Repair bracket

Abstract

The present application relates to the technical field of medical supplies, and particularly relates to a repair stent. The repair stent comprises a support main body and a mesh tube, the support main body is provided with an inner cavity, and the mesh tube is arranged in the inner cavity; the mesh tube is a mesh-shaped tube structure woven by braided wires, and the mesh tube is loaded with regenerative cells; wherein the support main body and the mesh tube are both made of degradable materials, and the wall thickness of the support main body is greater than the wire diameter of the braided wires. The present application provides a repair stent which can rigidly support the cervical stump and will not hinder tissue regeneration.

Description

Technical Field

[0001] This invention relates to the field of medical supplies technology, and more particularly to a repair stent. Background Technology Repairing the cervical stump after cervical cancer surgery is a crucial aspect of gynecological tumor treatment. Postoperatively, effective mechanical support is needed to prevent stump collapse and adhesions, while simultaneously promoting functional tissue regeneration to restore the normal physiological function of the cervix.

[0002] In existing technologies, stents used for cervical stump repair mainly have the following technical problems: Traditional non-degradable scaffolds (such as polypropylene mesh and metal scaffolds) can provide immediate postoperative support, but as permanent foreign bodies remaining in the body for a long time, they are prone to complications such as chronic inflammation and tissue erosion. Therefore, the use of biodegradable scaffolds is becoming increasingly common. Existing biodegradable scaffolds (such as injection-molded PLA scaffolds) have simple structures, and their degradation rate is difficult to match with the tissue regeneration rate. This can easily lead to problems such as insufficient support due to excessively rapid degradation, or hindered tissue ingrowth due to excessively slow degradation.

[0003] Therefore, this application provides a new repair stent to address the above-mentioned problems. Summary of the Invention

[0004] The purpose of this invention is to provide a repair stent that can provide rigid support for the cervical stump without hindering tissue regeneration.

[0005] To achieve the above objectives, the present invention provides a repair stent, comprising a support body and a mesh tube, wherein the support body is provided with an inner cavity and the mesh tube is disposed within the inner cavity; The mesh cylinder is a mesh-like cylindrical structure woven from braided yarn, and regenerating cells are attached to the mesh cylinder; Both the support body and the mesh cylinder are made of biodegradable materials, and the wall thickness of the support body is greater than the diameter of the braided thread.

[0006] Furthermore, the biodegradable material is polylactic acid, polycaprolactone, polylactic acid-glycolic acid copolymer, polyglycolic acid, or tricalcium phosphate composite material; The regenerated cells are human umbilical cord mesenchymal stem cells, bone marrow mesenchymal stem cells, adipose mesenchymal stem cells, amniotic mesenchymal stem cells, or autologous circulating endothelial progenitor cells.

[0007] Furthermore, the support body includes a support cylinder, which is a hollow cylindrical body. A support crown and a bottom cover are respectively provided at both ends of the support cylinder, and the support crown, the support cylinder, and the bottom cover together form the inner cavity. The wall thickness of the support cylinder, the support crown, and the bottom cover are all greater than the diameter of the braided yarn.

[0008] Furthermore, a reinforcing ring is provided on the outer wall of the support cylinder, and the reinforcing ring is located on the side of the support cylinder near the support crown; The reinforcing rings are provided in multiple ways, and the multiple reinforcing rings are arranged sequentially at intervals along the circumference of the support cylinder to form a reinforcing ring group; the reinforcing ring group is provided in multiple groups, and the multiple groups of reinforcing rings are arranged at intervals along the axial direction of the support cylinder, and the reinforcing rings in adjacent reinforcing ring groups are staggered.

[0009] Furthermore, the mesh cylinder is detachably disposed within the inner cavity; The support cylinder has an opening communicating with the inner cavity on the side near the bottom cover, and the bottom cover and the support cylinder are detachably connected. The repair bracket has a first use state, a second use state, and a third use state. When the repair bracket is in the first use state, the inner cavity is empty. When the repair bracket is in the second use state, a magnetothermal medium is provided in the inner cavity. When the repair bracket is in the third use state, the bottom cover is detached from the support cylinder, and the mesh cylinder is disposed in the inner cavity through the opening.

[0010] Furthermore, the magnetocaloric medium is Fe3O4 particles, γ-Fe2O3 particles, spinel ferrite, or FeCo alloy nanoparticles; The bottom cover and the support cylinder can be detachably connected by means of snap-fit ​​connection, threaded connection, interference fit connection, magnetic connection or adhesive.

[0011] Furthermore, the supporting crown includes a crown base plate and a plurality of crown side plates disposed on the crown base plate. The plurality of crown side plates are arranged sequentially along the circumference of the crown base plate. The crown base plate is connected to the supporting cylinder, and the crown side plates are disposed on the side of the crown base plate away from the supporting cylinder. The crown base plate is provided with a first connecting hole, and the crown side plate is provided with a second connecting hole.

[0012] Furthermore, the support body also includes a support column disposed in the inner cavity, the support column being provided with a communicating cavity, the communicating cavity extending through the entire support column along the axial direction of the support column, wherein one end of the support column abuts against the crown base plate of the support crown, and the communicating cavity communicates with the first connecting hole; When the repair bracket is in the first use state and the second use state, the other end of the support column abuts against the bottom cover, and when the repair bracket is in the second use state, the magnetothermal medium is disposed in the area of ​​the inner cavity located between the support cylinder and the support column; When the repair bracket is in the third use state, the mesh cylinder is located in the area between the support cylinder and the support column in the inner cavity, and the bottom cover is detached from the support cylinder, and the end of the communicating cavity away from the support crown is open.

[0013] Furthermore, when the repair bracket is in the first use state, the support body also includes a support plate disposed in the inner cavity, the support plate is sleeved outside the support column, and the inner peripheral surface of the support plate abuts against the outer wall surface of the support column, and the outer peripheral surface of the support plate abuts against the inner wall surface of the support cylinder; When the repair stent is in the second use state, the injection device loaded with the magnetothermal medium pierces the support plate and injects the magnetothermal medium into the area of ​​the inner cavity located between the support cylinder and the support column; When the repair bracket is in the third use state, the support plate is broken, and the debris of the support plate and the magnetothermal medium are removed from the inner cavity. Then, the mesh tube is sleeved outside the support column, so that the mesh tube is located in the area of ​​the inner cavity between the support tube and the support column.

[0014] Furthermore, the support disk has a plurality of breaking grooves on its surface, and the plurality of breaking grooves are spaced apart along the circumference of the support disk.

[0015] Furthermore, along the radial direction of the inner cavity, the mesh cylinder comprises multiple layers of mesh, and from the center of the inner cavity outward, the mesh density of the multiple layers of mesh gradually decreases, or the mesh aperture of the multiple layers of mesh gradually increases.

[0016] Furthermore, the supporting body is integrally formed by 3D printing, and the mesh cylinder is integrally formed by 3D printing.

[0017] By adopting the above technical solution, the repair stent of the present invention has at least the following beneficial effects: When used, this repair stent needs to be implanted into the cervix, so that the support body of the stent provides mechanical support to the cervical stump. The support body of this repair stent has an inner cavity, and its wall thickness is greater than the diameter of the braided mesh thread, giving it higher structural strength and a slower degradation rate, thus providing reliable mechanical support to the cervical stump. In the initial stage after stent implantation, the support body bears the main mechanical load, preventing tissue collapse and creating a stable mechanical environment for tissue repair.

