Polymer material for anti-displacement esophageal stent and preparation method thereof
By using materials such as polytetrahydrofuranyl and polycaprolactone macromolecular functional monomers, combined with covalent crosslinking and coordination crosslinking technology, esophageal stent materials with excellent chemical resistance to shift and shape memory are prepared, which solves the problems of difficult degradation, high shift rate and rigidity mismatch of existing esophageal stent materials, and achieves better therapeutic effects and biocompatibility.
Patent Information
- Application Number
- CN202411909607.1
- Authority / Receiving Office
- CN · China
- Patent Type
- Applications(China)
- Current Assignee / Owner
- Filing Date
- 2024-12-24
- Publication Date
- 2025-03-28
AI Technical Summary
The existing esophageal stent materials have disadvantages such as difficulty in degradation, high stent displacement rate, and high rigidity that is not matched with human tissue, which seriously affects the treatment effect.
Polymer materials with polytetrahydrofuranyl macromolecular functional monomer, polycaprolactone macromolecular functional monomer, metal ions and crosslinking agents as the main components are prepared by combining covalent crosslinking and coordination crosslinking to prepare esophageal scaffolding materials with excellent chemical shift resistance, reprocessable properties, antibacterial properties and shape memory characteristics.
The excellent mechanical properties and reprocessable properties of the esophageal stent material are achieved, the displacement rate of the stent is reduced, the matching with human tissue is enhanced, the treatment effect is improved, and good biosafety and antibacterial properties are achieved.
Smart Images
Figure CN119701103A_ABST
Abstract
Description
Technical Field
[0001] The invention belongs to the technical field of polymer materials, and in particular relates to a polymer material for an anti-displacement esophageal stent and a preparation method thereof. Background Art
[0002] Esophageal lesions often induce esophageal stenosis, which in turn affects the patient's eating and causes great pain to the patient. Esophageal stent implantation is one of the important methods for treating esophageal stenosis. This method achieves esophageal patency by inserting an esophageal stent into the esophageal stenosis of the patient. At present, the esophageal stent materials used in clinical practice are mainly shape memory nickel-titanium alloys. Its shape memory properties allow the stent to be delivered in a contracted state and trigger self-expansion at human body temperature to achieve mechanical support for the patient's esophagus. However, this type of stent material has the disadvantages of being difficult to degrade, having a high stent displacement rate (higher than 40%), and having a high rigidity that does not match human tissue, which seriously affects the treatment effect. The use of soft and degradable shape memory polymer materials to prepare esophageal stents is an effective means to solve the problems of high rigidity and difficulty in degradation of stent materials. However, due to relatively weak radial support and other reasons, the displacement rate of the obtained polymer stent is as high as 81.9%, which severely limits its application. The traditional method based on the design of stent anti-displacement structure belongs to the field of physics. However, since the esophageal cavity is often in a state of large-scale contraction and peristalsis, the anti-displacement ability of the stent designed based on this method is still limited. Introducing a chemical-based anti-displacement mechanism into shape memory polymer stent materials to enable the material to form an effective adhesion with the esophageal tissue is an important strategy. In addition, good processability, antibacterial properties, mechanical properties and shape memory properties are also important characteristics of anti-displacement esophageal stent materials.
[0003] In summary, the preparation of esophageal stent polymer materials with chemical anti-displacement properties, excellent processability, antibacterial properties, mechanical properties and shape memory properties is an urgent problem to be solved. Summary of the invention
[0004] In order to solve the deficiencies of the prior art, the present invention provides a polymer material for an anti-displacement esophageal stent and a preparation method thereof. The polymer material has excellent chemical anti-displacement properties, excellent processability, antibacterial properties, mechanical properties and shape memory properties.
[0005] The technical solution adopted by the present invention is:
[0006] 1. A polymer material for an anti-displacement esophageal stent
[0007] The polymer material is prepared by reacting at least one polytetrahydrofuran-based macromolecular functional monomer, at least one polycaprolactone-based macromolecular functional monomer, at least one metal ion and a crosslinking agent. In terms of mass fractions, the proportions of the polytetrahydrofuran-based macromolecular functional monomer, the polycaprolactone-based macromolecular functional monomer, the metal ion and the crosslinking agent are 42 to 62 parts, 34 to 54 parts, 0.005 to 0.15 parts and 0.52 to 1.95 parts respectively.
