Separating membrane for dentistry and method for manufacturing the same

Abstract

To provide a separating membrane for dentistry that includes a porous layer and a hydrophilic layer and a method for manufacturing the same.SOLUTION: The porous layer includes a porous structure formed from a biodegradable polymer and a bone regeneration material attached to the porous structure. Based on the total weight of the porous layer being 100 wt.%, the content of the porous structure is 22 wt.%to 50 wt.%, and the content of the bone regeneration material is 50 wt.% to 78 wt.%.SELECTED DRAWING: Figure 1

Description

Technical Field

[0001] The present invention relates to a dental shielding film and a method for manufacturing the same, and particularly to a dental shielding film for use in alveolar bone and a method for manufacturing the same.

Background Art

[0002] Before dental implant surgery, guided bone regeneration (GBR), generally known as bone augmentation surgery, is usually performed to solve the problem of alveolar bone atrophy due to long-term tooth loss in the implant area.

[0003] As shown in FIG. 1, in the bone regeneration induction method, first, the gum G is opened, and the bone defect is filled with bone powder B to promote bone growth on the tooth ridge R. In order to prevent soft tissues such as the gum G and oral mucosa from occupying the bone growth space during cell proliferation, the bone powder B is covered with a shielding film F to barrier the alveolar bone and the soft tissue, and finally the gum G is sutured. In this way, the purpose of growing bone cells in a specific space and reconstructing the tooth ridge R can be achieved.

[0004] Currently, the shielding film commonly used in the industry is made of collagen (hereinafter, collagen film). The physical properties of collagen are weak, and it is easily torn after implant surgery, leading to the detachment of artificial bone. In addition, the collagen film has no plasticity. In order to completely cover the wound, it is necessary for the doctor to fix the shape of the collagen film with sutures or other methods. Therefore, the collagen film has problems of poor physical properties and poor usability.

[0005] Therefore, how to improve the physical properties of the conventional barrier film and enhance its usability to overcome the above-mentioned drawbacks has become one of the important issues to be solved in this industry.

Summary of the Invention

Problems to be Solved by the Invention

[0006] The technical problem to be solved by the present invention is to provide a dental shielding film and a manufacturing method thereof for the deficiencies of the prior art.

Means for Solving the Problem

[0007] In order to solve the above technical problem, one technical means adopted by the present invention is to provide a dental shielding film including a porous layer and a hydrophilic layer. The porous layer includes a porous structure formed of a biodegradable polymer and a bone regeneration material attached to the porous structure. Taking the total weight of the porous layer as 100% by weight, the content of the porous structure is 22% to 50% by weight, and the content of the bone regeneration material is 50% to 78% by weight.

[0008] In one embodiment of the present invention, the thickness of the dental shielding film is 100 μm to 300 μm.

[0009] In one embodiment of the present invention, the porosity of the porous layer is 10% to 30%.

[0010] In one embodiment of the present invention, the bone regeneration material includes calcium phosphate.

[0011] In one embodiment of the present invention, the size of the bone regeneration material is 10 μm to 30 μm.

[0012] In one embodiment of the present invention, the biodegradable polymer includes 50% or more of polylactic acid based on the total weight of the biodegradable polymer being 100% by weight.

[0013] In one embodiment, the weight average molecular weight of the biodegradable polymer is 100,000 g / mol to 600,000 g / mol.

[0014] In one embodiment of the present invention, the hydrophilic substance includes hyaluronic acid.

[0015] To solve the above technical problems, another technical means adopted by the present invention is to provide a manufacturing method of a dental shielding film. The manufacturing method of the dental shielding film includes preparing a polymer solution, performing an electrospinning process for manufacturing a porous layer using the polymer solution, and immersing the porous layer in a treatment solution to form a hydrophilic layer for covering the porous layer. The polymer solution includes a solvent, a biodegradable polymer, and a bone regeneration material. Taking the solid content in the polymer solution as 100% by weight, the content of the biodegradable polymer is 22% to 50% by weight, and the content of the bone regeneration material is 50% to 78% by weight.