[0018] In addition, the mesh tube is woven from braided threads to form a grid-like cylindrical structure. Regenerating cells are attached to the mesh tube, and its grid structure provides space for cell adhesion, proliferation, and migration. The braided threads of the mesh tube have a small diameter, resulting in a large specific surface area and a faster degradation rate. As the mesh tube degrades, it gradually makes room for new tissue growth.

[0019] Furthermore, the mesh tube is placed within the cavity of the support body, placing the support body on the outer layer to provide mechanical support for the cervical stump, while the mesh tube is located on the inner layer, serving as a carrier for regenerating cells. Both the support body and the mesh tube are made of biodegradable materials, and the wall thickness of the support body is greater than the diameter of the mesh tube's braided threads, resulting in different degradation rates between the two: the support body degrades more slowly than the mesh tube. In other words, the thicker support body degrades more slowly, maintaining mechanical support in the early and middle stages of implantation; the smaller mesh tube degrades more quickly, rapidly degrading in the later stages of implantation, freeing up space for new tissue ingrowth.

[0020] Therefore, in the early stage of stent implantation, the supporting body maintains the integrity of the tissue structure and provides reliable mechanical support, while the regenerating cells on the internal mesh continuously proliferate and differentiate; in the middle stage of stent implantation, the supporting body begins to degrade, and the mesh rapidly degrades, making room for the growth of new tissue, which can grow along the wall of the supporting body and gradually form functional cervical tissue; in the later stage of stent implantation, the mesh completely degrades, the supporting body continues to degrade slowly, and is eventually completely absorbed.

[0021] In summary, in the repair scaffold of this invention, both the support body and the mesh tube are made of biodegradable materials. After implantation, they are completely degraded and metabolized by the body, leaving no long-term foreign body residue. This fundamentally eliminates the risks of chronic inflammation and tissue erosion associated with traditional non-degradable scaffolds. Furthermore, after implantation, the differentiated design of the support body wall thickness and the mesh tube diameter allows for different degradation rates: the mesh tube degrades faster, providing space for cell proliferation and tissue ingrowth before the support body is fully degraded, while the slow degradation of the support body maintains mechanical support until new tissue forms. This allows for a certain degree of matching between the degradation rate and tissue regeneration. This differentiated degradation rate design, to a certain extent, aligns with the dynamic process of tissue repair, resolving the contradiction between "support" and "regeneration" in existing technologies. Attached Figure Description

[0022] To more clearly illustrate the technical solutions of the embodiments of the present invention, the accompanying drawings used in the embodiments will be briefly introduced below. It should be understood that the following drawings only show some embodiments of the present invention and should not be regarded as a limitation of the scope. For those skilled in the art, other related drawings can be obtained based on these drawings without creative effort.

[0023] Figure 1 This is a schematic diagram of the structure of the repair stent provided in an embodiment of the present invention; Figure 2 A cross-sectional view of the repair stent provided in an embodiment of the present invention; Figure 3 This is a schematic diagram of the supporting crown in the repair stent provided in an embodiment of the present invention; Figure 4 This is a schematic diagram of the support cylinder in the repair bracket provided in an embodiment of the present invention; Figure 5 This is one of the structural schematic diagrams of the mesh cylinder in the repair support provided in the embodiments of the present invention; Figure 6 This is the second schematic diagram of the structure of the mesh cylinder in the repair support provided in the embodiment of the present invention; Figure 7 This is a schematic diagram of the structure of the repair bracket provided in this embodiment of the invention, showing the opening at the bottom cover of the mesh tube inserted into the inner cavity after the bottom cover is removed.

[0024] Figure label: 1-Support body; 11-Inner cavity; 12-Support cylinder; 121-Bayonet; 13-Support crown; 131-Crown side plate; 132-Second connecting hole; 133-Crown base plate; 135-First connecting hole; 14-Bottom cover; 15-Reinforcing ring; 21-Support column; 211-Communicating cavity; 22-Support plate; 221-Breaking groove; 3-Network tube; 31-Braided thread. Detailed Implementation

[0025] The technical solution of the present invention will now be clearly and completely described with reference to the accompanying drawings. Obviously, the described embodiments are only some, not all, of the embodiments of the present invention. Based on the embodiments of the present invention, all other embodiments obtained by those skilled in the art without creative effort are within the scope of protection of the present invention.

[0026] In the description of this invention, it should be noted that the terms "center," "upper," "lower," "left," "right," "vertical," "horizontal," "inner," and "outer," etc., indicate the orientation or positional relationship based on the orientation or positional relationship shown in the accompanying drawings. They are used only for the convenience of describing the invention and for simplifying the description, and do not indicate or imply that the device or element referred to must have a specific orientation, or be constructed and operated in a specific orientation. Therefore, they should not be construed as limitations on the invention. Furthermore, the terms "first," "second," and "third" are used for descriptive purposes only and should not be construed as indicating or implying relative importance.

[0027] In the description of this invention, it should be noted that, unless otherwise explicitly specified and limited, the terms "installation," "connection," and "linking" should be interpreted broadly. For example, they can refer to a fixed connection, a detachable connection, or an integral connection; they can refer to a mechanical connection or an electrical connection; they can refer to a direct connection or an indirect connection through an intermediate medium; and they can refer to the internal connection of two components. Those skilled in the art can understand the specific meaning of the above terms in this invention based on the specific circumstances.

[0028] Please see Figure 1 and Figure 2 and combined Figure 7 This embodiment provides a repair scaffold, which includes a support body 1 and a mesh cylinder 3. The support body 1 is provided with an inner cavity 11, and the mesh cylinder 3 is disposed in the inner cavity 11. The mesh cylinder 3 is a mesh-like cylindrical structure woven from braided yarn 31, and regenerated cells are attached to the mesh cylinder 3. Both the support body 1 and the mesh cylinder 3 are made of biodegradable materials, and the wall thickness of the support body 1 is greater than the diameter of the braided yarn 31.

[0029] It should be noted that the braided thread 31 is a thread with a circular cross-section, and the diameter of the braided thread 31 is the same as the diameter of the braided thread 31.

[0030] In this repair scaffold, the support body 1 has an inner cavity 11 with a relatively thick wall, providing reliable mechanical support. The wall thickness of the support body 1 is greater than the diameter of the braided wire 31 of the mesh tube 3, giving it higher structural strength and a slower degradation rate. In the early stages of scaffold implantation, the support body 1 bears the main mechanical load, preventing tissue collapse and creating a stable mechanical environment for tissue repair.

[0031] In addition, the mesh tube 3 is woven from braided threads 31 to form a mesh-like cylindrical structure. Regenerating cells are attached to the mesh tube 3, and its mesh structure provides space for cell adhesion, proliferation, and migration. The woven structure has good permeability, facilitating the exchange of nutrients and metabolic waste. Furthermore, the braided threads 31 of the mesh tube 3 have a small diameter, a large specific surface area, and a fast degradation rate. As the mesh tube 3 degrades, it gradually makes room for new tissue.

