KR102158012B1 - Dual Fluidic Channel with Porosity and Method for Preparing the Same - Google Patents

Abstract

The present invention relates to a porous dual flow channel manufactured using 3D bioprinting technology and a manufacturing method thereof. The porous dual flow channel of the present invention can be applied to various studies such as biofluid properties and flow studies, microfluidic system design and application technology development, medical device for medical treatment and biochip design. Since the method of the present invention uses a three-dimensional printing technique using a polymer or hydrogel material, the manufacturing process of the porous dual flow channel is very simple, and it is very advantageous in terms of cost and manufacturing time.

Description

Dual Fluidic Channel with Porosity and Method for Preparing the Same}

The present invention relates to a porous dual flow channel manufactured using a 3D bioprinting technology and a method for manufacturing the same.

Bio-microfluidic engineering is one of the emerging technologies. Bio-microfluidic engineering enables research in various fields, for example, biofluid properties and flow research, microfluidic system design and application technology development, medical device for medical treatment and biochip design. In order to use a microfluid, a flow channel having a size of tens to hundreds of microns must be manufactured, and various platform technologies for manufacturing a flow channel of this size are being studied. For example, microfluidic channels are mainly manufactured through microelectromechanical systems (MEMS) and polydimethylsiloxane (PDMS) molding processes.

As well as flow channels having a single layer, there are cases where porous dual flow channels are required for various assays and biological imitations. However, with the method developed so far, there are some limitations in fabricating a dual flow channel. Several process steps are required to create a porous double flow channel. In fact, in order to fabricate a porous dual flow channel using the Bio MEMS technology, it is necessary to fabricate a porous membrane, fabricate a flow channel through MEMS, and combine them.

3D bioprinting technology is one of the innovative technologies emerging in the field of bioengineering. 3D bioprinting technology has a great advantage in that it can make complex 3D structures by spraying polymers, various extracellular matrix (ECM) and cells at a desired location.

The patent documents and references mentioned in this specification are incorporated herein by reference to the same extent as if each document was individually and clearly specified by reference.

Republic of Korea Patent Publication No. 10-2017-0113253

The present inventors have made efforts to develop a dual fluidic channel that can be usefully used in bio-microfluidic engineering. As a result, the present invention was completed by experimentally confirming that a porous dual flow channel having a desired function can be manufactured at low cost through a simple process using a 3D printing technology using a polymer and a hydrogel.

Accordingly, an object of the present invention is to provide a method of manufacturing a porous dual flow channel using a three-dimensional printer.

Another object of the present invention is to provide a porous dual flow channel manufactured by the above method.

Other objects and technical features of the present invention are presented in more detail by the following detailed description, claims, and drawings.

According to an aspect of the present invention, there is provided a method of manufacturing a porous dual flow channel using a three-dimensional printer comprising the following steps:

(a) three-dimensional printing of the first flow channel using a polymer;

(b) 3D printing a micro porous structure using a polymer over the first flow channel;

(c) 3D printing a porous hydrogel on the microporous structure; And

(d) 3D printing a second flow channel using a polymer on top of the porous hydrogel.

Hereinafter, the method of the present invention will be described in detail according to each step.

Step (a): three-dimensional printing of the first flow channel using a polymer

In the present invention, the first flow channel is manufactured using a 3D printing technique using a 3D printer.

In the present specification, the term "three-dimensional printer" refers to a device that produces three-dimensional objects in a lamination method similar to that used in conventional inkjet printers, rather than milling or cutting. Since it is generally controlled by a computer, there are various forms that can be made, and It has the advantage of being easy to use compared to manufacturing technology.

In the present specification, the term "three-dimensional printing" refers to a manufacturing technology for creating a three-dimensional object by spraying a continuous layer of material using the three-dimensional printer. The 3D printing technology is divided into a "stacking manufacturing" method in which a powder or liquid material is hardened and stacked one by one, and a "cutting-off" method in which a shape is formed by cutting the material with a tool.

According to one embodiment of the present invention, the 3D printing method used in the present invention is an additive manufacturing method.

In this specification, the term "fluidic channel" refers to a channel having a structure through which a fluid can flow.

The shape or size of the first flow channel is not particularly limited, but may have a size range of several µm to several tens of cm, and may include a tube shape through which a fluid can flow.

According to an embodiment of the present invention, the width of the first flow channel is 2 mm or less, specifically 0.01 mm or more and 2 mm or less, and more specifically 0.1 mm or more and 2 mm or less. When the width of the first flow channel exceeds 2 mm, it is difficult to maintain the shape of the microfluidic channel, and it is difficult to 3D print the microporous structure on the top of the first flow channel.

