Thrombectomy device

Abstract

The application belongs to the technical field of medical devices, and discloses a thrombus taking device which comprises a pushing tube, a rotating tube and a cutting assembly. The proximal end of the pushing tube is connected with a handle; the rotating tube is connected with a rotating driving unit; the cutting assembly comprises an outer layer mesh disc and an inner layer mesh disc, the outer layer mesh disc is fixedly connected with the pushing tube, and the inner layer mesh disc is fixedly connected with the rotating tube; the outer layer mesh disc has a plurality of embedded mesh holes capable of being embedded into the inside of a thrombus; the rotating tube can drive the inner layer mesh disc to rotate and cut the thrombus embedded into the mesh holes. The thrombus taking device not only makes it possible to avoid the motion blind area in the cutting process of the thrombus, and is beneficial to completely remove the thrombus, but also can solve the problems of low thrombus cutting efficiency, single or limited cutting diameter and blood vessel damage caused by direct cutting of the thrombus of the current stent type device; the unique side cutting technology of the thrombus which drags out the thrombus in an integral block after reducing the length and volume of the thrombus from the side of the thrombus can avoid the risk of distal embolism or thrombus damage caused by complete circumferential cutting of the thrombus.

Description

Technical Field

[0001] This invention relates to the technical field of medical devices, and more particularly to thrombectomy devices. Background Technology

[0002] The treatment of pulmonary embolism has undergone profound changes, from symptomatic support to anticoagulation, and then to interventional and surgical interventions. Anticoagulation remains the cornerstone of pulmonary embolism treatment. In recent years, significant technological advancements have been made in interventional therapy, which allows for more precise thrombus management through minimally invasive methods. The main methods include catheter-directed thrombolysis and mechanical thrombectomy. Catheter-directed thrombolysis involves inserting a catheter directly into / around the thrombus to release thrombolytic drugs, allowing for more precise administration and reducing the risk of systemic bleeding. Mechanical thrombectomy uses a catheter to aspirate or remove the thrombus, rapidly restoring pulmonary circulation and avoiding the bleeding risks associated with thrombolytic drugs.

[0003] In existing thrombectomy techniques, the grasping and cutting of thrombi mostly relies on grinding or cutting heads embedded in the catheter. A common approach involves pushing pre-placed grinding or cutting components within the catheter lumen to the thrombus target area, where high-speed mechanical rotation directly grinds / cuts the thrombus. Some systems also simultaneously utilize high-speed circulating fluid to flush / transport the fragmented thrombus, thus completing the removal and intraluminal transport of the thrombus. In mechanical thrombectomy, the stent's support structure is primarily used to cut and remove the thrombus through stretching and rotation.

[0004] However, these abrasive thrombectomy devices generally have limitations in adaptability, failing to flexibly adapt to changes in vessel diameter. When the vessel diameter dilates, the burr head often struggles to effectively maintain contact with the vessel wall throughout the procedure, easily creating multiple blind spots during thrombus removal. Some thrombi attached to the vessel sidewall or branch openings may not be covered or contacted by the abrasive head, leading to thrombus omission and ultimately incomplete thrombus removal, significantly increasing the risk of re-embolism due to residual thrombi post-procedure. Secondly, stent devices have lower efficiency and remain challenging for fibrin-rich thrombi. Therefore, it is necessary to improve existing technologies to overcome these shortcomings in practical applications. Summary of the Invention

[0005] The purpose of this invention is to provide a thrombectomy device that solves the problems of low efficiency in cutting thrombi, difficulty in adapting the thrombus cutting structure to changes in blood vessel diameter, the presence of blind spots that can lead to thrombus retention, incomplete thrombus removal, and the risk of re-embolism in existing thrombectomy devices.

[0006] To achieve this objective, the present invention adopts the following technical solution: This invention provides a thrombectomy device, comprising: A push tube, the proximal end of which is connected to a handle; A rotating tube, the proximal end of which extends into the handle and is connected to the rotating drive unit; A cutting assembly, comprising an outer mesh disk and an inner mesh disk disposed inside the outer mesh disk, wherein the outer mesh disk is fixedly connected to the distal end of the pushing tube, and the inner mesh disk is fixedly connected to the distal end of the rotating tube; The outer mesh has multiple embedded mesh holes to embed into the thrombus, and the rotating tube can drive the inner mesh to rotate, thereby cutting the thrombus that has entered the embedded mesh holes.

