CN115382028A - A kind of degradable stapler material and its preparation method and application - Google Patents

Abstract

The invention discloses a degradable stapler material and its preparation method and application, comprising a multi-layer composite stapler body, the stapler body includes a metal layer, a drug layer and an antibacterial protective layer, and the metal layer, a drug layer and an antibacterial protective layer Composite to form a cylindrical stapler body. The four-layer composite structure of the present invention, in addition to the strength and mechanical properties of traditional pure metal staplers, also includes a slow-release layer for therapeutic drugs, a slow-release layer for growth-promoting factors, and an antibacterial protective layer, which can treat wounds while anastomosis Inflammation, wound canceration, accelerated wound healing, and the effect of preventing bacterial infection of the wound. At the same time, the material itself will slowly degrade into non-toxic small molecules as the wound heals in the body, which will be eliminated through the body's metabolism, avoiding secondary damage caused by the removal of the stapler. Secondary injury; the present invention adopts zinc-iron composite metal, has more suitable degradation rate, mechanical strength and biocompatibility with respect to pure zinc, pure magnesium, pure iron, and zinc alloy material, magnesium alloy material.

Description

A kind of degradable stapler material and its preparation method and application

technical field

The invention relates to the technical field of medical equipment, in particular to a degradable stapler material and a preparation method thereof.

Background technique

Stapler is a device used in medicine to replace manual suturing. The main working principle is to use the device to cut or staple tissue, similar to a stapler. According to the scope of application, it can be divided into skin staplers, digestive tract (esophagus, gastrointestinal, etc.) circular staplers, rectal staplers, circular hemorrhoid staplers, circumcision staplers, blood vessel staplers, hernia staplers , Lung cutting stapler, etc.

Traditional medical staplers use titanium alloys, nickel alloys, and tantalum alloys with excellent stability. Although they have good biocompatibility, their chemical properties are extremely stable, and they will remain in the body for a long time after surgical suturing. Surgical removal, causing secondary damage. In recent years, biodegradable materials have attracted more and more attention, including biodegradable polymer materials, inorganic nanomaterials, and organic-inorganic hybrid materials. Their unique biodegradable properties make them widely used in the field of biomedicine. widely used. However, the existing degradable stapler materials have single performance and single function.

Contents of the invention

In view of the deficiencies in the above-mentioned background technology, the present invention proposes a degradable stapler material and its preparation method, which solves the problem of single performance of the stapler in the prior art.

Technical scheme of the present invention is realized like this:

A degradable stapler material includes a multi-layer composite stapler body. The stapler body includes a metal layer, a drug layer and an antibacterial protective layer. The metal layer, the drug layer and the antibacterial protective layer are composited to form a cylindrical stapler body.

Further, the middle layer includes a therapeutic drug slow-release layer and a growth-promoting factor sustained-release layer, and the growth-promoting factor sustained-release layer is wrapped outside the therapeutic drug sustained-release layer.

Further, the metal layer has a filamentous structure, and the slow-release layer of therapeutic drug, slow-release layer of growth-promoting factor and protective layer are wrapped on the metal layer from inside to outside to form a columnar stapler body.

A method for preparing a degradable stapler material, including a method for preparing a metal layer, the method for preparing a metal layer includes the following steps:

A1. Prepare zinc sulfate dihydrate and ferric sulfate tetrahydrate into aqueous solutions with a concentration of 0.2-0.6 mol/liter and 0.5-0.8 mol/liter respectively, and then prepare an aqueous solution of sodium citrate with a concentration of 0.2-0.5 mol/liter. It is 0.1-0.3 mol/liter boric acid aqueous solution, and the concentration is 0.15-0.25 mol/liter sodium dihydrogen phosphate aqueous solution;

A2. The solution configured in step A1 is according to the volume ratio of zinc sulfate dihydrate solution: ferric sulfate tetrahydrate solution: sodium citrate aqueous solution: boric acid aqueous solution: sodium dihydrogen phosphate aqueous solution 2-3:3-5:5-7: Mix 3-7:2-5, then add short carbon fibers 0.2-0.35 times the mass of all materials, add a mixed solution of hydrochloric acid/sulfuric acid with a concentration of 1 mol/liter, adjust the pH of the system to 3-4, and the system at 30- Continue stirring for 30 minutes at 35°C to obtain a composite metal ion solution;

A3. Use graphite as the anode, and a thin iron wire with a diameter of 0.05-0.1 mm as the cathode. The cathode is first polished with sandpaper, and then the surface is cleaned 3 times with absolute ethanol and 3 times with acetone; the composite metal ion obtained in step A2 The solution is added to the electrolytic cell, and the cathode and anode are also placed in the electrolytic cell; then electrodeposited for 4 hours at a temperature of 40-55 ° C and a current density of 20-35 mA/cm2 to obtain the metal layer. Substrate.