[0008] The polytetrahydrofuran macromolecular functional monomer is a polytetrahydrofuran-based telechelic oligomer, both ends of which are capped by catechol groups and have a molecular weight of 3000-4200.
[0009] The polycaprolactone-based macromolecular functional monomer is a polycaprolactone-based telechelic oligomer, one end of which is capped by an allyl group and the other end is capped by a catechol group, and the molecular weight is 4500-8000.
[0010] The metal ion is one or both of zinc ion and copper ion, and the cross-linking agent is pentaerythritol tetrakis-3-mercaptopropionate.
[0011] 2. A method for preparing a polymer material for an anti-displacement esophageal stent
[0012] The polymer material is prepared by the following method:
[0013] 1) quantitatively weighing polytetrahydrofuran-based macromolecular functional monomers, polycaprolactone-based macromolecular functional monomers, a crosslinking agent and an ultraviolet light initiator and dissolving them in an organic solvent, then adding a solution containing metal ions, and obtaining a uniform polymer precursor solution after ultrasonic treatment;
[0014] 2) adding an alkaline solution to the precursor solution, stirring and mixing to obtain a viscous polymer solution;
[0015] 3) injecting the polymer solution into molds of different shapes, and further cross-linking and polymerizing under ultraviolet light to obtain a polymer gel having both covalent cross-linking and coordination cross-linking structures;
[0016] 4) The polymer gel is vacuum dried to obtain a cross-linked dry polymer material.
[0017] In the above 1), the ultraviolet light initiator is benzoin dimethyl ether, and the organic solvent is one or more of dichloromethane, chloroform, 1,2-dichloroethane, tetrahydrofuran, and dioxane.
[0018] In the above 1), the molar ratio of the polycaprolactone-based macromolecular functional monomer to the cross-linking agent is 3.0 to 4.0, calculated by mole fraction.
[0019] In the above 2), the alkaline solution is triethylamine.
[0020] 3. An anti-displacement esophageal stent
[0021] The polymer material of the anti-displacement esophageal stent is prepared or the polymer material of the anti-displacement esophageal stent prepared by the method is prepared.
[0022] Prepared by the following method:
[0023] 1) heating the polymer material to 140° C. and obtaining a sheet polymer of a desired thickness by hot pressing, and then cooling the polymer to room temperature;
[0024] 2) heating a sheet of polymer material having a desired thickness to 65-75° C., and then deforming the sheet of polymer material according to the desired size and shape of the esophageal stent;
[0025] 3) Maintaining the sheet polymer in the required size and shape of the esophageal stent, keeping the temperature at 120-140°C for 0.5-3 hours, and then cooling to room temperature to obtain an anti-displacement esophageal stent.
[0026] The application method of the anti-displacement esophageal stent in esophageal support is carried out through the following steps:
[0027] 1) heating the anti-displacement esophageal stent prepared according to the required size and shape to a temperature exceeding the melting point of the anti-displacement esophageal stent and curling and compressing the anti-displacement esophageal stent to obtain the anti-displacement esophageal stent in a compressed state; reducing the radial size of the stent so that the stent can be transported in the esophagus;
[0028] 2) cooling the compressed anti-displacement esophageal stent to below the crystallization temperature of the anti-displacement esophageal stent, so that the temporary shape of the compressed anti-displacement esophageal stent can be fixed, thereby obtaining the anti-displacement esophageal stent with a fixed temporary shape;
[0029] 3) After the anti-displacement esophageal stent with a fixed temporary shape is delivered to the targeted position of the esophagus, the anti-displacement esophageal stent responds to the temperature of the human body and recovers its shape, thereby achieving self-expansion, thereby achieving support for the narrow part of the esophagus.
[0030] 4. Application of anti-displacement esophageal stents in esophageal support based on near-infrared light-responsive shape memory characteristics
[0031] The application method of the anti-displacement esophageal stent in esophageal support is carried out through the following steps:
[0032] 1) heating the anti-displacement esophageal stent prepared according to the required size and shape to a temperature exceeding the melting point of the anti-displacement esophageal stent and curling and compressing the anti-displacement esophageal stent to obtain the anti-displacement esophageal stent in a compressed state; reducing the radial size of the stent so that the stent can be transported in the esophagus;
[0033] 2) cooling the compressed anti-displacement esophageal stent to below the crystallization temperature of the anti-displacement esophageal stent, so that the temporary shape of the compressed anti-displacement esophageal stent can be fixed, thereby obtaining the anti-displacement esophageal stent with a fixed temporary shape;
[0034] 3) After the anti-displacement esophageal stent with a fixed temporary shape is delivered to the targeted position of the esophagus, it is irradiated with near-infrared light;
[0035] 4) Near-infrared light penetrates human tissue and acts on the anti-displacement esophageal stent with a fixed temporary shape. The anti-displacement esophageal stent undergoes a photothermal conversion effect and then recovers its shape. The anti-displacement esophageal stent with a fixed temporary shape is deployed in the esophagus, thereby achieving support for the narrow part of the esophagus.
