CN214209031U - Biodegradable three-dimensional artificial support - Google Patents

Abstract

The utility model relates to a three-dimensional artificial support of biodegradability, it utilizes and is used for actively realizing the three-dimensional form and the bioabsorbable material of the tissue regeneration of defective part, possesses excellent biocompatibility and mechanical strength from this, and can decompose and absorb or discharge in vivo, its characterized in that, it includes: a plurality of first layer structure lines extending in a 1 st direction and arranged at predetermined intervals in a 2 nd direction intersecting the 1 st direction at a predetermined angle; and a plurality of layer 2 structure lines extending in the 2 nd direction on a first layer formed of the plurality of first layer structure lines and arranged at predetermined intervals along the 1 st direction, wherein the plurality of first layer structure lines and the layer 2 structure lines are formed of a bioabsorbable material and cross at an angle of 30 to 90 degrees, and the first layer and the layer 2 are stacked while being overlapped with each other.

Description

Biodegradable three-dimensional artificial support

Technical Field

The present invention relates to a biodegradable three-dimensional artificial support having a three-dimensional structure for reconstructing congenital or acquired tissue defects.

The present invention relates to a result obtained as part of the industry of technical demonstration of the medical device industry by 3D printing of the ministry of industrial general commercial resources and the korea industry technical prosperity (P0008811, a customized 3D printing of tooth implantation demonstration for the inner surface surgery of both jaws using a biodegradable polymer material).

Background

In general, when bone and soft tissue are damaged by trauma, tumor, deformity, physiological phenomenon, or the like, a graft material is filled into the site to form a tissue.

In general, the most common methods for reconstructing a tissue at a defect site include an autograft method in which a part of a tissue is collected from a vacant part of a patient himself and transplanted, an allograft method in which an allograft tissue is transplanted, and a xenograft method in which a tissue obtained from an animal is processed into a product to be transplanted into the body.

Among them, the best clinical prognosis is known as the autograft method. However, such an autograft method requires a secondary operation on the vacant part, and therefore, the risk of infection and blood loss at the surgical site increases, and there is a limit to obtaining tissue from the vacant part to a degree sufficient for reconstructing the deficient site.

In addition, in the case of the xenograft method, immune rejection reaction, foreign body reaction, and the like may occur after the transplantation, and there is a potential risk of viral infection between the species and the like.

As a measure against such medical problems, there is a demand for a biodegradable implant material which can easily obtain a sufficient amount of tissue, does not have the possibility of infection of diseases, has a performance capable of replacing conventional implants, has high biodegradability, is absorbed in a suitable period at a site to be implanted later, and can be regenerated and reconstructed into bone and soft tissue.

On the other hand, in the field of Tissue Engineering (Tissue Engineering), as a technical field for regenerating a damaged organ, a small amount of cells obtained from a Tissue of a patient are cultured in vitro in a large amount, and then differentiated into a three-dimensional Tissue to regenerate the Tissue and the organ, and recently, in the field of Tissue Engineering, studies have been made in various ways similar to each other in order to restore functions of various tissues and organs of a damaged human body.

In tissue engineering, in order to perform three-dimensional culture of a tissue, an artificial scaffold for recognizing cells using a three-dimensional environment is required, and such an artificial scaffold needs to have an appropriate extracellular matrix (ECM) structure so as to smoothly deposit, propagate, and differentiate by cells. In addition, in order to permeate blood vessels, move cells, promote metabolism, and supply nutrients, it is necessary to have a porous structure connected to each other in an appropriate size, and to maintain appropriate strength to the extent that it can maintain its form during tissue regeneration.

A considerable number of tissues or organs in the form of anatomical membranes (membranes) are present in the human body, and in recent years, artificial supports in the form of meshes (meshes) capable of replacing or regenerating such damaged tissues in the form of membranes, in particular thin bone tissues, have been demanded. However, when such an artificial support having a mesh form is produced, it is difficult to adjust the size of the voids, and the mechanical strength is very weak, so that it is difficult to regenerate the tissue.

In view of the above, the present invention provides an in vivo absorptive three-dimensional artificial support having optimized materials and structures for reconstructing a defective portion.