[0032] Furthermore, the mesh tube 3 is disposed within the inner cavity 11 of the support body 1, forming a nested relationship in space. The support body 1 is located on the outer layer, providing mechanical support, while the mesh tube 3 is located on the inner layer, serving as a cell carrier. Both the support body 1 and the mesh tube 3 are made of biodegradable materials, and the wall thickness of the support body 1 is greater than the diameter of the braided thread 31 of the mesh tube 3, resulting in different degradation rates between the support body 1 and the mesh tube 3: the degradation rate of the support body 1 is slower than that of the mesh tube 3. In other words, the support body 1, with its larger wall thickness, degrades more slowly, maintaining mechanical support in the early and middle stages of implantation; the mesh tube 3, with its smaller thread diameter, degrades more quickly, rapidly degrading in the middle and late stages of implantation, releasing space for the ingrowth of new tissue.

[0033] Therefore, when this repair stent is used, the support body 1 provides rigid support to the cervical stump to prevent collapse and adhesion. In the early stages of stent implantation, the support body 1 maintains the integrity of the tissue structure, providing reliable mechanical support, while the regenerating cells on the internal mesh tube 3 continuously proliferate and differentiate. In the middle stages of stent implantation, the support body 1 begins to degrade, and the mesh tube 3 degrades rapidly, creating space for the growth of new tissue. This new tissue can grow along the wall of the support body 1, gradually forming functional cervical tissue. In the later stages of stent implantation, the mesh tube 3 completely degrades, while the support body 1 continues to degrade slowly and is eventually completely absorbed.

[0034] In summary, in the repair scaffold of this invention, both the support body 1 and the mesh tube 3 are made of biodegradable materials. After implantation, they are completely degraded and metabolized by the body, leaving no long-term foreign body residue, fundamentally eliminating the risks of chronic inflammation and tissue erosion associated with traditional non-degradable scaffolds. Furthermore, after implantation, the differentiated design of the wall thickness of the support body 1 and the wire diameter of the mesh tube 3 achieves two different degradation rates. The mesh tube 3 degrades faster, providing space for cell proliferation and tissue ingrowth before the support body 1 is fully degraded. The slow degradation of the support body 1 maintains mechanical support until new tissue forms, precisely matching the degradation rate with the tissue regeneration rate. This differentiated degradation rate design, to a certain extent, aligns with the dynamic process of tissue repair, resolving the contradiction between "support" and "regeneration" in existing technologies.

[0035] Optionally, the degradable material is polylactic acid, polycaprolactone, polylactic acid-glycolic acid copolymer, polyglycolic acid, or tricalcium phosphate composite material; the regenerated cells are human umbilical cord mesenchymal stem cells, bone marrow mesenchymal stem cells, adipose mesenchymal stem cells, amniotic mesenchymal stem cells, or autologous circulating endothelial progenitor cells.

[0036] Preferably, the biodegradable material is polylactic acid (PLA). PLA, also known as polylactide, is a bio-based material of lactic acid. Its main degradation mechanisms include in vivo degradation, ultraviolet degradation, thermal degradation, and microbial degradation. After degradation, it breaks down into water and carbon dioxide, making it a biodegradable biomaterial. The acidic pH value of PLA after degradation is suitable for the vagina, which is inherently a weakly acidic environment (3.8-4.5). The lactic acid (acidic environment) produced by PLA degradation is beneficial to the vagina because it maintains the vaginal acidic environment (self-cleaning function) and inhibits bacteria such as Escherichia coli, Gardnerella vaginalis, and Candida albicans.

[0037] Polycaprolactone (PCL) is a polymer with excellent biocompatibility and a relatively long degradation period of 2-3 years. It is suitable for clinical applications requiring longer support periods, such as in the repair of complex cervical insufficiency, and its degradation products are non-toxic. Polylactic-glycolic acid copolymer (PLGA) allows for precise control of the degradation rate from several months to over a year by adjusting the monomer ratio of lactic acid (LA) to glycolic acid (GA), for example, 50:50, 75:25, or 85:15. Polyglycolic acid (PGA) degrades faster than polylactic acid and is mainly suitable for scenarios requiring rapid degradation and complete space release in a short period; however, its strong hydrophilicity leads to a rapid initial decline in mechanical strength. Tricalcium phosphate composite material (PLA / β-TCP) introduces an inorganic ceramic phase to improve the rigidity and compressive strength of the scaffold and simulate a bone / hard tissue environment while maintaining bioabsorbability.

[0038] In summary, all of the above materials are medical-grade biodegradable polymers or composite materials, possess good biocompatibility, and can be hydrolyzed or enzymatically degraded in vivo.

[0039] Preferably, the regenerative cells used in this invention are human umbilical cord mesenchymal stem cells (hUC-MSCs). Bone marrow mesenchymal stem cells are a classic source of MSCs, exhibiting strong osteogenic and chondrogenic differentiation capabilities; adipose-derived mesenchymal stem cells are readily available, minimally invasive, and have rapid cell proliferation. Amniotic mesenchymal stem cells have extremely low immunogenicity and stronger anti-inflammatory and anti-fibrotic capabilities; autologous circulating endothelial progenitor cells (EPCs) focus more on vascular repair.

[0040] In summary, all of the above-mentioned cells are pluripotent or adult stem cells, possessing the potential for self-renewal and multi-directional differentiation. They can all serve as "seed cells" loaded onto the mesh 3 to promote the functional regeneration of damaged tissues.

[0041] Preferably, please refer to Figure 2The support body 1 includes a support cylinder 12, which is a hollow cylindrical body. Support crown 13 and bottom cover 14 are respectively provided at both ends of the support cylinder 12, and the support crown 13, support cylinder 12 and bottom cover 14 together form an inner cavity 11. The wall thickness of the support cylinder 12, the wall thickness of the support crown 13 and the wall thickness of the bottom cover 14 are all greater than the diameter of the braided thread 31.

[0042] It should be noted that the support crown 13 is located on the side of the support tube 12 closest to the tissue remnant, while the bottom cover 14 is located on the side of the support tube 12 furthest from the tissue remnant. The support crown 13 is used to connect the remaining tissue after surgery, and the support tube 12 provides reliable radial support.

[0043] Optionally, the diameter of the braided thread 31 is 0.2mm-0.5mm, for example, the diameter of the braided thread 31 is 0.2mm, 0.3mm, 0.4mm, or 0.5mm. Preferably, in this invention, the diameter of the braided thread 31 is 0.3mm. The mesh structure woven from braided threads with a diameter of 0.2mm-0.5mm has a high specific surface area and good permeability, providing an ideal microenvironment for the adhesion, proliferation, and differentiation of stem cells.

[0044] Specifically, the thicker wall of the support tube 12 provides a longer degradation time, maintaining mechanical support in the early and middle stages of implantation; the finer braided thread 31 of the mesh tube 3 provides a larger specific surface area, degrades faster, and quickly releases space in the middle and late stages of implantation. The two achieve time-controlled degradation rate through size difference.

[0045] For example, in this embodiment, the support cylinder 12 is a cervical cylindrical structure, and its external dimensions match the cervical anatomy of the target application scenario. This biomimetic design enables the stent to fit tightly against the cervical stump, providing uniform radial support force, while also providing a template for tissue regeneration.

[0046] Preferably, please refer to Figure 4 The outer wall of the support cylinder 12 is provided with a reinforcing ring 15, which is located on the side of the support cylinder 12 near the support crown 13. Multiple reinforcing rings 15 are provided, and the multiple reinforcing rings 15 are arranged sequentially at intervals along the circumference of the support cylinder 12 to form a reinforcing ring group. Multiple reinforcing ring groups are provided, and the multiple reinforcing ring groups are arranged at intervals along the axial direction of the support cylinder 12, and the reinforcing rings 15 in adjacent reinforcing ring groups are staggered.