[0016] In one embodiment of the present invention, in the step of preparing the polymer solution, the solvent is selected from the group consisting of acetone, butanone, ethylene glycol, isopropanol, deacetylated chitin, N,N-dimethylformamide, dimethylacetamide, dimethyl sulfoxide, and diethyl ether.

[0017] In one example, in the electrospinning process, the discharge rate of the polymer solution is 5 ml / hour to 10 ml / hour.

[0018] In one embodiment of the present invention, in the step of immersing the porous layer in the treatment solution, the treatment solution contains 10% to 30% by weight of hyaluronic acid.

Advantages of the Invention

[0019] As an advantageous effect of the present invention, the dental shielding film and its manufacturing method according to the present invention improve the physical properties of the dental shielding film by technical features such as "taking the total weight of the porous layer 10 as 100% by weight, the content of the porous structure is 22% to 50% by weight, and the content of the bone regeneration material is 50% to 78% by weight", and the dental shielding film can achieve the effect of assisting the growth of bone cells.

Brief Description of the Drawings

[0020]

Figure 1

Figure 2

Figure 3

Figure 4

Embodiments for Carrying Out the Invention

[0021] For a better understanding of the features and technical content of the present invention, please refer to the following detailed description of the present invention and the accompanying drawings. However, the provided accompanying drawings are for reference and explanation only, and are not intended to limit the scope of the claims of the present invention.

[0022] Hereinafter, the "dental shielding film and its manufacturing method" will be described according to a specific embodiment. Those skilled in the art can understand the advantages and effects of the present invention based on the content disclosed in this specification. The present invention can be implemented or applied according to other different specific embodiments, and for each detail in this specification, various modifications and changes can be made based on different viewpoints and applications without departing from the concept of the present invention. Also, as explained in advance, the accompanying drawings of the present invention are simple schematic explanations and are not drawn based on the actual size. The technical content of the present invention will be described in more detail based on the following embodiments, but the disclosed content does not limit the protection scope of the present invention. Also, the term "or" used in this specification may include any one or a combination of multiple items listed in relation according to the actual situation.

[0023] The dental shielding film according to the present invention can be applied to the bone regeneration induction method and is used as a shielding film for bone powder and soft tissue. Since the dental shielding film has good physical properties and flexibility, it can improve the problem that the shielding film is easily torn in conventional implant treatments, and the shape of the dental shielding film can be deformed to fit the affected part. Furthermore, the dental shielding film of the present invention contains a component that promotes the regeneration of alveolar bone cells and, in addition to its function as a shielding film, is used as a substitute for some bone powder.

[0024] [First Embodiment] As shown in FIG. 1, the dental shielding film according to the present invention includes a porous layer 10 and a hydrophilic layer 20 that covers the porous layer 10.

[0025] The porous layer 10 is the main structure of the dental shielding film. By effectively blocking epithelial cells and bone cells, it is possible to avoid the space where bone cells can grow being occupied by the proliferation of epithelial cells. Since the porous layer 10 has good physical properties and flexibility, the overall physical properties of the dental shielding film can be improved.

[0026] From the perspective of ease of use and the mechanical strength of the dental shielding film, the thickness of the porous layer 10 is 100 μm to 300 μm, for example, 125 μm, 150 μm, 175 μm, 200 μm, 225 μm, 250 μm, or 275 μm.

[0027] The porous layer 10 includes a porous structure 11 and a bone regeneration material 12 attached to the porous structure 11.

[0028] The porous structure 11 is formed by winding a plurality of polymer fibers. In the winding process, the polymer fibers cannot completely overlap, and pores are formed between the plurality of polymer fibers, so that the porous structure 11 having pores is formed.

