KR101242672B1 - Scaffold and fabricating method of the same - Google Patents

Abstract

The present invention relates to an artificial support in the form of a mesh and a method of manufacturing the same. The artificial support according to the embodiment of the present invention extends along a first direction and is disposed at regular intervals along a second direction crossing the first direction and a plurality of first fibers and the second on the first fiber. And a plurality of second fibers extending along the direction and disposed at regular intervals along the first direction.

Description

Artificial support and manufacturing method thereof {SCAFFOLD AND FABRICATING METHOD OF THE SAME}

The present invention relates to an artificial support and a method of manufacturing the same, and more particularly, to an artificial support in the form of a mesh (mesh) and a method of manufacturing the same.

Tissue engineering is a technology field in which a small amount of cells collected from a patient's tissue is cultured in vitro and then differentiated into 3D tissue and regenerated into tissues and organs in order to regenerate damaged organs. Recently, research has been conducted in various approaches to restore the function of various tissues and organs of the damaged body.

Tissue engineering requires artificial scaffolds that can recognize cells in a three-dimensional environment for three-dimensional cultures of tissues. These scaffolds are suitable for extracellular substrates that allow cells to induce smooth deposition, proliferation, and differentiation. must have a cellular matrix (ECM) structure. In addition, it must have a porous structure interconnected to the appropriate size for cell migration, metabolism promotion, and vascular infiltration for nutrient supply, and should be maintained at a strength sufficient to maintain its shape during tissue regeneration.

On the other hand, a large number of anatomically shaped tissues or organs are present in the human body, and recently, a mesh-type artificial support for replacing or regenerating damaged tissues, particularly thin bone tissues, is required. . However, it is difficult to control the size of the pores in manufacturing the artificial scaffold in the form of a mesh, the mechanical strength is very weak, there is a problem in the difficulty in tissue regeneration.

The present invention is to solve the above problems of the background, it is an object to provide an artificial support in the form of a mesh excellent in biocompatibility and mechanical strength.

It is also an object of the present invention to provide a method for preparing an artificial support that can control the size of pores and does not use toxic organic solvents.

Artificial support according to an embodiment of the present invention is a plurality of first fibers and a plurality of first fibers arranged in a predetermined interval along a second direction extending in a first direction and intersecting the first direction said And a plurality of second fibers extending along a second direction and disposed at predetermined intervals along the first direction. The plurality of first fibers and the plurality of second fibers each comprise a biopolymer.

The width measured along the second direction of each of the plurality of first fibers may be 50 μm to 300 μm, and the width measured along the first direction of each of the plurality of second fibers is 50 μm to 300 μm.

The thickness measured along the third direction crossing the first direction and the second direction of each of the plurality of first fibers and the plurality of second fibers may be 50 μm to 100 μm.

The spacing between the adjacent plurality of first fibers may be 500 μm to 300 μm, and the spacing between the adjacent plurality of second fibers may be 500 μm to 300 μm.

The biopolymer may be polylactic acid (PLA), polyglycolic acid (Poly-glycolic acid, PGA), polycaprolactone (Polycaprolactone, PCL), polylactic-co-glycolic acid, PLGA) or mixtures thereof.

The plurality of first fibers and the plurality of second fibers may further include hydroxyapatite or tri-calcium phosphate.

In a method of manufacturing an artificial support according to an embodiment of the present invention, a biopolymer is injected into a syringe, and the biopolymer injected into the syringe is injected to uniform a plurality of first fibers extending along a first direction. Forming a plurality of second fibers extending along a second direction intersecting the first direction by spraying the biopolymer injected into the syringe onto the plurality of first fibers at regular intervals; It includes.

The width measured along the second direction of each of the plurality of first fibers may be 50 μm to 300 μm, and the width measured along the first direction of each of the plurality of second fibers is 50. It may be formed to a micrometer to 300 ㎛.

The thickness measured in the third direction crossing the first direction and the second direction of each of the plurality of first fibers and the plurality of second fibers may be 50 μm to 100 μm.

The spacing between the adjacent plurality of first fibers may be formed to 50 μm to 300 μm, and the spacing between the adjacent plurality of second fibers may be formed to 50 μm to 300 μm.

The biopolymer may be polylactic acid, polyglycolic acid, polycaprolactone, polylacticcoglycolic acid, or mixtures thereof.

The syringe may be injected with hydroxyapatite or tricalcium phosphate together with a biopolymer.

According to an embodiment of the present invention, the biocompatibility of the artificial support in the form of a mesh is excellent, and the mechanical strength and flexibility of the artificial support are excellent.