[0047] In other words, the reinforcing ring 15 is an annular protrusion extending from the outer wall of the support cylinder 12. It enhances the structural strength and compressive strength of the support cylinder 12, as well as increasing the frictional resistance between the support cylinder 12 and the cervical structure, making the support of the support cylinder 12 more reliable and stable. The reinforcing ring 15 is located on the side of the support cylinder 12 closest to the support crown 13, i.e., the front section of the support cylinder 12. This area is the main part bearing mechanical loads, and the reinforcing ring 15 effectively improves the deformation resistance of this area.

[0048] In this embodiment, the cross-section of the reinforcing ring 15 is semi-circular, rectangular, or trapezoidal.

[0049] In this design, multiple reinforcing rings 15 are evenly distributed along the circumference of the support cylinder 12 at the same axial position, with equal spacing between adjacent reinforcing rings 15. This circumferentially spaced distribution design enhances structural strength while preserving part of the original surface of the outer wall of the support cylinder 12, which is beneficial for tissue adhesion and growth.

[0050] In addition, multiple sets of reinforcing rings are provided, and these sets are spaced apart along the axial direction of the support cylinder 12. Specifically, the multiple sets of reinforcing rings are arranged sequentially from the front end to the rear end along the length of the support cylinder 12, with an axial spacing of 0.5 mm between adjacent sets. In this embodiment, three sets of reinforcing rings are provided: an upper section reinforcing ring set, a middle section reinforcing ring set, and a lower section reinforcing ring set, which are distributed sequentially along the axial direction of the support cylinder 12.

[0051] Furthermore, the reinforcing rings 15 in adjacent reinforcing ring groups are staggered, that is, the reinforcing rings 15 in the previous group of reinforcing rings and the reinforcing rings 15 in the next group of reinforcing rings are staggered in the circumferential position and are not on the same axis.

[0052] This design, with the reinforcing ring 15 as a raised annular structure, increases the moment of inertia of the support cylinder 12, improving its compressive and bending resistance. The staggered arrangement of the reinforcing rings 15 ensures that the load is evenly distributed in the circumferential and axial directions of the support cylinder 12, avoiding stress concentration and reducing the risk of local deformation and failure. The use of spaced rather than continuous rings for the reinforcing rings 15 reduces material usage and the weight of the support while ensuring strength, thus improving wearing comfort. The gaps between the reinforcing rings 15 preserve the original outer wall surface of the support cylinder 12, providing attachment points for tissue ingrowth and promoting the integration of the support with the surrounding tissue. The staggered arrangement of adjacent reinforcing ring groups makes the distribution of the reinforcing rings 15 more uniform, avoiding excessive local rigidity caused by continuous "reinforcing ribs" in the axial direction, achieving a balance between rigidity and flexibility. In addition, the reinforcing rings 15 can be designed with sutures passing through them, promoting tissue fusion and enhancing fixation through the suture structure, thereby enhancing the connection strength and stability between the support cylinder 12 and the residual tissue.

[0053] Preferably, the mesh cylinder 3 is detachably disposed in the inner cavity 11, and the support cylinder 12 has an opening communicating with the inner cavity 11 on the side near the bottom cover 14. The bottom cover 14 and the support cylinder 12 are detachably connected. The repair bracket has a first use state, a second use state, and a third use state.

[0054] When the repair stent is in the first use state, the inner cavity 11 is a cavity, and the repair stent is used to provide mechanical support for the cervical stump; when the repair stent is in the second use state, the inner cavity 11 is filled with a magnetothermal medium; when the repair stent is in the third use state, the bottom cover 14 is removed from the support cylinder 12, and the mesh cylinder 3 is placed in the inner cavity 11 through the opening.

[0055] This configuration, with the detachable connection between the bottom cover 14 and the support cylinder 12, allows the opening of the inner cavity 11 to be opened and closed. When the bottom cover 14 is connected to the support cylinder 12, the opening is closed, and the inner cavity 11 is sealed to prevent the contents of the inner cavity 11, such as the magnetothermal medium, from escaping. When the bottom cover 14 is detached from the support cylinder 12, the opening is opened, and operations such as loading or unloading the magnetothermal medium and inserting the mesh cylinder 3 can be performed on the inner cavity 11 through the opening at the end of the support cylinder 12.

[0056] The repair stent has a first use state, a second use state, and a third use state.

[0057] Please see Figure 2 The first use state is the support state. When the repair stent of the present invention is used, the repair stent is placed on the cervical stump, so that the support body 1 provides mechanical support to the cervical stump. At this time, the repair stent is in the first use state.

[0058] The second usage state is the magnetothermal therapy state, mainly used to kill residual cancer cells after cervical cancer surgery. The high temperature of 56℃±1℃ generated by magnetothermal therapy can effectively kill residual cancer cells and reduce the risk of recurrence. Specifically, the operation procedure is as follows: disassemble the bottom cover 14 from the support cylinder 12 to open the opening, place the magnetothermal medium (not shown in the figure), such as Fe3O4 magnetic nanoparticles with a particle size of 20nm, into the inner cavity through the opening, close the bottom cover 14, seal the inner cavity 11, and finally place the repair bracket in the alternating magnetic field. The magnetothermal medium generates heat under the action of the magnetic field to perform thermotherapy on the surrounding tissue.

[0059] In this embodiment, for example, the loading amount of the magnetothermal medium is 100mg±1mg. This loading amount has been experimentally verified to raise the temperature from 37°C to 56°C within 5-6 minutes under the action of an alternating magnetic field of 255kHz and 15mA, and maintain it for 40 minutes.

[0060] Please see Figure 7The third usage state is the tissue regeneration state. In the third usage state, the bottom cover 14 is detached from the support cylinder 12, and the mesh cylinder 3 is placed in the inner cavity 11, with regenerating cells such as human umbilical cord mesenchymal stem cells (hUC-MSCs) attached to the mesh cylinder 3. The operation procedure is as follows: Open the bottom cover 14, remove the magnetothermal medium from the inner cavity 11 from the second usage state by suction or washing, and then place the mesh cylinder 3 with regenerating cells into the inner cavity 11 through the opening. Close the bottom cover 14 to seal the inner cavity 11. The regenerating cells on the mesh cylinder 3 proliferate and differentiate in vivo, promoting tissue regeneration.

[0061] In this embodiment, the first use state, the second use state, and the third use state are three stages of sequential use. The first use state is used to support the stump, and then the second use state is used to perform magnetic thermotherapy. After the magnetic thermotherapy is completed, the magnetic thermomedia is removed, and the system switches to the third use state of tissue regeneration, thus realizing an integrated sequential treatment of "support first, treatment then repair".

[0062] In summary, the repair stent of the present invention, through the detachable connection between the bottom cover 14 and the support cylinder 12, the detachable setting of the mesh cylinder 3, and the switching between the first, second, and third usage states, achieves the following technical effects: One device for three uses, sequential treatment: The same stent device can be used at different stages for magnetothermal therapy to kill residual cancer cells and for tissue regeneration and repair, simplifying the treatment process. Functional separation, no interference: The functions in the three states are independent and do not interfere with each other. Furthermore, the repair stent has a compact structure and high integration: The three usage states share the same support body 1, eliminating the need to replace the stent and reducing surgical trauma and operational steps. Moreover, the repair stent of the present invention has a reliable seal to prevent leakage: When the bottom cover 14 is closed, the sealing structure ensures that the contents of the inner cavity 11—the magnetothermal medium—will not leak, guaranteeing treatment safety.

