Plugging device

Abstract

The utility model relates to the technical field of medical instruments, and discloses a plugging device which mainly comprises an implantation body and a retractable first supporting net. The implantation body is responsible for achieving effective plugging of the left auricle, the first supporting net is formed by weaving the first weaving wires and connected with the far end of the implantation body so as to adapt to the far-end anatomical structure in the auricle, necessary buffering capacity is provided, oppression of the plugging device on the wall of the auricle in the implantation process is remarkably reduced, and the plugging effect is improved. On the other hand, in the implanting process, the first supporting net makes contact with the left auricle wall, certain resistance change feedback is generated, an operator can perceive the interaction between the first supporting net and the left auricle wall through the resistance change, accurate control over the implanting depth is achieved, and the implanting efficiency is improved. Excessive compression or damage to the auricle wall is avoided, and meanwhile stable positioning of the plugging device is ensured.

Description

Technical Field

[0001] This application relates to the technical field of medical devices, and further relates to a occluding device. Background Art

[0002] Heart diseases are one of the major health problems globally. Atrial fibrillation is one of the most common arrhythmias, which significantly increases the risk of stroke in patients. The left atrial appendage is the main site of thrombus formation in the heart, and its management is crucial for preventing stroke.

[0003] The left atrial appendage extends anteroinferiorly along the anterior lateral wall of the left atrium, being a narrow, curved blind-ended structure with rich pectinate muscles and trabeculae attached to its inner wall. The thickness of the weakest part of the atrial appendage wall is only about 1 mm, and its anatomical morphology is diverse. Existing occluding devices often have difficulty in taking into account both the anatomical characteristics of the left atrial appendage and the safety of the operation. The distal structure of some devices may cause damage to the atrial appendage wall during implantation. Continuously improving the distal structure of the left atrial appendage occluder to enhance the safety of device implantation still has great significance for the clinical application of the device. Summary of the Utility Model

[0004] Aiming at the above technical problems, the purpose of this application is to provide an occluding device that can adapt to the relatively small internal space at the distal end of the left atrial appendage, and at the same time does not damage tissues when penetrating deep into the left atrial appendage, providing a safer and more effective occluding technique.

[0005] To achieve the above purpose, this application provides an occluding device, including:

[0006] An implantation main body for occluding the left atrial appendage;

[0007] A contractible first support net, which is woven by a plurality of first braided wires, and the proximal end of the first support net is connected to the distal end of the implantation main body to adapt to the distal structure in the atrial appendage.

[0008] Optionally, the distal end of the first support net converges on a first converging element, and the proximal end of the first support net converges on a second converging element.

[0009] Optionally, the radial dimension range of the first braided wire is between 0.025 and 0.085 mm.

[0010] Optionally, the number range of the first braided wires is between 24 and 96.

[0011] Optionally, the implantation main body is woven by a plurality of second braided wires, and the radial supporting force of the implantation main body is greater than that of the first support net.

[0012] Optionally, the radial supporting force of the first supporting net is 1 / 5 to 1 / 2 of the radial supporting force of the implant body.

[0013] Optionally, the circumferential surface of the first supporting net is provided with a concave structure, and the concave structure is used to improve the compressibility of the first supporting net in its axial direction.

[0014] Optionally, the first supporting net includes a first part and a second part arranged along its axial direction;

[0015] Both the first part and the second part are conical bodies with a monotonically decreasing cross-sectional area, and are symmetrically distributed with respect to the radial median line of the first supporting net, so that the first supporting net forms a net structure with a cross-sectional area on both sides smaller than that of the middle part;

[0016] Or,

[0017] The first part is a conical body with a monotonically decreasing cross-sectional area, the cross-sectional area of the second part remains the same in the axial direction of the first supporting net, and the large-diameter part of the first part is connected to the distal end of the second part.