[0007] Optionally, the outer mesh is woven from circular braided wires to form a plurality of the embedded mesh openings.

[0008] Optionally, the inner mesh is composed of woven filaments with edges to cut thrombi using the edges.

[0009] Optionally, multiple cutting components are provided at intervals from the distal end to the proximal end, and the diameter of the multiple cutting components increases from the distal end to the proximal end.

[0010] Optionally, an outer sleeve is provided between two adjacent outer mesh disks, and an inner sleeve is provided between two adjacent inner mesh disks, with the inner sleeve rotatably connected inside the outer sleeve.

[0011] Optionally, the inner cannula includes a first segment and a second segment connected by a one-way snap fastener. The first segment is connected to one of the inner mesh discs, and the second segment is connected to another inner mesh disc. The one-way snap fastener can restrict the rotation of the second segment so that the rotating tube can only drive the inner mesh disc connected to the first segment to rotate and cut the thrombus.

[0012] Optionally, the inner stencil has multiple developing sections spaced apart, and these developing sections can form an indicator image when the inner stencil rotates.

[0013] Optionally, the mesh density of the cutting assembly is greater on the side near the distal end than on the side near the proximal end; and / or The surface of the cutting assembly is coated with an anticoagulant drug coating; An external suction tube is sleeved on the outside of the push tube. One end of the external suction tube is connected to the suction device, and the other end extends to the far end of the push tube.

[0014] Optionally, the thrombectomy device further includes: A guide head is disposed at the distal end of the cutting assembly. The guide head has a suction chamber inside and a suction port on its surface that communicates with the suction chamber and is used to aspirate thrombus fragments. A suction tube is inserted through the rotating tube and the cutting assembly. The suction tube has a suction channel that communicates with the suction chamber. The suction channel is connected to the suction device to extract thrombus fragments.

[0015] Optionally, the surface of the guide head is provided with a protrusion, the protrusion having a suction slope, the angle between the suction slope and the axis of the rotating tube being greater than 0° and less than 90°, and the suction port being opened on the suction slope.

[0016] The beneficial effects of this invention are: During the procedure, the cutting component is pushed to the designated location via a push tube. The outer wall of the outer mesh disc presses against the inner wall of the blood vessel, compressing the thrombus attached to the vessel wall. This forces a portion of the thrombus to enter the outer mesh disc through the mesh openings. A rotating drive unit at the handle drives the rotating tube to rotate, which in turn rotates the inner mesh disc, allowing it to cut the thrombus. The inner mesh disc does not contact the vessel wall during rotation, ensuring no damage to the vessel. When cutting a portion of the thrombus, single-sided or double-sided cutting techniques are used to reduce the length and volume of the thrombus from its sides. This weakens the adhesion between the thrombus and the vessel wall, allowing the entire thrombus to be extracted and removed, avoiding excessive circumferential cutting that would produce too many thrombus fragments. Therefore, when this thrombectomy device is used, the outer mesh layer presses firmly against the vessel wall, ensuring that the thrombus at that location can enter the interior of the outer mesh layer through the embedded mesh. The inner mesh layer then rotates to cut the thrombus, eliminating blind spots during the cutting process and facilitating complete removal of the thrombus, reducing the possibility of thrombus residue and thus decreasing the risk of re-embolism. The cutting range of both the inner and outer mesh layers automatically increases as the thrombus shrinks, adapting to the thrombus cutting needs of different vessel diameters and overcoming the limitations of current technologies with single or limited cutting diameters. The unique weaving method of the inner mesh layer allows the thrombus exposed through the outer mesh layer to rotate left and right, accelerating thrombus detachment and addressing the low thrombus cutting efficiency of current stent devices. Attached Figure Description

