CN113304304B - Drug-loaded degradable and absorbable medical suture and preparation method thereof - Google Patents
Drug-loaded degradable and absorbable medical suture and preparation method thereof Download PDFInfo
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- CN113304304B CN113304304B CN202110683459.6A CN202110683459A CN113304304B CN 113304304 B CN113304304 B CN 113304304B CN 202110683459 A CN202110683459 A CN 202110683459A CN 113304304 B CN113304304 B CN 113304304B
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- A61L17/00—Materials for surgical sutures or for ligaturing blood vessels ; Materials for prostheses or catheters
- A61L17/005—Materials for surgical sutures or for ligaturing blood vessels ; Materials for prostheses or catheters containing a biologically active substance, e.g. a medicament or a biocide
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- A61L17/00—Materials for surgical sutures or for ligaturing blood vessels ; Materials for prostheses or catheters
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- A61L2300/00—Biologically active materials used in bandages, wound dressings, absorbent pads or medical devices
- A61L2300/20—Biologically active materials used in bandages, wound dressings, absorbent pads or medical devices containing or releasing organic materials
- A61L2300/216—Biologically active materials used in bandages, wound dressings, absorbent pads or medical devices containing or releasing organic materials with other specific functional groups, e.g. aldehydes, ketones, phenols, quaternary phosphonium groups
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Abstract
The invention discloses a drug-loaded degradable absorbable medical suture and a preparation method thereof, the suture takes a polylactic acid-based material as a silk thread substrate, the silk thread substrate, a middle drug-loaded layer and an external lubricating layer are bonded into a whole through drug-loaded protein hydrogel, and the suture is prepared through a special synthesis process; the prepared suture can effectively control the degradation and absorption period of human skin; the innovative combination of the polylactic acid silk matrix and the drug-loading coating layer can effectively improve the antibacterial, hemostatic and anti-inflammatory effects of the suture; the outer lubricating layer can effectively improve the lubricating property of the suture line, reduce the pain of patients in the operation process and improve the operability of the operation. The suture line has the advantages of degradable and absorbable raw materials, good biocompatibility and physiological activity, simple preparation method and process, convenient operation, wide raw material source and good application prospect.
Description
Technical Field
The application relates to a medical suture in the medical field, in particular to a drug-loaded degradable absorbable medical suture and a preparation method thereof.
Background
The medical operation suture line is a sterile line for wound healing, tissue ligation and tissue fixation, and has an important effect on the initial healing of the wound. However, the suture on the market at present has the following problems: 1. the direct use of the medicine brings the defects of poor selectivity, large toxic and side effect, fast metabolism, short half-life period, poor stability and the like; 2. the common silk thread can not be automatically degraded and is only used for suturing the skin outside the wound, and the wound needs to be removed after healing to cause secondary pain after the operation of a patient; 3. the existing non-biological degradable suture line has the defects of poor degradation effect, poor compatibility, incomplete absorption and easy suture scar remaining; 4. people have higher and higher requirements on the aesthetic degree and the health degree of the recovery of the suture wound. There is therefore a need for a more sophisticated absorbable suture for use in the medical field.
Disclosure of Invention
The application provides a drug-loaded degradable absorbable medical suture and a preparation method thereof.
In some embodiments of the present application, a drug-loaded degradable absorbable medical suture is provided, the suture consisting of a polylactic acid-based thread, a drug-loaded protein hydrogel, an intermediate drug-loaded layer, an outer lubricious layer;
the lactic acid-based yarn is prepared by spinning a polylactic acid-glycolic acid material which is generated by heating and condensing oligomeric lactic acid-glycolic acid synthesized by an L-lactic acid aqueous solution and a glycolic acid aqueous solution;
the drug-loaded protein hydrogel is prepared by mixing silk fibroin solution and drugs;
preparing polycaprolactone, an L-glutamic acid polymer and an organic solvent into a carrier solution, mixing a required drug emulsion and the carrier solution to prepare a drug-loaded finishing liquid, soaking the drug emulsion in a polylactic acid-based silk thread, and wrapping a drug on the outer layer of the polylactic acid-based silk thread through drug-loaded protein hydrogel to form an intermediate drug-loaded layer;
the external lubricating layer is an organic lubricating layer and is prepared by dissolving polycaprolactone and calcium stearate in ethyl acetate.