Further, the therapeutic drug slow-release layer is a glutathione (GSH)-responsive and redox-species (ROS)-responsive polymer prodrug gel grown on the surface of the metal layer.

Further, the preparation method of the therapeutic drug slow-release layer comprises the following steps:

B1. modify the camptothecin linked by disulfide bond, the doxorubicin linked by disulfide bond, the camptothecin linked by phenylboronic acid trigger motif and the doxorubicin linked by phenylboronic acid trigger motif on the acrylic acid monomer, the above The four monomers are mixed together in an equal molar ratio, adding 0.1-0.5% of the total mass of azobisisobutyronitrile, adding 1-3 times the total mass of N-methylpyrrolidone solution, and stirring at room temperature for 30 minutes to obtain polymerization system;

B2. The substrate of the metal layer obtained in step A3 is stretched and polished to obtain a cylindrical composite metal filament with a diameter of 0.3-0.5 mm; The surface is treated under plasma conditions, and the composite metal filaments treated with argon gas plasma are put into the polymerization system obtained in step B1, and the metal filaments are evenly arranged;

B3. Then vacuumize the entire polymerization system, replace it with an argon environment, and polymerize at 150°C for 2-3 hours; cool the system to room temperature naturally, and take out the metal filament; then polish the gel layer on the surface of the metal filament A composite metal filament containing a drug release layer with a uniform thickness and a diameter of 0.5-0.6 mm is obtained.

Further, the argon plasma treatment conditions are as follows: voltage 2-3.5V, current 0.8-1.5A, single treatment time 30 minutes, a total of 10 treatments.

Further, the growth-promoting factor slow-release layer is a composite layer of polymer-modified fibrin loaded with epidermal growth factor, natural aloe gel and polymethyl alkyl ether, and the preparation method of the growth-promoting factor slow-release layer Include the following steps:

C1. The succinate polypropylene with a molecular weight of 350-600W side group modified ester bond and fibrin are mixed in a molar mass ratio of 1:20-30, and added to a phosphate buffered saline solution with a pH equal to 7.4, stirring at 37°C for 4 hours, then adding epidermal growth factor, stirring at 37°C for 12 hours, and freeze-drying to obtain polymer-modified fibrin loaded with epidermal growth factor;

C2. then the polymer modified fibrin loaded with epidermal growth factor that step C1 obtains: natural aloe vera gel: polymethyl alkyl ether mixes by mass ratio 3-5:1-2:1-1.5, adds anhydrous Ethanol, stirred at 37°C for 2 hours, then put the composite metal filaments containing the drug-releasing layer into the system, soaked at 37°C for 4 hours; took out the filaments and dried them naturally, and then polished the filaments to obtain uniform thickness, Filamentous material with a diameter of 0.6-0.7 mm.

Further, the antibacterial protective layer is a composite material layer composed of various polymer components, and the preparation method of the antibacterial protective layer is as follows:

Polylysine, poly[2-methacrylic acid-2-methyl-(N,N-dimethylamino)ethyl ester], [−(N,N-−dimethylamino)ethyl ester] and ester group The end-capped polyphenylcarbamate is mixed according to the mass ratio: 2-3:3-4:2-5:1-2, and then the mixed system is heated and melted at 150-200°C, and the prepared step C2 The filament material with a three-layer structure is quickly pulled through the molten liquid, so that its surface is evenly coated with a layer of polymer layer, and cooled naturally at room temperature; after grinding and polishing, it is uniform in thickness and about 0.8-0.9 mm in diameter. Biodegradable stapler material.

Further, the metal layer is used to stabilize the shape of the stapler; the therapeutic drug slow-release layer activates and releases the drug contained inside when the tissue is lesioned, and is used for inflammation treatment or killing harmful cells; The growth-promoting factor slow-release layer is used for slowly releasing cell growth-promoting factors to accelerate the recovery of the wound site; the antibacterial protective layer is used to prevent bacterial infection at the wound site.