Documents of the prior art

Patent document

Korean registered patent No. 10-1269127

SUMMERY OF THE UTILITY MODEL

Problem to be solved by utility model

The present invention has been developed in order to solve the above-mentioned problems of the prior art, and provides a biodegradable artificial support body comprising: the three-dimensional form and the bioabsorbable material for positively realizing the tissue regeneration at the defect site are used, and thus the biodegradable medical device has excellent biocompatibility and mechanical strength, and can be decomposed in the body and absorbed or excreted.

Means for solving the problems

The utility model discloses a three-dimensional artificial support of biodegradability includes: a plurality of first layer structure lines extending in a 1 st direction and arranged at predetermined intervals in a 2 nd direction intersecting the 1 st direction at a predetermined angle; and a plurality of layer 2 structure lines extending in the 2 nd direction on a first layer composed of the plurality of first layer structure lines and arranged at a predetermined interval along the 1 st direction, wherein the plurality of first layer structure lines and the layer 2 structure lines are composed of a bioabsorbable material and cross at an angle of 30 to 90 degrees, and the first layer and the layer 2 are overlapped and laminated.

Preferably, the width of the 1 st structure line constituting the first layer of the biodegradable artificial support of the present invention is about 50 to 200 μm, the width of the 2 nd structure line constituting the 2 nd layer formed on the first layer (i.e., the thickness of the line) is also about 50 to 200 μm, the interval between adjacent 1 st structure lines is 50 to 1500 μm, and the interval between adjacent 2 nd structure lines is also 50 to 1500 μm.

The widths of the 1 st structural line and the 2 nd structural line are formed to be a predetermined width or may be changed within the above range at a predetermined ratio, and the intervals between the adjacent plural 1 st structural lines or 2 nd structural lines are also formed to be a predetermined interval or may be changed within the above range at a predetermined ratio.

In addition, the bioabsorbable material includes a biodegradable polymer, and optionally, a ceramic material or a biomaterial.

The biodegradable polymer is at least one selected from the group consisting of PCL (Polycaprolactone), PGA (Polyglycolic acid), PLA (Polylactic acid), PLGA (poly-lactic-co-glycolic acid), PLLA (poly (L-lactic acid)), poly (L-lactic acid), PCL (Polycaprolactone), PHB (Polyhydroxybutyrate), PHV (Polyhydroxyvalerate), PDO (Polydioxanone), and PTMC (Polytrimethylenecarbonate).

The ceramic material is Hydroxyapatite (HA), Tricalcium phosphate (TCP), Bioglass (Bioglass), or calcium carbonate (calcium carbonate), and the biomaterial is at least one selected from the group consisting of collagen, chitosan, hyaluronic acid, carboxymethylcellulose, heparan sulfate, dextran and alginate, Bone Morphogenetic Protein (BMP), epithelial cell Growth factor (EGF), Fibroblast Growth Factor (FGF), transforming Growth factor (TGFbeta), platelet-derived factor (PDGF), vascular endothelial Growth factor (VEGE), insulin-like Growth factor (IGF-1), Thioredoxin (TRX), Stem Cell Factor (SCF), Hepatocyte Growth Factor (HGF), Human Growth Hormone (Human Growth Hormone), and Angiogenin (Angiogenin).

Effect of the utility model

According to the utility model discloses, the form through connecting all inside spaces allows the removal of peripheral cell, nutrient substance to tissue reconstruction in the defect position carries out easily. Meanwhile, the three-dimensional artificial support manufactured has excellent biocompatibility of the material, and achieves excellent mechanical strength by the structure of repeated lamination.

Drawings

Fig. 1 to 3 are a perspective view, a right side view, and a plan view of a triangular laminated biodegradable three-dimensional artificial support according to an embodiment of the present invention.

Fig. 4 is a view schematically showing the structure of a triangular laminated biodegradable three-dimensional artificial support.

Fig. 5 to 7 are a perspective view, a right side view, and a plan view of a biodegradable three-dimensional artificial support of another embodiment of the present invention.

Fig. 8 is a view schematically showing the structure of a biodegradable three-dimensional artificial support of a quadrangular laminate type.

Fig. 9 is a view schematically showing the structure of a multiaxial stacking system for producing a biodegradable three-dimensional artificial support according to the present invention.