[0036] The innovation of the present invention is:
[0037] 1. The polymer material has both stable crosslinking points based on covalent chemical bonds and dynamic crosslinking points based on the coordination of catechol-zinc ions and catechol-copper ions. The covalent chemical crosslinking points can provide the polymer with excellent mechanical properties, and the dynamic crosslinking points can provide the polymer with excellent network dynamic properties, which can enable the polymer to obtain excellent reprocessability through dynamic bond exchange. In addition, catechol-zinc ion complexes and catechol-copper ion complexes can give the polymer excellent antibacterial properties by slowly releasing zinc ions and copper ions.
[0038] 2. Both polytetrahydrofuran and polycaprolactone have excellent biocompatibility and hydrophobicity. Excellent biocompatibility is conducive to the application of polymer materials in the biomedical field, while hydrophobicity is conducive to the polymer materials being able to effectively resist the swelling effect of body fluids after being implanted in the organism to maintain their mechanical strength. At the same time, polytetrahydrofuran has a melting point lower than human body temperature, and polycaprolactone has a melting point higher than human body temperature. After the two polymers are introduced into the same polymer network, the human body temperature response shape memory characteristics can be achieved by component regulation. In addition, since the catechol-zinc ion complex and the catechol-copper ion complex have good light absorption capacity in the near-infrared region, the resulting polymer material also has good photothermal conversion ability and can exhibit good near-infrared light response shape memory characteristics. These two shape memory characteristics make the application of polymers in vivo more flexible.
[0039] 3. There are a large number of catechol groups in the polymer material, some of which will be oxidized by zinc ions and copper ions in the polymer network, and then undergo a slow Michael addition reaction with polar groups such as amino groups and thiol groups on the surface of human esophageal tissue to form covalent bonds, so that the polymer material adheres to the esophageal surface through chemical action, thereby achieving reliable anti-displacement ability.
[0040] The beneficial effects of the present invention are as follows:
[0041] 1. The anti-displacement esophageal stent polymer material of the present invention has excellent mechanical properties and reprocessability, and the anti-displacement esophageal stent can be processed and customized according to different needs of patients.
[0042] 2. The esophageal stent polymer material prepared by the present invention has good shape memory properties in response to human body temperature and near-infrared light, has the advantages of low-damage or non-damage implantation, and has both active human body temperature response and passive deployment in response to near-infrared light, and is more flexible in application.
[0043] 3. The esophageal stent polymer material prepared by the present invention has anti-displacement ability based on chemical tissue adhesion, which can well solve the problem of easy displacement and falling off of esophageal stents currently faced in clinical practice.
[0044] 4. The esophageal stent polymer material prepared by the present invention has good biosafety and antibacterial properties, and the preparation method is simple, which can effectively reduce the infection risk caused by stent implantation. BRIEF DESCRIPTION OF THE DRAWINGS
[0045] Figure 1 is the chemical structural formula of the polytetrahydrofuran-based macromolecular functional monomer used in Example 1;
[0046] Figure 2 is the chemical structural formula of the polycaprolactone-based macromolecular functional monomer used in Example 1;
[0047] Figure 3 is a schematic diagram of the structure of the polymer network in Example 1;
[0048] Figure 4 The scanning electron microscope and zinc ion distribution images of the polymer in Example 1;
[0049] Figure 5 The cell activity data of polymer extracts of different concentrations and a control group in Example 1;
[0050] Figure 6 This is the human body temperature response shape memory curve of the polymer in Example 1. DETAILED DESCRIPTION
[0051] The specific implementation is described in detail below in conjunction with the accompanying drawings, but it should be understood that the protection scope of the present invention is not limited by the specific implementation. The raw materials and reagents used in the examples are all commercially available unless otherwise specified.