Beneficial effects of the present invention: the present invention has a four-layer structural composite material, which has the same strength and mechanical properties as traditional pure metal stapler materials; at the same time, the present invention includes a therapeutic drug slow-release layer, a growth-promoting factor slow-release layer and antibacterial protection While anastomosing the wound, it can also treat wound inflammation, wound canceration, accelerate wound healing, and prevent bacterial infection of the wound. At the same time, the material itself will slowly degrade into non-toxic small molecules as the wound heals in the body. , cleared through the body's metabolism, avoiding the secondary damage caused by the removal of the stapler; the present invention uses zinc-iron composite metal, which has a more suitable degradation rate than pure zinc, pure magnesium, pure iron, and zinc alloy materials and magnesium alloy materials. speed, mechanical strength and biocompatibility.

Description of drawings

In order to illustrate the embodiments of the present invention more clearly, the accompanying drawings used in the description of the embodiments will be briefly introduced below. Obviously, the accompanying drawings in the following description are only some embodiments of the present invention. As far as the skilled person is concerned, other drawings can also be obtained based on these drawings on the premise of not paying creative work.

Fig. 1 is a schematic structural view of the degradable stapler material of the present invention;

Figure 2 is a schematic structural view of the disulfide bond triggering motif of the present invention;

Fig. 3 is a schematic structural view of the phenylboronic acid trigger unit of the present invention.

Detailed ways

The following will clearly and completely describe the technical solutions in the embodiments of the present invention with reference to the accompanying drawings in the embodiments of the present invention. Obviously, the described embodiments are only some, not all, embodiments of the present invention. Based on the embodiments of the present invention, all other embodiments obtained by persons of ordinary skill in the art without making creative efforts belong to the protection scope of the present invention.

As shown in Figure 1, a degradable stapler material described in Example 1, specifically, the degradable stapler material is a multilayer overlapping cylindrical material, which is divided into four layers, respectively It is the metal layer of the core layer, the second layer of therapeutic drug release layer, the third layer of growth-promoting factor slow-release layer and the fourth layer of antibacterial protective layer. As shown in FIG. 1 , the core layer is a metal layer of a metal composite material, which is used to stabilize the shape of the stapler and the mechanical properties of the material.

A method for preparing a degradable stapler material, including a method for preparing a metal layer, the method for preparing the metal layer is as follows: configure zinc sulfate dihydrate into an aqueous solution with a concentration of 0.4 mol/liter, and configure 0.6 mol/liter of sulfuric acid tetrahydrate Aqueous iron solution, then configuration concentration is the sodium citrate aqueous solution of 0.3 mol/liter, the concentration is the boric acid aqueous solution of 0.25 mol/liter, and the concentration is the sodium dihydrogen phosphate aqueous solution of 0.2 mol/liter. Then mix according to the volume ratio of zinc sulfate dihydrate solution:: ferric sulfate tetrahydrate solution: sodium citrate solution: boric acid solution: sodium dihydrogen phosphate solution volume ratio 2:3:5:5:3, and then add 0.3 times the mass of all materials Short carbon fiber, add a mixed solution of hydrochloric acid/sulfuric acid with a concentration of 1 mol/liter, adjust the pH value of the system to 3.5, and keep stirring the system at 35°C for 30 minutes to obtain a composite metal ion solution. Then graphite is used as the anode, and a thin iron wire with a diameter of 0.05 mm is used as the cathode. The cathode is firstly polished with sandpaper, and then the surface is cleaned with absolute ethanol for 3 times and acetone for 3 times. The metal ion solution is added to the electrolytic cell, and the negative and positive electrodes are also placed in the electrolytic cell. Then electrodeposit for 4 hours under the conditions of 40-55° C. and current density of 25-35 mA/cm2. Obtain the base material of the metal layer.

The product was placed in a simulated body fluid (Hank's solution) at 37°C for an experiment in vitro, and the measured corrosion rate was 0.20mm/year, which can meet people's needs for use.