In some embodiments of the present application, a preparation method of the drug-loaded degradable absorbable medical suture is further provided, which includes preparation of polylactic acid-glycolic acid, preparation of a drug-loaded protein hydrogel, preparation of a drug-loaded finishing liquid, preparation of a lubricating coating liquid, and molding of the drug-loaded degradable medical suture.
In some embodiments of the present application, the preparation process of the polylactic acid-glycolic acid is: firstly, mixing oligomeric lactic acid-glycolic acid and biomass creatinine according to a certain mass ratio, reacting for 96-170 hours in a reaction kettle with the temperature of 150-.
In some embodiments of the present application, the oligomeric lactic acid-glycolic acid is obtained by reacting an L-lactic acid aqueous solution and a glycolic acid aqueous solution at a temperature of 130 ℃ and 150 ℃ in a nitrogen-filled reaction kettle liner for 1-3 h.
In some embodiments of the application, the drug-loaded silk fibroin hydrogel is prepared by putting beneficial drugs and silk fibroin solution into a reaction kettle, and stirring the beneficial drugs and the silk fibroin solution for 30 minutes in a constant-temperature water bath kettle at 90 ℃ by using a magnetic stirrer to obtain the drug-loaded silk fibroin hydrogel.
In some embodiments of the present application, the silk fibroin solution is prepared by degumming silkworm cocoons, dissolving the degummed silkworm cocoons in an anhydrous calcium chloride-ethanol-water ion dissolving system with a molar ratio of 1: 2: 8 at a constant temperature of 80 ℃ for 120 minutes to obtain a silk fibroin solution, and then pouring the obtained silk fibroin solution into a dialysis bag to dialyze the solution in deionized water for 3 days to obtain a pure silk fibroin solution.
In some embodiments of the application, the drug-loaded finishing liquid is prepared by preparing a solution with a certain concentration from polycaprolactone and an L-glutamic acid polymer, pouring an organic solvent ethyl acetate, and stirring under a magnetic stirrer to prepare a carrier solution; and uniformly mixing the required drug emulsion and the carrier solution, and stirring the mixture for 30 minutes in a magnetic stirrer to obtain the drug-loaded finishing liquid.
In some embodiments of the present application, the lubricating coating liquid is prepared by mixing ethyl acetate, polycaprolactone, calcium stearate and tween-60, and stirring the mixture with a magnetic stirrer to prepare the lubricating coating liquid.
In some embodiments of the present application, the polylactic acid based drug-loaded degradable medical suture is formed by the following process: preparing the prepared polylactic acid-glycolic acid into silk threads, namely polylactic acid-based silk threads, by adopting a wet spinning method; and weaving the polylactic acid based silk thread into a suture line body in a hemp-flower type mode, soaking the drug-loaded finishing liquid, drying at room temperature, then bonding and drying the suture line body soaked with the drug-loaded finishing liquid by using drug-loaded protein hydrogel, coating the dried drug-loaded suture line body with a lubricating coating liquid, and drying to obtain a finished product.
In some embodiments of the present application, the desired drug emulsion is formulated with amoxicillin, etamsylate, glycerol, tween-60, and deionized water.
In some embodiments of the application, raw materials used by the medical suture line can be degraded and absorbed, the prepared suture line can be effectively degraded and absorbed in human skin or tissues, and the antibacterial, hemostatic and anti-inflammatory effects of the suture line are improved by innovatively combining the polylactic acid silk thread matrix and the drug-loaded coating layer.
In some embodiments of the present application, the beneficial agent can be aspirin, dexamethasone, or the like.