[0063] Optionally, the magnetothermal medium is Fe3O4 particles, γ-Fe2O3 particles, spinel ferrite, or FeCo alloy nanoparticles; the bottom cover 14 and the support cylinder 12 are detachably connected by means of snap-fit ​​connection, threaded connection, interference fit connection, magnetic connection, or adhesive bonding.

[0064] Preferably, in the repair scaffold of the present invention, the magnetothermal medium is Fe3O4 particles. γ-Fe2O3 magnetohyperite has a similar crystal structure and magnetic properties to Fe3O4, but is more chemically stable and less prone to oxidation, and its heat generation efficiency is comparable to Fe3O4. Spinel-type ferrite MFe2O4, where M is a metal ion such as Mn, Zn, Co, or Ni, can be doped with different metal ions to adjust the Curie temperature Tc or specific absorptivity SAR of the material, achieving therapeutic temperatures under low magnetic field strength. FeCo alloy nanoparticles have high saturation magnetization and a heat generation efficiency far higher than Fe3O4, but require surface passivation treatment to improve biocompatibility.

[0065] In summary, all of the above materials belong to magnetic nanomaterials. Under the action of an alternating magnetic field, they can all generate heat based on hysteresis loss, Nell relaxation or Brownian relaxation mechanisms, and can all achieve the purpose of "magnetothermal therapy" in this invention.

[0066] Additionally, for example, when the bottom cover 14 is snapped together with the support cylinder 12, please refer to [reference needed]. Figure 4 The support cylinder 12 is provided with a bayonet 121, and the bottom cover 14 is provided with a locking protrusion. The two can be connected by the locking protrusion engaging with the bayonet 121. Alternatively, when the bottom cover 14 is threadedly connected to the support cylinder 12, the support cylinder 12 is provided with an external thread, and the bottom cover 14 is provided with an internal thread. The two are screwed together to achieve the connection. The threaded connection has a self-locking function, and the sealing performance is better than that of ordinary snap-fit ​​connection. Moreover, the repair bracket is not easy to loosen when subjected to vibration in the body. Alternatively, when the bottom cover 14 is interference-fitted to the support cylinder 12, the two are fitted together by thermal expansion and contraction. Taking advantage of the difference in the thermal expansion coefficients of metals or specific polymers, the bottom cover 14 is heated and then fitted onto the support cylinder 12. After cooling, To achieve a tight, secure fit, this solution has the simplest structure and no additional protrusions. Alternatively, when the bottom cover 14 and the support cylinder 12 are magnetically connected, tiny magnetic objects, such as medical-grade neodymium iron boron gold-plated magnetic rings, are embedded in the contact surfaces of the bottom cover 14 and the support cylinder 12. Magnetic force is used to achieve a seal that allows the two to open and close. This solution is extremely convenient to operate, requiring no alignment of the clips or rotation. Alternatively, when the bottom cover 14 and the support cylinder 12 are bonded together, medical-grade bio-adhesive / adhesive can be used for sealing. After the bottom cover 14 and the support cylinder 12 are initially positioned through an interference fit, biodegradable medical adhesive, such as fibrin glue, is used for edge sealing. This solution combines physical and chemical sealing, providing dual protection.

[0067] Preferably, please refer to Figure 3 The supporting crown 13 includes a crown base plate 133 and a plurality of crown side plates 131 disposed on the crown base plate 133. The plurality of crown side plates 131 are arranged sequentially along the circumference of the crown base plate 133. The crown base plate 133 is connected to the supporting cylinder 12, and the crown side plates 131 are disposed on the side of the crown base plate 133 away from the supporting cylinder 12. The crown base plate 133 is provided with a first connecting hole 135, and the crown side plates 131 are provided with a second connecting hole 132.

[0068] In use, the supporting crown 13 is placed at the cervical stump, so that multiple coronal lateral plates 131 are in contact with the remaining tissue. Surgical sutures are passed sequentially through the second connecting holes 132 on the coronal lateral plates 131 and the first connecting holes 135 on the coronal base plate 133 to suture and fix the supporting crown 13 to the remaining tissue. Multi-point fixation allows the supporting crown 13 to stably connect with the remaining tissue and prevents the stent from shifting.

[0069] It should be noted that the supporting crown 13 is located at the front end of the supporting tube 12 near the tissue remnant and is used to connect the residual tissue after surgery. The crown base plate 133 is a disc-shaped structure and is connected to the front end of the supporting tube 12. Specifically, the back side of the crown base plate 133 (the side facing the supporting tube 12) is fixedly connected to the end of the supporting tube 12. The two can be integrally formed by 3D printing, or connected by bonding or welding.

[0070] For example, in this embodiment, there are four coronary lateral plates 131, which are evenly distributed around the coronary base plate 133, and the included angle between adjacent coronary lateral plates 131 is 90°.

[0071] Each coronal lateral plate 131 is provided with a second connecting hole 132. In this embodiment, the second connecting hole 132 is a circular through hole with a diameter of 1.0mm-1.5mm. The multiple second connecting holes 132 on the multiple coronal lateral plates 131 provide multiple fixing points, enabling the supporting crown 13 to be fixed to the residual tissue at multiple points, thereby enhancing the stability and firmness of the connection.

[0072] Preferably, please refer to Figure 2 The support body 1 also includes a support column 21 disposed in the inner cavity 11. The support column 21 is provided with a connecting cavity 211, which extends through the entire support column along the axial direction of the support column 21. One end of the support column 21 abuts against the crown base plate 133 of the support crown 13, and the connecting cavity 211 communicates with the first connecting hole 135. When the repair bracket is in the first and second use states, the other end of the support column 21 abuts against the bottom cover 14. When the repair bracket is in the second use state, the magnetothermal medium is disposed in the area of ​​the inner cavity 11 between the support cylinder 12 and the support column 21. When the repair bracket is in the third use state, the mesh cylinder 3 is disposed in the area of ​​the inner cavity 11 between the support cylinder 12 and the support column 21, and the bottom cover 14 is detached from the support cylinder 12, and the end of the connecting cavity 211 away from the support crown 13 is open.

[0073] In this embodiment, the support column 21 is a hollow cylinder extending along the axial direction of the support cylinder 12.

[0074] In both the first and second use states, the bottom cover 14 is mounted on the support cylinder 12, and the end of the support column 21 abuts against the bottom cover 14, providing central axial support and enhancing the overall structural strength of the support body 1. In addition, the bottom cover 14 closes the end opening of the connecting cavity 211, making the connecting cavity 211 a closed channel. Thus, in the second use state, the magnetothermal medium (such as Fe3O4 magnetic nanoparticles, 100mg±1mg, particle size 20nm) is filled between the support cylinder 12 and the support column 21 to prevent leakage of the magnetothermal medium.