[0017] Figure 1 This is a schematic diagram of the thrombectomy device in an embodiment of the present invention; Figure 2 This is a partial cross-sectional view of the push tube and rotating tube of the thrombectomy device in an embodiment of the present invention; Figure 3 This is a partially enlarged structural schematic diagram of the cutting component of the thrombectomy device in an embodiment of the present invention; Figure 4 This is a schematic diagram of the cutting component of the thrombectomy device in an embodiment of the present invention, which adopts a 1-press 1-braid method; Figure 5 This is a schematic diagram of the cutting component of the thrombectomy device in an embodiment of the present invention, which adopts a 2-press 1-braid design; Figure 6 This is a schematic diagram of the structure of multiple cutting components and inner sleeve of the thrombectomy device in an embodiment of the present invention; Figure 7 This is a cross-sectional view of the outer sleeve, inner sleeve, and guide head of the thrombectomy device in an embodiment of the present invention; Figure 8 This is a schematic diagram of the guide head of the thrombectomy device in an embodiment of the present invention.

[0018] In the picture: 1. Push tube; 2. Rotating tube; 3. Cutting assembly; 31. Outer mesh tray; 32. Inner mesh tray; 321. Developing section; 4. Handle; 5. Outer sleeve; 51. Limiting ring; 6. Inner sleeve; 61. One-way buckle; 62. First section; 63. Second section; 7. Guide head; 71. Suction chamber; 72. Suction port; 73. Protrusion; 8. Suction tube; 81. Suction channel. Detailed Implementation

[0019] Embodiments of the present invention are described in detail below. Examples of these embodiments are shown in the accompanying drawings, wherein the same or similar reference numerals denote the same or similar components or components having the same or similar functions throughout. The embodiments described below with reference to the accompanying drawings are exemplary and intended to explain the present invention, and should not be construed as limiting the present invention.

[0020] In the description of this invention, unless otherwise explicitly specified and limited, the terms "connected," "linked," and "fixed" should be interpreted broadly. For example, they can refer to a fixed connection or a detachable connection; a mechanical connection or an electrical connection; a direct connection or an indirect connection through an intermediate medium; or the internal communication of two components or the interaction between two components. Those skilled in the art can understand the specific meaning of the above terms in this invention according to the specific circumstances.

[0021] In the description of this invention, unless otherwise expressly specified and limited, "above" or "below" the second feature can include direct contact between the first and second features, or contact between the first and second features through another feature between them. Furthermore, "above," "over," and "on top" of the second feature includes the first feature being directly above or diagonally above the second feature, or simply indicates that the first feature is at a higher horizontal level than the second feature. "Below," "below," and "under" the second feature includes the first feature being directly below or diagonally below the second feature, or simply indicates that the first feature is at a lower horizontal level than the second feature.

[0022] The technical solution of the present invention will be further described below with reference to the accompanying drawings and specific embodiments.

[0023] like Figures 1 to 8 As shown, the present invention provides a thrombus removal device.

[0024] The thrombectomy device includes a push tube 1, a rotating tube 2, and a cutting assembly 3. The proximal end of the push tube 1 is connected to a handle 4; the proximal end of the rotating rod extends into the handle 4 and is connected to a rotation drive unit; the cutting assembly 3 includes an outer mesh plate 31 and an inner mesh plate 32 disposed inside the outer mesh plate 31. The outer mesh plate 31 is fixedly connected to the distal end of the push tube 1, and the inner mesh plate 32 is fixedly connected to the distal end of the rotating tube 2; wherein, the outer mesh plate 31 has multiple embedding mesh holes to be embedded inside the thrombus, and the rotating tube 2 can drive the inner mesh plate 32 to rotate, thereby cutting the thrombus that has entered the embedding mesh holes.

[0025] During the procedure, the cutting component 3 is pushed to the designated position via the push tube 1. The outer wall of the outer mesh 31 presses against the inner wall of the blood vessel, compressing the thrombus attached to the vessel wall. This allows a portion of the thrombus to enter the outer mesh 31 through the mesh. The rotating drive unit at the handle 4 drives the rotating tube 2 to rotate, which in turn rotates the inner mesh 32. The inner mesh 32 then cuts the thrombus. During rotation, the inner mesh 32 does not contact the vessel wall, ensuring no damage to the blood vessel. Therefore, when this thrombectomy device is used, the outer mesh 31 presses against the vessel wall, ensuring that the thrombus at that location can enter the outer mesh 31 through the mesh. The rotation of the inner mesh 32 then cuts the thrombus, eliminating blind spots during the cutting process. This facilitates thorough removal of the thrombus, reduces the possibility of thrombus residue, and thus reduces the risk of re-embolism. Moreover, the cutting range of the inner mesh disk 32 and the outer mesh disk 31 will automatically increase as the thrombus becomes smaller, adapting to the thrombus cutting needs of different blood vessel diameters and solving the limitations of the current technology in cutting a single or limited diameter.