Fig. 10 and 11 are views schematically showing a process for producing a biodegradable three-dimensional artificial support of the quadrangular laminate type.

Fig. 12 is an electron micrograph of the biodegradable three-dimensional artificial support of the four-corner laminate type according to the present invention.

Fig. 13 and 14 are electron micrographs of the triangular laminated biodegradable three-dimensional artificial support according to the present invention.

Fig. 15 is an electron micrograph showing a deformed structure of the biodegradable three-dimensional artificial support according to the present invention.

FIG. 16 is an electron micrograph showing that a biomaterial (collagen) is further included in the biodegradable three-dimensional artificial support according to the present invention.

(symbol description)

10: the integrated control device 20: data model

30: the temperature controller 40: pressure controller

50: the gas compressor 100: multi-axis lamination system

110: the working table 120: x-axis displacement moving part

130: y-axis displacement moving unit 140: z-axis displacement moving unit

150: lamination head 151: suction tube

153: nozzle 155: heating device

200: artificial support 210: no. 1 structural wire

220: no. 2 structural line

Detailed Description

Hereinafter, embodiments of the present invention will be described in detail with reference to the accompanying drawings so that those skilled in the art can easily implement the present invention. On the other hand, the dimensions of the respective constituent elements are arbitrarily shown in the drawings for convenience of explanation, and the present invention is not limited to the illustrated cases.

Fig. 1 to 3 are a perspective view, a right side view, and a plan view of a triangular laminated type tri-vitamin biodegradable artificial support according to an embodiment of the present invention.

Referring to fig. 1 to 3, the triangular laminated type tri-vitamin degradable artificial support of the present embodiment has a mesh shape including a plurality of voids. Specifically, the artificial support of the present embodiment includes a plurality of 1 st structure lines extending in the lateral direction (hereinafter, referred to as '1 st direction') of fig. 1 to 3 and a plurality of 2 nd structure lines extending in the longitudinal direction (hereinafter, referred to as '2 nd direction') of fig. 1 to 3. The plurality of 1 st structure lines are arranged at a predetermined interval along the 2 nd direction, and the plurality of 2 nd structure lines are formed on the plurality of 1 st structure lines and arranged at a predetermined interval along the 1 st direction.

Conventionally, titanium artificial supports have been widely used because they have excellent mechanical strength and cell compatibility. However, when the titanium artificial support is used in bone tissue by being embedded in the body, a problem arises in connection with the peripheral bone. In addition, a secondary operation is required to remove the implant after it is embedded in the body.

Thus, in the present example, a biopolymer having excellent biocompatibility and excellent biodegradability was used in the production of the artificial support.

The structure line 1 and the structure line 2 of the artificial support of the present invention are made of a bioabsorbable material such as a biodegradable polymer, and examples of the biodegradable polymer include at least one selected from the group consisting of PCL (Polycaprolactone), PGA (Polyglycolic acid), PLA (Polylactic acid), PLGA (poly-lactic-co-glycolic acid), PLLA (poly-L-lactic acid), PCL (Polycaprolactone), PHB (Polyhydroxybutyrate), PHV (Polyhydroxyvalerate), PDO (Polydioxanone), and PTMC (polytrimethylenepolycarbonate), or a mixture thereof.

In addition to such a biopolymer, ceramics of bone structural components such as Hydroxyapatite (HA), Tricalcium phosphate (TCP), Bioglass (Bioglass), calcium carbonate (calcium carbonate), and the like may be included.

When the artificial support is formed by mixing the bone structural component ceramic and the biopolymer, the effect of improving the cell adhesion efficiency is achieved by increasing the surface roughness of the artificial support in addition to improving the mechanical strength of the artificial support.

Thus, the mesh-shaped artificial support of the present example composed of a biopolymer has superior bioaffinity compared to titanium. Further, the structural lines having a predetermined thickness are arranged with directionality, and therefore have excellent mechanical strength, and have sufficient elastic force and flexibility (flexibility) because the line length is long compared to the line width.

