Intravascular resection device

Abstract

The invention relates to an endovascular resection device, comprising: a handle housing having an accommodating portion; the catheter extends in the axial direction, the near end of the catheter is rotationally connected with the handle shell, and a rotary cutting tool bit is arranged at the far end of the catheter; the bending adjusting assembly comprises a sliding rod, a wire drawing ring, a button and a bending adjusting wire, the sliding rod is rotationally arranged in the containing part, the sliding rod is provided with a sliding rod inner cavity, the guide pipe penetrates through the sliding rod inner cavity and is fixedly connected with the sliding rod, the sliding rod is sleeved with the wire drawing ring in the mode that the wire drawing ring can slide relatively but cannot rotate relatively, and the button is arranged on the bending adjusting wire. The button is rotationally arranged on the wire drawing ring in a sleeving mode, the far end of the bending adjusting wire is fixed to the far end side of the catheter, and the near end of the bending adjusting wire is fixed to the wire drawing ring. According to the excision device, bending adjustment of the catheter can be achieved, the catheter can be integrally rotated to change the bending direction after bending adjustment, and therefore the rotary cutting tool bit can be better attached to the diseased region by adjusting the position of the rotary cutting tool bit, excision efficiency is improved, and adaptability is improved.

Description

Technical Field

[0001] The present invention relates to the field of medical instruments, and in particular to an intravascular resection device. Background Art

[0002] Arteriosclerosis obliterans (ASO) of the lower extremities refers to a chronic progressive disease caused by atherosclerosis, which forms plaques and thickens the intima of the blood supply artery, leading to stenosis or occlusion of the lumen, insufficient blood supply to the affected limb, and clinical manifestations such as decreased skin temperature, resting pain, pale complexion, and intermittent claudication. The most common site is the femoral popliteal artery, which is more common in the elderly. The incidence rate of people over 70 years old is 15-20%, and the proportion of male patients is slightly higher than that of female patients. With the improvement of people's living standards and the aggravation of aging, the incidence rate of ASO of the lower extremities has been increasing year by year.

[0003] Currently, plaques in blood vessels are removed by atherectomy. Plaque removal technology directly reduces the plaque load of the target blood vessel and can obtain good lumen preparation, which is in line with the current concept of "intervention without implantation" of ASO intracavitary treatment. However, the current plaque removal device has limited bending function and poor adaptability. Summary of the invention

[0004] Based on this, it is necessary to provide an intravascular resection device to address the above-mentioned problems, comprising: a handle shell, the handle shell having a receiving portion; a catheter, extending axially, a proximal end of which is rotatably connected to the handle shell, and a rotary cutting head is provided at the distal end; a bending adjustment assembly, the bending adjustment assembly comprising a sliding rod, a drawing ring, a button and a bending adjustment wire, the sliding rod being rotatably arranged in the receiving portion, the sliding rod having a sliding rod inner cavity, the catheter passing through the sliding rod inner cavity and being fixedly connected to the sliding rod, the drawing ring being axially slidable relative to the sliding rod but being unable to be rotatably mounted on the sliding rod relative to the sliding rod, the button being rotatably mounted on the drawing ring, the distal end of the bending adjustment wire being fixed to the distal side of the catheter, and the proximal end being fixed to the drawing ring.

[0005] Furthermore, it also includes a catheter connector, which is rotatably connected to the proximal side of the shell; the catheter passes through the catheter connector and is fixedly connected thereto, and the distal end of the slide rod is fixedly connected to the proximal end of the catheter connector.

[0006] Furthermore, a first limiting member extending axially is disposed on the outer periphery of the sliding rod, and a second limiting member cooperating with the first limiting member is disposed on the inner wall of the wire drawing ring. The first limiting member can slide relative to the second limiting member but cannot rotate.

[0007] Furthermore, the button comprises a button ring, and the button ring is rotatably sleeved on the wire drawing ring.

[0008] Furthermore, the button also includes a button body connected to the button ring, and the button body is connected to a limiting unit; a limiting plate extending along the axial direction is provided in the handle shell, and the limiting unit is slidingly connected to the limiting plate, and a plurality of limiting protrusions for limiting the movement of the limiting unit are axially spaced on the limiting plate.