[0018] Optionally, the peripheral wall of the first supporting net is provided with friction elements to provide additional friction;

[0019] And / or,

[0020] The peripheral wall of the first supporting net is provided with sensing elements to sense the resistance between the peripheral wall of the first supporting net and the atrial appendage structure.

[0021] Optionally, the occlusion device further includes an anchoring structure, and the anchoring structure is arranged on the peripheral wall of the implant body. BRIEF DESCRIPTION OF THE DRAWINGS

[0022] The following briefly describes the drawings used in the description of the embodiments of the present application.

[0023] Figure 1 is a schematic diagram of the application scenario of the occlusion device in the prior art;

[0024] Figure 2 is a schematic diagram of the overall structure of an occlusion device provided by an embodiment of the present application;

[0025] Figure 3 is a schematic diagram of the structure of a first supporting net provided by an embodiment of the present application;

[0026] Figure 4 is a schematic diagram of the structure of another first supporting net provided by an embodiment of the present application;

[0027] Figure 5It is a schematic structural diagram of one of the first support meshes provided by the embodiments of the present application;

[0028] Figure 6 It is a schematic overall structural diagram of another plugging device provided by the embodiments of the present application;

[0029] Figure 7 It is a schematic structural diagram of an implantation main body provided by the embodiments of the present application.

[0030] Explanation of the reference numerals in the drawings: 100, the first support mesh; 101, the first braided wire; 110, the first bundling element; 120, the second bundling element; 1001, the first part; 1002, the second part; 200, the implantation main body; 201, the second braided wire; 210, the third bundling element; 220, the fourth bundling element; 300, the anchoring structure; 400, the concave structure; 501, the aorta; 502, the aortic valve; 503, the left ventricle; 504, the left atrium; 505, the mitral valve; 506, the left atrial appendage; 507, the right ventricle; 508, the right atrium; 509, the tricuspid valve; 510, the interatrial septum; 511, the superior vena cava; 512, the inferior vena cava. Detailed implementation manners

[0031] In order to more clearly illustrate the technical solutions in the embodiments of the present application or the prior art, the specific implementation manners of the present application will be described below with reference to the accompanying drawings. Obviously, the accompanying drawings in the following description are only some embodiments of the present application. For those of ordinary skill in the art, without creative efforts, other drawings can be obtained based on these drawings, and other implementation manners can also be obtained.

[0032] To make the drawings concise, only the parts related to the application are schematically shown in each drawing, and they do not represent the actual structure of the product. In addition, to make the drawings concise and easy to understand, in some drawings, for components with the same structure or function, only one of them is schematically shown, or only one of them is marked. In this document, "one" not only means "only this one", but also means the situation of "more than one".

[0033] It should be further understood that the term " / and" used in the specification and appended claims of the present application refers to any combination and all possible combinations of one or more of the related listed items, and includes these combinations.

[0034] In this text, it should be noted that unless otherwise clearly specified and defined, the terms "install", "connect", and "join" should be understood in a broad sense. For example, it can be a fixed connection, a detachable connection, or an integral connection; it can be a mechanical connection or an electrical connection; it can be a direct connection or an indirect connection through an intermediate medium, and it can be the communication inside two components. For those of ordinary skill in the art, the specific meanings of the above terms in this application can be understood according to specific circumstances.

[0035] In the embodiments shown in the drawings, the indication of directions (such as up, down, left, right, front, and back, etc.) when describing the structures and movements of various components is not absolute but relative, and is not used to limit the directions during the actual use of the product.

[0036] In the embodiments of this application, "proximal" and "distal" are used to describe the position or direction of the associated (or described) object (referred to as the associated object) relative to the operator (such as a doctor or operator) from the perspective of the operator. For example, "proximal" refers to the end closer to the operator during the normal operation of the medical device by the operator; "distal" refers to the end farther from the operator during the normal operation of the medical device by the operator, or the end that first enters the patient's body. By way of example, the "proximal" end of A refers to the end of A closer to the operator; the "distal" end of A refers to the end of A farther from the operator. Or, the "proximal" end of A refers to the end of A farther from the patient (or the affected area, or the implantation position); the "distal" end of A refers to the end of A closer to the patient (or the affected area, or the implantation position).