In the artificial supports shown in fig. 1 to 3, the widths of the structure lines (1 st structure line, 2 nd structure line) constituting the respective layers (for example, the first layer and the 2 nd layer) are set to be in the range of about 50 μm to 500 μm, and the interval between the adjacent structure lines is set to be in the range of 500 μm to 300 μm. The width and the interval of such structure lines may be predetermined widths and intervals, but may be changed to an appropriate extent.

More specifically, as shown in fig. 4, the structural line constituting the first layer is arranged so as to intersect with the structural line constituting the 2 nd layer formed thereon at a predetermined angle, and in particular, the respective layers may intersect at an angle of 60 degrees.

As shown in fig. 4, the structure lines of the lowermost first layer are arranged horizontally (0 degrees) apart, the structure lines of the 2 nd layer are arranged above the first layer at an angle of 60 degrees, and the 3 rd layer is arranged at an angle of 120 degrees (with respect to the first layer). As shown in fig. 1 to 3, in the triangular laminate type artificial support, the first to 3 rd layers become basic repeating units (basic repeating units), and a plurality of repeating units are appropriately laminated to form the artificial support.

In the case where the structure lines of the respective layers constituting the artificial support are formed by being discharged using a 3D printer as shown in fig. 4, the structure lines of the respective layers are arranged at predetermined intervals in a continuous connection manner without being broken as shown in (a), (b), and (c) of fig. 4

As another embodiment of the present invention, as shown in fig. 5 to 7, the structural lines of the respective layers constituting the artificial support are arranged at an angle of 90 degrees. That is, the structure lines of the first layer disposed at the lowermost position are disposed horizontally (0 degree) apart, and then the structure lines of the 2 nd layer are disposed at an angle of 90 degrees above the first layer. As shown in fig. 8 (a) to (c), in the four-corner laminated artificial support, the first layer and the 2 nd layer constitute a basic repeating unit (basic repeating unit), and a plurality of repeating units are appropriately laminated to form the artificial support.

Fig. 9 is a view schematically showing the structure of a multi-axis lamination system for manufacturing a dummy support according to an embodiment of the present invention, and fig. 10 and 11 are views schematically showing a process of manufacturing a four-angle lamination type dummy support according to an embodiment of the present invention. Next, a method for manufacturing an artificial support according to an embodiment of the present invention will be described with reference to the drawings.

In the present embodiment, the multi-axis lamination system 100 is used for manufacturing the artificial support. The solid freeform fabrication method is a technique of converting solid freeform information obtained from CAD data into a G code (G-code) based on a rapid prototyping (rapid prototyping) technique and layering materials one by one to fabricate a desired three-dimensional shape, and the multi-axis layering system (multi-head layering system)100 is a system for fabricating a three-dimensional artificial support for tissue engineering by applying such a solid freeform fabrication (solid-form fabrication) method.

The multi-axis lamination system 100 is a system in which the position, temperature, and pressure can be controlled independently of each other, and a three-dimensional artificial support is manufactured by melting a material by a thermal melting method and then spraying the material by air pressure.

Referring to fig. 9, the multi-axis lamination system 100 includes a lamination head 150 that ejects a manual support material at a predetermined width. The lamination head 150 includes pipettes (syring) 151 into which materials are flowed and stored, nozzles 153 for dispersing the materials flowed into the pipettes 151, and a heater 155 for appropriately maintaining the temperature of the materials, and in this embodiment, the artificial support 200 is formed by injecting biopolymers into the pipettes 151 of the lamination head 150 and spraying the biopolymers through the respective nozzles 153. On the other hand, when the biopolymer is injected in this embodiment, the bone structural component ceramic may be injected together.

In order to drive the lamination head 150 not only in the plane coordinates including the x-axis and the y-axis but also in the z-axis in the up-down direction, the multi-axis lamination system 100 includes an x-axis displacement moving unit 120 for driving the lamination head 15 in the x-axis direction, a y-axis displacement moving unit 130 for driving the lamination head 150 in the y-axis direction, and a z-axis displacement moving unit 140 for driving the lamination head 150 in the up-down direction in the z-axis direction, respectively.

In the multi-axis lamination system 100, a bio-polymer as an artificial support material is laminated in a matrix on the table 110, and a three-dimensional artificial support 200 to be shaped is manufactured.