[0052] Example 1
[0053] Weigh 250.5 mg of polytetrahydrofuran macromolecular functional monomer with a number average molecular weight of 3000, 313.1 mg of polycaprolactone macromolecular functional monomer with a number average molecular weight of 4500, 26.1 mg of zinc chloride solution with a mass fraction of 5%, 9.7 mg of pentaerythritol tetra-3-mercaptopropionate, and 2.5 mg of benzoin dimethyl ether, and dissolve them in dichloromethane, and ultrasonically obtain a uniform solution. Then add 120 μl of 0.1 mol / L triethylamine solution to the obtained solution, stir and mix evenly, and then pour the obtained viscous polymer solution into a polytetrafluoroethylene mold. Place the poured polymer solution under ultraviolet light for photocrosslinking for 1 hour, and then vacuum dry it at 40°C to constant weight to obtain the target polymer material. After heating the obtained polymer material to 140°C, a 0.1 mm thick polymer sheet is obtained by hot pressing and cooling. The obtained polymer sheet is heated to 65°C and deformed into a cylindrical shape with a given stent structure under the action of external force. It is then placed at a constant temperature of 130oC for 1h and then cooled to room temperature, so that the polymer undergoes permanent plastic deformation to obtain a given stent shape, and finally a shape memory esophageal stent with anti-displacement function is prepared. The antibacterial rates of the obtained polymer material against Escherichia coli and Staphylococcus aureus are 98.6% and 97.4%, respectively. The tensile strength of the polymer is 21.4MPa, the adhesion strength is 13.5kPa, and it also exhibits excellent shape memory properties in response to human body temperature and near-infrared light.
[0054] Figure 1 is the chemical structural formula of the polytetrahydrofuran macromolecular functional monomer used in this embodiment.
[0055] Figure 2 is the chemical structural formula of the polycaprolactone macromolecular functional monomer used in this embodiment.
[0056] Figure 3 This is a schematic diagram of the structure of the polymer network prepared in this embodiment. The microstructure of the obtained polymer is a polymer network with both chemical covalent crosslinking and catechol-zinc ion coordination dynamic crosslinking. It can be seen from the figure that the chemical covalent crosslinking points and the catechol-zinc ion coordination crosslinking points are constructed by pentaerythritol tetrakis-3-mercaptopropionate and catechol-zinc ion complexes, respectively.
[0057] Figure 4 The scanning electron microscope image of the polymer in this embodiment and the distribution diagram of the zinc element are shown in the figure. As shown in the figure, the obtained polymer has a uniform microstructure, and the catechol-zinc ion complex is uniformly distributed in the polymer network.
[0058] Figure 5The cell activity data of polymer extracts of different concentrations and the control group in this embodiment were tested by MTT method. The test material object was 10 mg / ml polymer extract, and the test cells were mouse fibroblast L929. As shown in the figure, the experimental results of the negative control (Negative), positive control (Positive) and blank control (Blank) were consistent with expectations. For polymer extracts with a concentration of 25% to 100%, the cell activity was not significantly inhibited, and the cell activity was higher than 90%, indicating that the polymer has good cell compatibility.
[0059] Figure 6 This is the human body temperature response shape memory curve of the polymer in this embodiment. As shown in the figure, tensile stress is applied to the long sample at 37°C to cause the sample to produce elongation strain, and then the temperature is lowered to -10°C. This strain is fixed and remains stable after the stress is removed. The temperature is then raised to 37°C again, and the sample recovers its shape as the temperature rises. This shape fixation and shape recovery process was repeated three times, and all of them showed good human body temperature response shape memory characteristics. The shape fixation rate of the three experimental samples exceeded 98%, and the shape recovery rate exceeded 85%.
