KR20240064429A - 3d printing ink composition for artificial organ and hydrogel for artificial organ prepared therefrom - Google Patents

Abstract

Based on 100 parts by weight of water, 0.5 to 6 parts by weight of agarose, 6 to 42.5 parts by weight of acrylamide, 0.007 to 0.03 parts by weight of N,N'-methylenebis(acrylamide), and 0.1 to 0.1 parts by weight of poly(ethylene glycol) diacrylate. 3 parts by weight of at least one crosslinking agent selected from the group consisting of 0.1 to 0.6 parts by weight of 2-hydroxy-6'-(2-hydroxyethoxy)-2-methylpropiophenone and water-soluble diphenyl (2,4, A 3D printing ink composition for artificial organs containing at least one photoinitiator selected from the group consisting of 0.1 to 0.25 parts by weight of 6-trimethylbenzoyl)phosphine oxide, and a hydrogel for artificial organs manufactured therefrom are provided.

Description

3D printing ink composition for artificial organs and hydrogel for artificial organs manufactured therefrom {3D PRINTING INK COMPOSITION FOR ARTIFICIAL ORGAN AND HYDROGEL FOR ARTIFICIAL ORGAN PREPARED THEREFROM}

The present invention relates to a 3D printing ink composition for artificial organs and a hydrogel for artificial organs produced therefrom.

Representative 3D printing methods include DIW (Direct Ink Writing) type printing, in which printing material is extruded from a nozzle and printed, and Polyjet, in which material comes out from a nozzle and photocrosslinks each layer by a light source such as ultraviolet (UV) light. ) type printing, and DLP (Digital Light Processing) type printing, which prints by lifting a substrate from an ink tank and irradiating a light source in real time.

In 3D printing, the production of ink with a viscosity that can pass through the nozzle smoothly and print the desired model is considered an important factor.

Additionally, ink used in 3D printing must have rheological characteristics that can maintain the 3D structure even after printing.

Meanwhile, hydrogels with high hydrophilicity and biocompatibility are attracting attention as artificial organ materials. Since the development of calcium alginate hydrogel around 1980, various hydrogels for biomaterials using natural or synthetic polymers have been developed, and various types of hydrogels are being developed as a result of many studies on the physicochemical properties of hydrogels. Hydrogels can absorb at least 20% of moisture of the total weight, and those that absorb more than 95% of water are called highly absorbent hydrogels.

However, despite various studies on artificial organs based on natural or synthetic hydrogels, three-dimensional artificial organs obtained from hydrogels may exhibit different physical properties depending on the composition and environment, leading to biocompatibility, printing suitability, and electrocautery suitability. , it shows significant limitations in biological and physical aspects such as rheological properties.

Among them, in the case of organs and body parts with high toughness and tensile strength inside the body, it is difficult to simulate artificial organ tissue using hydrogel as close to the real thing due to the nature of the hydrogel material in which water accounts for most of the composition.

The present invention provides a 3D printing ink composition capable of producing artificial organs with texture and physical properties similar to actual human organs, and a hydrogel for artificial organs manufactured therefrom.

According to one aspect of the present invention, based on 100 parts by weight of water, 0.5 to 6 parts by weight of agarose, 6 to 48 parts by weight of acrylamide, 0.007 to 0.03 parts by weight of N,N'-methylenebis(acrylamide), and poly( 0.01 to 3 parts by weight of ethylene glycol) diacrylate, at least one crosslinking agent selected from the group consisting of 0.1 to 0.6 parts by weight of 2-hydroxy-6'-(2-hydroxyethoxy)-2-methylpropiophenone, and A 3D printing ink composition for artificial organs containing at least one photoinitiator selected from the group consisting of 0.1 to 0.25 parts by weight of water-soluble diphenyl (2,4,6-trimethylbenzoyl) phosphine oxide is provided.

In one embodiment, it may further include 2.5 to 7.5 parts by weight of lithium sodium magnesium silicate based on 100 parts by weight of water.

In one embodiment, the water content of the 3D printing composition may be 60 to 90 parts by weight.

In one embodiment, the weight ratio of the acrylamide to the agarose may be 1 to 35.