In some embodiments of the application, in the preparation of the oligomeric lactic acid-glycolic acid, the L-lactic acid aqueous solution is an industrial-grade L-lactic acid aqueous solution with the purity of 90%, the glycolic acid aqueous solution is a glycolic acid aqueous solution with the purity of 70%, the molar mass ratio of the two is 1: 1, the two are poured into a reaction kettle inner container, and the mixture is uniformly stirred.
In some embodiments of the application, a nitrogen bottle is used for inflating the inner container of the reaction kettle, air is exhausted, after repeated operation is carried out for three times, the bottle cap of the inner container is quickly closed, and screwing and sealing are carried out; further, the reaction kettle is placed into an electric heating blowing drying oven under normal pressure, the temperature is 140 ℃, and the time is 6 hours.
In some embodiments of the present application, the synthesized oligo lactic acid-glycolic acid OLGA and the biomass creatinine are poured into a reaction kettle in a mass ratio of 264: 1; putting the reaction kettle into a drying oven, cooling to room temperature, pouring into ethyl acetate, uniformly mixing, pouring into 0 ℃ ethanol, filtering the solution to obtain polylactic-co-glycolic acid (PLGA), and vacuum-drying at 50 ℃ for 36 hours, wherein the temperature of normal pressure is 190 ℃ for 124 hours.
In some embodiments of the present application, the preparation of the drug-loaded fibroin hydrogel comprises silk fibroin hydrogel solution preparation and drug-loaded silk fibroin hydrogel preparation; the specific process for preparing the silk fibroin hydrogel is to prepare a sodium carbonate solution with the mass fraction of 1% by using deionized water and anhydrous sodium carbonate; further, pouring the silkworm cocoons into a sodium carbonate solution, placing the silkworm cocoons into a magnetic stirrer, cooling to room temperature at 90 ℃ for 30 minutes, repeatedly washing with deionized water, and drying to obtain degummed silk fibroin; further, preparing a dissolving system with the molar ratio of anhydrous calcium chloride-ethanol-water ions being 1: 2: 8, weighing degummed silk fibroin, pouring the degummed silk fibroin into the dissolving system, placing the system in a stirrer, keeping the temperature at 80 ℃ for 120 minutes, finishing after no obvious white flocculent precipitate exists, and cooling to room temperature; further, pouring the dissolved silk fibroin solution into a dialysis bag and putting the dialysis bag into deionized water for 3 days; and further pouring out the dialyzed solution, standing for one day, and filtering to obtain a purer silk fibroin solution.
In some embodiments of the application, the specific process for preparing the drug-loaded silk fibroin hydrogel comprises the steps of placing a silk fibroin solution in a magnetic stirrer, keeping the temperature at 90 ℃ for 60 minutes, taking out the silk fibroin solution after the silk fibroin solution is completely solidified into gel, and cooling the silk fibroin solution to room temperature; further, beneficial medicines (aspirin, dexamethasone and the like) and deionized water are prepared into a medicine water solution with the medicine mass fraction of 10%; further, uniformly mixing the silk fibroin hydrogel and the drug aqueous solution, putting the mixture into a magnetic stirrer, keeping the temperature at 90 ℃ for 30 minutes, finishing the solidification to obtain gel, and cooling at room temperature to obtain the drug-loaded protein hydrogel.
In some embodiments of the application, in the specific process of preparing the drug-loaded finishing solution, Polycaprolactone (PCL) and L-glutamic acid Polymer (PGA) are prepared into a solution of 0.075g/m1, an organic solvent ethyl acetate is poured into the solution, the solution is stirred under a magnetic stirrer at the rotation speed of 800r/min and the temperature of 50 ℃ to prepare a carrier solution; further, preparing a medicine emulsion by amoxicillin, etamsylate, Tween-60 of glycerol and deionized water; further, uniformly mixing the carrier solution and the drug emulsion, and stirring the mixture in a magnetic stirrer at the rotation speed of 1000r/min and the temperature of 50 ℃ for 30 minutes to prepare a drug-loaded finishing liquid;
in some embodiments of the present application, in the preparation of the lubricating coating liquid, the organic solvents of ethyl acetate, Polycaprolactone (PCL), calcium stearate and tween-60 are uniformly mixed, and the mixture is placed in a magnetic stirrer at a rotation speed of 800r/min and a temperature of 50 ℃ to prepare the lubricating coating liquid.
