding, the damage rate of collagen can be lowered, and the cryoprotection step can be performed by a simple method using hyaluronic acid, and it is confirmed that it is effectively engrafted by thawing and transplanting the physically processed tissue into a living body. This invention was completed.
    [11] After all, the main object of the present invention is to provide a method for producing a collagen biorestore material.
    [12] Another object of the present invention is to provide a biological restorative material based on collagen biological tissues of mammals produced by the electric method.
    权利要求:
    Claims (7)
    [1" claim-type="Currently amended] (i) obtaining collagen biological tissue from a mammal;
    (ii) treating the previously obtained biological tissue with a polyepoxy compound to obtain a biological tissue comprising crosslinked collagen;
    (iii) removing cells from the previously obtained biological tissue to obtain acellular tissue; And,
    (iv) immersing the cell-free tissue obtained in the cryopreservation solution containing hyaluronic acid and lyophilizing.
    [2" claim-type="Currently amended] The method of claim 1,
    Collagen biological tissues can be found in mammalian fascia, amnion, placenta, dermal layer or
    Characterized in that the epidermal layer
    Method for producing a biological restorative material.
    [3" claim-type="Currently amended] The method of claim 1,
    Polyepoxy compounds are polyglycerol polyglycidyl ether
    polyglycidyl ether) or polyethylene glycol glycidyl
    It is characterized in that the ether (polyethylene glycol glycidyl ether)
    Method for producing a biological restorative material.
    [4" claim-type="Currently amended] The method of claim 1,
    Polyepoxy at 1-7% (w / v) concentration, pH 8-11, 30-45 ℃
    Characterized in that the treatment for 10-20 hours
    Method for producing a biological restorative material.
    [5" claim-type="Currently amended] The method of claim 1,
    Lyophilized acellular tissues were placed in a liquid nitrogen-filled impact grinding container.
    Characterized by further comprising the step of lyophilization
    Method for producing a biological restorative material.
    [6" claim-type="Currently amended] The method of claim 1,
    Rehydrating and cleaving the lyophilized acellular tissue further
    Characterized in that it comprises
    Method for producing a biological restorative material.
    [7" claim-type="Currently amended] A biological restorative material produced by the collagen biological tissue of a mammal prepared by the method of claim 1.
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    同族专利:
    公开号 | 公开日
    WO2003024496A1|2003-03-27|
    US20040059430A1|2004-03-25|
    KR100514582B1|2005-09-13|
    CN1556715A|2004-12-22|
    CN1227040C|2005-11-16|
    引用文献:
    公开号 | 申请日 | 公开日 | 申请人 | 专利标题
    法律状态:
    2001-09-05|Priority to KR1020010054489
    2001-09-05|Priority to KR20010054489
    2001-09-13|Priority to KR20010056337
    2001-09-13|Priority to KR1020010056337
    2002-09-05|Application filed by 한스바이오메드 주식회사
    2003-07-16|Publication of KR20030060767A
    2005-09-13|Application granted
    2005-09-13|Publication of KR100514582B1
    优先权:
    申请号 | 申请日 | 专利标题
    KR1020010054489|2001-09-05|
    KR20010054489|2001-09-05|
    KR20010056337|2001-09-13|
    KR1020010056337|2001-09-13|
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