The shape of the artificial support 200 to be manufactured and the like are input to the integrated control device 10 through the data model 20. In this case, it is preferable that the data model 20 of the artificial support 200 sets the coordinate values of the three-dimensional artificial support 200 to be input to the 3d cad data.

The integrated control device 10 controls the operation of the multi-axis layered system 100 based on the three-dimensional shape data model of the artificial support 200. Thus, the multi-axis lamination system 100 alternately ejects a mixed material of a bio-polymer or a biopolymer and a bone structural component ceramic, which is an artificial support material, by driving the lamination head 150 at a coordinate value to be set, based on the three-dimensional shape data of the artificial support 200 transmitted from the integrated control device 10.

The temperature controller 30 is connected to the lamination head 150 of the multi-axis lamination system 100 to control the temperature of the suction pipe 151 of the lamination head 150. Specifically, the temperature controller 30 is connected to the heater 155 attached to the lamination head 150 to control this so that the biopolymer or the mixed material of the biopolymer and the bone structural component ceramic inside the suction tube 151 of the lamination head 150 is heated or maintained at a predetermined temperature, whereby the biopolymer or the mixed material of the biopolymer and the bone structural component ceramic is changed or maintained in a state suitable for ejection, and is ejected through the suction tube 151 of the lamination head 150 at a predetermined thickness.

On the other hand, the temperature controller 30 is connected not only to the multi-axis lamination system 100 but also to the integrated control device 10, and operates in conjunction with the driving of the lamination head 150.

The pressure controller 40 is connected to the lamination head 150 of the multi-axis lamination system 100 and controls the pressure delivered to the lamination head 150. That is, the pressure controller 40 may cause the biopolymer or the mixed material of the biopolymer and the bone structural component ceramic ejected through the nozzle 153 of the lamination head 150 to be ejected at different ejection speeds as a means for controlling the pressure transmitted to the pressure transmitter of the lamination head 150.

The pressure controller 40 of the present embodiment pneumatically transmits pressure to the pressure transmitter of the lamination head 150. For this purpose, the three-dimensional artificial support manufacturing system includes the air compressor 50 that applies direct pressure to the pressure conveyor of the lamination head 150, and the air compressor 50 is operated by the pressure controller 40. At this time, the air compressor 50 is independently connected to each axis of the multi-axis lamination system 100 to adjust to different air pressures for each axis.

Next, a method for manufacturing a dummy support using the multi-axis lamination system 100 will be specifically described.

First, the artificial support is designed according to desired shape information using a CAD program. The shape information of the artificial support 200 thus designed is transmitted from the data model 20 to the integrated control device 10. The integrated control device 10 controls the temperature controller 30, the pressure controller 40, and the displacement moving portions 120, 130, and 140 in the respective axial directions based on the transmitted shape information.

After injecting a biodegradable polymer or a mixture of a biodegradable polymer and a bone structural component ceramic into the suction pipe 151 of the lamination head 150, the temperature of the suction pipe 151 is adjusted by the temperature controller 30 and the heater 155 so as to be in a state suitable for ejection.

In this case, as the biodegradable polymer, at least one selected from the group consisting of PCL (Polycaprolactone), PGA (Polyglycolic acid), PLA (Polylactic acid), PLLA (poly-lactic-co-glycolic acid), PLLA (poly (L-lactic acid)), poly (levolactic acid), PCL (Polycaprolactone), PHB (Polyhydroxybutyrate), PHV (Polyhydroxyvalerate), PDO (Polydioxanone), and PTMC (Polytrimethylenecarbonate) may be used, and as the ceramic material of the bone structural component that can be injected with such a biodegradable polymer, Hydroxyapatite (HA), Tricalcium phosphate (tricacium phosphate), glass (TCP), etc. may be used.

Then, the lamination head 150 is controlled by the displacement moving unit (120, 130, 140) and the pressure controller 40, and the biopolymer is ejected onto the table 110 through the nozzle 153 of the lamination head 150, thereby forming the artificial support 200.

Referring to fig. 10, a biopolymer or a mixture of a biopolymer and a bone structural component ceramic melted in a straw is sprayed a plurality of times in the 1 st direction at predetermined intervals to form a plurality of 1 st structural lines 210. At this time, the width W and the thickness T of the respective 1 st structure lines 210 are formed in the range of about 50 μm to about 200 μm, respectively. In addition, the interval D between the adjacent 1 st structure lines 210 is formed to be about 50 to 1500 μm.

