A 3D bioprinting matrix material based on corn alcohol-soluble protein and a preparation method and application thereof
By introducing polypeptide segments into zein and reacting them with Pluronic F127, a 3D bioprinting matrix material with temperature-sensitive properties and low gel concentration was prepared. This solved the problems of hydrophobicity of zein and the hazards of high concentration of F127, and achieved excellent performance in terms of biocompatibility and cell scaffold materials.
Patent Information
- Authority / Receiving Office
- CN · China
- Patent Type
- Patents(China)
- Current Assignee / Owner
- GUANGZHOU MEDICAL UNIV
- Filing Date
- 2025-01-16
- Publication Date
- 2026-05-19
AI Technical Summary
The application of existing zein as a matrix material for 3D bioprinting is limited by its hydrophobicity. Although Pluronic F127 has reverse thermosensitivity, its molecular chain segments are biologically inert, which is detrimental to cells and causes in vivo damage at high concentrations. In addition, its high gelation concentration is difficult to reduce.
By introducing polypeptide segments into zein and reacting them with terminal alkyne Prönnick F127, a 3D bioprinting matrix material with significantly reduced critical gel concentration, excellent biocompatibility and mechanical properties was prepared. It was able to be molded and stabilized in a body temperature environment by utilizing its temperature-sensitive properties.
It achieves stable gelation of materials at low concentrations, solves the problem of human health hazards from high concentrations of F127, and provides excellent biocompatibility and cell adhesion and proliferation effects, making it suitable for 3D bioprinting to prepare cell scaffold materials.
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Abstract
Description
Technical Field
[0001] This invention belongs to the field of natural polymer material modification and its application technology, and specifically relates to a 3D bioprinting matrix material based on zein, its preparation method and application, and more specifically to a zein-Planick F127 graft and its preparation method and its application in 3D bioprinting. Background Technology
[0002] Tissue engineering scaffolds can provide a suitable extracellular matrix environment for cell growth, improving cell retention and survival rates. Commonly used methods for constructing tissue engineering scaffold materials include vacuum freeze-drying, gas foaming, particle dissolution, electrospinning, and 3D bioprinting. Among these, 3D bioprinting has received widespread attention due to its advantages such as high precision in material construction and the ability to achieve personalized designs according to specific needs.
[0003] Zein is a large-molecule protein derived from the natural plant corn. It has good biocompatibility and has attracted attention from scholars at home and abroad in recent years as a tissue engineering scaffold material. However, its strong hydrophobicity limits its application as a matrix material for 3D bioprinting.
[0004] Pluronic F127 is a polyoxyethylene-polyoxypropylene-polyoxyethylene (PEO-PPO-PEO) triblock copolymer, a polymer approved by the US Food and Drug Administration (FDA) for human use. It exhibits reverse thermosensitivity; below the critical temperature, the polymer solution is in a sol state, while at high temperatures it becomes a gel. However, its disadvantages include the fact that its molecular chain segments are biologically inert, and the material itself lacks the ability to promote cell adhesion and proliferation. Furthermore, its gelation concentration is relatively high, requiring a concentration greater than 18% (w / v) to gel. High-concentration F127 has a denser pore structure, which is not conducive to the exchange of cellular nutrients and metabolites. In addition, high-concentration F127 can damage the body in vivo. For example, Zhao et al. (PloS noe, 2013, 8(8):73178) reported that F127 damaged the cornea when used in ophthalmic treatment. Most current studies use F127 to be blended with other substances to improve the biocompatibility of the material, but it is difficult to reduce the concentration of F127 used.
[0005] The present invention aims to construct a thermosensitive gel material with good biocompatibility and stability and apply it to the field of 3D bioprinting. Summary of the Invention
[0006] In order to overcome the shortcomings and deficiencies of the prior art, the primary objective of this invention is to provide a 3D bioprinting matrix material based on zein.
[0007] This invention provides a 3D bioprinting matrix material based on zein and Pluronic F127. Polypeptide segments are introduced into the structure, resulting in a material with a significantly reduced critical gel concentration, excellent biocompatibility, safety and non-toxicity, and excellent mechanical properties, meeting the requirements and application scenarios of 3D printing.
[0008] Another object of the present invention is to provide a method for preparing the above-mentioned 3D bioprinting matrix material.
[0009] Another object of the present invention is to provide the application of the above-mentioned 3D bioprinting matrix material in 3D bioprinting, particularly for the preparation of cell scaffold materials by 3D printing technology.