[0037] Atrial fibrillation (AF) is a common clinical arrhythmia, and its prevalence increases significantly with age. AF not only increases the patient's risk of death but also may lead to a series of serious complications such as stroke, heart failure, cognitive dysfunction, and dementia, seriously threatening the patient's quality of life and health and safety. With the accelerating aging of the global population, the prevalence of AF is expected to continue to rise, bringing unprecedented challenges to the healthcare system.

[0038] In the treatment strategy of AF, stroke prevention is the core content. Percutaneous left atrial appendage closure (LAAC), as an emerging minimally invasive interventional treatment method, prevents thrombus formation by occluding the left atrial appendage, thereby reducing the risk of stroke caused by AF.

[0039] See Figure 1The heart is a hollow muscular organ with four chambers, namely the left atrium 504, the left ventricle 503, the right atrium 508 and the right ventricle 507. The four chambers of the heart are connected to different blood vessels. The left ventricle 503 is connected to the aorta 501. The aorta 501 orifice is located above and right in front of the left atrioventricular orifice, and the semilunar aortic valve 502 is attached to the periphery. The left atrium 504 is connected to the pulmonary vein, the right ventricle 507 is connected to the pulmonary artery, and the right atrium 508 is connected to the superior vena cava 511 and the inferior vena cava 512. The left atrium 504 and the right atrium 508 are separated by an atrial septum 510. The part of the front of the left atrium 504 that protrudes to the right front is the left atrial appendage 506. The left ventricle 503 and the right ventricle 507 are separated by a ventricular septum. There is an atrioventricular valve (hereinafter referred to as valve) between the atrium and the ventricle. When the ventricle relaxes, the valve opens and blood flows from the atrium to the ventricle; when the ventricle contracts, the valve closes to prevent blood from flowing back from the ventricle to the atrium. The valve between the left atrium 504 and the left ventricle 503 is the mitral valve 505, and the valve between the right atrium 508 and the right ventricle 507 is the tricuspid valve 509.

[0040] Theoretically, through left atrial appendage occlusion surgery, an interventional surgical method is used to puncture the femoral vein, and the occluder is delivered through the femoral vein to the landing area in the left atrial appendage 506 and then deployed to block the left atrial appendage 506. This can prevent the blood clot formed in the left atrial appendage 506 from dislodging and forming an embolism, and can reduce the chance of atrial fibrillation embolism by at least 90%.

[0041] Traditional left atrial appendage occlusion devices usually use metal frames or plastic mesh structures, but these devices have shortcomings in adapting to the anatomical structure of the left atrial appendage, providing effective occlusion, and reducing surgical risks.

[0042] Since the left atrial appendage 506 is a complex bag-like structure with anatomical features of gradually narrowing from the proximal end to the distal end and possibly tending to be flat, this structure makes the design and implantation of the left atrial appendage occlusion device challenging, and existing devices may not provide sufficient support force, resulting in incomplete occlusion or damage to surrounding tissues.

[0043] Based on the problems in the prior art, the implant device provided in the present application can ensure that no tissue is damaged when penetrating deep into the left atrial appendage 506, thereby improving the safety of the operation.

[0044] The design of the blocking device in this application is described below in conjunction with the accompanying drawings:

[0045] First, if Figure 2 As shown, the occlusion device includes an implant body 200 and a first support mesh 100 connected thereto. In the implanted state, the implant body 200 is fixed at the entrance of the left atrial appendage 506 to form a stable occlusion foundation. Figure 3As shown, the first support mesh 100 is woven by a number of first braided wires 101, and its proximal end is connected to the distal end of the implant body 200. During the implantation process, the first support mesh 100 can contract to a certain extent. As the implantation device gradually penetrates deeper into the left atrial appendage 506, the first support mesh 100 enters the atrial appendage interior ahead of the implant body 200. Its braided structure will undergo adaptive deformation when contacting the atrial appendage wall, making the contact between it and the atrial appendage wall softer and reducing the mechanical stimulation to the atrial appendage wall.