In the present invention, the material material used in manufacturing the first flow channel using the 3D printing technology is a polymer material.

According to one embodiment of the present invention, the polymer material used for manufacturing the first flow channel is poly(ethylene-co-vinyl acetate) (Poly(ethylene-co-vinyl acetate), PEVA), polylactic-co-glycolic acid ( PLGA), polycaprolactone (PCL), polylactic acid (PLA), polyglycolic acid (PGA), polyethylene glycol (PEG), polyethylene oxide (PEO), polyglycolic acid (PGA), polyethersulfone (PES), poly Urethane (PU), polyacrylic acid (PAA), polyvinyl alcohol (PVA) polyvinylpyrrolidone (PVP), polystyrene (PS), polyaniline (PAN), poly [(3-hydroxybutyrate)-co-(3) -Hydroxyvalerate)](PHBV), polydioxanone (PDO), poly[(L-lactide)-co-(caprolactone)], poly(ester urethane)(PEUU), poly[(L-lac) Tide)-co-(D-lactide)], poly[ethylene-co-(vinyl alcohol)] may be one or more selected from the group consisting of, but is not limited thereto.

Step (b): 3D printing the microporous structure by using a polymer on the top of the first flow channel

After 3D printing the first flow channel, a microporous structure is formed on the first flow channel by a 3D printing technique using a polymer.

According to another embodiment of the present invention, in the present invention, the size of the micropores in the longitudinal direction is 700 μm or less, specifically 0.1 μm or more to 700 μm or less, more specifically 1 μm or more to 700 μm or less, more More specifically, it is 10 μm or more and 700 μm or less.

In addition, the thickness (width) of the micropores is 700 μm or less, specifically 0.1 μm or more to 700 μm or less, more specifically 0.1 μm or more to 500 μm or less, 0.1 μm or more to 400 μm or less, 0.1 μm or more It is ~ 200 μm or less, more specifically 1 μm or more to 200 μm or less, and most specifically 5 μm or more to 200 μm or less.

The micropores serve as a support capable of supporting the hydrogel in the case of printing the hydrogel above the structure having micropores as described below.

For the micropores, the shape and size of the micropores to be formed through 3D printing technology are first designed, and then the designed micropores are manufactured through 3D printing technology. The shape and size of the micropores may be determined by adjusting or changing a 3D printing condition, such as a nozzle size or a printing speed.

In the present invention, when a structure having micropores is manufactured using a 3D printing technology, the material material used for printing is a polymer material.

According to an embodiment of the present invention, the polymer used for preparing the microporous structure is poly(ethylene/vinyl acetate) (Poly(ethylene-co-vinyl acetate), PEVA), polylactic-co-glycolic acid (PLGA) , Polycaprolactone (PCL), polylactic acid (PLA), polyglycolic acid (PGA), polyethylene glycol (PEG), polyethylene oxide (PEO), polyglycolic acid (PGA), polyethersulfone (PES), polyurethane ( PU), polyacrylic acid (PAA), polyvinyl alcohol (PVA) polyvinylpyrrolidone (PVP), polystyrene (PS), polyaniline (PAN), poly [(3-hydroxybutyrate)-co-(3-hydride) Roxyvalerate)](PHBV), polydioxanone (PDO), poly[(L-lactide)-co-(caprolactone)], poly(ester urethane) (PEUU), poly[(L-lactide) -co-(D-lactide)], poly[ethylene-co-(vinyl alcohol)] may be one or more selected from the group consisting of, but is not limited thereto.

Step (c): 3D printing a porous hydrogel on the microporous structure

The porous hydrogel is 3D printed on top of the structure having micropores prepared in step (b).

The term "hydrogel" as used herein refers to a material having a hydrophilic structure capable of holding a large amount of water in a crosslinked three-dimensional network structure thereof as a polymer material.

The hydrogel material that can be used in the method of the present invention may be a natural material or a synthetic material in its origin.

The hydrogel material that can be used in the method of the present invention is, for example, polyvinyl alcohol, starch, cellulose, gelatin, polyethylene, agarose, chitosan, guar gum, gellan gum, glycol chitosan, alginate. (Alginate), hydroxamic acid alginates, alginate beads, fibrin, scleroglucan, poly(acrylic-co-vinylsulfonic) acid, polyacrylamide, poly It may be one or more materials selected from the group consisting of acrylamide/guar gum graft copolymer, cells and extracellular matrix (ECM), but is not limited thereto.