[0010] The 3D bioprinting matrix material of this invention has excellent biocompatibility. The bioscaffold material prepared using it can achieve excellent cell adhesion and proliferation. It also has a low critical gel concentration, which solves the problem of the human health hazards of high concentrations of F127. Its suitable temperature sensitivity allows it to be formed and remain stable in a body temperature environment.
[0011] The objective of this invention is achieved through the following solution:
[0012] In a first aspect, the present invention provides a 3D bioprinting matrix material based on zein, which is obtained by reacting terminal alkyne Prönnick F127 with polypeptide-modified zein.
[0013] In the technical solution of the present invention, the mass ratio of the polypeptide-modified zein to terminal alkyne Prönnick F127 can be 1:1-1:100; more preferably 1:1-1:20.
[0014] Furthermore, the reaction conditions can be a stirred reaction at 30-70°C for 6-24 days.
[0015] Furthermore, the reaction is carried out under the catalysis of copper sulfate pentahydrate and sodium ascorbate. The mass ratio of copper sulfate pentahydrate to sodium ascorbate used can be 0.4:0.6.
[0016] Furthermore, the mass ratio of the system of copper sulfate pentahydrate and sodium ascorbate to the mass of the polypeptide-modified zein can be 0.5:1-1.5:1.
[0017] Furthermore, the reaction is carried out in an inert gas atmosphere, such as nitrogen; the reaction solvent may be dimethyl sulfoxide (DMSO).
[0018] Furthermore, after the reaction is completed, the product can be obtained by dialysis, lyophilization, or other treatments, such as dialysis using a MWCO=50000 dialysis bag.
[0019] In the technical solution of the present invention, the terminal alkyne-based Prönnick F127 can be obtained by reacting Prönnick F127 with bromoalkynes.
[0020] Furthermore, the bromoalkynyl is a compound with bromine substitution at one end and an alkyne group at the other end, such as 3-bromopropyne, 4-bromo-1-butyne, etc.
[0021] Furthermore, the mass ratio of Prönnik F127 to bromoalkynylene used can be 1:0.1-1:10. The reaction time can be reflux for 6-24 hours. The reaction is preferably carried out in an organic solvent environment, such as tetrahydrofuran.
[0022] Furthermore, the reaction is carried out under the catalysis of a strong base, such as sodium hydride, sodium hydroxide, or potassium hydroxide. The amount of strong base used can be 20-50 wt% of the mass of Prönnicke F127.
[0023] Furthermore, after the reaction is complete, the supernatant is separated and precipitated with diethyl ether to obtain the product; and it can be further dried.
[0024] In the technical solution of the present invention, the polypeptide-modified zein can be obtained by reacting zein with γ-2-azidoethyl-L-glutamate N-carboxylic acid anhydride through ring-opening polymerization.
[0025] Furthermore, the mass ratio of γ-2-azidoethyl-L-glutamate N-carboxylic acid anhydride to zein can be 1:1 to 1:10.
[0026] Furthermore, the reaction solvent can be N,N-dimethylformamide (DMF); the reaction is carried out under an inert gas atmosphere, such as nitrogen. The reaction can be carried out at room temperature, preferably with stirring for 1-5 days.
[0027] Furthermore, after the reaction is complete, diethyl ether is added to precipitate the product; and the product can be further dried under vacuum to obtain the final product.
[0028] Furthermore, the γ-2-azidoethyl-L-glutamate N-carboxylic acid anhydride can be prepared by conventional methods.
[0029] Secondly, the present invention provides a method for preparing the above-mentioned 3D bioprinting matrix material.
[0030] This invention first obtains polypeptide-modified zein through ring-opening polymerization of N-carboxylic acid anhydride monomers, and then grafts Pluronic F127 onto the polypeptide chain segments to obtain a 3D bioprinting matrix material that has a significantly reduced critical gel concentration, excellent biocompatibility, is safe and non-toxic, and has excellent mechanical properties, meeting the requirements and application scenarios of 3D printing.
[0031] Thirdly, the present invention also provides the application of the above-mentioned 3D bioprinting matrix material in 3D bioprinting, particularly for the preparation of cell scaffold materials by 3D printing technology.
[0032] The 3D bioprinting matrix material of this invention has excellent biocompatibility. The bioscaffold material prepared using it can achieve excellent cell adhesion and proliferation. It also has a low critical gel concentration, which solves the problem of the human health hazards of high concentrations of F127. Its suitable temperature sensitivity allows it to be formed and remain stable in a body temperature environment.