[0026] Specifically, both the handle 4 and the rotation drive unit can employ existing technologies, which are not the inventive points of this invention and will not be elaborated upon. The push tube 1 is a catheter with openings at both ends. It can be a multi-segment composite catheter composed of one or more of the following: a helical spring tube, a braided tube, or a laser-cut hypotube. The push tube 1 may not rotate, but under specific surgical operation requirements, it can also be driven to rotate independently in conjunction with the rotation module. The proximal end of the push tube 1 is connected to the handle 4, and the distal end of the push tube 1 is fixedly connected to the outer mesh disk 31. A contrast-enhancing ring or other contrast markers are also provided at the distal end of the push tube 1. In this invention, the end closer to the handle 4 is designated as the proximal end, and the other end as the distal end.

[0027] The rotating tube 2 is inserted into the pushing tube 1. The rotating tube 2 is also a catheter with open ends. It can be a multi-segment composite catheter composed of one or more of the following: a spring tube, a braided tube, or a laser-cut hypotube. The rotating tube 2 can still transmit rotational torque even in curved paths. For example, in pulmonary artery thrombectomy and stenting surgery, the rotating tube 2 enters the thrombectomy device from the femoral artery. Therefore, there are curved anatomical structures along the path from the inferior vena cava to the right atrium, tricuspid valve, right ventricle, and pulmonary artery. The pushing tube 1 and rotating tube 2, constructed as described above, can adapt to the curvature of the blood vessel, reduce the pressure of the tube on the blood vessel, and prevent the rotating tube 2 from swinging during rotation, thus avoiding additional pressure on the blood vessel or tissue. In this embodiment, both the pushing tube 1 and the rotating tube 2 are equipped with at least one hypotube segment. The hypotube has a ball-shaped, H-shaped, or diamond-shaped head design, which ensures smooth transmission of rotational torque while also adjusting the bending tension of the tube at the bending point through its own structural deformation during bending, allowing the tube to pass more smoothly through tortuous blood vessels or rotate more smoothly at tortuous blood vessels.

[0028] The outer mesh 31 is woven from braided filaments, and its surface has multiple embedded mesh holes. The diameter of the embedded mesh holes can be designed according to different thrombus sizes. The inner mesh 32 is located inside the outer mesh 31, and there is a certain gap between the outer surface of the inner mesh 32 and the inner surface of the outer mesh 31. The gap distance can be controlled between 20μm and 300μm, and the specific gap distance can be adjusted according to the actual cutting requirements.

[0029] The inner mesh 32 is connected to the distal end of the rotating tube 2, and the proximal end of the rotating tube 2 is connected to the rotation drive unit, which can rotate within the push tube 1 to drive the inner mesh 32 to rotate, thereby creating a cutting effect where the outer mesh 31 remains stationary while the inner mesh 32 rotates. It should be understood that under specific surgical requirements, the rotating tube 2 may not rotate, and the specific setting can be determined according to the actual surgical procedure.

[0030] Optionally, the outer mesh 31 is woven from circular braided wires to form multiple embedded mesh openings.

[0031] Specifically, the circular braided yarns have an arc-shaped surface, making the outer surface of the outer mesh 31 smoother. This allows the outer mesh 31 to effectively protect the vessel wall when pressed against it, reducing the possibility of damage. Furthermore, the braiding process can employ a 1-over-1 or 2-over-1 method. A 1-over-1 method involves alternating weft and warp threads, resulting in a denser structure with uniform and regular mesh openings. This provides better adhesion to the vessel, facilitating stable thrombus compression and reducing the likelihood of displacement. A 2-over-1 method creates fewer nodes, making the outer mesh 31 more flexible, reducing irritation to the vessel wall and improving the smoothness of the implantation process. The specific braiding method can be designed according to the actual surgical requirements.