[0029] The pores of the porous structure 11 can allow blood or nutrients to pass through, but the number of pores in the porous structure 11 should not be too many or too few. If there are too many pores, it will affect the structural strength of the dental barrier membrane, making it unsuitable for use by doctors during surgery. Furthermore, soft tissues such as gums and oral mucosa may penetrate the dental barrier membrane and occupy the growth space of bone cells. On the other hand, if there are too few pores, it will be difficult for blood and nutrients to pass through.

[0030] Specifically, the porosity of the porous layer 10 is 10% - 30%, preferably 15% - 25%. For example, the porosity of the porous layer 10 may be 12.5%, 15%, 17.5%, 20%, 22.5%, 25% or 27.5%.

[0031] The porous structure 11 is formed of a biodegradable polymer. For example, the biodegradable polymer may be selected from the group consisting of polylactic acid (PLA), polycaprolactone (PCL), polyhydroxyalkanoate (PHA), and polyglycolic acid (PGA). From the perspective of biocompatibility, the biodegradable polymer is preferably polylactic acid (PLA). In one embodiment, the biodegradable polymer is a mixture of polylactic acid and other biodegradable polymers.

[0032] Since the porous structure 11 plays a role in supporting the entire dental barrier membrane, the biodegradable polymer needs to have a certain mechanical strength. In one embodiment, the molecular weight of the biodegradable polymer may be 100,000 g / mol - 600,000 g / mol, preferably 150,000 g / mol - 350,000 g / mol. For example, it may be 200,000 g / mol, 250,000 g / mol or 300,000 g / mol.

[0033] The bone regeneration material 12 is used as an alternative to some bone powder to assist the growth of bone cells. Therefore, the dental barrier membrane according to the present invention can serve the roles of both the barrier membrane and the bone powder. Specifically, in addition to adhering to the porous structure 11, the bone regeneration material 12 can also be attached to the pores of the porous structure 11. The scanning electron microscope image of the dental barrier membrane according to the present invention is as shown in FIG. 2.

[0034] During the use process, the bone regeneration material 12 is gradually released from the dental barrier membrane and can play the role of promoting the growth of bone cells. Therefore, the relative relationship between the porosity of the porous structure 11 and the size of the bone regeneration material 12 is important. The porosity of the porous structure 11 and the size of the bone regeneration material 12 affect both the loading amount of the bone regeneration material 12 in the dental barrier membrane and the release rate of the bone regeneration material 12.

[0035] In one example, the bone regeneration material 12 contains calcium phosphate (Ca3(PO4)2). Specifically, the bone regeneration material 12 is osteoconductive calcium phosphate (β-tricalcium phosphate, β-TCP) for promoting the growth of bone cells.

[0036] The bone regeneration material 12 may exist in a particulate form. In that case, the average particle diameter (D50) of the bone regeneration material 12 is 10 μm to 30 μm. If it is within this range of the average particle diameter, the bone regeneration material 12 can be just attached to the porous structure 11 and is advantageous for the growth of bone cells. If the average particle diameter is too large, it is disadvantageous for cell use. If the average particle diameter is too small, it is disadvantageous for loading on the porous structure 11. Therefore, the average particle diameter of the bone regeneration material 12 may be 12 μm, 14 μm, 16 μm, 18 μm, 20 μm, 22 μm, 24 μm, 26 μm or 28 μm.

[0037] In the present invention, the weight ratio of the bone regeneration material 12 in the porous layer 10 exceeds 50% by weight. The bone regeneration material 12 contained in a high ratio is used as an alternative to some bone powder. Also, the bone regeneration material 12 can play the role of improving the mechanical strength of the dental barrier membrane.

[0038] Specifically, taking the total weight of the porous layer 10 as 100% by weight, the content of the porous structure 11 is 22% to 50% by weight, and the content of the bone regeneration material 12 is 50% to 78% by weight.

[0039] It should be noted that it is not always the case that the higher the content of the bone regeneration material 12, the better. If the content of the bone regeneration material 12 is too high, the growth of bone cells will not be as good as expected. An experiment explaining the influence of different contents of the bone regeneration material 12 on the growth state of bone cells will be described later.