In some embodiments of the present application, the molding method of the polylactic acid-based drug-loaded degradable absorbable medical suture is characterized in that the prepared polylactic acid-glycolic acid (PLGA) material is made into a silk thread by a wet spinning method, i.e. a polylactic acid-based silk thread; the polylactic acid based silk threads are woven into suture thread bodies in a hemp flower type mode, and are soaked in the drug-loaded finishing liquid for 60-120 minutes and dried at room temperature; then, adhering the suture line body soaked in the overload drug finishing liquid by using drug-loaded protein hydrogel, and drying at room temperature; further, coating the dried drug-loaded suture line body with a lubricating coating liquid, and drying at room temperature to obtain a finished product.
Compared with the prior art, the application has the advantages and positive effects that:
1. the suture thread has the drug-loading mode that drug molecules are released at certain concentration at specific parts in vivo, so as to achieve the purpose of fully exerting the drug effect. The stability and the delivery efficiency of the medicine can be improved, the toxic and side effects caused by overhigh medicine concentration in blood can be avoided, the action time of the medicine is prolonged, the waste of the medicine is reduced, and the high-efficiency and low-toxicity medicine treatment effect is obtained;
2. the suture line is made of biodegradable high polymer material polylactic acid, has good biocompatibility, and degradation products have no toxic or side effect on cells and can be completely metabolized and degraded in vivo;
3. the middle drug-loaded layer is made of two biodegradable materials with different degradation speeds, and the degradation period of the suture line coating is controlled by adjusting the proportion of the two biodegradable materials, so that the release period of the drug is controlled, the suture line coating is suitable for wounds with different healing periods, and the wound healing period and the drug release period are basically synchronous;
4. the suture has excellent multifunction, biocompatibility, biodegradability, low immunogenicity, flexibility, tension resistance, easy processing, controllable in vitro degradability and the like, and is widely used for tissue engineering, carriers for controlling and releasing drug delivery, tissue regeneration materials and regeneration composite materials, and wound closure repair replacement surgery.
Drawings
In order to more clearly illustrate the technical solutions in the embodiments of the present application, the drawings required to be used in the description of the embodiments are briefly introduced below, and it is obvious that the drawings in the description below are only some embodiments of the present application, and it is obvious for those skilled in the art to obtain other drawings and embodiments based on these drawings without creative efforts.
FIG. 1 is a schematic cross-sectional structure diagram of a polylactic acid-based drug-loaded degradable absorbable medical suture;
FIG. 2 is a schematic representation of the hemp-type bond of the drug-loaded degradable absorbable medical sutures according to some embodiments of the present application;
FIG. 3 is a synthesis equation for OLGA in some embodiments of the present application for drug-loaded degradable absorbable medical suture fabrication;
FIG. 4 is an equation for the synthesis of PLGA in a method of making a drug-loaded degradable absorbable medical suture according to some embodiments of the present application;
FIG. 5 is a flow chart of a process for preparing a drug-loaded degradable absorbable medical suture according to some embodiments of the present application;
in the figure: 1. a polylactic acid-based yarn; 2. carrying a drug protein hydrogel; 3. a middle drug-loaded layer; 4. an outer lubricant layer;
Detailed Description
The following examples are provided to further illustrate the embodiments of the present application. The following examples are intended to further illustrate the present application but are not intended to limit the scope of the present application.