In one embodiment, the 3D printing ink composition may further include an ionic material selected from the group consisting of CaCl ₂ , NaCl, FeCl ₃ , and ZrOCl ₂ .

In one embodiment, the molar concentration of the ionic material may be 0.25 to 6 M.

In one embodiment, the ink composition can be used in DLP (Digital Light Processing) type 3D printing.

In one embodiment, the ink composition can be used for DIW (Direct Ink Writing) type or Polyjet type 3D printing.

According to another aspect of the present invention, a hydrogel for artificial organs obtained by 3D printing an ink composition, comprising polyacrylamide obtained by polymerization of the acrylamide, and the agarose and the polyacrylamide have an IPN structure or a semi- A hydrogel for artificial organs forming an IPN structure is provided.

In one embodiment, the hydrogel for artificial organs may have an elastic modulus of 40 to 500 kPa, a tensile strength of 20 to 200 kPa, and a toughness of 3 to 1600 KJ/m ³ .

The 3D printing ink composition for artificial organs of the present invention is UV curable and has a curing time suitable for 3D printing, so it can be usefully used in the manufacture of artificial organs through DLP type printing.

Since the 3D printing ink composition for artificial organs of the present invention has rheological properties suitable for printing, it can be usefully used in DIW type or polyjet type printing.

The hydrogel for artificial organs produced using the 3D printing ink composition for artificial organs of the present invention can produce artificial organs with complex structures and properties very similar to human organs.

Artificial organs produced with a 3D printer using the printing ink composition for artificial organs of the present invention can be usefully used to produce customized surgical practice models according to individual needs according to the diversity of patients and the advancement of medical technology.

Figures 1 and 2 are photographs showing the gelation characteristics of the 3D printing ink composition for artificial organs according to an embodiment of the present invention.

Below, one aspect of the present specification will be described. However, the description in this specification may be implemented in various different forms, and therefore is not limited to the embodiments described herein. In order to clearly explain one aspect of the present specification, parts unrelated to the description have been omitted.

Throughout the specification, when it is said that a part “includes” a certain element, this means that other elements may be further included rather than excluding other elements, unless specifically stated to the contrary.

Tissues of the human body can be largely divided into epithelial tissue and connective tissue. Throughout the specification, artificial organs may refer to artificial organ connective tissue.

When a range of numerical values is described herein, unless the specific range is stated otherwise, the value has the precision of significant figures given in accordance with the standard rules in chemistry for significant figures. For example, the number 10 includes the range 5.0 to 14.9, and the number 10.0 includes the range 9.50 to 10.49.

3D printing ink composition for artificial organs

One aspect of the present invention, a 3D printing ink composition for artificial organs, includes agarose; acrylamide; At least one crosslinking agent selected from the group consisting of N,N'-methylenebis(acrylamide) and poly(ethylene glycol)diacrylate; At least one photoinitiator selected from the group consisting of 2-hydroxy-6'-(2-hydroxyethoxy)-2-methylpropiophenone and water-soluble diphenyl(2,4,6-trimethylbenzoyl)phosphine oxide; and water as a solvent.

Agarose is a hydrophilic polymer that is cross-linked by hydrogen bonds, and upon curing forms an interpenetrating polymer network (IPN) or semi-interpenetrating polymer network (semi-IPN) structure with acrylamide, which will be described later. do. In this way, the hydrogel, which has an interpenetrating complex structure formed by agarose and acrylamide, has the advantage of excellent biocompatibility as it does not exhibit cytotoxicity.

The content of agarose may be 0.5 to 6 parts by weight, preferably 0.6 to 4.8 parts by weight, and more preferably 1.2 to 3.6 parts by weight, based on 100 parts by weight of water. If the agarose content is too low, the hydrogel may not harden sufficiently or the electrocautery function may be weakened, and conversely, if the content is too high, it may be difficult to uniformly dissolve the agarose in the solvent.

Acrylamide is a water-swellable monomer that polymerizes by curing to form an interpenetrating polymer network (IPN) or semi-interpenetrating polymer network (semi-IPN) structure with agarose.