[0040] In other embodiments, the content of the porous structure 11 may be 25% by weight, 30% by weight, 35% by weight, 40% by weight, or 45% by weight. The content of the bone regeneration material 12 may be 55% by weight, 60% by weight, 65% by weight, 70% by weight, or 75% by weight.

[0041] The hydrophilic layer 20 covers the porous layer 10. More specifically, the hydrophilic layer 20 adheres to the surfaces of the porous structure 11 and the bone regeneration material 12 so as to improve the hydrophilicity of the dental barrier membrane. By installing the hydrophilic layer 20, the usability of the dental barrier membrane can be improved. Since the dental barrier membrane has better fit, it adheres to the alveolar bone and bone powder, and promotes the passage of blood and nutrients.

[0042] Since the hydrophilic layer 20 completely covers the porous layer 10, a part of the hydrophilic layer 20 is installed inside the porous layer 10 and filled into some pores in the porous structure 11 so as to promote the passage of hydrophilic substances or nutrients.

[0043] The hydrophilic layer 20 is formed of a hydrophilic substance. Preferably, the hydrophilic substance is a substance that the human body does not reject. The hydrophilic substance is selected from the group consisting of hyaluronic acid or its derivatives, and water-soluble vitamins (for example, vitamin C and vitamin B group), and preferably, it is hyaluronic acid. The dental barrier membrane according to the present invention can absorb water in a shorter time and reach a softened state with plasticity.

[0044] Thus, the outer surface of the dental masking film has a water contact angle of less than 80°, thereby significantly reducing the soaking time before use and, after the dental masking film is completely wetted, having better plasticity and coating fitness. In the present invention, the contact angle between the outer surface of the dental masking film and water is less than 60°, preferably less than 30°, and most preferably less than 10°.

[0045] However, in a situation where the effects of the invention are not significantly impaired, as one embodiment, hydrophilization treatment can also be performed using a substance containing other hydrophilic groups. For example, substances containing a hydroxyl group, a carboxyl group, a sulfonic acid group, an ether group, an epoxy group, an amino group, etc. can be mentioned.

[0046] As supplementary explanation, when the hydrophilic substance is hyaluronic acid, the molecular weight of hyaluronic acid is not particularly limited, but it is preferably 10,000 to 1,000,000, and more preferably 10,000 to 700,000. When the molecular weight of hyaluronic acid is less than 10,000, it is disadvantageous for binding hyaluronic acid to the living porous layer 10. When the molecular weight of hyaluronic acid exceeds 1,000,000, it is disadvantageous for hyaluronic acid to penetrate into the porous layer 10.

[0047] Since the hydrophilic layer 20 covers the porous layer 10 and the thickness of the hydrophilic layer 20 itself is extremely thin, the thickness of the dental masking film is 100 μm to 300 μm, which is almost the same as the thickness of the porous layer 10. For example, the thickness of the dental masking film may be 125 μm, 150 μm, 175 μm, 200 μm, 225 μm, 250 μm or 275 μm.

[0048] The tensile strength of the dental masking film according to the present invention under the conditions of 25°C and an absolute humidity of 50% is 0.3 MPa to 5 MPa. Also, the adhesion strength of the dental masking film according to the present invention measured based on ASTM D3121-2006 is 0.3 N to 0.7 N.

[0049] In this specification, the features of the dental barrier membrane according to the present invention will be described by taking guided bone regeneration as an example. However, the dental barrier membrane according to the present invention is used in other human surgeries.

[0050] [Second Embodiment] As shown in FIG. 3, the second embodiment of the present invention provides a method for manufacturing a dental barrier membrane capable of manufacturing the dental barrier membrane of the first embodiment. The method for manufacturing the dental barrier membrane of the present invention includes a step S100 of preparing a polymer solution, a step S102 of manufacturing a porous layer using the polymer solution, and a step S104 of forming a hydrophilic layer on the surface of the porous layer. Hereinafter, specific implementation methods of each step will be described with reference to FIG. 1.