[0033] Fourthly, the present invention also provides a 3D printing method for the above-mentioned 3D bioprinting matrix material, specifically including the following steps: dissolving the 3D bioprinting matrix material in a solvent under low temperature conditions, equilibrating it at room temperature, and then printing it using a 3D bioprinter.
[0034] Furthermore, the low-temperature condition refers to a temperature of 2-10℃.
[0035] Furthermore, the solvent may be water or PBS buffer (pH=7.4).
[0036] Furthermore, the room temperature refers to a temperature of 20-25℃.
[0037] Furthermore, the equilibration time is preferably 3 hours or more.
[0038] Furthermore, the temperature of the printing platform can be controlled at 37±5℃.
[0039] The 3D bioprinting matrix material of the present invention has temperature-sensitive properties. It is in a flowable sol state at room temperature (25°C) and in a gel state at body temperature. Therefore, the bioscaffold material prepared using it can be formed and exist stably in a body temperature environment.
[0040] The present invention has the following advantages and effects compared with the prior art:
[0041] (1) The main components of the 3D bioprinting matrix material of the present invention are zein, polypeptide chain segments and Pluronic F127, all of which have good biocompatibility and are safe and non-toxic.
[0042] (2) The 3D bioprinting matrix material of the present invention has temperature-sensitive properties. It is in a flowable sol state at room temperature (25°C) and in a gel state at body temperature.
[0043] (3) The 3D bioprinting matrix material of the present invention has a significantly lower critical gel concentration than Pluronic F127. It can maintain a stable gel state even at a concentration as low as 4%, which solves the problem of the high human health hazards of F127 and can be formed and exist stably in a body temperature environment.
[0044] (4) The 3D bioprinting matrix material of the present invention has good biocompatibility and can be used as a 3D bioprinting matrix material, especially for the preparation of cell scaffold materials. Attached Figure Description
[0045] To more clearly illustrate the technical solutions of the embodiments of the present invention, the accompanying drawings used in the embodiments will be briefly introduced below. It should be understood that the following drawings only show some embodiments of the present invention and should not be regarded as a limitation on the scope. For those skilled in the art, other related drawings can be obtained based on these drawings without creative effort.
[0046] Figure 1 This is the NMR spectrum of the 3D bioprinting matrix material of the present invention.
[0047] Figure 2 This is a state diagram of the 3D bioprinting matrix material solution of the present invention. Among them, (a) is a flowable sol state at room temperature (25°C); (b) is a gelled state at body temperature (37°C).
[0048] Figure 3 This is a cross-sectional view of the lyophilized gel prepared from the 3D bioprinting matrix material of the present invention.
[0049] Figure 4 This is a cross-sectional view of the freeze-dried gel prepared by Prönkel F127.
[0050] Figure 5 This is a test curve of the gelation time of gels prepared at different concentrations of the 3D bioprinting matrix material of the present invention.
[0051] Figure 6 This is a graph showing the proliferation of mouse bone marrow mesenchymal stem cells on a scaffold material. *P < 0.05. Detailed Implementation
[0052] The present invention will be further described in detail below with reference to embodiments, but the implementation of the present invention is not limited thereto. Unless otherwise specified, all materials involved in the following embodiments are commercially available. Unless otherwise specified, all methods described are conventional methods. All components are expressed in parts by mass and parts by volume, in g and mL.
[0053] Example 1: Preparation of 3D bioprinting matrix materials
[0054] (1) Preparation of γ-2-azidoethyl-L-glutamic acid: L-glutamic acid (20.00 parts by mass) was dispersed in 50 parts by volume of 2-azidoethanol, cooled to 0°C, and concentrated sulfuric acid (8 parts by volume, 98%) was added dropwise over 30 min. The mixture was stirred overnight at room temperature and then slowly poured into 200 parts by volume of triethylamine. The precipitate was obtained by filtration and washed with methanol to obtain the product γ-2-azidoethyl-L-glutamic acid.
[0055] (2) Preparation of γ-2-azidoethyl-L-glutamate N-carboxylic acid anhydride: Under nitrogen protection, γ-2-azidoethyl-L-glutamic acid (5.00 parts by mass) was dispersed in 100 parts by volume of dry THF. The mixture was heated to 50°C, and phosgene (3.90 parts by mass) was added. The solution immediately became clear. After reacting for 30 min, the mixture was cooled to room temperature, and the solvent was removed by rotary evaporation. The brown oily substance was dissolved in 100 parts by volume of ethyl acetate and washed with a saturated sodium bicarbonate ice-water solution until no gas was produced. The solution was then washed three times with ice water. The organic phase was dried with anhydrous magnesium sulfate and then rotary evaporated to obtain the brown oily product γ-2-azidoethyl-L-glutamate N-carboxylic acid anhydride.