The content of acrylamide may be 6 to 48 parts by weight, preferably 9 to 48 parts by weight, and more preferably 12 to 48 parts by weight, based on 100 parts by weight of water. If the content of acrylamide is too low, the hydrogel may not harden sufficiently or the physical properties may be somewhat insufficient, and conversely, if the content is too high, the physical properties may be different from the actual organs due to excessive increase in modulus.

According to one example, the weight ratio of acrylamide to agarose may be 1 or more and 35 or less, and preferably 3 or more and 32 or less. When the weight ratio of acrylamide to agarose satisfies the above range, it may be more advantageous to secure physical properties similar to actual organs.

N,N'-methylenebis(acrylamide) and poly(ethylene glycol) diacrylate are components added as crosslinking agents.

The content of N,N'-methylenebis(acrylamide) may be 0.007 to 0.03 parts by weight, preferably 0.0072 to 0.029 parts by weight, based on 100 parts by weight of water. If the content of N,N'-methylenebis(acrylamide) is too low, crosslinking may not be sufficiently achieved, and conversely, if the content is too high, the degree of chemical crosslinking will become too large, which will lead to a decrease in the physical properties such as toughness of the hydrogel. You can.

The content of poly(ethylene glycol) diacrylate may be 0.01 to 3 parts by weight, preferably 0.05 to 0.5 parts by weight, and more preferably 0.05 to 0.3 parts by weight, based on 100 parts by weight of water. If the content of poly(ethylene glycol) diacrylate is too low, crosslinking may not be sufficiently achieved, and if the content is too high, the degree of chemical crosslinking may become too large and physical properties such as toughness of the hydrogel may be reduced.

2-Hydroxy-6'-(2-hydroxyethoxy)-2-methylpropiophenone and water-soluble diphenyl(2,4,6-trimethylbenzoyl)phosphine oxide are components added as photoinitiators, and are exposed to light ( Polymerization is initiated by forming radicals by uv).

The content of 2-hydroxy-4'-(2-hydroxyethoxy)-2-methylpropiophenone may be 0.1 to 0.6 parts by weight, preferably 0.15 to 0.55 parts by weight, and more preferably 0.18 to 0.55 parts by weight. It may be 0.52 parts by weight. If the content of 2-hydroxy-4'-(2-hydroxyethoxy)-2-methylpropiophenone is too low, photocurability will be low and curing time will be long. Conversely, if the content is too high, residual components after crosslinking will occur. exists, and the radical reaction rate can rapidly accelerate.

The content of water-soluble diphenyl (2,4,6-trimethylbenzoyl)phosphine oxide may be 0.1 to 0.25 parts by weight based on 100 parts by weight of water. If the content of water-soluble diphenyl(2,4,6-trimethylbenzoyl)phosphine oxide is too low, photocurability will be low and curing time will be long. Conversely, if the content is too high, residual components will exist after crosslinking and radical reaction will occur. The speed can increase dramatically.

According to one example, the water content of the 3D printing ink composition may be 60 to 90 parts by weight. When the water content satisfies the above range, it is easy to control the concentration of the polymer and the strength according to curability is improved, which can be advantageous for producing a hydrogel whose toughness and tensile strength are similar to those of actual organs. In addition, after swelling in an aqueous solution, it remains thermodynamically stable and can exhibit mechanical and physicochemical properties corresponding to an intermediate form between a liquid and a solid.

According to one example, the 3D printing ink composition may further include an ionic material. The ionic material may be one or more selected from the group consisting of CaCl ₂ , NaCl, FeCl ₃ , and ZrOCl ₂ , but is not limited thereto. Cations contained in ionic materials can form a coordination complex with an organic ligand on the hydrogel network, improving the physical properties of the hydrogel, especially the elastic modulus.

The molar concentration of the ionic material may be 0.25 to 6M, preferably 0.5 to 4M. When the content of the ionic material satisfies the above range, the physical properties of the hydrogel are improved, electrical conductivity is appropriately controlled, and electrocautery is improved, and as a result, it can be suitably used as an artificial organ for surgical training.

Not only is the 3D printing ink composition of the present invention capable of UV curing and its curing time is suitable for 3D printing, but the hydrogel produced by 3D printing exhibits texture and physical properties very similar to actual human organs, making it a DLP-type artificial It can be suitably used as a long-term 3D printing ink composition.