[0051] In step S100, the polymer solution contains a bone regeneration material, a biodegradable polymer, and a solvent.

[0052] The solid content in the polymer solution can be adjusted according to the manufacturing method of step S102. For example, the porous layer may be manufactured by non-woven spinning, freeze-drying, or electrospinning. In the second embodiment, electrospinning will be described as an example. Also, depending on the operation of electrospinning, with the total weight of the polymer solution being 100% by weight, the solid content in the polymer solution is 1% to 50% by weight, and the solvent content is 50% to 99% by weight.

[0053] The solid content in the polymer solution includes a biodegradable polymer and a bone regeneration material. In the present invention, with the total weight of the porous layer 10 being 100% by weight, the content of the porous structure 11 is 22% to 50% by weight, and the content of the bone regeneration material 12 is 50% to 78% by weight.

[0054] In actual application, the solvent is selected from the group consisting of acetone, butanone, ethylene glycol, isopropanol, deacetylated chitin (DAC), N,N-dimethylformamide (DMF), dimethylacetamide (DMAC), dimethyl sulfoxide (DMSO), and diethyl ether. Preferably, it is acetone or a mixture of acetone and dimethylacetamide.

[0055] As raw materials for the biodegradable polymer and the bone regeneration material, calcium phosphate composite particles and polylactic acid may be used. Specifically, the calcium phosphate composite particles contain calcium phosphate and polylactic acid, and the polylactic acid particles contain 100% by weight of polylactic acid. Therefore, the solid content in the polymer solution contains calcium phosphate and polylactic acid.

[0056] Specifically, taking the total weight of the calcium phosphate composite particles as 100% by weight, the content of calcium phosphate is 10% to 90% by weight, but the present invention is not limited thereto. To control the content ratio of the bone regeneration material and the biodegradable polymer, the added weight ratio of polylactic acid to calcium phosphate composite particles (polylactic acid:calcium phosphate composite particles) is 1:0.9 to 1:5.

[0057] In step S102, the porous layer is manufactured by electrospinning using a polymer solution. After electrospinning and drying, the solid content in the polymer solution forms the porous layer 10. Here, a porous structure 11 is formed of polylactic acid, and calcium phosphate adheres to the porous structure 11 or a bone regeneration material 12 is formed to fill the pores of the porous structure 11.

[0058] In the process of electrospinning, the prepared polymer solution is placed in a liquid storage tank, and each of the nozzle and the collector plate is electrically connected to the positive and negative electrodes of a high-voltage power supply. After applying the high-voltage power supply, the polymer solution is ejected from the nozzle. Under the action of an electric field, the polymer solution is cured to form polymer fibers, and the polymer fibers are deposited on the collector plate. By controlling the movement of the nozzle, the polymer fibers can be densely deposited, overlapped or interwoven in a specific direction to form a porous layer 10 with a uniform thickness.

[0059] Next, a drying process is performed to constitute the porous layer 10 according to the present invention by volatilizing the solvent contained in the polymer solution and only retaining the porous structure 11 and the bone regeneration material 12.

[0060] Regarding the parameters in the electrospinning process, the temperature of electrospinning may be 5°C to 95°C, preferably 10°C to 90°C. The voltage intensity of the high-voltage power supply is 10 to 36 kilovolts (kV), preferably 10 to 25 kV. The ejection rate of the electrospinning solution is 5 cc / hour to 10 cc / hour. The collection distance between the nozzle and the collector plate is 15 to 90 cm.

[0061] In step S104, the porous layer 10 is immersed in a treatment solution containing a hydrophilic substance at room temperature. After immersion, the hydrophilic substance adheres to the surface of the porous layer 10 and penetrates into the interior of the porous layer 10, thereby forming a hydrophilic layer 20 covering the surface of the porous layer 10.

[0062] Next, a drying process is performed to constitute the hydrophilic layer 10 according to the present invention by volatilizing the solvent contained in the treatment solution and only retaining the hydrophilic substance adhering to the surfaces of the porous structure 11 and the bone regeneration material 12.