[0009] Furthermore, the distal side wall of the slide rod is provided with a slide rod through groove connected to the inner cavity of the slide rod. After the proximal end of the bending wire extends out from the tube wall of the catheter, it passes through the slide rod through groove and is fixedly connected to the wire drawing ring.

[0010] Furthermore, a wire drawing ring limiting portion is also provided on the outer periphery of the sliding rod, and the wire drawing ring limiting portion has a notch groove, and the wire drawing ring can abut against the wire drawing ring limiting portion, and the proximal end of the bending wire passes through the notch groove and is fixedly connected to the wire drawing ring.

[0011] Furthermore, a spiral shaft is inserted into the catheter, a power assembly is arranged in the receiving portion, the distal end of the spiral shaft is fixedly connected to the rotary cutting cutter head, and the proximal end is connected to the power assembly.

[0012] Furthermore, a three-way joint is arranged in the receiving portion, and the three-way joint includes a main body tube having a three-way joint cavity, the spiral shaft passes through the three-way joint cavity, and the proximal side of the sliding rod is rotatably sealed and connected to the distal side of the main body tube.

[0013] Furthermore, the outer circumference of the spiral shaft has a spiral structure, and the spiral structure extends axially from the distal end side of the spiral shaft to the three-way joint cavity.

[0014] Furthermore, it also includes a connecting tube, the proximal end of which is sealed and connected to the main tube, and the distal end of the connecting tube has an expanded section, and the expanded section is rotatably and sealedly connected to the proximal end of the slide rod.

[0015] Furthermore, it also includes a transmission sealing shell arranged in the accommodating portion, the transmission sealing shell has a sealed cavity, the power component includes a power transmission component, the power transmission component is arranged in the sealed cavity, and the spiral shaft extends from the three-way joint cavity into the sealed cavity to be connected with the power transmission component.

[0016] Furthermore, the transmission sealing shell further includes a motor mounting portion, the power assembly further includes a motor, the motor has a motor shaft, the motor is mounted in the motor mounting portion, and the motor shaft is connected to the power transmission assembly.

[0017] The technical solution of the present invention has the following beneficial effects: the intravascular resection device adopted by the present invention has a bending device, which can realize the bending operation of the catheter on the one hand, and on the other hand, the catheter can be rotated as a whole, and the bending direction of the catheter can be adjusted after the bending is completed, thereby increasing the adaptability of the bending operation, and can adapt to various types of lesions such as eccentric lesions, diffuse lesions, and large vessel lesions in the blood vessels. After the catheter head end is bent, the rotary cutting head can be more closely fitted to the lesion site, thereby improving the resection efficiency and reducing the damage to the blood vessels where no lesions have occurred. In addition, because the rotary cutting head can be adjusted in an adjustable bending direction, a larger vascular lumen diameter can be obtained after surgery on the vascular lesion site, providing convenience and possibility for subsequent treatment. BRIEF DESCRIPTION OF THE DRAWINGS

[0018] Figure 1 is an overall appearance view of the cutting device in the first embodiment;

[0019] Figure 2 is a three-dimensional structural diagram of the cutting device in the first embodiment with the outer shell removed;

[0020] Figure 3 is an overall exploded structural diagram of the cutting device in the first embodiment;

[0021] Figure 4 is an overall cross-sectional view of the resection device in the first embodiment;

[0022] Figure 5 It is a structural diagram of the transmission sealing housing of the cutting device in the first embodiment;

[0023] Figure 6 for Figure 4 A magnified view of point B in FIG.

[0024] Figure 7 is a structural diagram of a slide bar of a cutting device in the first embodiment;

[0025] Figure 8 is a button structure diagram of the cutting device in the first embodiment;

[0026] Fig. 9 It is a structural diagram of the wire drawing ring of the cutting device in the first embodiment;

[0027] Fig.10 A partial view of the cutting device in the first embodiment involving the limiting unit;

[0028] Fig.11 A partial view of the bending adjustment structure of the cutting device in the first embodiment;

[0029] Fig.12 for Fig.11 The enlarged view at C in the figure;

[0030] Fig.13 It is a schematic diagram of the bending operation of the cutting device in the first embodiment;