In addition, in the preparation of the artificial scaffold, no toxic organic solvent is used, so that there is no cytotoxicity, thereby improving cell proliferation.

Figure 1a is a photograph showing an artificial support according to an embodiment of the present invention.
1B is an enlarged photograph of the artificial support of FIG. 1.
2 is a view schematically showing the configuration of a multi-axis lamination system for manufacturing an artificial support according to an embodiment of the present invention.
3A and 3B are views sequentially showing a process of manufacturing an artificial support according to an embodiment of the present invention.
4 is a graph showing the evaluation of cell proliferation in the artificial support according to Experimental Example 1 of the present invention.
5a and 5b is a photograph showing an enlarged view of the cells after proliferating the artificial support in Experimental Example 1 of the present invention.
6 is a graph showing the tensile test results according to the material of the artificial support in Experimental Example 2 of the present invention.
7A and 7B are photographs showing surface roughnesses according to materials of artificial supports in Experimental Example 3 of the present invention, respectively.
8 to 10 are graphs showing ALP, Runx2 and calcium contents, respectively, according to the material of the artificial support in Experimental Example 3 of the present invention.

Hereinafter, exemplary embodiments of the present invention will be described in detail with reference to the accompanying drawings so that those skilled in the art may easily implement the present invention. On the other hand, the size of each component in the drawings are arbitrarily shown for convenience of description, the present invention is not necessarily limited to the illustrated in the drawings.

1A is a photograph showing an artificial support according to an embodiment of the present invention, and FIG. 1B is an enlarged photograph of the artificial support of FIG. 1.

1A and 1B, the artificial support according to the present embodiment has a mesh shape including a plurality of voids. Specifically, the artificial support according to the present embodiment includes a plurality of first fibers extending along the transverse direction (hereinafter, referred to as 'first direction') of FIGS. 1A and 1B and the longitudinal direction of the FIGS. 1A and 1B. , A second plurality of fibers extending along the second direction. The plurality of first fibers are disposed at regular intervals along the second direction, and the plurality of second fibers are formed on the plurality of first fibers and disposed at regular intervals along the first direction.

Currently, artificial supports made of titanium are widely used because of their excellent mechanical strength and excellent cell compatibility. However, since the artificial support made of titanium is generally piled into fibrous tissue when embedded in the body, when used in bone tissue, it may cause a problem in binding to surrounding bone. In addition, there is a disadvantage that the second operation must be performed to remove it after the meal in the body.

Accordingly, the present embodiment uses a biopolymer having excellent biocompatibility and excellent biodegradability in preparing an artificial support.

The first and second fibers of the artificial support are polylactic acid (PLA), polyglycolic acid (PGA), polycaprolactone (PCL), and polylacticcoglycolic acid, respectively. (Poly-lactic-co-glycolic acid, PLGA) or a mixture of these may be made of a biopolymer.

Meanwhile, the biopolymer may further include bone component ceramics such as hydroxyapatite (HA) and tri-calcium phosphate (TCP). In the case of forming the artificial support by mixing the bone constituent ceramic with the biopolymer, the mechanical strength of the artificial support may be improved, and the surface roughness of the artificial support may be increased to increase the cell adhesion efficiency. It will be described later.

As described above, the mesh support of the present embodiment made of a biopolymer has excellent biocompatibility compared to titanium. In addition, since fibers of constant thickness are arranged in a directional manner, they have excellent mechanical strength, and have a sufficient elastic force and flexibility because the line length is longer than the line width.

2 is a view schematically showing the configuration of a multi-axis lamination system for manufacturing an artificial support according to an embodiment of the present invention, Figures 3a and 3b is a process for manufacturing an artificial support in accordance with an embodiment of the present invention With the drawings shown in sequence, the following describes a method for manufacturing an artificial support according to an embodiment of the present invention with reference to these.

In this embodiment, a multi-axis lamination system 100 is used to manufacture an artificial support. The free form manufacturing method is a technology for producing a desired three-dimensional shape by converting free shape information obtained from CAD data into a G code based on a rapid prototype technology and further stacking materials. As a multi-head deposition system (100) is a system for manufacturing an artificial scaffold for three-dimensional tissue engineering by applying such a solid free-form fabrication method.

The multi-axis lamination system 100 is a system capable of controlling position, temperature, and pressure independently of each other, and manufactures a three-dimensional artificial support by melting the material by hot melting and then spraying it by pneumatically.