[0060] Example 2
[0061] Weigh 350.6 mg of polytetrahydrofuran macromolecular functional monomer with a number average molecular weight of 3000, 192.3 mg of polycaprolactone macromolecular functional monomer with a number average molecular weight of 4500, 1.18 mg of zinc chloride solution with a mass fraction of 5%, 6.0 mg of pentaerythritol tetra-3-mercaptopropionate, and 2.4 mg of benzoin dimethyl ether, and dissolve them in dioxane, and ultrasonically obtain a uniform solution. Then add 20 μl of 0.1 mol / L triethylamine solution to the obtained solution, stir and mix evenly, and then pour the obtained viscous polymer solution into a polytetrafluoroethylene mold. Place the poured polymer solution under ultraviolet light for photocrosslinking for 1 hour, and then vacuum dry it at 40°C to constant weight to obtain the target polymer material. After heating the obtained polymer material to 140°C, a 0.15 mm thick polymer sheet is obtained by hot pressing and cooling. The obtained polymer sheet is heated to 75°C and deformed into a cylindrical shape with a given stent structure under the action of an external force. It is then placed at a constant temperature of 140°C for 0.5h and then lowered to room temperature, so that the polymer undergoes permanent plastic deformation to obtain a given stent shape, and finally a shape memory esophageal stent with anti-displacement function is prepared. The antibacterial rates of the obtained polymer material against Escherichia coli and Staphylococcus aureus are 76.5% and 69.2%, respectively. The tensile strength of the polymer is 11.6MPa, and the adhesion strength is 19.3kPa. It also exhibits excellent shape memory properties in response to human body temperature and near-infrared light. The shape fixation rate and shape recovery rate of the human body temperature response shape memory are 88.1% and 98.4%, respectively.
[0062] Example 3
[0063] Weigh 300.1 mg of polytetrahydrofuran macromolecular functional monomer with a number average molecular weight of 3500, 385.7 mg of polycaprolactone macromolecular functional monomer with a number average molecular weight of 8000, 44.7 mg of zinc chloride solution with a mass fraction of 5%, 7.8 mg of pentaerythritol tetra-3-mercaptopropionate, and 2.8 mg of benzoin dimethyl ether, and dissolve them in trichloroethane, and ultrasonically obtain a uniform solution. Then add 180 μl of 0.1 mol / L triethylamine solution to the obtained solution, stir and mix evenly, and then pour the obtained viscous polymer solution into a polytetrafluoroethylene mold. Place the poured polymer solution under ultraviolet light for photocrosslinking for 1 hour, and then vacuum dry it at 40°C to constant weight to obtain the target polymer material. After heating the obtained polymer material to 140°C, a 0.1 mm thick polymer sheet is obtained by hot pressing and cooling. The obtained polymer sheet is heated to 75°C and deformed into a cylindrical shape with a given stent structure under the action of an external force. It is then placed at a constant temperature of 120°C for 3 hours and then lowered to room temperature, so that the polymer undergoes permanent plastic deformation to obtain a given stent shape, and finally a shape memory esophageal stent with anti-displacement function is prepared. The antibacterial rates of the obtained polymer material against Escherichia coli and Staphylococcus aureus are 98.9% and 99.2%, respectively. The tensile strength of the polymer is 27.4MPa, and the adhesion strength is 13.2kPa. It also exhibits excellent shape memory properties in response to human body temperature and near-infrared light. The shape fixation rate and shape recovery rate of the human body temperature response shape memory are 99.1% and 92.6%, respectively.
[0064] Example 4
[0065] Weigh 284.5 mg of polytetrahydrofuran macromolecular functional monomer with a number average molecular weight of 4200, 247.8 mg of polycaprolactone macromolecular functional monomer with a number average molecular weight of 4500, 19.4 mg of copper chloride solution with a mass fraction of 5%, 9.0 mg of pentaerythritol tetra-3-mercaptopropionate, and 2.2 mg of benzoin dimethyl ether and dissolve them in 1,2-dichloroethane, and ultrasonically obtain a uniform solution. Then add 100 μl of 0.1 mol / L triethylamine solution to the obtained solution, stir and mix evenly, and then pour the obtained viscous polymer solution into a polytetrafluoroethylene mold. After the poured polymer solution is placed under ultraviolet light for photocrosslinking for 1 hour, it is vacuum dried at 40°C to constant weight to obtain the target polymer material. After heating the obtained polymer material to 140°C, a 0.1 mm thick polymer sheet is obtained by hot pressing and cooling in sequence. The obtained polymer sheet is heated to 75°C and deformed into a cylindrical shape with a given stent structure under the action of external force. It is then placed at a constant temperature of 140oC for 0.5h and then cooled to room temperature, so that the polymer undergoes permanent plastic deformation to obtain a given stent shape, and finally a shape memory esophageal stent with anti-displacement function is prepared. The antibacterial rates of the obtained polymer material against Escherichia coli and Staphylococcus aureus are 85.2% and 82.1%, respectively. The tensile strength of the polymer is 33.1MPa, and the adhesion strength is 12.7kPa. It also exhibits excellent shape memory properties in response to human body temperature and near-infrared light. The shape fixation rate and shape recovery rate of the human body temperature response shape memory are 98.4% and 91.7%, respectively.