[0075] In the third usage state, the bottom cover 14 is detached from the support cylinder 12, the end of the support column 21 no longer abuts against the bottom cover 14, the end of the connecting cavity 211 away from the support crown 13 is open, and the side of the support column 21 closer to the support crown 13 is connected to the first connecting hole 135. In this embodiment, the connecting cavity 211 and the first connecting hole 135 together constitute a sperm channel to allow sperm to pass through. Specifically, the front end of the connecting cavity 211 is connected to the outside through the first connecting hole 135, and the end is open, forming a complete through channel from the front end to the end of the support, allowing sperm to enter from the front end and exit from the end, entering the uterus.

[0076] It should be noted that the cervix is ​​the essential passage for sperm to enter the uterus. After cervical stent repair surgery for cervical cancer, it is necessary to preserve the patient's fertility, that is, to allow sperm to enter the uterus from the vagina through the stent. Therefore, this application incorporates a penetrating sperm passage in the center of the stent.

[0077] Preferably, please refer to Figure 2 When the repair bracket is in its first use state, the support body 1 also includes a support plate 22 disposed in the inner cavity 11. The support plate 22 is sleeved outside the support column 21, and the inner peripheral surface of the support plate 22 abuts against the outer wall surface of the support column 21, while the outer peripheral surface of the support plate 22 abuts against the inner wall surface of the support cylinder 12.

[0078] When the repair stent is in the second use state, an injection device containing magnetothermal medium, such as a syringe, pierces the support plate 22 and injects the magnetothermal medium into the area of ​​the inner cavity 11 between the support cylinder 12 and the support column 21. When the repair stent is in the third use state, the support plate 22 is broken, and the debris of the support plate 22 and the magnetothermal medium are removed from the inner cavity 11. Then, the mesh cylinder 3 is placed outside the support column 21, so that the mesh cylinder 3 is placed in the area of ​​the inner cavity 11 between the support cylinder 12 and the support column 21.

[0079] With this configuration, when the support bracket is in its first use state, the support column 21 and the support plate 22 together form the internal support skeleton within the inner cavity 11. The support column 21 provides central axial support, and the support plate 22 provides radial support. The two work together to enhance the overall structural strength of the support body 1.

[0080] Specifically, the two ends of the support column 21 abut against the support crown 13 and the bottom cover 14 respectively, forming axial support. This abutment structure allows the support column 21 to provide support between the support crown 13 and the bottom cover 14. When the support body 1 is subjected to axial pressure, the support column 21 can effectively bear and transfer the load, preventing the support cylinder 12 from undergoing axial compression deformation. The outer peripheral surface of the support plate 22 is in close contact with the inner wall surface of the support cylinder 12, forming radial support. This abutment relationship allows the support plate 22 to transfer the radial load on the support cylinder 12 to the support column 21, while distributing the load on the support column 21 to the support cylinder 12, achieving coordinated force distribution between the inner and outer structures.

[0081] It should be noted that the thickness of the support plate 22 is 1mm-1.5mm. By piercing the support plate 22 with a syringe, the magnetothermal medium can be injected into the inner cavity 11.

[0082] Preferably, please refer to Figure 2 The support plate 22 has multiple breaking grooves 221 on its surface, and the multiple breaking grooves 221 are spaced apart along the circumference of the support plate 22.

[0083] The puncture groove 221 can serve as a puncture guide point for the syringe. Doctors can perform puncture operations at the groove position. The concave structure of the groove helps guide the positioning of the puncture needle. In addition, the puncture groove 221 is a structurally weak area on the support plate 22. The syringe can puncture the support plate 22 at the puncture groove 221, thereby making the operation more time-saving and labor-saving.

[0084] Optionally, the number of breaking grooves 221 is 12-24, preferably 18, and the breaking grooves 221 are circular grooves that do not penetrate the support plate 22.

[0085] In this embodiment, the support column 21, support crown 13, and bottom cover 14 are integrally formed by 3D printing to create a continuous, monolithic structure. This integral molding design ensures continuous force transmission and avoids stress concentration at the joints.

[0086] Preferably, please refer to Figure 5 and Figure 6 Along the radial direction of the inner cavity 11, the mesh cylinder 3 includes multiple layers of mesh, and from the center of the inner cavity 11 outward, the mesh density of the multiple layers of mesh gradually decreases, or the mesh aperture of the multiple layers of mesh gradually increases.

[0087] In other words, the mesh cylinder 3 is a grid-like cylindrical structure woven from braided yarn 31. Along the radial direction from the central axis of the mesh cylinder 3 to the outer periphery, the mesh cylinder 3 is composed of multiple layers of mesh, each layer of mesh being a grid-like structure, with adjacent mesh layers connected to each other or woven together as a single unit.

[0088] In this embodiment, the mesh cylinder 3 includes two mesh layers, namely an inner mesh layer and an outer mesh layer. The two mesh layers are arranged concentrically in the radial direction, with the inner mesh layer close to the central axis of the mesh cylinder 3 and the outer mesh layer located on the outer periphery of the inner mesh layer. The two mesh layers are combined into one piece by a weaving process.

[0089] Here, grid density refers to the number of grid pores per unit area. The higher the grid density, the smaller and denser the pores; the lower the grid density, the larger and sparser the pores. In this embodiment, from the center of the inner cavity 11 outwards, the grid density of the multi-layer mesh gradually decreases, or the grid pore size of the multi-layer mesh gradually increases. That is, the inner mesh has a larger grid density, providing a high specific surface area, which is conducive to initial cell attachment, while the outer mesh has a smaller grid density, providing large pores, which is conducive to cell migration and blood vessel ingrowth.

[0090] The inner high-density mesh provides dense attachment points for stem cells, facilitating initial cell adhesion and aggregation; the outer low-density mesh provides space for cell migration and expansion, promoting cell growth into the periphery of the scaffold and tissue ingrowth. This gradient structure, with decreasing density from the inside out, guides cells to migrate directionally from the inner to the outer layer, promoting three-dimensional tissue reconstruction.

[0091] Preferably, the support body 1 is integrally formed by 3D printing, and the mesh cylinder 3 is integrally formed by 3D printing.

[0092] For example, the support body 1 and the mesh cylinder 3 can be 3D printed as a single unit using DLP digital light processing technology, or they can be 3D printed as a single unit using SLA stereolithography, FDM fused deposition modeling, or bioprinting technology.

[0093] Preferably, the support body 1 and the mesh cylinder 3 are 3D printed as a single unit using DLP (Digital Light Processing) technology. SLA (Stereolithography) technology utilizes an ultraviolet laser beam to scan the surface of a liquid photosensitive resin for layer-by-layer curing. This technology offers high forming precision and a surface finish superior to LCD (Liquid Crystal Lamination), and can also fabricate biomimetic scaffolds with complex internal flow channels and microporous structures. Unlike DLP, SLA uses laser point scanning for forming, while DLP uses surface projection for one-time imaging. FDM (Fused Deposition Modeling) technology uses thermoplastic polymer filaments such as PLA and PCL, which are heated, melted, and then sprayed and deposited. Although its layer texture is more pronounced and its precision is slightly lower than photopolymerization, by optimizing printing parameters such as layer height below 0.1mm and nozzle temperature, open-mesh scaffolds can be fabricated at a lower cost. However, DLP forming is smoother than FDM; if the surface is too rough, it can easily damage cells. Furthermore, FDM struggles to achieve a thickness of 0.3mm, making it less suitable for high cell compatibility requirements and only a backup option. Bioprinting (3D Bioprinting) technology directly prints a mixture of cells and biomaterials. Although the process is more complex, it can achieve the directional distribution of cells and is a more advanced alternative.