[0056] (3) Preparation of polypeptide-modified zein: γ-2-azidoethyl-L-glutamate N-carboxylic acid anhydride (3 parts by mass) was dissolved in 200 parts by volume of dry N,N-dimethylformamide, and zein (15 parts by mass) was added under nitrogen protection. The mixture was stirred at room temperature for 3 days. After the reaction was completed, the product was precipitated with diethyl ether and dried under vacuum to obtain the product.
[0057] (4) Preparation of terminal alkyne F127: Pranic F127 (10 parts by mass) was dissolved in 100 parts by volume of dry tetrahydrofuran, sodium hydride (0.32 parts by mass) was added at 30°C, and after reacting for 2 h, bromopropyne (0.60 parts by volume) was added. After refluxing for 12 h, the mixture was centrifuged and the supernatant was collected. The supernatant was precipitated three times with diethyl ether and then dried to obtain the product.
[0058] (5) Preparation of 3D bioprinting matrix material: Polypeptide-modified zein (0.10 parts by mass) and terminal alkyne F127 (0.20 parts by mass) were dissolved in 30 parts by volume of DMSO. Under nitrogen protection, an appropriate amount of copper sulfate pentahydrate (0.04 parts by mass) was added. After purging with nitrogen for 10 min, sodium ascorbate (0.06 parts by mass) was added. The mixture was stirred at 50 °C for 3 days. Dialysis was performed using a MWCO=50000 dialysis bag for 3 days. The product (ZF-1) was obtained by freeze drying.
[0059] (6) ZF-1 was dissolved in 10 mL of PBS (pH = 7.4) at 4 °C. The solution was placed in a stainless steel container and equilibrated at 20 °C for at least 3 hours. The solution was then printed using a 3D bioprinter with the printing platform temperature controlled at 37 °C to obtain the ZF-1 scaffold material.
[0060] Example 2: Preparation of 3D bioprinting matrix materials
[0061] (1) Preparation of γ-2-azidoethyl-L-glutamic acid: L-glutamic acid (20.00 parts by mass) was dispersed in 50 parts by volume of 2-azidoethanol, cooled to 0°C, and concentrated sulfuric acid (8 parts by volume, 98%) was added dropwise over 30 min. The mixture was stirred overnight at room temperature and then slowly poured into 200 parts by volume of triethylamine. The precipitate was obtained by filtration and washed with methanol to obtain the product γ-2-azidoethyl-L-glutamic acid.
[0062] (2) Preparation of γ-2-azidoethyl-L-glutamate N-carboxylic acid anhydride: Under nitrogen protection, γ-2-azidoethyl-L-glutamic acid (5.00 parts by mass) was dispersed in 100 parts by volume of dry THF. The mixture was heated to 50°C, and phosgene (3.90 parts by mass) was added. The solution immediately became clear. After reacting for 30 min, the mixture was cooled to room temperature, and the solvent was removed by rotary evaporation. The brown oily substance was dissolved in 100 parts by volume of ethyl acetate and washed with a saturated sodium bicarbonate ice-water solution until no gas was produced. The solution was then washed three times with ice water. The organic phase was dried with anhydrous magnesium sulfate and then rotary evaporated to obtain the brown oily product γ-2-azidoethyl-L-glutamate N-carboxylic acid anhydride.
[0063] (3) Preparation of polypeptide-modified zein: γ-2-azidoethyl-L-glutamate N-carboxylic acid anhydride (3 parts by mass) was dissolved in 200 parts by volume of dry N,N-dimethylformamide, and zein (9 parts by mass) was added under nitrogen protection. The mixture was stirred at room temperature for 3 days. After the reaction was completed, the product was precipitated with diethyl ether and dried under vacuum to obtain the product.
[0064] (4) Preparation of terminal alkyne F127: Pranic F127 (10 parts by mass) was dissolved in 100 parts by volume of dry tetrahydrofuran, sodium hydride (0.32 parts by mass) was added at 30°C, and after reacting for 2 h, bromopropyne (0.60 parts by volume) was added. After refluxing for 12 h, the mixture was centrifuged and the supernatant was collected. The supernatant was precipitated three times with diethyl ether and then dried to obtain the product.