[0031] Fig.14 is a structural diagram of a cutter head assembly of a cutting device in a first embodiment;

[0032] Fig.15 for Figure 4 A in the enlarged view;

[0033] Figure 16-17 It is a structural diagram of the rotary cutting cutter head and the spiral shaft in the second embodiment;

[0034] Fig.18 is a cross-sectional view of the rotary cutting tool head in the second embodiment;

[0035] Figure 19a-19b FIG. 1 is an installation view of the rotary cutting cutter head and the spiral shaft in the second embodiment;

[0036] Figures 20a-20c It is a structural diagram of a cutter head with few edges, a cutter head with multiple edges, and a cutter head with full edges in the second embodiment;

[0037] Figures 21a-21c It is a structural diagram of the speed adjustment gears and different tool heads in the second embodiment;

[0038] Fig. 22 It is a three-dimensional structural diagram of the installation of the rotary cutting cutter head and the spiral shaft in the third embodiment;

[0039] Fig.23 is a sectional view of the installation of the rotary cutting cutter head and the spiral shaft in the third embodiment; DETAILED DESCRIPTION

[0040] In order to make the above-mentioned objects, features and advantages of the present invention more obvious and easy to understand, the specific embodiments of the present invention are described in detail below in conjunction with the accompanying drawings. In the following description, many specific details are set forth to facilitate a full understanding of the present invention. However, the present invention can be implemented in many other ways different from those described herein, and those skilled in the art can make similar improvements without violating the connotation of the present invention, so the present invention is not limited by the specific implementation disclosed below.

[0041] It should be noted that when an element is referred to as being "fixed to" or "disposed on" another element, it may be directly on the other element or there may be an element in the middle. When an element is considered to be "connected to" another element, it may be directly connected to the other element or there may be an element in the middle. The terms "upper", "lower", "left", "right" and similar expressions used to indicate directions are used for illustrative purposes only and are not intended to be the only implementation method. The specific directions are determined by Figure 2The figure shows that the cutting device is placed horizontally as a reference, wherein the XX direction is the distal-proximal direction, the YY direction is the front-rear direction, and the ZZ direction is the upper-lower direction or the vertical direction.

[0042] Unless otherwise defined, all technical and scientific terms used herein have the same meaning as those commonly understood by those skilled in the art of the present invention. The terms used herein in the specification of the present invention are only for the purpose of describing specific embodiments and are not intended to limit the present invention. The term "and / or" used herein includes any and all combinations of one or more related listed items.

[0043] It should be noted that, for medical devices, the end of the medical device that is relatively close to the operator is generally called the "proximal end", and the end of the medical device that is relatively far from the operator is called the "distal end", and the "proximal end" and "distal end" of any component of the delivery system are defined based on this principle, where "proximal end" and "distal end" are only used to describe the orientation, and do not only refer to the end face of the proximal end or the end face of the distal end; "axial" or "longitudinal axis" refers to the direction parallel to the line connecting the distal center and the proximal center of the medical device; "radial" or "transverse" refers to the direction perpendicular to the axial direction.

[0044] First embodiment

[0045] See also Figure 1 As shown, the present embodiment relates to an intravascular resection device 1, which is used to resect diseased tissue in a blood vessel. The intravascular diseased tissue in the present embodiment includes thrombus, plaque or a mixture thereof. The intravascular resection device 1 includes a handle shell 50, the distal side of the handle shell 50 is connected to a catheter 20, the proximal side is connected to a discharge tube 84, and a blade assembly 10 is arranged at the distal end of the catheter 20. A speed regulating assembly 30 and a bending adjusting assembly 10 are rotatably connected to the handle shell 50. A power assembly 70 is arranged in the handle shell 50, and the power assembly 70 transmits power to the blade assembly 10. After the blade assembly 10 resects the diseased tissue, the power is transported to the discharge tube 84 through the catheter and discharged from the human body.