As shown in the attached drawings, the application provides a drug-loaded degradable absorbable medical suture and a preparation method thereof, wherein the main structure of the suture comprises a polylactic acid-based thread 1, a drug-loaded protein hydrogel 2, a middle drug-loaded layer 3 and an external lubricating layer 4; the lactic acid-based thread 1 is prepared by spinning polylactic acid-glycolic acid (PLGA) material which is generated by heating and condensing oligomeric lactic acid-glycolic acid synthesized by L-lactic acid aqueous solution and glycolic acid aqueous solution; the drug-loaded protein hydrogel 2 is a gel prepared by mixing natural silk-dissolved protein water and beneficial drugs (aspirin, dexamethasone and the like); beneficial drugs of amoxicillin, etamsylate and the like are emulsified and dissolved into drug emulsion through Tween-60 of glycerol, the emulsion is used for soaking a polylactic acid matrix, and the drug is wrapped on the outer layers of three polylactic acid base threads 1 through drug-loaded protein hydrogel, namely a middle drug-loaded layer 3 is formed; the external lubricating layer 4 is an organic lubricating layer, and is a lubricating coating liquid prepared by dissolving polycaprolactone and calcium stearate in an organic solvent ethyl acetate, and is coated outside the lactic acid-based thread 1 and the middle drug-loaded layer 3 in a coating mode. The specific implementation method and process of the drug-loaded degradable absorbable medical suture line comprises the following five steps:
(1) preparation of polylactic-co-glycolic acid (PLGA)
Preparing polylactic acid-glycolic acid (PLGA), firstly synthesizing oligolactic acid-glycolic acid (OLGA), and then synthesizing PLGA by OLGA condensation;
the specific process for preparing the oligomeric lactic acid-glycolic acid comprises the steps of mixing 45.00g of industrial-grade L-lactic acid aqueous solution with the purity of 90% and 48.85g of glycolic acid aqueous solution with the purity of 70% in a molar mass ratio of 1: 1, pouring the mixture into a reaction kettle inner container with the capacity of 1000ml, and uniformly stirring; further, a nitrogen bottle is used for inflating the inner container of the reaction kettle, air is exhausted, the bottle cap of the inner container is quickly closed after repeated operation is carried out for three times, and the inner container is screwed tightly for sealing; further, the reaction kettle is placed into an electric heating blowing drying oven under normal pressure, the temperature is 140 ℃, and the time is 6 hours. Further, the synthesis equation of OLGA is shown in fig. 3;
the specific preparation process of the polylactic acid-glycolic acid (PLGA) comprises the steps of pouring 70.00g of synthesized oligomeric lactic acid-glycolic acid OLGA and 0.265g of biomass creatinine into a reaction kettle according to the mass ratio of 264: 1; further placing the reaction kettle into a drying oven, cooling to room temperature, further pouring into 70.00g of ethyl acetate, uniformly mixing, then pouring into 70.00g of ethanol at 0 ℃, filtering the solution to obtain polylactic-co-glycolic acid (PLGA), and carrying out vacuum drying at 50 ℃ for 36 hours, wherein the temperature is 190 ℃ under normal pressure and the time is 124 hours; further, the synthetic equation of PLGA is shown in fig. 4;
(2) preparation of drug-loaded protein hydrogel
The preparation of the drug-loaded fibroin hydrogel also comprises the preparation of a fibroin hydrogel solution and the preparation of the drug-loaded fibroin hydrogel; the specific process for preparing the silk fibroin hydrogel is to prepare a sodium carbonate solution with the mass fraction of 1% by 198g of deionized water and 2g of anhydrous sodium carbonate; further, pouring 10.00g of silkworm cocoons into a sodium carbonate solution, placing the silkworm cocoons into a magnetic stirrer, cooling to room temperature at 90 ℃ for 30 minutes, repeatedly washing with deionized water, and drying to obtain degummed silk