Referring to FIG. 2, the multiaxial lamination system 100 includes a lamination head 150 that ejects an artificial support material to a predetermined width. The stacking head 150 includes a syringe 151 for introducing and storing the material, a nozzle 153 for spraying the material introduced into the syringe 151, and a heater 155 for appropriately maintaining the temperature of the material. In this embodiment, the artificial support 200 is formed by injecting a biopolymer into the syringe 151 of the stacking head 150 and spraying through the respective nozzles 153. Meanwhile, in the present embodiment, bone component ceramics may be injected together when the biopolymer is injected.

In order to move the stacking head 150 not only in the plane coordinates composed of the x-axis and the y-axis, but also in the z-axis in the vertical direction, the multi-axis stacking system 100 moves the x-axis displacement to move the stacking head 150 in the x-axis direction. The y-axis displacement moving part 130 for moving the moving part 120, the lamination head 150 in the y-axis direction, and the z-axis displacement moving part 140 for moving the laminating head 150 up and down in the z-axis direction, respectively. Equipped.

The multi-axial lamination system 100 may produce an artificial support 200 having a three-dimensional shape to be shaped by laminating an artificial support material, that is, a biopolymer, on a work table 110 in a matrix manner.

The shape of the artificial support 200 to be manufactured is input to the integrated controller 10 through the data model 20. In this case, in order to input the data model 20 of the artificial support 200 as 3D CAD data, each coordinate value of the artificial support 200 having a three-dimensional shape is preferably set.

The integrated controller 10 controls the operation of the multi-axis stacking system 100 in accordance with the three-dimensional shape data model of the artificial support 200. As a result, the multi-axial stacking system 100 behaves at the coordinates of the artificial support material, i.e., while setting the stacking head 150 to coordinate values to be set according to the three-dimensional shape data of the artificial support 200 transmitted from the integrated control device 10. The biopolymer or a mixed material of the biopolymer and the bone component ceramic is alternately sprayed.

The temperature controller 30 is connected to the stacking head 150 of the multiaxial stacking system 100 to control the temperature of the syringe 151 of the stacking head 150. Specifically, the temperature controller 30 is connected to and controlled by the heater 155 attached to the stacking head 150, thereby controlling the biopolymer or the biopolymer and the bone constituent ceramic in the syringe 151 of the stacking head 150. The mixed material is heated or maintained at a predetermined temperature, thereby causing the biomaterial or the mixed material of the biopolymer and the bone constituent ceramic to be changed or maintained in a state suitable for being sprayed, thereby opening the syringe 151 of the stacking head 150. It may be sprayed through a predetermined thickness through. On the other hand, the temperature controller 30 is connected to the integrated control device 10 as well as the multi-axis stacking system 100, it can operate in conjunction with the behavior of the stacking head 150.

The pressure controller 40 is connected to the stacking head 150 of the multiaxial stacking system 100 to control the pressure delivered to the stacking head 150. That is, the pressure controller 40 is a means for controlling the pressure transmitted to the pressure transmitter of the stacking head 150, and the biopolymer or the biopolymer and the bone constituent ceramic ejected through the nozzle 153 of the stacking head 150. It is possible to vary the spraying speed of the mixed material.

The pressure controller 40 according to the present embodiment transfers the pressure to the pressure transmitter of the stacking head 150 by a pneumatic method. To this end, the three-dimensional artificial scaffold manufacturing system has a pneumatic device 50 that exerts a direct pressure on the pressure transmitter of the stacking head 150, which is operated by a pressure controller 40. At this time, the air compressor 50 may be independently connected to each axis of the multi-axis stacking system 100 to adjust the air pressure in various ways for each axis.

Hereinafter, a method of manufacturing an artificial support using the multiaxial lamination system 100 will be described in detail.

First, the artificial support is designed according to the desired shape information using a CAD program. The shape information of the artificial support 200 designed as described above transfers data from the data model 20 to the integrated controller 10. The integrated controller 10 controls the temperature controller 30, the pressure controller 40 and the displacement moving parts 120, 130, 140 in each axial direction based on the transmitted shape information.

After injecting the biopolymer or a mixed material of the biopolymer and the bone constituent ceramic into the syringe 151 of the stacking head 150, the temperature controller 30 and the heater 155 are maintained so that they are suitable for spraying. The temperature of the syringe 151 is adjusted. At this time, as described above, as the biopolymer, polylactic acid, polyglycolic acid, polycaprolactone, polylacticcoglycolic acid, or a mixture thereof may be used, and a bone composition which may be injected together with the biopolymer. As the component ceramic, hydroxyapatite or tricalcium phosphate can be used.