The extracellular matrix (ECM) is hyaluronic acid, collagen, gelatin, elastin, fibronectin, laminin, glycosaminoglycans, hepa Lansulfate (Heparan sulfate), chondroitin sulfate (Chondroitin sulfate), including, but not limited to, keratan sulfate (Keratan sulfate).

The cells include, but are not limited to, bone cells, chondrocytes, nerve cells, skin cells, epithelial cells, endothelial cells, muscle cells, secretory cells, adipocytes, blood cells, hepatocytes, or vascular cells.

According to an embodiment of the present invention, the hydrogel material that can be used in the method of the present invention may be a cell, collagen, glycosaminoclycan, laminin, hyaluronic acid, fibronectin, alginate, fibrin, or gelatin.

In the present invention, the strength of the porous hydrogel is very important for maintaining a stable double flow flow in a porous double flow channel.

According to one embodiment of the present invention, the strength of the 3D printed hydrogel may have an average storage modulus after crosslinking of 106.9±6.3 Pa or more.

When the strength of the porous hydrogel is less than a value of 106.9±6.3 Pa after crosslinking, the double flow flow is difficult to stably maintain in the porous double flow channel.

Step (d): 3D printing a second flow channel using a polymer on the porous hydrogel

A second flow channel is prepared by three-dimensional printing using a polymer on top of the porous hydrogel printed in step (c).

The shape or size of the second flow channel is not particularly limited, but may have a size ranging from several µm to several tens of cm, and may include a tube shape through which fluid can flow.

According to one embodiment of the present invention, the width of the second flow channel is 2 mm or less, specifically 0.01 mm or more and 2 mm or less, and more specifically 0.1 mm or more and 2 mm or less. When the width of the first flow channel exceeds 2 mm, it is difficult to maintain the shape of the microfluidic channel, and it is difficult to 3D print the microporous structure on the top of the first flow channel.

In the present invention, the material material used in manufacturing the second flow channel using the 3D printing technology is a polymer material.

According to one embodiment of the present invention, the polymer material used for manufacturing the second flow channel is poly(ethylene-co-vinyl acetate) (Poly(ethylene-co-vinyl acetate), PEVA), polylactic-co-glycolic acid ( PLGA), polycaprolactone (PCL), polylactic acid (PLA), polyglycolic acid (PGA), polyethylene glycol (PEG), polyethylene oxide (PEO), polyglycolic acid (PGA), polyethersulfone (PES), poly Urethane (PU), polyacrylic acid (PAA), polyvinyl alcohol (PVA) polyvinylpyrrolidone (PVP), polystyrene (PS), polyaniline (PAN), poly [(3-hydroxybutyrate)-co-(3) -Hydroxyvalerate)](PHBV), polydioxanone (PDO), poly[(L-lactide)-co-(caprolactone)], poly(ester urethane)(PEUU), poly[(L-lac) Tide)-co-(D-lactide)], poly[ethylene-co-(vinyl alcohol)] may be one or more selected from the group consisting of, but is not limited thereto.

According to another aspect of the present invention, there is provided a porous dual flow channel fabricated by using a three-dimensional printer comprising the following structure:

(a') a first flow channel three-dimensionally printed using a polymer;

(b') on the first flow channel, a micro porous structure 3D printed using a polymer;

(c') 3D printed porous hydrogel on the microporous structure; And

(d') A second flow channel 3D printed on the porous hydrogel using a polymer.

In the porous dual flow channel of the present invention, the "porosity" means including both the "porosity" in the microporous structure and the "porosity" of the porous hydrogel.

According to one embodiment of the present invention, the width of the first flow channel is 2 mm or less.

According to another embodiment of the present invention, the size of the micropores in the micropore structure is 700 μm or less in the longitudinal direction, and the thickness of the micropores is 700 μm or less.

The size of the micropores in the longitudinal direction is 700 μm or less, more specifically 0.1 μm or more to 700 μm or less, more specifically 1 μm or more to 700 μm or less, even more specifically 10 μm or more to 700 μm or less to be. In addition, the thickness (width) of the micropores is 700 μm or less, specifically 0.1 μm or more to 700 μm or less, more specifically 0.1 μm or more to 500 μm or less, 0.1 μm or more to 400 μm or less, 0.1 μm or more It is ~ 200 μm or less, more specifically 1 μm or more to 200 μm or less, and most specifically 5 μm or more to 200 μm or less.