[0032] Optionally, the inner mesh 32 is composed of braided filaments with edges to cut thrombi using the edges.

[0033] Specifically, the inner mesh disc 32 is woven from flat or diamond-shaped yarns, giving it multiple sharp edges that effectively cut thrombi when rotated. The inner mesh disc 32 uses a 2-over-1 weaving method, resulting in fewer interlacing nodes, larger gaps between warp and weft yarns, and greater rigidity of individual weaving yarns. This allows both warp and weft yarns to cut the thrombus sequentially during rotation, with different cutting times. The thrombus exposed to the inner mesh disc 32 is subjected to the rotational forces of the warp and weft yarns, accelerating the thrombus detachment rate and improving cutting efficiency, particularly suitable for cutting larger, denser thrombi. In another embodiment, a 1-over-1 weaving method can be used, where the warp and weft yarns of the inner mesh disc 32 alternately and uniformly protrude, also grinding the thrombus with rotation, thus facilitating rapid thrombus abrasion.

[0034] It should be understood that the weaving method and shape of the braided wires in the inner and outer mesh discs 32 and 31 can be selected according to the actual surgical effect, and are not limited to the specific examples mentioned above. Moreover, the braided wires are all shape memory alloys, which can automatically expand as the thrombus volume decreases during thrombus cutting. On the one hand, this ensures tight contact with the blood vessel wall, and on the other hand, it can increase the cutting diameter, thereby improving cutting efficiency.

[0035] Optionally, multiple cutting components 3 are provided at intervals from the distal end to the proximal end. The diameters of the multiple cutting components 3 may be the same or different, such as the diameters of the multiple cutting components 3 increasing from the distal end to the proximal end.

[0036] Specifically, the cutting components 3 can be distributed in three intervals, with the furthest cutting component 3 having the smallest diameter and the closest cutting component 3 having the largest diameter, to adapt to the radial support force tolerance limits of blood vessels of different diameters, thereby enabling the cutting of thrombi at different locations. Optionally, an outer sleeve 5 is provided between two adjacent outer layer mesh disks 31, and an inner sleeve 6 is provided between two adjacent inner layer mesh disks 32, with the inner sleeve 6 rotatably connected inside the outer sleeve 5.

[0037] Specifically, the two ends of the outer sleeve 5 are fixedly connected to the extensions of the two outer stencils 31, respectively, while the inner sleeve 6 is rotatably fitted inside the outer sleeve 5. Limiting rings 51 are also provided on the end face of the outer sleeve 5 to restrict the axial movement of the inner sleeve 6. By using the fitted arrangement of the inner sleeve 6 and the outer sleeve 5, the coaxiality and smoothness between the inner stencil 32 and the outer stencil 31 can be improved, and the distance between the inner stencil 32 and the outer stencil 31 can be limited at the distal end, ensuring that the inner stencil 32 will not come into contact with the outer stencil 31 during rotation, thus preventing wear and energy loss.

[0038] Optionally, the inner cannula 6 includes a first segment 62 and a second segment 63 connected by a one-way snap fastener 61. The first segment 62 is connected to an inner mesh disc 32, and the second segment 63 is connected to another inner mesh disc 32. The one-way snap fastener 61 can restrict the rotation of the second segment 63 so that the rotating tube 2 can only drive the inner mesh disc 32 connected to the first segment 62 to rotate and cut the thrombus.

[0039] Specifically, the one-way latch 61 can be a ratchet structure or other latching structures capable of one-way limiting. In this embodiment, the end faces of the first segment 62 and the second segment 63 are wedged together by ratchet. The rotation direction of the rotating tube 2 can be consistent with the reverse overtaking direction of the ratchet, so that the rotating tube 2 can only drive the proximal inner mesh disc 32 to rotate. For example, the rotating tube 2 only drives the inner mesh disc 32 closest to the proximal end to rotate, while the other two inner mesh discs 32 will not rotate in the reverse overtaking state of the ratchet, so as to cut only the proximal position of the thrombus. Generally, the proximal part of the thrombus has a long formation time and is not easy to cut. After cutting the proximal part, the overall length of the thrombus is reduced, and the remaining thrombus has low adhesion, so the thrombus can be pulled out as a whole. The unique side cutting technology of reducing the length and volume of the thrombus from the side and then dragging the thrombus in one piece avoids the risk of distal embolism or thrombus damage caused by completely cutting the thrombus in the circumferential direction. The specific number of inner mesh discs 32 that need to be rotated can be designed according to the actual surgical needs. Three inner mesh discs 32 can rotate simultaneously (with the ratchet in a forward drive state), or only one inner mesh disc 32 can rotate. This invention does not make a specific limitation on this.