[0063] Based on the total weight of the treatment solution (100 wt%), the content of the hydrophilic substance may be 10 wt% to 30 wt%, preferably 15 wt%, 20 wt%, 25 wt% or 30 wt%. In one exemplary embodiment, the hydrophilic substance is hyaluronic acid, and the treatment solution contains 95% ethanol, water, and hyaluronic acid. Here, the weight ratio of 95% ethanol to water (95% ethanol: water) is 1:1 to 3:2.

[0064] [Experimental data] In order to prove the effect of promoting the growth of osteocytes, in the present invention, dental barrier membranes with different contents of bone regeneration materials (calcium phosphate) were manufactured, and the osteocyte differentiation of the dental barrier membranes was measured. The measurement results are as shown in Table 1 and Table 2. The mechanical strength of the dental barrier membrane was measured, and the results are as shown in Table 3.

[0065] In Table 1, Table 2 and Table 3, the difference between each example and the comparative example is the content of the bone regeneration material in the porous layer.

[0066] Regarding Table 1 and Table 2, in the measurement test of osteocyte differentiation, the dental barrier membrane was cut into a square with a side length of 1 cm and placed in a 24-well plate. 60 μL (λ) of rat bone marrow mesenchymal stem cells (BMSC) containing 3×10 4 cells were planted on the cut dental barrier membrane and placed in a cell culture incubator at 37 °C with a carbon dioxide concentration of 5% for 1 hour to attach the rat bone marrow mesenchymal stem cells to the cut dental barrier membrane.

[0067] Once the rat bone marrow stem cells were completely attached, 500 μL of medium was added to a 24-well plate and placed in a cell culture incubator at 37 °C with a carbon dioxide concentration of 5% overnight. Then, the medium in the 24-well plate was removed, the osteogenic induction medium was added, and it was placed in a cell culture incubator at 37 °C with a carbon dioxide concentration of 5%. The cell culture incubator was replaced every 2 - 3 days and cultured for a total of 14 days or 12 days.

[0068] After culturing for 14 days or 12 days, the medium contained in the 24-well plate was removed, the cells were washed with phosphate buffered saline (PBS), fixed with formalin, and then the cells were washed with phosphate buffered saline (PBS). Finally, 500 μL of p-nitrophenylphosphate (p-NPP) with a concentration of 5 mg / mL was added to the 24-well plate, left at room temperature in the dark for 45 minutes, then 100 μL was taken as a sample, and the absorbance value at a wavelength of 405 nm was measured.

[0069] In Table 3, the tensile stress (dry) was the tensile stress measured when the dental masking film was at a temperature of 25 °C and an absolute humidity of 50%. The tensile stress (wet) was the tensile stress after immersing the dental masking film in physiological saline at 37 °C for 30 minutes.

[0070]

Table 1

[0071] [Table 2] TIFF2025100271000003.tif26145

[0072] [Table 3] TIFF2025100271000004.tif47147

[0073] According to the results in Table 1, after adding the bone regeneration material to the dental masking film, it can promote the growth of bone cells, and the higher the concentration of the bone regeneration material, the better the effect of promoting the growth of bone cells.

[0074] According to the results in Table 2, when the concentration of the bone regeneration material was too high, it tended to inhibit the growth of bone cells. Therefore, in the porous layer, the content of the bone regeneration material is preferably 50% to 78% by weight.

[0075] According to the results in Table 3, adding a bone regeneration material to the dental barrier membrane can not only promote the growth of bone cells, but also improve the mechanical strength of the dental barrier membrane. Even if the thickness is thin, the dental barrier membrane in the dry state still has good tensile stress.

[0076] [Advantageous effects according to the embodiment] As an advantageous effect of the present invention, the dental barrier membrane and its manufacturing method according to the present invention improve the physical properties of the dental barrier membrane by technical features such as "assuming that the total weight of the porous layer 10 is 100% by weight, the content of the porous structure 11 is 22% to 50% by weight, and the content of the bone regeneration material 12 is 50% to 78% by weight", and the dental barrier membrane can achieve the effect of assisting the growth of bone cells.