[0046] See also Figure 2-4As shown, the handle housing 50 constitutes the housing of the handle, and the cavity inside it constitutes a receiving portion 501 for receiving or supporting other parts of the handle. In order to facilitate installation and manufacturing, the handle housing 50 in this embodiment is divided into two parts and includes an upper housing 51 and a lower housing 52. A limit plate 502 extending along the axial direction is provided in the distal inner cavity of the upper and lower housings, and a plurality of limit protrusions 5021 extending vertically are provided on the limit plate 502 at intervals along the axial direction. Among them, the plate surface of the limit plate 502 is vertically arranged, that is, its plate surface is uprightly connected to the inner wall of the upper and lower housings. The speed regulating assembly 30 includes a speed regulating knob 31 and a speed regulating mainboard 32. The speed regulating mainboard 32 is electrically connected to the power supply 60 and the motor 71. By rotating the speed regulating knob 31, the motor 71 can be infinitely regulated. The specific speed regulation can be achieved by changing the current or using a PWM speed regulation mechanism. The switch 90 is used to turn on and off the vascular resection device 1, and is the main operating switch of the vascular resection device 1. A spiral shaft 75 is rotatably connected in the catheter 20, and the spiral shaft 75 passes through the catheter 20. The distal end of the spiral shaft 75 is connected to the cutter head assembly 10, and the proximal end is connected to the power assembly 70. The power assembly 70 drives the spiral shaft 75 to rotate, thereby realizing the rotary cutting function of the cutter head assembly 10. Specifically, the power assembly 70 includes a motor 71 and a power transmission assembly 70a. The input end of the power transmission assembly 70a is connected to the motor 71, and the output end thereof is connected to the spiral shaft 75, so that the power of the motor 71 is transmitted to the spiral shaft 75 through the power transmission assembly 70a.

[0047] See also Figure 5As shown, the structure of the transmission sealing shell 80 is described. The transmission sealing shell 80 is mainly used to encapsulate the power transmission assembly, and includes a left sealing shell 82 and a right sealing shell 81. The left sealing shell 82 is sealed and connected to the right sealing shell 81 (such as by dispensing or welding) to form an internal sealed cavity 801. The right sealing shell 81 includes a right sealing shell body 811 and a Luer connector 812 connected to the outside of the right sealing shell body 811. The Luer connector 812 is connected to the sealed cavity 801. A cap 813 is provided at the free end of the Luer connector 812. The cap 813 is used to close the open end of the Luer connector 812. A through hole (not shown in the figure) for the guide wire to pass through is provided on the cap 813. The guide wire can pass through the cap 813 and enter the sealed cavity 801. The left sealing shell 82 includes a left sealing shell body 821, which is used to cooperate with the right sealing shell 811 to form a sealed cavity 801. A motor mounting portion 823 and a three-way joint 822 are also provided at the distal end of the left sealing shell body 821. The motor mounting portion 823 and the three-way joint 822 can be connected to each other or arranged at intervals. The motor mounting portion 823 is cylindrical in shape as a whole, and has a motor mounting cavity 823a inside. The shape of the motor mounting cavity 823a matches the external shape of the motor 71. The three-way joint 822 includes a main body pipe 8221 having a three-way joint cavity 822a and a side branch pipe 8222 connected to the three-way joint cavity 822a, and the side branch pipe 8222 is connected to the discharge pipe 84.