[0040] Optionally, the inner stencil 32 has a plurality of developing sections 321 spaced apart, and the plurality of developing sections 321 can form an indicator image when the inner stencil 32 rotates.

[0041] Specifically, multiple imaging sections 321 can be staggered, allowing the inner stencil 32 to form dynamic patterns under high-speed rotation. These dynamic patterns can also produce different visual effects depending on the rotation speed, enabling doctors to quickly determine the rotation speed, position, number, and compression status of the inner stencil 32. In other embodiments, markings can be provided on the handle 4 or other structures for differentiation.

[0042] Optionally, the mesh density of the cutting component 3 on the far end side is greater than the mesh density on the near end side.

[0043] Specifically, to successfully capture the thrombus fragments after cutting, the inner mesh 32 and the outer mesh 31 have a higher mesh density on their distal sides, resulting in smaller mesh apertures on that side, which facilitates the collection of thrombus fragments generated after cutting. In other embodiments, the mesh density of the inner mesh 32 and the outer mesh 31 can be kept uniform, while a separate protective umbrella or other structure can be provided to collect thrombus fragments separately.

[0044] Optionally, the surface of the cutting component 3 is coated with an anticoagulant drug coating (not shown in the figure).

[0045] Specifically, both the inner and outer mesh disks 31 are coated with an anticoagulant coating to ensure that thrombus fragments do not adhere to the surface of the inner mesh disk 32, thereby reducing the possibility of the inner mesh disk 32 becoming stuck during rotation.

[0046] Optionally, an external suction tube (not shown in the figure) is sleeved on the outside of the push tube 1. One end of the external suction tube is connected to the suction device, and the other end extends to the far end of the push tube 1.

[0047] Specifically, an external suction tube is sleeved on the outside of the push tube 1, and a suction channel 81 is provided on the inside of the external suction tube to promptly extract thrombus fragments. The suction device can also be equipped with modules such as a blood collector and a filter to intercept thrombus fragments after blood is extracted and then return the blood to the patient's body.

[0048] Optionally, the thrombectomy device further includes a guide head 7 and a suction tube 8. The guide head 7 is located at the distal end of the cutting assembly 3, and has a suction chamber 71 inside. The surface of the guide head 7 has a suction port 72 that communicates with the suction chamber 71 and is used to aspirate thrombus fragments. The suction tube 8 passes through the rotating tube 2 and the cutting assembly 3, and has a suction channel 81 that communicates with the suction chamber 71. The suction channel 81 communicates with the suction device to extract thrombus fragments.

[0049] Specifically, in the farthest cutting component 3, a guide head 7 is provided at the far end of its outer sleeve 5. The guide head 7 has a cavity inside serving as a suction chamber 71. A suction tube 8 passes through the rotating tube 2, and a suction channel 81 is provided within the wall of the suction tube 8, communicating with the suction chamber 71. A through hole is formed on the surface of the guide head 7 as a suction port 72, which communicates with the suction chamber 71. The suction port 72 can be provided singly or in multiple intervals; this invention does not limit this.

[0050] After the thrombus is cut, the thrombus fragments can easily escape. The escaped thrombus fragments will flow with the blood towards the guide head 7, where they will be sucked into the suction chamber 71 by the suction port 72 and then drawn out along the suction channel 81, so as to remove the escaped thrombus fragments in time.

[0051] Optionally, the surface of the guide head 7 is provided with a protrusion 73, the protrusion 73 has a suction slope, the angle between the suction slope and the axis of the rotating tube 2 is greater than 0° and less than 90°, and the suction port 72 is opened on the suction slope.