According to another embodiment of the present invention, the polymer is poly(ethylene/vinyl acetate) (PEVA), polylactic-co-glycolic acid (PLGA), polycaprolactone (PCL), polylactic acid (PLA), polyglycolic acid. (PGA), polyethylene glycol (PEG), polyethylene oxide (PEO), polyglycolic acid (PGA), polyethersulfone (PES), polyurethane (PU), polyacrylic acid (PAA), polyvinyl alcohol (PVA) polyvinyl Pyrrolidone (PVP), polystyrene (PS), polyaniline (PAN), poly [(3-hydroxybutyrate)-co-(3-hydroxyvalerate)] (PHBV), polydioxanone (PDO), poly [(L-lactide)-co-(caprolactone)], poly(ester urethane) (PEUU), poly[(L-lactide)-co-(D-lactide)], poly[ethylene-co- (Vinyl alcohol)] is one or more selected from the group consisting of.

According to another embodiment of the present invention, the strength of the 3D printed hydrogel has an average storage modulus after crosslinking of 106.9±6.3 Pa or more.

According to another embodiment of the present invention, the hydrogel is polyvinyl alcohol, starch, cellulose, gelatin, polyethylene, agarose, chitosan, guar gum, gellan gum, glycol chitosan, alginate ), Hydroxamated alginates, Alginate bead, Fibrin, Scleroglucan, poly(acrylic-co-vinylsulfonic) acid, polyacrylamide, polyacrylamide / Guar gum graft copolymer, is one or more materials selected from the group consisting of cells and extracellular matrix, the extracellular matrix is hyaluronic acid, collagen, gelatin, elastin, fibronectin, laminin, glycosaminoglycan, heparan sulfate , Chondroitin sulfate, and keratin sulfate may be included, but are not limited thereto.

According to another embodiment of the present invention, the hydrogel may be a cell, collagen, glycosaminoclycan, laminin, hyaluronic acid, fibronectin, alginate, fibrin or gelatin.

The features and advantages of the present invention are summarized as follows:

(i) The present invention relates to a porous dual flow channel manufactured using a three-dimensional printing technology and a method for manufacturing the same.

(Ii) The porous dual flow channel manufactured by the present invention can be applied to various studies such as biofluid properties and flow research, microfluidic system design and application technology development, medical device for medical treatment and biochip design.

(Iii) A method of manufacturing a dual flow channel using a three-dimensional printing technology is a novel manufacturing method that has not been tried so far.

(Iv) Since the method of the present invention uses a three-dimensional printing technique using a polymer or hydrogel material, the manufacturing process of the porous double flow channel is very simple, and it is very advantageous in terms of cost and manufacturing time.

(v) The method of the present invention can easily control the double flowability in the produced porous double flow channel by adjusting the micropore structure and the hydrogel of the porous double flow channel without being restricted by the manufacturing process environment or conditions.

1A is a schematic diagram of a vertical cross-sectional structure of a porous dual flow channel manufactured through the method of the present invention.
1B shows a three-dimensional cross-sectional view in the middle of a porous dual flow channel.
1C is a photograph of a porous dual flow channel manufactured by 3D printing technology as seen from the outside through the method of the present invention.
2A shows in more detail a horizontal cross section of a structure having micropores in the structure of a porous dual flow channel manufactured by the method of the present invention.
Figure 2b shows the structure of the hydrogel printed on top of the structure of the porous dual flow channel manufactured by the method of the present invention.
2C shows a 3D printing path for manufacturing a structure having micropores and a microporous structure manufactured according to this path.
3A shows a result of measuring the flow of a fluid using a porous dual flow channel manufactured by the method of the present invention.
3B shows a result of measuring the flow of a fluid when a high-concentration fluid and a low-concentration fluid are flowed using a porous dual flow channel manufactured by the method of the present invention.
4 is a result of measuring the strength of a suitable hydrogel for maintaining a safe double flow when a double flow channel is manufactured using a collagen-based hydrogel by a viscoelastic measurement method (Rheology test).

Example

Example 1: Fabrication of porous dual flow channels using 3D printing technology

In order to fabricate a dual flow channel using 3D printing technology, various processes must be considered: (i) a sequential 3D printing process, (ii) a hydrogel for a porous dual flow channel, and (iii) ) A structure having micro pores serving as a support on which the hydrogel can be placed should be printed on the flow channel.