[0065] (5) Preparation of 3D bioprinting matrix material: Polypeptide-modified zein (0.10 parts by mass) and terminal alkyne F127 (0.30 parts by mass) were dissolved in 30 parts by volume of DMSO. Under nitrogen protection, an appropriate amount of copper sulfate pentahydrate (0.04 parts by mass) was added. After purging with nitrogen for 10 min, sodium ascorbate (0.06 parts by mass) was added. The mixture was stirred at 50 °C for 3 days. Dialysis was performed using a MWCO=50000 dialysis bag for 3 days. The product (ZF-2) was obtained by freeze drying.
[0066] (6) Dissolve ZF-2 in 10 mL PBS (pH = 7.4) at 4 °C. Pour the solution into a stainless steel container and equilibrate at 20 °C for at least 3 hours. Print using a 3D bioprinter with the printing platform temperature controlled at 37 °C to obtain ZF-2 scaffold material.
[0067] Example 3: Preparation of 3D bioprinting matrix materials
[0068] (1) Preparation of γ-2-azidoethyl-L-glutamic acid: L-glutamic acid (20.00 parts by mass) was dispersed in 50 parts by volume of 2-azidoethanol, cooled to 0°C, and concentrated sulfuric acid (8 parts by volume, 98%) was added dropwise over 30 min. The mixture was stirred overnight at room temperature and then slowly poured into 200 parts by volume of triethylamine. The precipitate was obtained by filtration and washed with methanol to obtain the product γ-2-azidoethyl-L-glutamic acid.
[0069] (2) Preparation of γ-2-azidoethyl-L-glutamate N-carboxylic acid anhydride: Under nitrogen protection, γ-2-azidoethyl-L-glutamic acid (5.00 parts by mass) was dispersed in 100 parts by volume of dry THF. The mixture was heated to 50°C, and phosgene (3.90 parts by mass) was added. The solution immediately became clear. After reacting for 30 min, the mixture was cooled to room temperature, and the solvent was removed by rotary evaporation. The brown oily substance was dissolved in 100 parts by volume of ethyl acetate and washed with a saturated sodium bicarbonate ice-water solution until no gas was produced. The solution was then washed three times with ice water. The organic phase was dried with anhydrous magnesium sulfate and then rotary evaporated to obtain the brown oily product γ-2-azidoethyl-L-glutamate N-carboxylic acid anhydride.
[0070] (3) Preparation of polypeptide-modified zein: γ-2-azidoethyl-L-glutamate N-carboxylic acid anhydride (3 parts by mass) was dissolved in 200 parts by volume of dry N,N-dimethylformamide, and zein (3 parts by mass) was added under nitrogen protection. The mixture was stirred at room temperature for 3 days. After the reaction was completed, the product was precipitated with diethyl ether and dried under vacuum to obtain the product.
[0071] (4) Preparation of terminal alkyne F127: Pranic F127 (10 parts by mass) was dissolved in 100 parts by volume of dry tetrahydrofuran, sodium hydride (0.32 parts by mass) was added at 30°C, and after reacting for 2 h, bromopropyne (0.60 parts by volume) was added. After refluxing for 12 h, the mixture was centrifuged and the supernatant was collected. The supernatant was precipitated three times with diethyl ether and then dried to obtain the product.
[0072] (5) Preparation of 3D bioprinting matrix material: Polypeptide-modified zein (0.10 parts by mass) and terminal alkyne F127 (1.00 parts by mass) were dissolved in 30 parts by volume of DMSO. Under nitrogen protection, an appropriate amount of copper sulfate pentahydrate (0.04 parts by mass) was added. After purging with nitrogen for 10 min, sodium ascorbate (0.06 parts by mass) was added. The mixture was stirred at 50 °C for 3 days. Dialysis was performed using a MWCO=50000 dialysis bag for 3 days. The product (ZF-3) was obtained by freeze drying.
[0073] (6) Dissolve ZF-3 in 10 mL of PBS (pH = 7.4) at 4 °C. Pour the solution into a stainless steel container and equilibrate at 20 °C for at least 3 hours. Print using a 3D bioprinter with the printing platform temperature controlled at 37 °C to obtain ZF-3 scaffold material.