[0046] At the same time, the first support mesh 100 provided in this embodiment, due to its elasticity, can generate resistance feedback when contacting the atrial appendage wall, allowing the operator or medical staff to feel the interaction between the occlusion device and the atrial appendage wall, thereby more accurately judging the positioning and fixation of the occlusion device. Through this resistance feedback, the surgeon can monitor the implantation process of the occlusion device in real time, avoid excessive advancement or mispositioning, reduce the risk of damage to the atrial appendage wall, significantly improve the safety of the operation, and protect the patient's heart tissue while ensuring the occlusion effect.

[0047] In addition, please refer to the accompanying drawings of the specification. The distal end of the first support mesh 100 converges on the first converging element 110, and its proximal end converges on the second converging element 120. The first converging element 110 is used to converge the distal end of the first support mesh 100, and the second converging element 120 is used to converge the proximal end of the first support mesh 100. Through the coordinated work of the first converging element 110 and the second converging element 120, the first support mesh 100 can achieve different degrees of tension at its distal and proximal ends, which helps to reduce the pressure on the atrial appendage wall, reduce the risk of damage, and at the same time ensure the stability of the occlusion device.

[0048] At the same time, as Figure 7 shown, the distal end of the implant body 200 converges on the third converging element 210 and is connected to the second converging element 120 of the first support mesh 100, enhancing the integrity and stability of the structure and ensuring the close cooperation between the implant body 200 and the first support mesh 100; the proximal end of the implant body 200 converges on the fourth converging element 220. The surgeon can make the implant body 200 closely fit near the entrance of the left atrial appendage 506 by operating the third converging element 210 and the fourth converging element 220, while maintaining appropriate elasticity to adapt to the size changes of the left atrial appendage 506 of different patients.

[0049] Of course, in some cases, the implant body 200 and the first support mesh 100 are integrally formed, ensuring the continuity and integrity of the structure, eliminating the possible connection gaps or looseness problems in the traditional split design, and thus improving the overall stability and reliability of the device.

[0050] In one embodiment, the implant body 200 is woven from a number of second braided filaments 201. This braided structure not only ensures good flexibility and support of the implant body 200, but also ensures uniform force distribution when it is subjected to external forces.

[0051] More importantly, the radial support force of the implant body 200 is greater than that of the first support mesh 100, which ensures that the implant body 200 plays a major support role in the occlusion device, providing the necessary stability. Although the first support mesh 100 has a smaller radial support force, its design focus is on providing buffering and adaptability. The smaller radial support force enables it to better adapt to the shape and size changes of the atrial appendage wall, achieving effective buffering to reduce damage to the atrial appendage wall. The combination of the larger radial support force of the implant body 200 and the smaller radial support force of the first support mesh 100 achieves gentle contact with the atrial appendage wall while maintaining the occlusion effect of the occlusion device.

[0052] Optionally, the radial support force of the first support mesh 100 is 1 / 5 to 1 / 2 of the radial support force of the implant body 200, so that the first support mesh 100 can maintain sufficient softness to adapt to the anatomical structure of the left atrial appendage 506 while providing the necessary structural support, thereby preventing damage to the atrial appendage wall.

[0053] Based on the above embodiments, in another embodiment, an anchoring structure 300 is provided on the peripheral wall of the implant body 200, which is mainly responsible for cooperating with the implant body 200 to fix the entire occlusion device in a preset position, improving the stability of the occlusion device in the atrial appendage, reducing the risk of displacement or detachment caused by cardiac pulsation, and ensuring the safety and success rate of the surgery.