fibroin; further, 31.98g, 26.54g and 41.48g of anhydrous calcium chloride-ethanol-water ions are weighed, a dissolving system with the molar ratio of the anhydrous calcium chloride-ethanol-water ions being 1: 2: 8 is prepared, 10.00g of degummed silk fibroin is weighed and poured into the dissolving system, the obtained mixture is placed in a stirrer, the temperature is 80 ℃, the time is 120 minutes, no obvious white flocculent precipitate exists, and then the mixture is cooled to room temperature; further, pouring the dissolved silk fibroin solution into a dialysis bag and putting the dialysis bag into deionized water for 3 days; further, pouring out the dialyzed solution, standing for one day, and filtering to obtain a purer silk fibroin solution;
the specific process for preparing the drug-loaded silk fibroin hydrogel comprises the steps of placing a silk fibroin solution in a magnetic stirrer at the temperature of 90 ℃ for 60 minutes, taking out the silk fibroin solution after the silk fibroin solution is completely solidified into gel, and cooling the silk fibroin solution to room temperature; further, 1.00g of aspirin, 1.00g of dexamethasone and 18g of deionized water are prepared into a drug water solution with the drug mass fraction of 10%; further, uniformly mixing 50.00g of silk fibroin hydrogel and 10% of drug water solution, putting the mixture into a magnetic stirrer, keeping the temperature at 90 ℃ for 30 minutes, finishing the solidification to obtain gel, and cooling at room temperature to obtain drug-loaded protein hydrogel;
(3) preparation of drug-loaded finishing liquid
The preparation specific process of the drug-loaded finishing liquid comprises the following steps: preparing a 0.075g/ml solution from 4.20g of Polycaprolactone (PCL) and 1.80g of L-glutamic acid Polymer (PGA), pouring 80ml of organic solvent ethyl acetate, stirring under a magnetic stirrer at the rotation speed of 800r/min and the temperature of 50 ℃ to prepare a carrier solution; further, 1.0g of amoxicillin, 1.0g of etamsylate, 0.3g of glycerol, Tween-60 and 80ml of deionized water are prepared into a medicine solution; further, uniformly mixing the carrier solution and the drug solution, and stirring the mixture in a magnetic stirrer at the rotation speed of 1000r/min and the temperature of 50 ℃ for 30 minutes to prepare a drug-loaded finishing liquid;
(4) preparation of lubricating coating fluid
The preparation process of the lubricating coating liquid comprises the steps of uniformly mixing 40ml of organic solvent ethyl acetate, 2.00g of Polycaprolactone (PCL), 2.5g of calcium stearate and 0.2g of Tween-60, placing the mixture in a magnetic stirrer at the rotating speed of 800r/min and the temperature of 50 ℃ to prepare the lubricating coating liquid.
(5) Forming method of polylactic acid-based drug-loaded degradable medical suture
The forming method of the polylactic acid based drug-loaded degradable absorbable medical suture is characterized in that the prepared polylactic acid-glycolic acid (PLGA) material is prepared into a silk thread, namely a polylactic acid based silk thread, by adopting a wet spinning method; the polylactic acid based silk threads are woven into suture thread bodies in a hemp flower type mode, and are soaked in the drug-loaded finishing liquid for 60-120 minutes and dried at room temperature; then, adhering the suture line body soaked in the overload finishing liquid by using drug-loaded protein hydrogel, and drying at room temperature; further, coating the dried drug-loaded suture line body with a lubricating coating liquid, and drying at room temperature to obtain a finished product.
The above is only a preferred embodiment of the present application and is not intended to limit the present application, it should be noted that, for those skilled in the art, several improvements and modifications can be made without departing from the technical principle of the present application, and these improvements and modifications should also be regarded as the protection scope of the present application.