[0066] The foregoing description of specific exemplary embodiments of the present invention is for the purpose of illustration and demonstration. These descriptions are not intended to limit the present invention to the precise form disclosed, and it is clear that many changes and variations can be made based on the above teachings. The purpose of selecting and describing the exemplary embodiments is to explain the specific principles of the present invention and its practical application, so that those skilled in the art can realize and utilize various different exemplary embodiments of the present invention and various different selections and changes. The scope of the present invention is intended to be limited by the claims and their equivalents.
Claims
1. A polymer material for an anti-displacement esophageal stent, characterized in that: The invention is prepared by reacting at least one polytetrahydrofuran-based macromolecular functional monomer, at least one polycaprolactone-based macromolecular functional monomer, at least one metal ion and a cross-linking agent.
2. The polymer material for an anti-displacement esophageal stent according to claim 1, characterized in that: In terms of mass fractions, the proportions of the polytetrahydrofuran-based macromolecular functional monomer, the polycaprolactone-based macromolecular functional monomer, the metal ion, and the crosslinking agent are 42 to 62 parts, 34 to 54 parts, 0.005 to 0.15 parts, and 0.52 to 1.95 parts, respectively.
3. The polymer material for an anti-displacement esophageal stent according to claim 1, characterized in that: The polytetrahydrofuran-based macromolecular functional monomer is a polytetrahydrofuran-based telechelic oligomer, both ends of which are capped by catechol groups and have a molecular weight of 3000-4200.
4. The polymer material for an anti-displacement esophageal stent according to claim 1, characterized in that: The polycaprolactone macromolecular functional monomer is a polycaprolactone telechelic oligomer, one end of which is capped by an allyl group and the other end is capped by a catechol group, and the molecular weight is 4500 to 8000. The metal ion is one or both of zinc ion and copper ion, and the crosslinking agent is pentaerythritol tetrakis-3-mercaptopropionate.
5. A method for preparing a polymer material for an anti-displacement esophageal stent according to any one of claims 1 to 5, characterized in that: The polymer material is prepared by the following method: 1) quantitatively weighing polytetrahydrofuran-based macromolecular functional monomers, polycaprolactone-based macromolecular functional monomers, a crosslinking agent and an ultraviolet light initiator and dissolving them in an organic solvent, then adding a solution containing metal ions, and obtaining a uniform polymer precursor solution after ultrasonic treatment; 2) adding an alkaline solution to the precursor solution, stirring and mixing to obtain a viscous polymer solution; 3) injecting the polymer solution into molds of different shapes, and further cross-linking and polymerizing under ultraviolet light to obtain a polymer gel having both covalent cross-linking and coordination cross-linking structures; 4) The polymer gel is vacuum dried to obtain a cross-linked dry polymer material.
6. The method for preparing a polymer material for an anti-displacement esophageal stent according to claim 5, characterized in that: In the step 1), the ultraviolet light initiator is benzoin dimethyl ether, and the organic solvent is one or more of dichloromethane, chloroform, 1,2-dichloroethane, tetrahydrofuran, and dioxane.
7. The method for preparing a polymer material for an anti-displacement esophageal stent according to claim 5, characterized in that: In the step 1), the molar ratio of the polycaprolactone-based macromolecular functional monomer to the cross-linking agent is 3 to 4 in molar fraction.
8. The method for preparing a polymer material for an anti-displacement esophageal stent according to claim 5, characterized in that: In the step 2), the alkaline solution is triethylamine.
9. An anti-displacement esophageal stent, characterized in that: The invention is prepared by comprising a polymer material of the anti-displacement esophageal stent described in any one of claims 1 to 5 or a polymer material of the anti-displacement esophageal stent prepared by the method described in any one of claims 6 to 9.
10. Use of the polymer material for an anti-displacement esophageal stent according to any one of claims 1 to 4 or the polymer material for an anti-displacement esophageal stent prepared by the preparation method of the polymer material for an anti-displacement esophageal stent according to any one of claims 5 to 9, characterized in that: Application of the polymer material for the anti-displacement esophageal stent in an esophageal stent.