[0048] See again Figure 2-4 And combined Figure 5, the power transmission assembly 70a of the vascular resection device in this embodiment is described. The power transmission assembly 70a includes a driving gear 74, a transmission gear 77, a second bearing 72b, a transmission shaft 77, and a third bearing 72c arranged in a sealed cavity 801. The front end of the motor 71 (the side with the motor shaft 711) is installed in the motor installation cavity 823a, and the motor shaft 711 is fixedly connected to the driving gear 74 installed in the sealed cavity 801. In this embodiment, the fixed connection between the motor shaft 711 and the driving gear 74 is achieved by the connecting shaft 73. The distal end side of the connecting shaft 73 is fixedly sleeved on the motor shaft 711, and the proximal end side extends into the driving gear 74 and is fixedly connected thereto. Of course, in other embodiments, the connecting shaft 73 may not be provided so that the motor shaft 711 is directly fixedly connected to the driving gear 74. The first bearing 72a is also provided in the motor installation cavity 823a, and the first bearing 72a is sleeved on the outside of the motor shaft 711 to limit and guide the motor shaft 711. The outer circumference of the transmission shaft 76 is sleeved with a second bearing 72b, a transmission gear 77, a third bearing 72c and a sealing gasket 78 in sequence from the distal end to the proximal end. The first bearing 72a, the second bearing 72b and the third bearing 72c in this embodiment have similar structures, and all have inner rings and outer rings that are rotatably connected to each other, and the inner and outer rings are respectively connected to different components to realize the rotational connection between the two. For example, for the second bearing 72b, its outer ring is fixedly mounted on the inner wall of the sealed cavity 801, and the inner ring is fixedly sleeved on the distal outer circumference of the transmission shaft 76, so as to realize the rotational connection between the transmission shaft 76 and the transmission sealing shell 81. The transmission gear 77 is fixedly sleeved on the transmission shaft 76 and meshes with the driving gear 74. Through the above arrangement, the power of the motor 71 can be transmitted to the transmission shaft 76, that is, the transmission shaft 76 is used for the power output shaft to output the power of the motor 71. The transmission shaft 76 is a shaft-like structure with a cavity inside, and a spiral shaft 75 is fixedly connected inside. The interior of the spiral shaft 75 has a cavity that runs through its distal end to the proximal end, and its proximal end side extends into the transmission shaft 76 and is fixedly connected thereto, and the distal end side is arranged in the catheter 20 and is concentrically connected to the rotary cutting blade 11. The exterior of the spiral shaft 75 is axially provided with a spiral structure extending from the distal end to the proximal end, and the spiral structure may be a convex or groove structure. For the convenience of installation, the connection part of the proximal side of the spiral shaft 75 with the transmission shaft 76 may not be provided with a spiral structure. When the transmission shaft 76 is installed in the sealed cavity 801, the transmission shaft 76, the spiral shaft 75 and the Luer connector 812 will be axially aligned and connected. By sleeve-arranging a sealing pad 78 on the proximal periphery of the transmission shaft 76, the transmission shaft 76, the spiral shaft 75 and the Luer connector 812 are sealed and connected. The guide wire can extend into the spiral shaft 75 through the Luer connector 812, and extend from the distal side of the spiral shaft 75 to enter a specific part in the human body.When the motor 71 drives the motor shaft 711 to rotate, the motor shaft 711 will drive the driving gear 74 fixedly connected thereto to rotate, the driving gear 74 drives the transmission gear 77 meshing therewith to rotate, the transmission gear 77 drives the transmission shaft 76 to rotate, and the transmission shaft 76 drives the spiral shaft 75 fixedly arranged in its inner cavity to transmit, so that through the above-mentioned power transmission component, the power of the motor 71 is transmitted to the spiral shaft 75, and finally drives the rotary cutting head 11 to rotate to achieve the removal of the diseased tissue. The speed of the motor 71 is adjusted by rotating the speed knob 31, and then the cutting speed of the rotary cutting head 11 can be synchronously adjusted. Specifically, the speed regulating assembly 30 has the function of adjusting the rotation speed of the rotary cutting head 11, which can realize the adjustment of the rotation speed of the rotary cutting head 11 from 0 to the maximum. The speed regulating gear in this embodiment includes the OFF gear (switch gear), the MIN gear (low speed gear), the MID gear (medium speed gear) and the MAX gear (high speed gear). When the speed knob 31 is in the OFF position, the peeling cutter head 11 does not rotate; when the speed knob 31 is in the MIN position, the rotation speed of the peeling cutter head 11 is low speed, which is 2000-10000 r / min; when the speed knob 31 is in the MID position, the rotation speed of the peeling cutter head 11 is medium speed, which is 10000-20000 r / min; when the speed knob 31 is turned to the MAX position, the rotation speed of the peeling cutter head 11 is high speed, which is 20000-26000 r / min.

[0049] In this embodiment, the power transmission assembly is encapsulated by the transmission sealing shell 80, and the power transmission assembly is arranged in the sealing cavity 801. On the one hand, the above-mentioned encapsulation can realize the modular setting of the power transmission assembly, that is, the power transmission assembly is encapsulated in the transmission sealing shell 80 to form a power transmission module, and in the actual installation process, the module can be installed on the housing 50 as a whole, which is convenient for assembly and disassembly; on the other hand, the power transmission module is sealed and encapsulated, which can protect the power transmission assembly and reduce the noise during the operation of the power transmission assembly, thereby reducing the working noise of the intravascular resection device 1.