According to one example, the 3D printing ink composition may further include 2.5 to 7.5 parts by weight of lithium sodium magnesium silicate based on 100 parts by weight of water.

If the content of lithium sodium magnesium silicate is less than 2.5 parts by weight, gelation of the ink does not proceed, and the loss modulus (G'') becomes larger than the storage modulus (G'), which affects the rheology for extrusion. On the other hand, if it exceeds 7.5 parts by weight, the storage modulus (G') may become too large, making it difficult to mix the materials uniformly.

Since the 3D printing ink composition containing lithium sodium magnesium silicate has rheological properties suitable for printing, it can be suitably used as a DIW type or polyjet type 3D printing ink composition for artificial organs.

The 3D printing ink composition of the present invention is used for artificial organs such as artificial kidney, artificial liver, artificial small intestine, artificial large intestine, artificial stomach, artificial gallbladder, artificial blood vessel, artificial bladder, artificial heart, artificial lung, artificial uterus, artificial colon, artificial thyroid, etc. It can be used to construct connective tissue, artificial skeletal muscle, or skin.

For example, when 30 to 40 parts by weight of acrylamide, 1.5 to 3.5 parts by weight of agarose, and 0.007 to 0.03 parts by weight of N,N'-methylenebis(acrylamide) are included per 100 parts by weight of water, the elastic modulus upon curing is 90. It is ~200kPa and can be used to fabricate connective tissue for artificial kidneys.

For example, when 12 to 24 parts by weight of acrylamide, 1 to 2 parts by weight of agarose, and 0.007 to 0.03 parts by weight of N,N'-methylenebis(acrylamide) are included per 100 parts by weight of water, the elastic modulus upon curing is 40. At ~100 kPa, it can be used to fabricate connective tissue for artificial gallbladders.

For example, when 24 to 36 parts by weight of acrylamide, 2 to 3 parts by weight of agarose, and 0.007 to 0.03 parts by weight of N,N'-methylenebis(acrylamide) are included per 100 parts by weight of water, the elastic modulus upon curing is 5. It is ~200kPa and can be used to fabricate artificial skeletal muscles.

For example, when 42 to 48 parts by weight of acrylamide, 2 to 3 parts by weight of agarose, and 0.007 to 0.03 parts by weight of N,N'-methylenebis(acrylamide) are included per 100 parts by weight of water, the elastic modulus during curing is It is 394~476kPa and can be used to manufacture the connective tissue of the artificial colon, especially the ascending colon.

For example, when 24 to 36 parts by weight of acrylamide, 2.5 to 3.5 parts by weight of agarose, and 0.1 to 3 parts by weight of poly(ethylene glycol) diacrylate are included per 100 parts by weight of water, the elastic modulus upon curing is 90 to 200 kPa. It can be used to fabricate connective tissue for artificial kidneys.

For example, when 12 to 36 parts by weight of acrylamide, 1 to 2 parts by weight of agarose and 0.1 to 3 parts by weight of poly(ethylene glycol) diacrylate are included per 100 parts by weight of water, the elastic modulus upon curing is 40 to 100 kPa. It can be used to fabricate connective tissue for an artificial gallbladder.

For example, when 24 to 36 parts by weight of acrylamide, 2 to 3 parts by weight of agarose, and 0.1 to 3 parts by weight of poly(ethylene glycol) diacrylate are included per 100 parts by weight of water, the elastic modulus upon curing is 5 to 200 kPa. It can be used to manufacture artificial skeletal muscles.

For example, when 24 to 36 parts by weight of acrylamide, 1 to 2 parts by weight of agarose and 0.1 to 3 parts by weight of poly(ethylene glycol) diacrylate are included per 100 parts by weight of water, the elastic modulus upon curing is 9 to 50 kPa. It can be used to fabricate connective tissue for an artificial thyroid gland.

For example, when 6 to 18 parts by weight of acrylamide, 3 to 4 parts by weight of agarose, and 0.1 to 3 parts by weight of poly(ethylene glycol) diacrylate are included per 100 parts by weight of water, the elastic modulus upon curing is 394 to 476 kPa. It can be used to fabricate the connective tissue of an artificial colon, especially the ascending colon.