(1) Fabrication of the first flow channel

The width of the flow channel on a transparent sterile poly(methylmethacrylate (PMMA) plate using a three-dimensional printing method using poly(ethylene/vinyl acetate) (PEVA, Polysciences Inc., Warrington, PA, USA) as the material. A first flow channel (flow channel 1) was fabricated so that it was less than 2 mm.

(2) Fabrication of structures with micro pores

Using a three-dimensional printing method using poly(ethylene/vinyl acetate) (PEVA, Polysciences Inc., Warrington, PA, USA) as a material on the upper side of the first flow channel 3D printed on the PMMA plate, having micropores The structure was built. In the above structure, the size of the fine pores was manufactured to be 700 μm or less in the length direction, and the thickness (width) of the fine pores was manufactured to be 200 μm or less. The formation of the micropores is performed by setting a 3D printing path marked in green as shown in the left panel figure in FIG. 2C, and then setting suitable printing conditions (nozzle size, printing speed) according to the set path and printing. Completed.

(3) Fabrication of porous hydrogel

A porous hydrogel was printed on top of the structure having micropores prepared above by 3D printing using a collagen-based bio-ink. In addition, in addition to collagen-based bio-ink, the porous hydrogel was printed by three-dimensional printing using alginate-based bio-ink or fibrin-based bio-ink. In a dual flow flow using a porous dual flow channel, the strength of a hydrogel printed on a structure having micropores is very important in that it must be supported so that the dual flow flow can be maintained. It was confirmed that the strength of a hydrogel suitable for maintaining a safe double flow in a double flow channel should have an average storage modulus of at least 106.9±6.3 Pa after crosslinking when using a 1.5% collagen-based hydrogel. (See Fig. 4).

(4) Fabrication of the second flow channel

A second flow channel (flow channel 2) using a three-dimensional printing method using poly(ethylene/vinyl acetate) (PEVA, Polysciences Inc., Warrington, PA, USA) on the top of the three-dimensional printed hydrogel as a material Was produced.

The structure of the porous dual flow channel manufactured through the above method is shown in FIGS. 1A to 1C.

1A is a schematic diagram of the structure of a porous dual flow channel manufactured through the above method, FIG. 1B is a three-dimensional cross-sectional view in the middle of a porous dual flow channel, and FIG. 1C is an actual manufactured 3D bioprinted porous dual flow channel Shows.

2A shows in more detail the structure having micropores in the structure of the porous dual flow channel manufactured through the above method. 2B shows the structure of the hydrogel printed on top of the structure of the porous dual flow channel manufactured through the above method. 2C shows a 3D printing path for manufacturing a structure having micropores and a microporous structure manufactured according to this path.

Example 2: Measurement of fluid flow in dual flow channels

Using the porous dual flow channel prepared in Example 1, the flow of the fluid was measured. As a result of measuring the fluid flow in the porous dual flow channel by flowing fluids having different colors, it was confirmed that the fluid did not mix with each other in the dual flow channel and had a dual flow flow (FIG. 3A).

In addition, in the case of flowing a high concentration fluid (blue) and general distilled water, it was confirmed whether the fluids were mixed with each other. Among the dual flow channels, when a high concentration solution flows in the upper flow channel and a low concentration solution flows in the lower flow channel, the high concentration solution flowing in the upper flow channel becomes a low concentration solution flowing in the lower flow channel. Due to the flow did not flow, it was confirmed that the two types of fluids mixed with each other did not mix (Fig. 3b).

From the above experimental results, regardless of whether or not a solution of high concentration and low concentration is used, it was found that even for solutions having different concentrations, the porous dual flow channel can be sufficiently used to separate and use two types of different fluids. Confirmed.

The specific embodiments described herein are meant to represent preferred embodiments or examples of the present invention, and the scope of the present invention is not limited thereby. It will be apparent to those skilled in the art that variations and other uses of the invention do not depart from the scope of the invention described in the claims of this specification.

Claims (12)