[0050] The bending adjustment assembly 40 in this embodiment is described below. Figure 2-4 6, the bending adjustment assembly includes a slide bar 45, a wire drawing ring 44, a button 42, a bending adjustment wire 48 and a bending adjustment ring 49. The bending adjustment ring 49 is fixedly arranged on the distal end side of the catheter 20, one end of the bending adjustment wire 48 is fixed to the bending adjustment ring 49, and the other end is fixed to the wire drawing ring 44. By pushing the button 42 to slide, the wire drawing ring 44 is driven to move axially, thereby pulling the bending adjustment wire 48 to achieve the bending operation of the catheter 20.

[0051] See also Figure 7As shown, the structure of the slide bar 45 is described. The slide bar 45 is a rod-shaped structure extending in the axial direction, and has a slide bar inner cavity 454 running through its proximal side and distal side, and a first stopper 452 is arranged on its outer periphery. Exemplarily, the first stopper 452 is a protruding structure extending in the axial direction. In other embodiments, the first stopper 452 can also be a groove structure extending in the axial direction. On the proximal side of the slide bar 45, a bearing stopper 453 and a wire drawing ring stopper 457 are arranged in sequence from the distal end to the proximal end. The bearing stopper 453 is an annular protruding structure, which is used to abut against the bearing set on the slide bar 45 to limit it axially. The wire drawing ring stopper 457 is also an annular protruding structure, which is used to abut against the wire drawing ring 48 set on the slide bar 45 to limit it axially. A notch groove 458 is also provided on the wire drawing ring stopper 457, and the notch groove 458 extends in the axial direction so that the wire drawing ring stopper 457 is a circular ring structure with a notch in the circumferential direction. On the distal side of the wire drawing ring stopper 457, a slide bar through groove 455 communicating with the slide bar inner cavity 454 is provided on the outer circumference of the slide bar 45. The slide bar through groove 455 extends in the axial direction and can extend to the distal end face of the slide bar 45, and its proximal end is closer to the distal end of the slide bar 45 than the wire drawing ring stopper 457.

[0052] See also Figure 8 As shown, the structure of the button 42 is described. The button 42 includes a button body 421, which is a rod-shaped structure extending in the axial direction, and a button portion 422 is provided on its rear end side, and a button ring 423 is provided on the other side opposite to the button portion 422, that is, on the front section side of the button body 421. When the button is installed on the housing 50, the central axis of the button ring 423 is parallel to the axis of the catheter 20. A rod unit 424 extending in the vertical direction is also provided on the upper and lower walls of the button body 421. Of course, in other embodiments, the rod unit can be provided only on the upper wall or the lower wall.

[0053] See also Fig. 9As shown, the structure of the wire drawing ring 44 is described. The wire drawing ring 44 is a cylindrical structure with a wire drawing ring inner cavity 443 as a whole, and the inner cavity allows the two ends of the wire drawing ring 44 to pass through in the axial direction. The wire drawing ring 44 includes a wire drawing ring body 441 and a limiting flange 442 arranged on the proximal side of the wire drawing ring body 441, and the limiting flange 442 is used to axially limit the bearing sleeved thereon. A second limiting member 444 is arranged on the inner wall of the wire drawing ring inner cavity 443. The second limiting member 444 in this embodiment is a groove structure that cooperates with the first limiting member 452 on the slide rod 45, and extends axially from one end of the wire drawing ring 44 to the other end. Of course, in other embodiments, when the first limiting member is a groove structure, the second limiting member is a protruding structure that cooperates therewith. In addition, a bending wire fixing hole 445 is also arranged on the wire drawing ring 44, and the distal side of the bending wire is fixedly arranged in the bending wire fixing hole 445.