Hydrogels for artificial organs

Another aspect of the present invention provides a hydrogel for artificial organs formed by 3D printing the above-described 3D printing ink composition.

The hydrogel for artificial organs of the present invention may contain polyacrylamide obtained by polymerization of acrylamide, and agarose and polyacrylamide may form an IPN structure or a semi-IPN structure. In this case, it is possible to provide a structurally stable three-dimensional network structure with little fluidity due to external forces.

According to one example, the elastic modulus (Young's modulus) of the hydrogel for artificial organs may be 40 to 500 kPa. When the elastic modulus of the hydrogel for artificial organs satisfies the above range, it can provide elasticity, toughness, sealability, color, and texture very similar to real organs.

According to one example, the tensile strength of the hydrogel for artificial organs may be 20 to 200 kPa. When the tensile strength of the hydrogel for artificial organs satisfies the above range, it can provide properties similar to actual organs in that it is not easily torn during surgical training and can be sutured.

According to one example, the toughness of the hydrogel for artificial organs may be 3 to 1600 KJ/m ³ . If the toughness of the hydrogel for artificial organs meets the above range, it can provide properties similar to real organs in that it is not easily torn during surgical training and can be sutured.

Hydrogels for artificial organs can be preferably applied as artificial organs.

In the present invention, there is no particular limitation on the method of manufacturing an artificial organ by 3D printing, but for example, it can be manufactured including the following steps (a) to (d).

(a) Obtaining DICOM data by imaging human organs with CT or MRI

(b) 3D modeling the DICOM data using a 3D slicer

(c) converting the 3D modeled data into gcode format and applying it to a 3D printer

(d) Printing 3D printing ink using a 3D printer to which the gcode is applied.

Steps (a), (b), and (c) may be performed by methods known in the art.

According to one example, the printing speed in step (d) may be 5 to 80 mm/s, preferably 7 to 70 mm/s, and more preferably 10 to 60 mm/s. If the printing speed is too low, the stability of the ink may decrease during the ink extrusion process, and conversely, if the printing speed is too high, the adhesion to the substrate or the underlying layer may decrease.

According to one example, the pneumatic pressure in step (d) may be 20 to 100 Pa. If the pneumatic pressure is too low, ink may not be discharged or may be discharged unevenly. Conversely, if it is too high, strong pressure may be applied to the nozzle, resulting in an excessively large discharge amount. On the other hand, since printing speed and pneumatic pressure are closely related to each other, an organic setting is necessary. For example, when increasing the printing speed, the pneumatic pressure also needs to be increased accordingly.

Hereinafter, embodiments of the present specification will be described in more detail. However, the following experimental results describe only representative experimental results among the above examples, and the scope and content of the present specification cannot be interpreted as being reduced or limited by the examples. Each effect of various implementations of the present specification that are not explicitly presented below will be described in detail in the corresponding section.

Example 1

In 20g of distilled water heated to 90℃, 0.3g of agarose, 2.4g of acrylamide, 0.00144g of N,N'-methylenebis(acrylamide) (MBA), and 2-hydroxy-4'-(2-hydroxyethoxy )-2-Methylpropiophenone (Igacure 2959) 0.030 g was dissolved and cooled to 40°C.

A 3D printing ink composition was prepared by mixing 0.5 g of lithium sodium magnesium silicate (Laponite RD) with the cooled mixture.

Examples 2 to 12

A 3D printing ink composition and hydrogel were prepared in the same manner as Example 1, except that the amounts of each component contained in the 3D printing ink composition were changed as shown in Table 1 below. In each example, the content of lithium sodium magnesium silicate (Laponite RD) was kept constant at 0.5 g.

Example 13

In 20g of distilled water heated to 90℃, 0.5g of agarose, 4.8g of acrylamide, 0.22g of poly(ethylene glycol) diacrylate (PEGDA), and 2-hydroxy-4'-(2-hydroxyethoxy)-2 -0.03 g of methylpropiophenone (Igacure 2959) was dissolved and cooled to 40°C.

A 3D printing ink composition was prepared by mixing 0.5 g of lithium sodium magnesium silicate (Laponite RD) with the cooled mixture.