Referring to fig. 11, a biopolymer or a mixed material of a biopolymer and a bone structural component ceramic is sprayed on a plurality of 1 st structural lines 210 at predetermined intervals along a 2 nd direction intersecting the 1 st direction a plurality of times to form a plurality of 2 nd structural lines 220. In this case, it is preferable that the ranges of the width and thickness of the respective 2 nd structure lines 220 and the range of the distance between the adjacent 2 nd structure lines 220 are formed in the same manner as in the case of the 1 st structure line 210, but may be formed differently.

In this way, the artificial support 200 having the lattice-shaped voids is manufactured from the plurality of 1 st configuration wires 210 and the plurality of 2 nd configuration wires 220 by the multi-axis lamination system 100. According to the method for producing an artificial support, since a toxic organic solvent is not separately used in the production process, an artificial support having cell affinity can be produced.

On the other hand, when various biopolymers having different cellular, chemical, and physical properties are mixed and used, different processing conditions must be selected in order to produce an artificial support by applying a thermal fusion method depending on different glass transition temperatures, melting temperatures, and the like.

In contrast, in the present embodiment, the temperature and the air pressure can be individually adjusted by the multi-axis lamination system 100, and the manufacturing conditions different depending on the material can be easily reflected.

Further, the width of the configuration lines 210 and 220 constituting the artificial support 200 can be easily adjusted by adjusting the temperature, the air pressure, and the nozzle transfer speed, and the size of the gap and the thickness of the artificial support can be easily adjusted by the CAD/CAM method, so that an appropriate artificial support can be easily manufactured according to various tissues in the body. Further, the CAD/CAM system is applied to repeatedly produce artificial supporters having the same shape.

The present invention will be explained below by way of specific examples and experimental examples.

[ example 1]

In this example, artificial supports having a length and a thickness of 3cm, 3cm and 0.2mm in the transverse direction and the longitudinal direction, respectively, were designed. The width of each structural line of the artificial support was designed to be 150 μm, and the size of the gap (corresponding to the interval between the structural lines) in the mesh-like artificial support was designed to be 250 μm. The entire thickness of the artificial support is designed to be 200 μm, and in this connection, it can be adjusted by the number of layers to be laminated, and in this embodiment, a layer of 100 μm thickness is designed to be 200 μm by laminating it twice.

The CAD shape information of the artificial support thus designed is converted into G code (G-code) information.

On the other hand, in the present example, as the biopolymer for forming the structural thread of the artificial support, a biopolymer obtained by mixing polylactic-co-glycolic acid (PLGA) and Polycaprolactone (PCL) in a ratio of 1: 1, the polylactic-co-glycolic acid (PLGA) is prepared by mixing polylactic acid (PLA) and polyglycolic acid (PGA) in a ratio of 85: 15, and mixing the components in a ratio of 15.

Such a biopolymer material is injected into a pipette mounted on a multiaxial stacking system, and the pipette is heated to a temperature of 120 to 130 ℃. At this time, the temperature is controlled to a desired temperature of about 150 ℃ by the temperature controller.

Since the biopolymer thus melted has a high viscosity but is in a fluid state, it is ejected in a form of a structural line through the nozzle when a high-pressure air pressure is applied, and in this example, the biopolymer is ejected by applying an air pressure of about 6 atmospheres, which is 650 kPa. The transport speed of the nozzle was set to about 100mm/min so that the width of the jetted structure line was 150 μm.

The thickness of one layer of the structured wire thus produced was 100 μm, the position of the nozzle was moved 100 μm in the z-axis direction, and the second layer was ejected as a lattice by rotating it by 90 ° on the first layer. Thus, an artificial support having a mesh form with a thickness of 200 μm was produced, and the result is shown in FIG. 12.

On the other hand, the elasticity and flexibility of the artificial support are important matters to be considered in manufacturing the artificial support, and in the present embodiment, the thickness is formed to a small size of 200 μm, and the line length is formed to be sufficiently long compared to the line width, so that the elasticity and flexibility of the artificial support are excellent.