[0074] The products and scaffolds prepared in the examples were tested:
[0075] (1) Nuclear magnetic resonance analysis of the 3D bioprinting matrix material of the present invention. Figure 1 ZF-2, the 3D bioprinting matrix material in Example 2, was used in d 6 The NMR spectrum in DMSO clearly shows the NMR peaks of zein and the F127 structure, confirming the successful synthesis of the zein-F127 graft. Other examples yielded similar results, which will not be detailed here.
[0076] (2) The 3D bioprinting matrix material of the present invention was dissolved in PBS (pH=7.4) and its gelation state was observed under different temperature conditions. Figure 2 This is a state diagram of a 10wt% solution of the ZF-2 3D bioprinting matrix material from Example 2. As can be seen from the diagram, at room temperature, the material solution of this invention is in a flowable sol state, while at body temperature it transforms into a gel state, exhibiting excellent temperature sensitivity. Results for other examples are similar and will not be described in detail.
[0077] (3) After the above gel is freeze-dried, observe its cross section. Figure 3 This is a cross-sectional view of the 10wt% ZF-2 gel lyophilized from the 3D bioprinting matrix material in Example 2. The clear gel pore structure is clearly visible in the figure. Results from other examples are similar and will not be described in detail. Figure 4 The image shows a cross-sectional view of F127 in a 20wt% gel lyophilized state. It can be seen that the pores are dense, and the overly dense pore structure is not conducive to cell survival and proliferation.
[0078] (4) The gelation time of the 3D bioprinting matrix material of the present invention at different concentrations was detected at 37°C. The results are shown in the figure. Figure 5As shown in the figure, the material of this invention exhibits a significantly reduced gel concentration, achieving rapid gelation at body temperature even at concentrations as low as 4 wt%, while F127 gel requires concentrations as high as 20% to achieve gelation transition. Figure 5 b). This invention confirms that the 3D bioprinting matrix material of this invention can rapidly gel at low concentrations. It solves the problem of the high critical gel concentration of Pluronic F127 in existing technologies, which poses a hazard to human health, while also allowing it to form and remain stable at body temperature.
[0079] (5) Following the method of Example 2, a scaffold material was prepared using the 3D bioprinting matrix of the present invention via 3D bioprinting technology, sterilized by UV irradiation for 2 hours, and placed in a confocal dish. Human bone marrow mesenchymal stem cells (hMSCs) were then added at a ratio of 1×10⁻⁶. 4 Cells were seeded at a density of 1 / well onto a 3D-printed hydrogel scaffold, cultured in a culture medium specifically for human bone marrow mesenchymal stem cells, and cell proliferation was observed. Figure 6 The figures show the proliferation of mouse bone marrow mesenchymal stem cells cultured on ZF-2 scaffold material for 1, 3, and 7 days. As can be seen from the figures, the cells exhibit excellent adhesion and proliferation on the scaffold material, showing a significantly improved effect compared to F127, indicating that the material of this invention has excellent biocompatibility.
[0080] The above embodiments are preferred embodiments of the present invention, but the embodiments of the present invention are not limited to the above embodiments. Any changes, modifications, substitutions, combinations, or simplifications made without departing from the spirit and principle of the present invention shall be considered equivalent substitutions and shall be included within the protection scope of the present invention.
Claims
1. A 3D bioprinting matrix material based on zein, characterized in that... It is obtained by reacting terminal alkyne-terminated Pluronic F127 with polypeptide-modified zein at 30-70℃ for 1-5 days in a mass ratio of 1:1-1:
100. The terminal alkyne-based Prönnick F127 is obtained by reacting Prönnick F127 with bromoalkynes in a mass ratio of 1:0.1-1:10 under reflux catalysis in an organic solvent environment for 6-24 hours. The polypeptide-modified zein was obtained by ring-opening polymerization of γ-2-azidoethyl-L-glutamate N-carboxylic acid anhydride with zein in a reaction solvent and stirring at room temperature for 1-5 days. The mass ratio of γ-2-azidoethyl-L-glutamate N-carboxylic acid anhydride to zein was 1:1-1:
10.
2. The application of the 3D bioprinting matrix material according to claim 1 in 3D bioprinting.
3. The application of the 3D bioprinting matrix material according to claim 1 in the preparation of cell scaffold materials by 3D printing technology.
4. A 3D printing method based on the 3D bioprinting matrix material according to claim 1, characterized in that... Specifically, the following steps are included: Under low temperature conditions, the 3D bioprinting matrix material described in claim 1 is dissolved in a solvent, equilibrated at room temperature, and then printed using a 3D bioprinter.