Examples 14 to 24

A 3D printing ink composition and hydrogel were prepared in the same manner as in Example 13, except that the amounts of each component contained in the 3D printing ink composition were changed as shown in Table 2 below. In each example, the content of lithium sodium magnesium silicate (Laponite RD) was kept constant at 0.5 g.

Experimental Example 1

After producing a hydrogel with a DIW type 3D printer using the 3D printing ink composition of each example, a sample of 10 mm x 30 mm x 3 mm in width x length x height was prepared. Afterwards, the physical properties were measured using the method below, and the results are shown in Tables 1 and 2 below.

(1) Toughness

Using a tensile tester (manufactured by Mark), the sample is stretched at a speed of 200 mm/min until the sample is cut, the stress-strain relationship is drawn on a graph, and the area of the stress-strain graph is calculated to determine the toughness. was measured.

(2) Tensile strength

A method of stretching the sample at a speed of 200 mm/min until the sample is cut using a tensile tester device (manufactured by Mark), drawing the stress-strain relationship on a graph, and then extracting the maximum stress value from the stress-strain graph. The tensile strength was measured.

(3) Young's modulus

Using a tensile tester device (manufactured by Mark), stretch the sample at a speed of 200 mm/min until the sample is cut, draw the stress-strain relationship as a graph, and then calculate the initial slope of the graph in the elastic region within the stress-strain graph. Young's modulus was measured by calculating .

After preparing a sample of 10 mm x 30 mm x 3 mm in width x length x height, the physical properties were measured in the following manner. The results are shown in Tables 1 to 4 below.

(1) Toughness

Using a tensile tester (manufactured by Mark), the sample is stretched at a speed of 200 mm/min until the sample is cut, the stress-strain relationship is drawn on a graph, and the area of the stress-strain graph is calculated to determine the toughness. was measured.

(2) Tensile strength

A method of stretching the sample at a speed of 200 mm/min until the sample is cut using a tensile tester device (manufactured by Mark), drawing the stress-strain relationship on a graph, and then extracting the maximum stress value from the stress-strain graph. The tensile strength was measured.

(3) Young's modulus

Using a tensile tester device (manufactured by Mark), stretch the sample at a speed of 200 mm/min until the sample is cut, draw the stress-strain relationship as a graph, and then calculate the initial slope of the graph in the elastic region within the stress-strain graph. Young's modulus was measured by calculating .

acryl
Amides (g) agarose
(g) MBA
(g) Igacure 2959
(g) tenacity
(KJ/ ^m3 ) tensile strength
(kPa) elastic modulus
(kPa) Example 1 2.4 0.3 0.00144 0.030 3.5 21.2 69.1 Example 2 4.8 0.00288 0.030 149.5 70.2 82.0 Example 3 7.2 0.00432 0.030 703.2 82.8 103.5 Example 4 9.6 0.00576 0.030 712.2 101.8 258.0 Example 5 2.4 0.5 0.00144 0.030 13.2 63.4 291.3 Example 6 4.8 0.00288 0.030 27.7 76.1 142.1 Example 7 7.2 0.00432 0.030 1556.9 145.3 115.6 Example 8 9.6 0.00576 0.030 1161.5 145.8 409.9 Example 9 2.4 0.7 0.00144 0.030 12.9 83.0 533.1 Example 10 4.8 0.00288 0.030 43.1 99.6 255.3 Example 11 7.2 0.00432 0.030 1212.5 156.7 197.5 Example 12 9.6 0.00576 0.030 1012.3 186.6 311.1

acryl
Amide
(g) agarose
(g) PEGDA
(g) Igacure 2959
(g) tenacity
(KJ/ ^m3 ) tensile strength
(kPa) elastic modulus
(kPa) Example 13 2.4 0.3 0.0112 0.030 76.7 50.0 52.5 Example 14 4.8 0.0224 0.030 155.7 57.4 47.9 Example 15 7.2 0.0336 0.030 598.5 95.8 46.5 Example 16 9.6 0.0448 0.030 783.9 132.5 107.3 Example 17 2.4 0.5 0.0112 0.030 103.4 135.6 236.4 Example 18 4.8 0.0224 0.030 293.2 105.8 106.9 Example 19 7.2 0.0336 0.030 375.0 123.5 104.7 Example 20 9.6 0.0448 0.030 717.7 119.2 79.4 Example 21 2.4 0.7 0.0112 0.030 131.8 211.8 473.8 Example 22 4.8 0.0224 0.030 314.4 146.8 156.6 Example 23 7.2 0.0336 0.030 348.9 143.7 94.0 Example 24 9.6 0.0448 0.030 690.8 175.8 260.1