[0054] Among them, the number of the anchoring structures 300 can be multiple, and the multiple anchoring structures 300 can be arranged between the distal end of the implant body 200 and its radial midline. This layout enables the anchoring structures 300 to cover a wide area of the implant body 200 from the distal end to the middle, providing continuous fixing force, enabling the occlusion device to fit more closely to the inner wall of the left atrial appendage 506 and reducing the chance of blood flowing into the left atrial appendage 506.

[0055] In addition, the anchoring structures 300 can also be arranged on both sides of the radial midline of the implant body 200, ensuring the balanced fixation of the occluder in the left atrial appendage 506, helping to evenly distribute the fixing force, avoiding local over-stretching or compression, and thus reducing the risk of damage to the inner wall of the left atrial appendage 506.

[0056] An adjustable anchoring element can also be provided on the implant body 200, allowing the operator to adjust the anchoring force according to the actual needs during the surgery, or designing multiple sizes and shapes of the anchoring structures 300 for the implant body 200 to adapt to different sizes and shapes of the left atrial appendage 506.

[0057] Further, the related design of the first support net 100 in the above embodiments will be described:

[0058] In one embodiment, in the occlusion device of the present application, the first support net 100 is formed by the staggered distribution of a plurality of first braided wires 101. The adjacent first braided wires 101 are arranged at a preset angle. These braided wires are interwoven to form an overall mesh structure, providing necessary flexibility and buffering ability, so that during the implantation process of the first support net 100, it can deform in the radial and axial directions, thereby reducing the local pressure on the atrial appendage wall and avoiding potential tissue damage. To adapt to the anatomical structure of the left atrial appendage 506.

[0059] Among them, the radial deformation ability of the first support net 100 enables the support net to adapt to the inner walls of atrial appendages with different diameters, while the axial deformation ability enables the first support net 100 to synchronously make adaptive adjustments to the irregular morphology at the distal end of the atrial appendage structure during the implantation process of the implant body 200, ensuring the smoothness and safety of the implantation process.

[0060] The deformation ability of the first support net 100 also depends to a certain extent on the setting of the first braided wire 101. In some cases, the radial dimension of the first braided wire 101 can have a greater impact. In one embodiment provided by the present application, the radial dimension range of the first braided wire 101 is between 0.025 and 0.085 mm. If the radial dimension of the first braided wire 101 is lower than 0.025 mm, it may lead to insufficient mechanical strength of the braided wire and inability to withstand the mechanical loads that may be encountered during the implantation process and after long-term implantation. In addition, too thin braided wires may be more likely to break during the braiding process, affecting the durability and reliability of the first support net 100. On the contrary, if the radial dimension of the braided wire exceeds 0.085 mm, it may reduce the softness and adaptability of the first support net 100, and at the same time increase the pressure on the atrial appendage wall, increasing the risk of damaging the atrial appendage tissue and triggering an inflammatory reaction.

[0061] More specifically, in one embodiment, similar to the radial dimension setting in the above embodiment, setting an appropriate number of the first braided wires 101 can ensure that the first support net 100 provides appropriate support force on the basis of providing sufficient buffering. As the number of the first braided wires 101 increases, the overall support force of the first support net 100 will increase accordingly, playing a certain auxiliary support role, but it must be controlled on the premise of not damaging the atrial appendage tissue. And as the number of the first braided wires 101 decreases, the first support net 100 may not be able to provide enough surface area to disperse the force, thereby increasing the local pressure on the atrial appendage wall and the risk of damage. In a specific setting, the first support net 100 can be composed of 24 to 96 first braided wires 101.

[0062] In addition, the overall shape of the first support mesh 100 also plays a certain role in its ability to contract and deform. Please refer to the attached drawings of the specification. Figure 6 Specific recessed structures 400 are provided on the circumferential surface of the first support mesh 100. The main purpose of these structures is to increase the compressibility of the first support mesh 100 in its axial direction. Through this design, the first support mesh 100 can better adapt to the spatial shape inside the left atrial appendage 506, especially in the relatively narrow area at the distal end of the left atrial appendage 506.