Claims (7)
1. The drug-loaded degradable absorbable medical suture is characterized by consisting of a polylactic acid-based thread, a drug-loaded protein hydrogel, a middle drug-loaded layer and an external lubricating layer; the lactic acid-based yarn is prepared by spinning a polylactic acid-glycolic acid material which is generated by heating and condensing oligomeric lactic acid-glycolic acid synthesized by an L-lactic acid aqueous solution and a glycolic acid aqueous solution; the drug-loaded protein hydrogel is prepared by mixing silk fibroin solution and drugs; preparing polycaprolactone, an L-glutamic acid polymer and an organic solvent into a carrier solution, mixing a required drug emulsion and the carrier solution to prepare a drug-loaded finishing liquid, soaking the drug emulsion in a polylactic acid-based silk thread, and wrapping a drug on the outer layer of the polylactic acid-based silk thread through drug-loaded protein hydrogel to form an intermediate drug-loaded layer; the external lubricating layer is an organic lubricating layer and is prepared by dissolving polycaprolactone and calcium stearate in ethyl acetate;
the preparation method of the drug-loaded silk fibroin hydrogel comprises the steps of putting beneficial drugs and silk fibroin solution into a reaction kettle, and stirring for 30 minutes by a magnetic stirrer in a constant-temperature water bath kettle at 90 ℃ to obtain the drug-loaded silk fibroin hydrogel;
the silk fibroin solution is prepared by degumming silkworm cocoons, dissolving the degummed silkworm cocoons for 120 minutes in an anhydrous calcium chloride-ethanol-water ion dissolving system with the molar ratio of 1: 2: 8 at the constant temperature of 80 ℃ to obtain a silk fibroin solution, pouring the obtained silk fibroin solution into a dialysis bag, and dialyzing the silk fibroin solution in deionized water for 3 days to obtain a pure silk fibroin solution;
the drug-loaded finishing liquid is prepared by preparing a solution with a certain concentration from polycaprolactone and an L-glutamic acid polymer, pouring an organic solvent ethyl acetate, and stirring under a magnetic stirrer to prepare a carrier solution; and uniformly mixing the required drug emulsion and the carrier solution, and stirring the mixture for 30 minutes in a magnetic stirrer to obtain the drug-loaded finishing liquid.
2. The preparation method of the drug-loaded degradable absorbable medical suture line of claim 1, which comprises the steps of preparation of polylactic acid-glycolic acid, preparation of drug-loaded protein hydrogel, preparation of drug-loaded finishing liquid, preparation of lubricating coating liquid and molding of the drug-loaded degradable medical suture line based on polylactic acid.
3. The preparation method according to claim 2, wherein the preparation process of the polylactic acid-glycolic acid comprises the following steps: firstly, mixing oligomeric lactic acid-glycolic acid and biomass creatinine according to a certain mass ratio, reacting for 96-170 hours in a reaction kettle with the temperature of 150-.
4. The method as claimed in claim 3, wherein the oligomeric lactic acid-glycolic acid is obtained by reacting an L-lactic acid aqueous solution with a glycolic acid aqueous solution at a temperature of 130 ℃ and 150 ℃ in a nitrogen-filled reaction vessel liner for 1-3 h.
5. The preparation method according to claim 2, wherein the lubricating coating liquid is prepared by uniformly mixing organic solvents of ethyl acetate, polycaprolactone, calcium stearate and tween-60, and stirring the mixture under a magnetic stirrer to prepare the lubricating coating liquid.
6. The preparation method according to any one of claims 2 to 5, wherein the polylactic acid-based drug-loaded degradable medical suture is formed by the following steps: preparing the prepared polylactic acid-glycolic acid into silk threads, namely polylactic acid-based silk threads, by adopting a wet spinning method; and weaving the polylactic acid-based silk threads into suture threads in a hemp flower type mode, soaking the drug-loaded finishing liquid, drying at room temperature, then bonding and drying the suture threads soaked in the drug-loaded finishing liquid by using drug-loaded protein hydrogel, coating the dried drug-loaded suture threads with lubricating coating liquid, and drying to obtain the finished product.
7. The method of claim 2, wherein the desired drug emulsion is formulated with amoxicillin, etamsylate, glycerol tween-60, and deionized water.
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