(a) three-dimensional printing of the first flow channel using a polymer;
(b) 3D printing a micro porous structure using a polymer over the first flow channel;
(c) 3D printing a porous hydrogel on the microporous structure; And
(D) 3D printing a second flow channel using a polymer on the porous hydrogel; Including,
The shape and size of the microporous structure is formed by adjusting the nozzle size or printing speed of 3D printing,
In addition to cells, the porous hydrogel is polyvinyl alcohol, starch, cellulose, gelatin, polyethylene, agarose, chitosan, guar gum, gellan gum, glycol chitosan, alginate, hydroxamic acid. Alginate (Hydroxamated alginates), Alginate bead (Allginate bead), fibrin (fibrin), Scleroglucan (Scleroglucan), poly(acrylic-co-vinylsulfonic) acid, polyacrylamide, polyacrylamide/gua gum graft 3D free using bio-ink further comprising at least one material selected from the group consisting of polymer, hyaluronic acid, collagen, elastin, fibronectin, laminin, glycosaminoglycan, heparan sulfate, chondroitin sulfate, and keratin sulfate Characterized in that produced by Ting,
A method of manufacturing a porous dual flow channel for biofluid research using a 3D printer.
The method of claim 1, wherein the width of the first flow channel in step (a) is 2 mm or less.
The method of claim 1, wherein the size of the micropores in the step (b) is 700 µm or less in the length direction, and the thickness of the micropores is 700 µm or less.
The method of claim 1, wherein the polymer is poly(ethylene/vinyl acetate) (PEVA), polylactic-co-glycolic acid (PLGA), polycaprolactone (PCL), polylactic acid (PLA), and polyglycolic acid (PGA). , Polyethylene glycol (PEG), Polyethylene oxide (PEO), Polyglycolic acid (PGA), Polyethersulfone (PES), Polyurethane (PU), Polyacrylic acid (PAA), Polyvinyl alcohol (PVA) Polyvinylpyrrolidone (PVP), polystyrene (PS), polyaniline (PAN), poly[(3-hydroxybutyrate)-co-(3-hydroxyvalerate)](PHBV), polydioxanone (PDO), poly[(L -Lactide)-co-(caprolactone)], poly(ester urethane) (PEUU), poly[(L-lactide)-co-(D-lactide)], poly[ethylene-co-(vinyl alcohol) )] Method for producing a porous dual flow channel, characterized in that at least one selected from the group consisting of.
delete The method of claim 1, wherein the strength of the three-dimensionally printed porous hydrogel in step (c) has an average storage modulus after crosslinking of 106.9±6.3 Pa or more. .
(a') a first flow channel three-dimensionally printed using a polymer;
(b') on the first flow channel, a micro porous structure 3D printed using a polymer;
(c') 3D printed porous hydrogel on the microporous structure; And
(d′) a second flow channel 3D printed using a polymer on top of the porous hydrogel; including,
The shape and size of the microporous structure is formed by adjusting the nozzle size or printing speed of 3D printing,
In addition to cells, the porous hydrogel is polyvinyl alcohol, starch, cellulose, gelatin, polyethylene, agarose, chitosan, guar gum, gellan gum, glycol chitosan, alginate, hydroxamic acid. Alginate (Hydroxamated alginates), Alginate bead (Allginate bead), fibrin (fibrin), Scleroglucan (Scleroglucan), poly(acrylic-co-vinylsulfonic) acid, polyacrylamide, polyacrylamide/gua gum graft Three-dimensional printing using bio-ink containing at least one material selected from the group consisting of polymer, hyaluronic acid, collagen, elastin, fibronectin, laminin, glycosaminoglycan, heparan sulfate, chondroitin sulfate, and keratin sulfate Characterized in that produced by,
Porous dual flow channel for biofluid research made using a 3D printer.
8. The porous dual flow channel of claim 7, wherein the width of the first flow channel is 2 mm or less.
8. The porous dual flow channel according to claim 7, wherein the size of the micropores is 700 µm or less in the length direction, and the thickness of the micropores is 700 µm or less.
The method of claim 7, wherein the polymer is poly(ethylene/vinyl acetate) (PEVA), polylactic-co-glycolic acid (PLGA), polycaprolactone (PCL), polylactic acid (PLA), polyglycolic acid (PGA). , Polyethylene glycol (PEG), Polyethylene oxide (PEO), Polyglycolic acid (PGA), Polyethersulfone (PES), Polyurethane (PU), Polyacrylic acid (PAA), Polyvinyl alcohol (PVA) Polyvinylpyrrolidone (PVP), polystyrene (PS), polyaniline (PAN), poly[(3-hydroxybutyrate)-co-(3-hydroxyvalerate)](PHBV), polydioxanone (PDO), poly[(L -Lactide)-co-(caprolactone)], poly(ester urethane) (PEUU), poly[(L-lactide)-co-(D-lactide)], poly[ethylene-co-(vinyl alcohol) )] Porous dual flow channel, characterized in that at least one selected from the group consisting of.
delete The porous dual flow channel of claim 7, wherein the three-dimensional printed porous hydrogel has an average storage modulus after crosslinking of 106.9±6.3 Pa or more.

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