[0063] Among them, the recessed structures 400 can be a series of uniformly distributed grooves, pits or concave rings, which are arranged along the circumferential surface of the first support mesh 100 to form a regular geometric pattern. Without sacrificing the structural integrity, these recessed structures 400 provide additional compression space for the first support mesh 100. When the first support mesh 100 contacts the atrial wall, the presence of the recessed structures 400 enables the first support mesh 100 to be appropriately compressed, reducing local pressure on the atrial wall and enhancing the safety of the operation.

[0064] Moreover, in other related embodiments, multiple recessed structures 400 can be provided on the circumferential surface of the first support mesh 100, or several recessed structures 400 with different sizes can be provided (these two cases are not shown in the drawings). By providing multiple recessed structures 400, multiple compression regions can be provided, enabling the first support mesh 100 to deform in multiple directions, thus better adapting to the complex anatomical structure inside the left atrial appendage 506; and by providing recessed structures 400 with different sizes, a wider compression range can also be provided, enabling the first support mesh 100 to more flexibly adapt to the size and shape of the left atrial appendage 506 of different patients, improving the versatility and effectiveness of the occlusion device.

[0065] In one embodiment, the related design of the first support mesh 100 is further optimized. Among them, friction elements (not shown in the drawings) are integrated on the circumferential wall of the first support mesh 100 to provide additional friction, and these friction elements are crucial for ensuring the stability of the occlusion device during the operation and after long-term implantation.

[0066] It can be understood that the friction elements increase the contact area with the inner wall of the left atrial appendage 506, achieving the effect of increasing the friction between the first support mesh 100 and the atrial wall, thereby improving the stability of the occlusion device and reducing the possibility of its displacement. Moreover, the friction elements can adopt a textured surface design, such as a concave-convex planar structure, to increase the friction coefficient of the contact surface.

[0067] In another embodiment, a sensing element is provided on the peripheral wall of the first support mesh 100. The main purpose of the sensing element is to monitor and feedback the contact resistance between the first support mesh 100 and the atrial appendage structure in real time. By precisely sensing the resistance changes at the contact points, an intuitive feedback system is provided, thereby enabling fine control of the implantation depth and position of the device during the surgical procedure.

[0068] By providing the sensing element, the resistance encountered by the first support mesh 100 during implantation can be precisely monitored, ensuring that the occluding device does not exert excessive pressure on the inner wall of the left atrial appendage 506 and avoiding damage. Among them, the layout range of the sensing element can cover the first support mesh 100 relatively comprehensively, ensuring uniform distribution on the entire peripheral wall of the first support mesh 100 to obtain comprehensive resistance information and avoid local over-compression of the atrial appendage wall. For example, the sensing element can adopt a highly sensitive pressure sensor that can detect the minute pressure changes generated due to the contact with the atrial appendage wall.

[0069] In one embodiment, reference may be made to the appended Figure 4 description. The first support mesh 100 is axially differentiated into a first part 1001 and a second part 1002. They are both designed as conical bodies with a monotonically decreasing cross-sectional area and are symmetrically distributed with respect to the radial midline of the first support mesh 100. This design makes the first support mesh 100 have a smaller cross-sectional area on both sides and a larger cross-sectional area in the middle part.

[0070] The larger cross-sectional area in the middle part of the first support mesh 100 helps to adapt to the relatively spacious area in the middle of the left atrial appendage 506, while the smaller cross-sectional area can fit the anatomically narrowing structure at the distal end of the left atrial appendage 506, reducing the pressure on the inner wall of the left atrial appendage 506 and thus lowering the risk of causing compression or damage to the atrial appendage wall, especially in the relatively weak area at the distal end of the atrial appendage.