[0054] Continue to see Figure 2-4 , combined with Figure 6-9 , the bending adjustment component 40 in this embodiment is explained. The catheter 20 extends axially, extends proximally and is inserted into the receiving portion 501 of the shell 50, extends distally and extends out of the handle shell 50, and a bending adjustment ring 49 is fixedly provided in the inner wall of the proximal side thereof. Among them, the catheter 20 is rotatably connected to the shell 50 through a catheter connector 46. Specifically, the catheter connector 46 is rotatably connected to the distal side of the shell 50, and the catheter connector 46 itself is elastic, which can constitute a stress buffer to relieve the stress at the connection between the catheter 20 and the shell 50. The catheter 20 is inserted into the catheter connector 46 and fixedly connected thereto. When the catheter connector 46 is rotated, the catheter 20 can be driven to rotate axially relative to the shell 50.

[0055] The slide bar 45 is fixedly sleeved on the outer periphery of the conduit 20 and is rotatably arranged in the receiving portion 501. When the conduit 20 rotates, the slide bar 45 can be driven to rotate relative to the housing 50 in the receiving portion 501. In this embodiment, the fourth bearing 41a and the fifth bearing 41c are sleeved on the outer periphery of the slide bar 45 to achieve the rotational connection between the slide bar 45 and the housing 50. A wire drawing ring 44 is slidably sleeved on the outer periphery of the slide bar 45, and the first stopper 444 on the wire drawing ring 44 cooperates with the first stopper 452 on the slide bar 44, thereby limiting the rotational freedom of the wire drawing ring 44, which can only slide relative to the slide bar 44 but cannot rotate. The button ring 423 of the button 42 is rotatably sleeved on the outer periphery of the wire drawing ring 44 and is rotatably connected with the wire drawing ring 44, and the button body 421 is arranged on the housing 50 and is slidably connected with the housing 50. In this embodiment, the fixed connection between the button ring 423 and the wire drawing ring 44 is achieved through the sixth bearing 41b. Specifically, the sixth bearing 41b is fixedly sleeved on the outer periphery of the wire drawing ring 44, and the button ring 423 is fixedly sleeved on the sixth bearing 41b, that is, the wire drawing ring 44 is fixed to the inner ring of the sixth bearing 41b, and the button ring 423 is fixed to the outer ring of the sixth bearing 41b, so that the button ring 423 can rotate relative to the wire drawing ring 44. In addition, the proximal side of the slide rod 45 is rotatably sealed and connected to the three-way joint 822. Specifically, in this embodiment, the rotational connection between the slide rod 45 and the three-way joint 822 is achieved through the connecting tube 47. The proximal side of the connecting tube 47 has an enlarged portion 471, and the end face of the enlarged portion 471 is connected to the proximal end of the slide rod 45 through the seventh bearing 41d. The provision of the enlarged portion 471 can increase the contact area between the connecting tube 47 and the seventh bearing 41d, and enhance the stability of the connection between the two. Among them, the seventh bearing 41d is a bearing structure with a sealing function, and a sealing structure is provided between its inner and outer rings, so as to realize the sealed connection between the enlarged portion 471 and the three-way joint 822. The proximal side of the connecting tube 47 is sealed and connected to the distal side of the three-way joint 822. In this embodiment, the proximal side of the connecting tube 47 extends into the three-way joint 822 to realize a sealed fixed connection. Of course, in other embodiments, the connecting tube 47 may not be provided, and the proximal end of the slide rod 45 is directly connected to the three-way joint 822 for rotation and sealing. The proximal side of the catheter 20 passes through the catheter connector 46, the slide rod 45, and the connecting tube 47 in sequence, and then communicates with the three-way joint cavity 822a of the three-way joint 822. Specifically, the proximal end face of the catheter 20 may be flush with the proximal end face of the connecting tube 47 or extend from the connecting tube 47 and extend into the three-way joint cavity 822a. For the spiral rod 75 , its proximal end passes through the catheter 20 and continues to extend proximally and passes through the connecting tube 47 to enter the three-way joint cavity 822a , and then enters the sealed cavity 801 from the three-way joint cavity 822a to be fixedly connected with the driven gear 77 .

[0056] See also Fig.10As shown, the limiting units 43 are rotatably connected to the rod units 424 on both sides of the button body 421. In this embodiment, the limiting units 43 can be set in the form of limiting rollers, which are rotatably connected to the rod units 424. When the button 42 slides axially on the shell 50, the limiting units 43 on both sides roll along the limiting plates 502 set in the upper and lower shells respectively. When the button 42 stops sliding, the limiting protrusion 5021 set on the limiting plate 502 will limit the limiting unit 43 and restrict its continued movement, so that the button 42 can stay at a certain position after the bending is completed to maintain the bending state. In other embodiments, the limiting member can also be set in other forms, such as a convex block form or other structures, as long as it can cooperate with the limiting protrusion 5021 and be limited by the limiting protrusion 5021.