As shown in Figure 1, the second therapeutic drug slow-release layer is a layer of glutathione (GSH)-responsive and redox-species (ROS)-responsive polymer prodrugs grown on the substrate surface of the metal layer gel. This layer will activate when the tissue becomes lesioned, activate, and release the drugs contained in it, such as inflammation or cancer, and release the drugs contained in it to treat inflammation or kill cancer cells. The specific preparation method of the polymer prodrug gel is as follows: modify the camptothecin linked by the disulfide bond, the doxorubicin linked by the disulfide bond, and the camptothecin linked by the phenylboronic acid trigger element on the acrylic acid monomer 1. Doxorubicin connected with phenylboronic acid trigger unit, mix the above four monomers together in equal molar ratio, add 0.2% of the total mass of azobisisobutyronitrile, and add 1-3 times the total mass of N-formazycin The base pyrrolidone solution was stirred at room temperature for 30 minutes to obtain a polymerization system. The base material of the metal layer of the core layer is stretched and polished to obtain cylindrical composite metal filaments with uniform thickness and diameter of 0.3 mm. Then, the surface of the cylindrical composite metal filament is treated under the condition of argon plasma, so that the polymer gel layer can be bonded more firmly on the surface of the metal composite. Specifically, the argon plasma treatment conditions are: voltage 2-3.5V, current 1-1.5A, single treatment time 30 minutes, a total of 10 treatments. The composite metal filaments treated with argon gas plasma are put into the polymerization system, and the metal filaments are evenly arranged. Then the whole system is evacuated, replaced with an argon environment, and polymerized at 150° C. for 2-3 hours, so that a polymer gel layer is formed on the surface of the metal filament. The system was naturally cooled to room temperature, and the metal filaments were taken out. Then, the gel layer on the surface of the metal filament is polished to obtain a composite metal filament with a uniform thickness and a diameter of 0.5 mm containing a drug releasing layer.

Specifically, the triggering motifs in the monomers of the glutathione (GSH) responsive and redox species (ROS) responsive polymer prodrug gels include disulfide bond triggering motifs and phenylboronic acid triggering motifs , the specific structure is shown in Figure 2 and Figure 3, Figure 2 is a disulfide bond triggering motif, Figure 3 is a phenylboronic acid triggering motif, and the values of n and m are 4-100.

Weigh 1 mg of the above-prepared drug-releasing layer gel material loaded with camptothecin and doxorubicin, add 10 ml of PBS into an EP tube, mix evenly, shake at 37°C, and set the temperature at 0h, 1h, 2h, 4h, 8h, 12h, respectively. At 24h, 48h, and 72h, ELISA kits were used to monitor the drug release concentration in the supernatant. The control group was pure unprocessed medicine.

Table 1 The results of in vitro sustained release of therapeutic drug sustained release layer (%)

As shown in FIG. 1 , the function of the growth-promoting factor slow-release layer of the third layer is to slowly release cell growth-promoting factors to achieve the purpose of rapid wound recovery. Specifically, the slow-release layer of the growth-promoting factor is composed of polymer-modified fibrin loaded with epidermal growth factor, natural aloe vera gel, and polymethyl alkyl ether composite layer. The specific preparation method is as follows: mix succinate polypropylene with a molecular weight of 350-600W side group modified ester bond and fibrin at a molar mass ratio of 1:25, and add it to a phosphate buffered saline solution with a pH equal to 7.4 , stirred at 37° C. for 4 hours, then added epidermal growth factor, stirred at 37° C. for 12 hours, and freeze-dried to obtain polymer-modified fibrin loaded with epidermal growth factor. Then the polymer-modified fibrin loaded with epidermal growth factor: natural aloe vera gel: polymethyl alkyl ether was mixed in a mass ratio of 3:1.5:1, added absolute ethanol, and stirred at 37°C for 2 Hours, and then put the composite metal filaments containing the drug-releasing layer into the system, and soak for 4 hours at 37°C. After taking out the filaments, air-dry them naturally, and then grind the filaments to obtain a filament material with a uniform thickness and a diameter of 0.6 mm.

The method for determining sustained release of drugs was as described above, and the control group was simple unprocessed drugs.

Table 2 In vitro sustained-release results of the growth-promoting factor sustained-release layer (%)

The effect of growth-promoting factor slow-release layer on the migration ability of fibroblasts was determined. Inoculate 1×106 fibroblasts in a six-well plate. When the cells proliferate to 80-90%, make scratches. Add serum-free medium containing growth-promoting factor slow-release layer to the experimental group, and add serum-free culture to the control group. After further culturing for 12 hours, the area of the scratch gap was compared. The area of the experimental group was (0.61±0.03) mm ² significantly lower than that of the control group (1.19±0.02) mm ² , indicating that the slow-release layer of growth-promoting factors improved the migration ability of fibroblasts.

As shown in Figure 1, the fourth layer of antibacterial protective layer has three main functions: 1. prevent the formation of bacterial film on the surface of the material itself; 2. release antibacterial factors to prevent bacterial infection at the wound site; Reinforces protective action against unwanted release of internal active content.