Thereafter, the stacking head 150 is controlled by the displacement moving parts 120, 130, and 140 and the pressure controller 40, and the biopolymer on the work table 110 through the nozzle 153 of the stacking head 150. By spraying the artificial support 200 is formed.

Referring to FIG. 3A, a plurality of first fibers 210 are formed by spraying a plurality of biopolymers or a mixture of biopolymers and bone constituent ceramics melted in a syringe a plurality of times along a first direction at predetermined intervals. In this case, the width W of each of the first fibers 210 may be formed to about 50 μm to about 300 μm, and the thickness T may be formed to about 50 μm to 100 μm. In addition, the distance D between the adjacent first fibers 210 may be formed to about 50㎛ to 300㎛.

Referring to FIG. 3B, a plurality of biopolymers or mixed materials of biopolymers and bone constituent ceramics are sprayed a plurality of times along a second direction crossing the first direction at predetermined intervals on the plurality of first fibers 210. To form a second fiber 220. At this time, the range of the width and thickness of each of the second fibers 220 and the range of the distance between the adjacent second fibers 220 may be formed in the same manner as in the case of the first fiber (210).

As described above, the artificial support 200 in which the plurality of first fibers 210 and the plurality of second fibers 220 are formed in a lattice shape with a plurality of first fibers 210 and 220 may be formed using the multiaxial lamination system 100.

According to the method for preparing the artificial support, a cell-friendly artificial support can be produced by using no toxic organic solvents in the manufacturing process.

Meanwhile, in the case of using a mixture of biopolymers having different cellular, chemical, and physical properties, in order to fabricate an artificial support by applying a thermal melting method due to different glass transition temperatures and melting temperatures, Processing conditions should be adopted.

Thus, in this embodiment, by using the multi-axis lamination system 100, it is possible to adjust the individual temperature and pneumatic pressure to easily reflect the manufacturing conditions according to the material.

In addition, it is possible to easily adjust the width of the fibers (210, 220) constituting the artificial support 200 by adjusting the temperature, pneumatic and nozzle feed rate, and the size and size of the pores in a CAD / CAM (CAD / CAM) method Since the thickness of the artificial support can be easily adjusted, it is possible to easily prepare a suitable artificial support according to various tissues in the body. In addition, by applying a CAD / CAM (CAD / CAM) method it is possible to repeatedly produce the artificial support of the same shape.

Hereinafter, the present invention will be described through specific examples and experimental examples.

Example  One

In this embodiment, the artificial scaffold is designed to have width, length and thickness of 3 cm, 3 cm and 0.2 mm, respectively. The width of each fiber of the artificial support is designed to 150 μm, and the pore size of the artificial support in the form of a mesh is designed to be 250 μm. The artificial support is designed to have a thickness of 200 μm, which is adjustable by the number of layers to be laminated. In this embodiment, a layer having a thickness of 100 μm is laminated twice to be 200 μm.

The CAD shape information of the designed artificial support is converted into G code information.

Meanwhile, in the present embodiment, polylactic glycolic acid (PLGA) and polycaprolactone (PCL) obtained by mixing polylactic acid (PLA) and polyglycolic acid (PGA) at 85:15 as a biopolymer for forming fibers of an artificial support. Is used in a 1: 1 mixture.

This biopolymer material is injected into a syringe mounted in a multiaxial lamination system and heated to a temperature of 120 ° C to 130 ° C. At this time, the temperature can be controlled as desired up to about 150 ℃ through the temperature controller.

Since the molten biopolymer is high in viscosity but flows, it is sprayed into a fiber through a nozzle when high pressure pneumatic pressure is applied. In this embodiment, the biopolymer is injected by applying 650 kPa, that is, about 6 atm pneumatic pressure.

The feed rate of the nozzle is set at about 100 mm / min so that the width of the fiber to be sprayed is 150 m.

The thickness of one layer of the fiber thus produced is 100 μm, and the nozzle is moved by 100 μm in the z-axis direction, and the second layer is rotated by 90 ° onto the first layer and sprayed into the grid. As a result, an artificial support in the form of a mesh having a thickness of 200 μm can be manufactured.

On the other hand, the elasticity and flexibility of the artificial support is an important factor to be considered when fabricating the artificial support. In this embodiment, the thickness of the artificial support is small to 200 μm and the length of the line is sufficiently long as compared with the line width. Flexibility is excellent.