[0094] In summary, the aforementioned processes DLP, SLA, FDM, and bioprinting all belong to additive manufacturing 3D printing technology. Their core commonality lies in "layered manufacturing based on digital models," and they can all break through the limitations of traditional mold forming, achieving the "personalized biomimetic morphology" and "complex double-layer heterogeneous density mesh structure" required by this invention.

[0095] This embodiment employs Digital Light Processing (DLP) technology to 3D print the support body 1 as a single unit. DLP technology projects ultraviolet light images onto the surface of liquid photosensitive resin using a digital micromirror device (DMD), causing the resin to solidify layer by layer. This method offers advantages such as high molding precision, fast printing speed, and good surface quality.

[0096] The supporting crown 13, supporting cylinder 12, bottom cover 14, supporting column 21, and supporting plate 22 are integrally formed by 3D printing, creating a continuous overall structure. This integral molding design avoids assembly errors and weak connection points, ensuring the integrity of the structure and the continuity of mechanical transmission.

[0097] In this embodiment, the mesh cylinder 3 is integrally formed by 3D printing. The mesh cylinder 3 also employs surface projection photopolymerization (DLP) technology for 3D printing. The high-resolution XY-axis resolution of DLP technology, reaching 35μm, meets the printing requirements for the fine mesh structure of the mesh cylinder 3. The mesh cylinder 3 and the supporting body 1 use the same photosensitive resin PLA material to ensure consistent degradation characteristics and biocompatibility.

[0098] In this embodiment, the support body 1 is customized based on the patient's medical imaging data. The customization process is as follows: Image acquisition: Three-dimensional image data of the patient's cervical region is acquired via CT or MRI. Three-dimensional reconstruction: A three-dimensional model of the cervical stump is reconstructed based on the image data to determine the shape and size of the defect. Stent design: Based on the reconstructed three-dimensional model, the overall dimensions of the support body 1, including height, diameter, and wall thickness, are designed to ensure precise matching of the stent to the patient's anatomical structure. 3D printing: The customized stent model is integrally formed using 3D printing.

[0099] 3D printing technology allows for the customization of scaffolds based on each patient's specific anatomical structure, achieving "one-person-one-model" precision medicine and resolving the mismatch between standardized products and personalized needs. In this embodiment, the support body 1 can be customized according to the anatomical features of the target application scenario. The customization process is as follows: Image acquisition: Obtain three-dimensional image data of the corresponding anatomical region through CT or MRI.

[0100] 3D reconstruction: Reconstructing a 3D model of the target anatomical structure based on image data to determine the shape and size of the defect.

[0101] Scaffold design: Based on the reconstructed 3D model, the overall dimensions of the support body 1, such as height, diameter, and wall thickness, are designed to ensure that the scaffold is precisely matched with the target anatomical structure.

[0102] 3D printing: Creating personalized bracket models using 3D printing.

[0103] It should be added that the dimensions of each part of the repair stent of the present invention are matched with the cervical anatomy of the target application scenario, such as being applicable to humans or pets. The following description uses the application of the repair stent to humans and mice as examples.

[0104] When the repair scaffold is applied to mice: The total height of the repair bracket is 20mm.

[0105] The total height of the supporting crown 13 is 5mm, the wall thickness of the crown side plate 131 is 0.7mm, the thickness of the crown base plate 133 ranges from 0.3mm to 0.4mm, the diameter of the first connecting hole 135 is 1.5mm, the diameter of the first connecting hole 135 is equal to the inner diameter of the connecting cavity 211, and the diameter of the second connecting hole is 0.5mm to 2mm.

[0106] The wall thickness of the support cylinder 12 can be 0.5mm-0.9mm, such as 0.5mm, 0.6mm, 0.7mm, 0.8mm or 0.9mm. Among them, the wall thickness of 0.5mm-0.9mm ensures that the support cylinder 12 has sufficient structural strength and can effectively prevent postoperative tissue collapse.

[0107] Preferably, in this invention, the wall thickness of the support cylinder 12 is 0.7 mm. The wall thickness of the support cylinder 12 is 0.7 mm, which is greater than the wire diameter of the braided thread 31 (0.3 mm). This size difference causes the degradation rate of the support cylinder 12 to be slower than that of the mesh cylinder 3.

[0108] The total height of the support cylinder 12 can be 15mm, the outer diameter is 7.5mm, and the diameter of the inner cavity 11 is 6.1mm.

[0109] The reinforcing ring 15 has a ring diameter of 1 mm, a radial protrusion height of 1 mm, an axial width of 1 mm, a distance of 0.35 mm from the inner edge of the ring to the outer wall of the support cylinder 12, and a spacing of 0.5 mm between the upper and lower reinforcing ring groups.

[0110] The outer diameter of the support column 21 is 6.1 mm, the inner diameter (i.e., the diameter of the connecting cavity 211) is 1.5 mm, and the wall thickness is 0.7 mm.

[0111] The thickness of the support plate 22 is 1mm. The diameter of the puncture groove 221 on the support plate 22 is 0.5mm, and the groove depth is 0.2mm-0.5mm, preferably 0.3mm, so as not to penetrate the support plate 22.

[0112] The outer diameter of the bottom cover 14 is 8.9 mm and the thickness is 0.7 mm.

[0113] In the mesh tube 3, the total height is 15mm, the total diameter is 6.1mm, the braided wire 31 has a diameter of 0.3mm, and the inner hole diameter is 2.9mm. The inner hole diameter matches the outer diameter of the support column 21. This hole diameter is much larger than the size of the mouse sperm head (<0.005 mm), which can ensure that the sperm can pass through smoothly.

[0114] When a repair stent is applied to the human body, the cervix of a non-pregnant / normal adult woman is approximately 25mm-30mm in length and 20mm-25mm in diameter. The total height of the repair bracket is 28mm.

[0115] The total height of the supporting crown 13 is 8mm, the wall thickness of the crown side plate 131 is 1.8mm, the thickness of the crown base plate 133 is 0.8mm, the diameter of the first connecting hole 135 is 6mm, the diameter of the first connecting hole 135 is equal to the inner diameter of the connecting cavity 211, and the diameter of the second connecting hole is 0.5mm-2mm.

[0116] The wall thickness of the support cylinder 12 can be 1.5mm-2mm, such as 1.5mm, 1.6mm, 1.7mm, 1.8mm, 1.9mm, or 2mm. The wall thickness of 1.5mm-2mm ensures that the support cylinder 12 has sufficient structural strength and can effectively prevent postoperative tissue collapse.

[0117] Preferably, in this invention, the wall thickness of the support cylinder 12 is 1.8 mm. The wall thickness of the support cylinder 12 is 1.8 mm, which is greater than the wire diameter of the braided thread 31 by 0.3 mm. This size difference makes the degradation rate of the support cylinder 12 slower than that of the mesh cylinder 3.

[0118] The total height of the support cylinder 12 can be 20mm, the outer diameter is 22mm, and the diameter of the inner cavity 11 is 18.4mm.

[0119] The reinforcing ring 15 has a diameter of 2mm, a radial protrusion height of 2mm, a distance of 0.9mm from the inner edge of the ring to the outer wall of the support cylinder 12, and a spacing of 2.5mm between the upper and lower reinforcing ring groups.

[0120] The outer diameter of the support column 21 is 9.6 mm, the inner diameter (i.e., the diameter of the connecting cavity 211) is 6 mm, and the wall thickness is 1.8 mm.