Specifically, the antibacterial protective layer is a composite material composed of various polymer components. The preparation method of the described antibacterial protective layer is as follows: polylysine: poly[2-methacrylic acid-2-methyl-(N,N-dimethylamino)ethyl]:poly[(N,N- −Dimethylamino)ethyl ester]: Ester-terminated polyphenylcarbamate is mixed in a mass ratio of 2:3.5:3:1, and then the mixed system is heated and melted at 150-200°C, and the above-mentioned Metal filaments with a three-layer structure are pulled quickly through the molten liquid, so that the surface is evenly covered with a layer of polymer layer, and cooled naturally at room temperature. After grinding and polishing, a degradable stapler material with a uniform thickness and a diameter of about 0.8 mm was obtained.

The antibacterial effect test method is as follows: the prepared degradable stapler containing antibacterial composite material and the degradable stapler without antibacterial composite material in the control group were respectively placed in a petri dish, and then coated with the same biodegradable stapler on the petri dish. Then put the petri dish into the incubator for storage, count the number of bacterial colonies after 24 hours, and calculate the bacteriostatic rate; the higher the bacteriostatic rate, the better the antibacterial effect.

Bacterial inhibition rate=((number of original colonies-number of colonies after 24h)/number of original colonies)×100%

Table 3 Antibacterial test results of antibacterial protective layer

Escherichia coli inhibition rate Staphylococcus aureus inhibition rate Degradable Stapler Containing Antibacterial Composite Materials 98.9% 98.4% Degradable Stapler Without Antimicrobial Composite 78.4% 69.7%

The above descriptions are only preferred embodiments of the present invention, and are not intended to limit the present invention. Any modifications, equivalent replacements, improvements, etc. made within the spirit and principles of the present invention shall be included in the scope of the present invention. within the scope of protection.

Claims (10)

1. A degradable stapler material, characterized in that: the anastomat comprises a multi-layer composite anastomat body, wherein the anastomat body comprises a metal layer, a medicine layer and an antibacterial protective layer, and the metal layer, the medicine layer and the antibacterial protective layer are compounded to form a cylindrical anastomat body.

2. The degradable stapler material of claim 1, wherein: the middle layer comprises a therapeutic drug sustained-release layer and a growth-promoting factor sustained-release layer, and the growth-promoting factor sustained-release layer is wrapped outside the therapeutic drug sustained-release layer.

3. The degradable stapler material of claim 2, wherein: the metal layer is of a filamentous structure, and the therapeutic drug slow-release layer, the growth promoting factor slow-release layer and the protective layer are wrapped on the metal layer by layer from inside to outside to form a columnar anastomat body.

4. A method of making a degradable stapler material according to any one of claims 1~3, wherein the method comprises: the preparation method of the metal layer comprises the following steps:

A1. preparing zinc sulfate dihydrate and ferric sulfate tetrahydrate into aqueous solutions with the concentrations of 0.2-0.6 mol/L and 0.5-0.8 mol/L respectively, and then preparing a sodium citrate aqueous solution with the concentration of 0.2-0.5 mol/L, a boric acid aqueous solution with the concentration of 0.1-0.3 mol/L and a sodium dihydrogen phosphate aqueous solution with the concentration of 0.15-0.25 mol/L;

A2. and B, mixing the solution prepared in the step A1 according to a zinc sulfate dihydrate solution: iron sulfate tetrahydrate solution: sodium citrate aqueous solution: boric acid aqueous solution: mixing sodium dihydrogen phosphate aqueous solution in a volume ratio of 2-3:3-5:5-7:3-7:2-5, adding short carbon fibers with the mass of 0.2-0.35 times of that of all the materials, adding a hydrochloric acid/sulfuric acid mixed solution with the concentration of 1 mol/liter, adjusting the pH value of the system to 3-4, and continuously stirring the system at 30-35 ℃ for 30 minutes to obtain a composite metal ion solution;

A3. taking graphite as an anode and a fine iron wire with the diameter of 0.05-0.1 mm as a cathode, polishing the cathode by using sand paper, cleaning the surface by using absolute ethyl alcohol for 3 times, and cleaning the surface by using acetone for 3 times; adding the composite metal ion solution obtained in the step A2 into an electrolytic bath, and placing the anode and the cathode into the electrolytic bath; and then electrodepositing for 4 hours under the conditions that the temperature is 40-55 ℃ and the current density is 20-35 milliampere/square centimeter to obtain the substrate of the metal layer.