Hereinafter, specific experimental results for evaluating the cell suitability of the artificial support of the mesh form produced by the above embodiment will be described.

Example  2

In this embodiment, polycaprolactone (PCL) was used as the biopolymer, and the size, shape, and the like of the artificial support are formed in the same manner as in Example 1.

Example  3

In this embodiment, polylactic glycolic acid (PLGA) was used as the biopolymer, and the size, shape, and the like of the other artificial support are formed in the same manner as in Example 1.

Example  4

In this embodiment, a material obtained by mixing polycaprolactone (PCL) and polylactic glycolic acid (PLGA) was used as a biopolymer, and tricalcium phosphate (TCP) was mixed at a 20% weight ratio. The size, shape, and the like of the other artificial support are formed in the same manner as in Example 1.

Experimental Example  One

In vitro experiments were performed to verify the cell suitability of the artificial scaffold in mesh form according to Example 1. For the experiment, MC3T3-E1, a pre-osteoblast, and NIH-3T3, a fibroblast, were used, and 2 × 10 ⁵ cells were implanted per artificial scaffold.

A cell counting kit-8 (CCK-8, Dojindo, Japan) was used to evaluate cell proliferation, and proliferation evaluation up to 7 days was performed.

4 is a result of evaluating the cell suitability of the artificial scaffold according to Experimental Example 1 of the present invention, referring to the two kinds of cells proliferate actively in the mesh-shaped artificial scaffold for 7 days through the optical density (optical density) You can check it.

5A and 5B are enlarged pictures of cells after proliferating cells in an artificial support according to Experimental Example 1 of the present invention. Specifically, after the 7-day proliferation experiment, the artificial support was fixed in a 10% formalin solution. It is a photograph observed after the electron microscope.

5A and 5B, it can be seen that the cells evenly cover and secrete extracellular matrix (ECM) on an artificial support in the form of a mesh.

Through this, the mesh-type artificial scaffold according to the present embodiment can verify that there is no cytotoxicity, as well as confirm that the cells have the property to adhere and proliferate.

In particular, it can be inferred that the artificial scaffold of this embodiment is effective in regenerating fibrous tissues such as bone tissue or skin tissue through two kinds of cells, MC3T3-E1 and NIH-3T3.

Experimental Example  2

In this experimental example, the mechanical tensile test of the artificial support of the mesh form produced by each example was performed.

Figure 6 is a graph showing the tensile test results according to the material of the artificial support according to Experimental Example 2 of the present invention, referring to this, in the case of the artificial support of Example 2 using polycaprolactone (PCL) as a biopolymer, the fracture is It can be seen that although the stress occurring is higher than that of the artificial support formed from other materials, the amount of deformation occurring before the fracture occurs is greatest. In addition, it can be seen that the mechanical coefficient corresponding to the slope of the stress rise curve until fracture occurs is the lowest.

Through this, polycaprolactone (PCL) can be said to be a suitable material when a lot of elasticity and flexibility is required.

In the case of the artificial support of Example 3 using the polylactic glycolic acid (PLGA) as a biopolymer, it can be seen that the stress rise curve before breaking occurs is the steepest, that is, the mechanical coefficient is high, and the breaking occurs also the fastest. have.

Accordingly, it can be seen that polylactic glycolic acid (PLGA) has brittleness, and the artificial support formed therefrom is easily broken.

In the case of Example 1 in which polylactic glycolic acid (PLGA) and polycaprolactone (PCL) are mixed with a biopolymer, it can be seen that the mechanical properties of the intermediate ranges of Examples 2 and 3 are shown. In other words, due to the component of polylactic glycolic acid (PLGA), the mechanical coefficient of the polycaprolactone (PCL) is not easily broken due to the component of polylactic glycolic acid (PLGA) exhibits a very large property.

As such, the artificial support in the form of a mesh may be formed using various biopolymers. At this time, the mechanical properties of the artificial support may vary depending on the type of biopolymer used, and the type of biopolymer that forms the artificial support in consideration of the tissue to be used, the purpose of use, and the required mechanical properties. You can decide.

Experimental Example  3

In this Experimental Example, the artificial scaffolds of Examples 1 and 4 were compared, and the effects of changes in surface roughness, cell proliferation and differentiation of the artificial scaffolds when bone ceramics were added were confirmed.

7A and 7B are enlarged photographs of the artificial scaffolds according to Examples 1 and 4, respectively. Referring to these examples, surface roughness of the artificial scaffold increases when the bone component ceramic is mixed with the biopolymer according to Example 4. can confirm. It is advantageous in the cell adhesion on the rough surface than the smooth surface, it can be seen that the cell adhesion efficiency can be improved when the bone constituent ceramic is mixed.