[0071] At the same time, the setting of this conical body makes the contact surface of the first support mesh 100 with the inner wall of the left atrial appendage 506 gradually increase during implantation, thus achieving a progressive contact and reducing the sudden impact on the atrial appendage wall.

[0072] In contrast, in another embodiment, as Figure 5As shown, the setting of the first part 1001 remains unchanged. The first part 1001 maintains its original conical body design with a monotonically decreasing cross-sectional area to provide elasticity and buffering effects. The cross-sectional area of the second part 1002 remains consistent in the axial direction of the first support mesh 100, ensuring a certain degree of stability and support force. The large-diameter part of the first part 1001 is connected to the distal end of the second part 1002, forming a structural transition region, which helps to enhance the overall stability of the device. When the first support mesh 100 is restricted by the internal structure of the left atrial appendage 506, the first part 1001 and the second part 1002 can work together to disperse the acting force and reduce the damage to the inner wall of the left atrial appendage 506.

[0073] Of course, the specific shape contour of the first support mesh 100 can also be adjusted according to the actual situation. In some other embodiments, the first support mesh 100 may be divided into more than just the first part 1001 and the second part 1002 in the axial direction, and there can be more segments, so that different regions of the first support mesh 100 can provide different degrees of flexibility and support to carry out targeted design for the internal structure of the left atrial appendage 506.

[0074] It should be noted that the above-mentioned embodiments can be freely combined according to needs. The above is only the preferred embodiment of the present application. It should be pointed out that for those of ordinary skill in the art, without departing from the principle of the present application, several improvements and refinements can be made, and these improvements and refinements should also be regarded as the protection scope of the present application.

Claims

1. A plugging device, characterized in that Comprising: An implant body for left atrial appendage occlusion; A contractible first support mesh, the first support mesh being woven by a plurality of first braided wires, and the proximal end of the first support mesh being connected to the distal end of the implant body to adapt to the distal structure within the atrial appendage.

2. The occlusion device according to claim 1, wherein: The distal end of the first support mesh converges at a first converging element, and the proximal end of the first support mesh converges at a second converging element.

3. The occlusion device according to claim 1, wherein: The radial dimension range of the first braided wire is between 0.025 and 0.085 mm.

4. The occlusion device according to claim 3, wherein: The number range of the first braided wires is between 24 and 96.

5. The occlusion device according to claim 1, wherein: The implant body is woven by a plurality of second braided wires, and the radial support force of the implant body is greater than the radial support force of the first support mesh.

6. The occlusion device according to claim 5, wherein: The radial support force of the first support mesh is 1 / 5 to 1 / 2 of the radial support force of the implant body.

7. The occlusion device according to claim 1, wherein: A concave structure is provided on the peripheral surface of the first support mesh, and the concave structure is used to increase the compressibility of the first support mesh in its axial direction.

8. The occlusion device according to claim 1, wherein: The first support mesh includes a first part and a second part arranged along its axial direction; Both the first part and the second part are conical bodies with a monotonically decreasing cross-sectional area, and are symmetrically distributed with respect to the radial midline of the first support mesh, so that the first support mesh forms a mesh structure with a cross-sectional area on both sides smaller than that of the middle part; Or, The first part is a conical body with a monotonically decreasing cross-sectional area, the cross-sectional area of the second part remains consistent in the axial direction of the first support mesh, and the large-diameter part of the first part is connected to the distal end of the second part.

9. The occlusion device according to claim 1, wherein: Friction elements are provided on the peripheral wall of the first support mesh to provide additional friction; And / or, Sensing elements are provided on the peripheral wall of the first support mesh to sense the resistance between the peripheral wall of the first support mesh and the atrial appendage structure.

10. The plugging device according to any one of claims 1-9, characterized in that, Further comprising: An anchoring structure, the anchoring structure being provided on the peripheral wall of the implant body.

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