From Tables 1 and 2, it can be seen that the hydrogels prepared according to Examples 1 to 24 have physical properties similar to real organs and can be preferably applied as artificial organs capable of incision surgery and electrocautery surgery training.

Experimental Example 2

In order to confirm the DIW type 3D printing printing suitability according to the lithium sodium magnesium silicate content, the laponite contents of the 3D printing ink compositions of Examples 2, 6, 10, 14, 18, and 22 were 0g, 0.25g, respectively. After adjusting to 0.5g and 0.75g, it was added to a 30mL vial. The vial was turned over to observe whether it maintained its original shape or flowed. The results are shown in Figures 1 and 2.

From Figures 1 and 2, it can be confirmed that when the lithium sodium magnesium silicate content is 2.5 parts by weight or more based on 100 parts by weight of water, it can be suitably used as a DIW type 3D printing ink composition.

The description of the present specification described above is for illustrative purposes, and a person skilled in the art to which an aspect of the present specification pertains can easily transform it into another specific form without changing the technical idea or essential features described in the present specification. You will be able to understand it. Therefore, the embodiments described above should be understood in all respects as illustrative and not restrictive. For example, each component described as single may be implemented in a distributed manner, and similarly, components described as distributed may also be implemented in a combined form.

The scope of the present specification is indicated by the claims described below, and all changes or modified forms derived from the meaning and scope of the claims and their equivalent concepts should be construed as being included in the scope of the present specification.

Claims (10)

For 100 parts by weight of water,
0.5 to 6 parts by weight of agarose;
6 to 48 parts by weight of acrylamide;
At least one crosslinking agent selected from the group consisting of 0.007 to 0.03 parts by weight of N,N'-methylenebis(acrylamide) and 0.01 to 3 parts by weight of poly(ethylene glycol) diacrylate; and
0.1 to 0.6 parts by weight of 2-hydroxy-6'-(2-hydroxyethoxy)-2-methylpropiophenone and 0.1 to 0.25 parts by weight of water-soluble diphenyl (2,4,6-trimethylbenzoyl)phosphine oxide. At least one photoinitiator selected from the group consisting of;
A 3D printing ink composition for artificial organs, comprising: According to paragraph 1,
A 3D printing ink composition for artificial organs, further comprising 2.5 to 7.5 parts by weight of lithium sodium magnesium silicate based on 100 parts by weight of water. According to paragraph 1,
A 3D printing ink composition for artificial organs, wherein the water content of the 3D printing composition is 60 to 90 parts by weight. According to paragraph 1,
A 3D printing ink composition for artificial organs, wherein the weight ratio of the acrylamide to the agarose is 1 to 35. According to paragraph 1,
The 3D printing ink composition for an artificial organ further comprises an ionic material selected from the group consisting of CaCl ₂ , NaCl, FeCl ₃ , and ZrOCl ₂ . According to clause 5,
A 3D printing ink composition for artificial organs, wherein the molar concentration of the ionic material is 0.25 to 6M. According to paragraph 1,
The ink composition is a 3D printing ink composition for artificial organs used in DLP (Digital Light Processing) type 3D printing. According to paragraph 2,
The ink composition is a 3D printing ink composition for artificial organs used in DIW (Direct Ink Writing) type or Polyjet type 3D printing. A hydrogel for artificial organs obtained by 3D printing the ink composition of any one of claims 1 to 8,
Including polyacrylamide obtained by polymerization of the above acrylamide,
A hydrogel for artificial organs in which the agarose and the polyacrylamide form an IPN structure or a semi-IPN structure. According to clause 9,
The hydrogel for artificial organs has an elastic modulus of 40 to 500 kPa, a tensile strength of 20 to 200 kPa, and a toughness of 3 to 1600KJ/m ³ .