5. The method for preparing a degradable stapler material according to claim 4, wherein: the therapeutic drug slow-release layer is formed by growing a layer of polymer prodrug gel with Glutathione (GSH) response and redox species (ROS) response on the surface of the metal layer.

6. The method for preparing a degradable stapler material according to claim 5, wherein: the preparation method of the therapeutic drug sustained-release layer comprises the following steps:

B1. modifying camptothecin connected by disulfide bonds, doxorubicin connected by disulfide bonds, camptothecin connected by phenylboronic acid trigger motifs and doxorubicin connected by phenylboronic acid trigger motifs on acrylic monomers, mixing the four monomers together according to an equal molar ratio, adding azodiisobutyronitrile with the total mass of 0.1-0.5%, adding N-methylpyrrolidone solution with the total mass of 1-3 times, and stirring at room temperature for 30 minutes to obtain a polymerization system;

B2. stretching and polishing the base material of the metal layer prepared in the step A3 to obtain cylindrical composite metal filaments with uniform thickness and diameters of 0.3-0.5 mm; then, processing the surface of the cylindrical composite metal filament under the condition of argon plasma, putting the composite metal filament processed by the argon plasma into the polymerization system obtained in the step B1, and uniformly distributing the metal filaments;

B3. then the whole polymerization system is vacuumized, replaced by an argon environment and polymerized for 2 to 3 hours at the temperature of 150 ℃; naturally cooling the polymerization system to room temperature, and taking out the metal filaments; then the polymer gel layer on the surface of the metal filament is polished to obtain the composite metal filament with uniform thickness and a drug-containing release layer with the diameter of 0.5-0.6 mm.

7. The method for preparing a degradable stapler material according to claim 6, wherein: the argon plasma treatment conditions are as follows: voltage is 2-3.5V, current is 0.8-1.5A, single treatment time is 30 minutes, and treatment is carried out for 10 times in total.

8. The method for preparing a degradable stapler material according to claim 7, wherein: the growth-promoting factor slow-release layer is a composite layer of polymer modified fibrin loaded epidermal growth factors, natural aloe gel and polymethyl alkyl ether, and the preparation method of the growth-promoting factor slow-release layer comprises the following steps:

C1. mixing succinate polypropylene with molecular weight of 350-600W and connected with a side group modified ester bond with fibrin according to a molar mass ratio of 1-20, adding the mixture into phosphate buffered saline solution with pH equal to 7.4, stirring the mixture at 37 ℃ for 4 hours, then adding epidermal growth factor, stirring the mixture at 37 ℃ for 12 hours, and freeze-drying the mixture to obtain polymer modified fibrin loaded with the epidermal growth factor;

C2. and then modifying the polymer loaded with the epidermal cell growth factor obtained in the step C1 with fibrin: natural aloe vera gel: mixing polymethyl alkyl ether according to the mass ratio of 3-5:1-2:1-1.5, adding absolute ethyl alcohol, stirring for 2 hours at 37 ℃, then putting the composite metal filament containing the drug release layer into the system, and soaking for 4 hours at 37 ℃; taking out the filaments, naturally drying the filaments, and then polishing the filaments to obtain the filament material with uniform thickness and diameter of 0.6-0.7 mm.

9. The method for preparing a degradable stapler material according to claim 8, wherein: the antibacterial protective layer is a composite material layer composed of a plurality of polymer components, and the preparation method of the antibacterial protective layer comprises the following steps:

polylysine, poly [ 2-methacrylic acid-2-methyl- (N, N-dimethylamino) ethyl ester ], [ - (N, N-dimethylamino) ethyl ester ] and ester group terminated polyphenyl carbamate are mixed according to the mass ratio: 2-3:3-4:2-5:1-2, heating and melting the mixed system at 150-200 ℃, rapidly pulling the filament material which is prepared in the step C2 and comprises a three-layer structure in molten liquid, uniformly wrapping the surface of the filament material with a polymer layer, and naturally cooling the filament material at room temperature; after grinding and polishing, the degradable anastomat material with uniform thickness and diameter of about 0.8-0.9 mm is obtained.

10. Use of the degradable stapler material of any one of claims 1~3, wherein: the metal layer is used for stabilizing the shape of the anastomat; the therapeutic drug slow-release layer activates and releases the drugs contained in the therapeutic drug slow-release layer when the tissues are diseased, and is used for treating inflammation or killing harmful cells; the growth-promoting factor slow-release layer is used for slowly releasing cell growth-promoting factors and accelerating the recovery of a wound part; the antimicrobial protective layer is used to prevent bacterial infection at the wound site.

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