[0052] Specifically, the protrusion 73 can be pointed and inclined on the side to serve as a suction slope. The suction port 72 is formed on the suction slope so that when the inner mesh disk 32 rotates, it will cause the blood to generate a vortex. The suction slope can correspond to the vortex, thereby improving the suction effect of the suction port 72 on blood clot fragments. In other embodiments, the protrusion 73 can also extend in the opposite direction to the rotating tube 2 to form a suction slope. The specific shape of the protrusion 73 is not specifically limited in this invention.

[0053] Obviously, the above embodiments of the present invention are merely examples for clearly illustrating the present invention, and are not intended to limit the implementation of the present invention. Those skilled in the art can make other variations or modifications based on the above description. It is neither necessary nor possible to exhaustively describe all embodiments here. Any modifications, equivalent substitutions, and improvements made within the spirit and principles of the present invention should be included within the scope of protection of the claims of the present invention.

Claims

1. A bolt removal device, characterized in that, include: Push tube (1), the proximal end of which is connected to handle (4); Rotating tube (2), the proximal end of which extends into the handle (4) and is connected to the rotating drive unit; The cutting assembly (3) includes an outer mesh disk (31) and an inner mesh disk (32) disposed inside the outer mesh disk (31). The outer mesh disk (31) is fixedly connected to the far end of the pushing tube (1), and the inner mesh disk (32) is fixedly connected to the far end of the rotating tube (2). The outer mesh disc (31) has multiple embedded mesh holes to embed into the thrombus, and the rotating tube (2) can drive the inner mesh disc (32) to rotate, thereby cutting the thrombus that enters the embedded mesh holes.

2. The thrombectomy device according to claim 1, characterized in that, The outer mesh (31) is woven from circular braided wires to form a plurality of the embedded mesh holes.

3. The thrombectomy device according to claim 1, characterized in that, The inner mesh (32) is composed of woven filaments with edges to cut thrombi using the edges.

4. The thrombectomy device according to claim 1, characterized in that, The cutting components (3) are arranged in multiple intervals from the distal end to the proximal end, and the diameter of the multiple cutting components (3) increases from the distal end to the proximal end.

5. The thrombectomy device according to claim 4, characterized in that, An outer sleeve (5) is provided between two adjacent outer mesh disks (31), and an inner sleeve (6) is provided between two adjacent inner mesh disks (32). The inner sleeve (6) is rotatably connected inside the outer sleeve (5).

6. The thrombectomy device according to claim 5, characterized in that, The inner cannula (6) includes a first segment (62) and a second segment (63) connected by a one-way buckle (61). The first segment (62) is connected to one of the inner mesh discs (32), and the second segment (63) is connected to another inner mesh disc (32). The one-way buckle (61) can restrict the rotation of the second segment (63) so that the rotating tube (2) can only drive the inner mesh disc (32) connected to the first segment (62) to rotate and cut the thrombus.

7. The thrombectomy device according to claim 1, characterized in that, The inner stencil (32) has a plurality of developing sections (321) spaced apart, and the plurality of developing sections (321) can form an indicator image when the inner stencil (32) rotates.

8. The thrombectomy device according to claim 1, characterized in that, The mesh density of the cutting component (3) on the distal side is greater than that on the proximal side; and / or The surface of the cutting component (3) is coated with an anticoagulant drug coating; An external suction tube is sleeved on the outside of the push tube (1). One end of the external suction tube is connected to the suction device, and the other end extends to the far end of the push tube (1).

9. The thrombectomizing device according to any one of claims 1 to 8, characterized in that, The thrombectomy device also includes: A guide head (7) is disposed at the distal end of the cutting assembly (3). A suction chamber (71) is disposed inside the guide head (7). A suction port (72) is disposed on the surface of the guide head (7) and communicates with the suction chamber (71) for suctioning thrombus fragments. A suction tube (8) is inserted between the rotating tube (2) and the cutting assembly (3). The suction tube (8) has a suction channel (81) that communicates with the suction chamber (71). The suction channel (81) is connected to the suction device to extract thrombus fragments.

10. The thrombectomy device according to claim 9, characterized in that, The surface of the guide head (7) is provided with a protrusion (73), the protrusion (73) has a suction slope, the angle between the suction slope and the axis of the rotating tube (2) is greater than 0° and less than 90°, and the suction port (72) is opened on the suction slope.

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