[0077] Furthermore, the dental barrier membrane according to the present invention contains a bone regeneration material in a high content, not only helps the growth of cells, but also improves the mechanical strength of the dental barrier membrane and is used as an alternative to some bone powder. Therefore, when in use, the dental barrier membrane can be directly contacted with the bone defect site or bone powder of the alveolar bone.

[0078] Furthermore, the dental barrier membrane according to the present invention can absorb water within a short time (within 5 minutes) and reach a softened state with plasticity by installing a hydrophilic layer, and can fit different three-dimensional shapes. In addition, the dental barrier membrane according to the present invention can firmly adhere to the affected area (such as bone defect), and by providing a sufficient growth space for the affected area, it can assist in the repair, regeneration, and integration of the affected area.

[0079] The content disclosed above is only a preferred feasible embodiment of the present invention, and the scope of the claims of the present invention is not limited thereto. Therefore, all equivalent technical changes made by using the content of the specification and drawings of the present invention are included in the scope of the claims of the present invention.

Description of Reference Numerals

[0080] 10 Porous layer 11 Porous structure 12 Bone regeneration material 20 Hydrophilic layer G Gum B Bone meal R Gum F Masking film

Claims

1. A dental barrier membrane comprising a porous layer and a hydrophilic layer covering the porous layer, wherein the porous layer comprises a porous structure formed of a biodegradable polymer and a bone regeneration material attached to the porous structure, with the content of the porous structure being 22 wt% to 50 wt% and the content of the bone regeneration material being 50 wt% to 78 wt%, based on 100 wt% of the total weight of the porous layer, wherein the hydrophilic layer is formed of a hydrophilic substance, and the dental barrier membrane is characterized by contacting alveolar bone or bone powder.

2. The dental barrier membrane according to claim 1, wherein the thickness of the dental barrier membrane is 100 μm to 300 μm.

3. The dental barrier membrane according to claim 1, wherein the porosity of the porous layer is 10% to 30%.

4. The dental barrier membrane according to claim 1, wherein the bone regeneration material comprises calcium phosphate.

5. The dental barrier membrane according to claim 1, wherein the size of the bone regeneration material is 10 μm to 30 μm.

6. The dental barrier membrane according to claim 1, wherein the biodegradable polymer comprises 50 wt% or more of polylactic acid, based on 100 wt% of the total weight of the biodegradable polymer.

7. The dental barrier membrane according to claim 1, wherein the weight average molecular weight of the biodegradable polymer is 100,000 g / mol to 600,000 g / mol.

8. The dental barrier membrane according to claim 1, wherein the hydrophilic substance comprises hyaluronic acid.

9. Preparing a polymer solution comprising a solvent, a biodegradable polymer, and a bone regeneration material; Performing an electrospinning process for manufacturing a porous layer using the polymer solution; Immersing the porous layer in a treatment solution to form a hydrophilic layer covering the porous layer, wherein, based on 100 wt% of the solid content in the polymer solution, the content of the biodegradable polymer is 22 wt% to 50 wt% and the content of the bone regeneration material is 50 wt% to 78 wt%, which is a method for manufacturing a dental barrier membrane.

10. In the step of preparing the polymer solution, the solvent is selected from the group consisting of acetone, butanone, ethylene glycol, isopropanol, deacetylated chitin, N,N-dimethylformamide, dimethylacetamide, dimethyl sulfoxide, and diethyl ether. The method for manufacturing a dental barrier membrane according to claim 9.

11. In the process of the electrospinning, the discharge rate of the polymer solution is 5 ml / hour to 10 ml / hour. The method for manufacturing a dental shielding film according to claim 9.

12. In the step of immersing the porous layer in the treatment solution, the treatment solution contains 10% by weight to 30% by weight of hyaluronic acid. The method for manufacturing a dental shielding film according to claim 9.

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