In the following examples, the production was carried out in the same manner as in example 1, but the arrangement of the structural wires of the respective layers was varied.

[ example 2]

The artificial support was produced by performing the production in the same manner as in example 1, rotating the second layer by 60 ° on the first layer to eject it in a grid, and further rotating the second layer by 60 ° for the third time to eject it in a grid, and the results thereof are shown in fig. 13 and 14, respectively.

[ example 3]

Fig. 15 is a schematic view of an electron micrograph of an artificial support according to another embodiment.

In the case of the artificial support shown in fig. 15, the interval between the structure lines of the lowermost layer and the uppermost layer is set to be very narrow, and then the structure lines constituting the intermediate layer between the uppermost layer and the lowermost layer (the 0-degree structure lines as the first layer in fig. 4 are not present) are formed at angles of only 60 degrees and 120 degrees (that is, the form constituted by only the second layer and the third layer).

That is, the artificial support was produced in such a structure that the first layer was not present in the triangular laminated artificial support shown in example 2, the intermediate layer was formed only by the structure in which the 2 nd layer and the 3 rd layer were repeatedly laminated, and the spacing between the structure lines of the intermediate layer was significantly narrower than the spacing between the structure lines of the uppermost layer and the lowermost layer. In this case, each structural wire is processed from a material in which a biodegradable Polymer (PCL) and a ceramic (TCP) are mixed.

[ example 4]

Fig. 16 discloses an electron micrograph of a three-dimensional artificial support composed of a biodegradable Polymer (PCL), a ceramic (TCP), and a biomaterial (collagen), and a three-dimensional artificial support including a biomaterial was manufactured by the following processes: the three-dimensional artificial support obtained by processing the material obtained by mixing the biodegradable Polymer (PCL) and The Ceramic (TCP) as described in example 3 above was immersed in a solution containing a biomaterial, and then the biomaterial was diffused into the inside of the three-dimensional artificial support by centrifugal force, and freeze-dried.

As described above, the present invention has been explained by the preferred embodiments, but the present invention is not limited to the above-described embodiments. That is, it is obvious to those skilled in the art that various modifications and variations can be made without departing from the concept and scope of the claims described below.

Claims (7)

1. A biodegradable three-dimensional artificial support, characterized in that it comprises:

a 1 st layer including a plurality of 1 st layer structured lines, the plurality of 1 st layer structured lines extending in a 1 st direction and being arranged at predetermined intervals in a 2 nd direction intersecting the 1 st direction at a predetermined angle; and

a 2 nd layer including a plurality of 2 nd-layer structured lines, the plurality of 2 nd-layer structured lines extending in the 2 nd direction on a 1 st layer including the plurality of 1 st-layer structured lines and being arranged at predetermined intervals along the 1 st direction,

the plurality of layer 1 structure lines and layer 2 structure lines are made of a bioabsorbable material, intersect at an angle of 30 to 90 degrees, and overlap and laminate the layer 1 and the layer 2.

2. The biodegradable three-dimensional artificial support according to claim 1, characterized in that,

the width of the layer 1 structure line is 50 μm to 200 μm,

the width of the layer 2 structure line is 50 μm to 200 μm.

3. The biodegradable three-dimensional artificial support according to claim 1, characterized in that,

the interval between the adjacent multiple layer 1 structure lines is 50 μm to 1500 μm,

the interval between adjacent multiple 2 nd layer structure lines is 50 μm to 1500 μm.

4. The biodegradable three-dimensional artificial support according to claim 1, characterized in that,

the layer 1 structured line and the layer 2 structured line are arranged to have directivity, respectively.

5. The biodegradable three-dimensional artificial support according to claim 1, characterized in that,

the line length of the 1 st layer structure line and the 2 nd layer structure line is longer than the line width.

6. The biodegradable three-dimensional artificial support according to claim 1, characterized in that,

the plurality of layer 1 structure lines and the plurality of layer 2 structure lines intersect at an angle of 60 degrees.

7. The biodegradable three-dimensional artificial support according to claim 1, characterized in that,

the plurality of layer 1 structure lines and the plurality of layer 2 structure lines intersect at an angle of 90 degrees.

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