8 to 10 are graphs showing the differentiation effect from the artificial support to bone tissue according to Examples 1 and 4, respectively.

FIG. 8 is a graph showing the expression level of alkaline phosphatase (ALP), which is a protein specifically expressed in bone tissue, in the case of mixing tricalcium phosphate (TCP), a bone constituent ceramic It can be seen that the ratio of alkaline phosphate (ALP) is high.

9 shows the results of real-time PCR at the RNA level, where the ratio of Runx2, a bone tissue specific marker, is high when tricalcium phosphate (TCP) is mixed.

FIG. 10 is a graph showing calcium content as an important clue for bone tissue formation, and it can be seen that the calcium content of the tissue grown on the artificial support mixed with tricalcium phosphate (TCP) is relatively high.

Through this experimental example, it can be inferred that the adhesion, proliferation and differentiation efficiency of cells may be increased when the artificial support is formed by mixing the ceramic component with the bone constituent ceramic in the biopolymer.

As mentioned above, although this invention was demonstrated through the preferable embodiment, this invention is not limited to the above-mentioned embodiment. That is, those skilled in the art to which the present invention pertains can readily understand that various modifications and variations are possible without departing from the concept and scope of the claims set out below.

10: Integrated Control 20: Data Model
30: temperature controller 40: pressure controller
50: pneumatic 100: multi-axis lamination system
110: work table 120: x-axis displacement moving part
130: y-axis displacement moving unit 140: z-axis displacement moving unit
150: lamination head 151: syringe
153: nozzle 155: heater
200: artificial support 210: first fiber
220: second fiber

Claims (12)

A plurality of first fibers extending along a first direction and disposed at predetermined intervals along a second direction crossing the first direction; And
A plurality of second fibers extending in the second direction on the plurality of first fibers and disposed at predetermined intervals along the first direction;
Including,
And the plurality of first fibers and the plurality of second fibers each comprise a biopolymer. The method of claim 1,
The width measured along the second direction of each of the plurality of first fibers is 50 μm to 300 μm,
An artificial scaffold, wherein the width measured along the first direction of each of the plurality of second fibers is between 50 μm and 300 μm. The method of claim 1,
The thickness of each of the plurality of first fibers and the plurality of second fibers measured along a third direction intersecting the first direction and the second direction is 50 μm to 100 μm. The method of claim 1,
The spacing between the adjacent plurality of first fibers is between 500 μm and 300 μm,
The spacing between the adjacent plurality of second fibers is between 500 μm and 300 μm. 5. The method according to any one of claims 1 to 4,
The biopolymer may be polylactic acid (PLA), polyglycolic acid (Poly-glycolic acid, PGA), polycaprolactone (Polycaprolactone, PCL), polylactic-co-glycolic acid, PLGA) or mixtures thereof. The method of claim 5,
And the plurality of first fibers and the plurality of second fibers further comprise hydroxyapatite or tri-calcium phosphate. Injecting the biopolymer into the syringe (syringe),
By spraying the biopolymer injected into the syringe to form a plurality of first fibers extending in a first direction at regular intervals,
The biopolymer injected into the syringe is sprayed onto the plurality of first fibers to form a plurality of second fibers extending along a second direction crossing the first direction at regular intervals, the method of manufacturing an artificial support. . The method of claim 7, wherein
The width measured along the second direction of each of the plurality of first fibers is formed to 50 μm to 300 μm,
The width | variety measured along the said 1st direction of each said 2nd some fiber is 50 micrometers-300 micrometers, The manufacturing method of the artificial support body. The method of claim 7, wherein
The thickness measured along the 3rd direction which cross | intersects the said 1st direction and the said 2nd direction of each of the said 1st some fiber and said some 2nd fiber is 50 micrometers-100 micrometers, The manufacturing method of the artificial support body . The method of claim 7, wherein
The spacing between the adjacent plurality of first fibers is formed to 50㎛ to 300㎛,
The spacing between the adjacent plurality of second fibers is formed 50㎛ to 300㎛, the manufacturing method of the artificial support. The method according to any one of claims 7 to 10,
The biopolymer is polylactic acid, polyglycolic acid, polycaprolactone, polylacticcoglycolic acid, or a mixture thereof. The method of claim 11,
A hydroxyapatite or tricalcium phosphate is injected into the syringe together with a biopolymer, to produce an artificial support.

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