[0121] The thickness of the support plate 22 is 1.5mm. The diameter of the puncture groove 221 on the support plate 22 is 1.5mm, and the groove depth is 0.8mm, which does not penetrate the support plate 22.

[0122] The outer diameter of the bottom cover 14 is 26mm and the thickness is 1.5mm.

[0123] In the mesh tube 3, the total height is 20mm, the total diameter is 18mm, the braided wire 31 has a diameter of 0.3mm, and the inner hole diameter is 9.6mm. The inner hole diameter matches the outer diameter of the support column 21. This hole diameter is much larger than the size of the human sperm head (<0.005 mm), which can ensure that the sperm can pass through smoothly.

[0124] Finally, it should be noted that the above embodiments are only used to illustrate the technical solutions of the present invention, and not to limit them; although the present invention has been described in detail with reference to the foregoing embodiments, those skilled in the art should understand that modifications can still be made to the technical solutions described in the foregoing embodiments, or equivalent substitutions can be made to some or all of the technical features; and these modifications or substitutions do not cause the essence of the corresponding technical solutions to deviate from the scope of the technical solutions of the embodiments of the present invention.

Claims

1. A repair stent, characterized in that, It includes a support body (1) and a mesh cylinder (3), wherein the support body (1) is provided with an inner cavity (11) and the mesh cylinder (3) is disposed in the inner cavity (11); The mesh tube (3) is a mesh-like cylindrical structure woven from braided yarn (31), and the mesh tube (3) is loaded with regenerating cells; The supporting body (1) and the mesh cylinder (3) are both made of biodegradable materials, and the wall thickness of the supporting body (1) is greater than the diameter of the braided thread (31).

2. The repair stent according to claim 1, characterized in that, The biodegradable material is polylactic acid, polycaprolactone, polylactic acid-glycolic acid copolymer, polyglycolic acid, or tricalcium phosphate composite material; The regenerated cells are human umbilical cord mesenchymal stem cells, bone marrow mesenchymal stem cells, adipose mesenchymal stem cells, amniotic mesenchymal stem cells, or autologous circulating endothelial progenitor cells.

3. The repair stent according to claim 1, characterized in that, The supporting body (1) includes a supporting cylinder (12), which is a hollow cylindrical body. The two ends of the supporting cylinder (12) are respectively provided with a supporting crown (13) and a bottom cover (14), and the supporting crown (13), the supporting cylinder (12) and the bottom cover (14) together form the inner cavity (11). The wall thickness of the support cylinder (12), the wall thickness of the support crown (13), and the wall thickness of the bottom cover (14) are all greater than the diameter of the braided thread (31).

4. The repair stent according to claim 3, characterized in that, The outer wall of the support cylinder (12) is provided with a reinforcing ring (15), which is located on the side of the support cylinder (12) near the support crown (13); The reinforcing rings (15) are provided in multiple ways, and the multiple reinforcing rings (15) are arranged sequentially at intervals along the circumference of the support cylinder (12) to form a reinforcing ring group; the reinforcing ring group is provided in multiple groups, and the multiple groups of reinforcing rings are arranged at intervals along the axial direction of the support cylinder (12), and the reinforcing rings (15) in adjacent reinforcing ring groups are staggered.

5. The repair stent according to claim 3, characterized in that, The mesh cylinder (3) is detachably disposed in the inner cavity (11); The support cylinder (12) has an opening communicating with the inner cavity (11) on the side near the bottom cover (14), and the bottom cover (14) and the support cylinder (12) are detachably connected. The repair bracket has a first use state, a second use state and a third use state. When the repair bracket is in the first use state, the inner cavity (11) is an empty cavity. When the repair bracket is in the second use state, a magnetothermal medium is provided in the inner cavity (11). When the repair bracket is in the third use state, the bottom cover (14) is detached from the support cylinder (12), and the mesh cylinder (3) is disposed in the inner cavity (11) through the opening.

6. The repair stent according to claim 5, characterized in that, The magnetocaloric medium is Fe3O4 particles, γ-Fe2O3 particles, spinel ferrite, or FeCo alloy nanoparticles. The bottom cover (14) and the support cylinder (12) can be detachably connected by means of snap-fit ​​connection, threaded connection, interference fit connection, magnetic connection or adhesive.

7. The repair stent according to claim 5, characterized in that, The supporting crown (13) includes a crown base plate (133) and a plurality of crown side plates (131) disposed on the crown base plate (133). The plurality of crown side plates (131) are arranged sequentially along the circumference of the crown base plate (133). The crown base plate (133) is connected to the supporting cylinder (12). The crown side plates (131) are disposed on the side of the crown base plate (133) away from the supporting cylinder (12). The crown base plate (133) is provided with a first connecting hole (135), and the crown side plate (131) is provided with a second connecting hole (132).

8. The repair stent according to claim 7, characterized in that, The support body (1) further includes a support column (21) disposed in the inner cavity (11). The support column (21) is provided with a communicating cavity (211). The communicating cavity (211) extends through the entire support column (21) along the axial direction of the support column (21). One end of the support column (21) abuts against the crown base plate (133) of the support crown (13), and the communicating cavity (211) communicates with the first connecting hole (135). When the repair bracket is in the first use state and the second use state, the other end of the support column (21) abuts against the bottom cover (14), and when the repair bracket is in the second use state, the magnetothermal medium is disposed in the area between the support cylinder (12) and the support column (21) of the inner cavity (11); When the repair bracket is in the third use state, the mesh tube (3) is located in the area between the support tube (12) and the support column (21) in the inner cavity (11), and the bottom cover (14) is removed from the support tube (12), and the end of the connecting cavity (211) away from the support crown (13) is open.

9. The repair stent according to claim 8, characterized in that, When the repair bracket is in the first use state, the support body (1) further includes a support plate (22) disposed in the inner cavity (11), the support plate (22) is sleeved outside the support column (21), and the inner peripheral surface of the support plate (22) abuts against the outer wall surface of the support column (21), and the outer peripheral surface of the support plate (22) abuts against the inner wall surface of the support cylinder (12); When the repair stent is in the second use state, the injection device loaded with the magnetothermal medium pierces the support plate (22) and injects the magnetothermal medium into the area of ​​the inner cavity (11) located between the support cylinder (12) and the support column (21). When the repair bracket is in the third use state, the support plate (22) is broken, and the debris of the support plate (22) and the magnetothermal medium are taken out from the inner cavity (11). Then, the mesh cylinder (3) is sleeved outside the support column (21), so that the mesh cylinder (3) is located in the area between the support cylinder (12) and the support column (21) in the inner cavity (11).

10. The repair stent according to claim 9, characterized in that, The support disk (22) has a plurality of breaking grooves (221) on its surface, and the plurality of breaking grooves (221) are arranged at intervals along the circumference of the support disk (22).

11. The repair stent according to any one of claims 1-10, characterized in that, Along the radial direction of the inner cavity (11), the mesh cylinder (3) includes multiple layers of mesh, and from the center of the inner cavity (11) outward, the mesh density of the multiple layers of mesh gradually decreases, or the mesh aperture of the multiple layers of mesh gradually increases.

12. The repair stent according to any one of claims 1-10, characterized in that, The supporting body (1) is integrally formed by 3D printing, and the mesh cylinder (3) is integrally formed by 3D printing.

Images