[0057] See also Figure 11-12 As shown, for the bending wire 48, after the proximal end of the bending wire 48 is fixed to the wire drawing ring 44, the distal end thereof is radially bent inward, passes through the notch groove 458 and enters the through groove 455 provided on the slide bar 45. Since the catheter 20 is inserted into the inner cavity of the slide bar 45, the bending wire 47 can enter the inner cavity or inner wall of the catheter 20 through the through groove 455, and extend toward the distal end along the catheter 20 to be fixedly connected with the bending ring 49. Among them, the notch groove 458 can realize the avoidance of the wire drawing ring limiter 457 to the bending wire 48, reduce the bending angle of the bending wire 48 on the way to the through groove 455, and improve the force transmission performance of the bending wire 48.

[0058] The bending assembly 40 in this embodiment can realize the bending operation of the catheter 20 on the one hand, and can drive the entire catheter to rotate after the bending is completed, thereby changing the bending direction of the catheter 20. Fig.13As shown, when the button 42 is pushed toward the proximal side, the button 42 will drive the wire drawing ring 44 connected to it to slide along the slide bar 45, thereby pulling the bending wire 48 fixed to the wire drawing ring 44 to achieve the bending operation of the catheter 20. After the bending is completed, due to the restriction of the limit plate 502 on the roller 43, the button 42 can be maintained at a specific bending position, and the button 42 will not be displaced due to the resilience of the bending wire 48. When the bending direction of the catheter 20 needs to be changed after the bending is completed, the catheter connector 46 can be manually rotated. At this time, the catheter connector 46 will drive the catheter 20, the slide bar 45, the wire drawing ring 44 and the bending wire 48 to rotate relative to the three-way joint 822 and the housing 50. Since the slide bar 45 is connected to the three-way joint 822 in a rotational sealing manner, the rotation of the slide bar 45 will not affect the connection sealing performance between it and the three-way joint 822. In addition, since the button 42 is rotatably connected to the wire drawing ring 44, although the button 42 does not rotate relative to the housing 50, it does not restrict the rotation of the wire drawing ring 44. In this embodiment, the catheter 20 can be driven to rotate around the axial direction by rotating the catheter connector 46 to adjust the bending direction, thereby expanding the applicable scope of the bending operation, so that the bending area can be oriented to a specific direction according to actual needs.

[0059] See also Figure 14-15As shown, the structure of the cutter head assembly 10 is explained. The cutter head assembly includes a rotary cutting cutter head 11, a sleeve 12 and a limit seat 13. Among them, the limit seat 13 is fixedly connected to the distal side of the catheter 20, and the sleeve 12 is fixedly sleeved on the outer periphery of the limit seat 13. The proximal end of the rotary cutting cutter head 11 is rotatably connected to the inner cavity formed by the sleeve 12 and the limit seat 13, and the distal side extends out of the sleeve 12 and is exposed to the sleeve 12. The rotary cutting cutter head 11 is fixedly connected to the distal end of the spiral shaft 75 (using a non-detachable connection method such as welding or bonding), and the rotary cutting cutter head 11 is driven to rotate by the spiral shaft 75 to achieve rotary cutting. The outer periphery of the spiral shaft 75 is provided with a spiral structure 75a. The rotary cutting cutter head 11 includes a first cutting portion 11a, a second cutting portion 11b and a connecting portion 11c that are interconnected from the distal end to the proximal end. The first cutting portion 11a has a plurality of first cutting edges 1110 arranged opposite to each other in the radial direction, and the second cutting portion 11b has a second cutting edge 1120 arranged at intervals in the circumferential direction. In this embodiment, two first cutting edges 1110 are provided, and four second cutting edges 1120 are provided. The connecting portion 11c is used for fixed connection with the spiral shaft 75, and a cutter head slot 1130 is provided between the second cutting portion 11b and the connecting portion 11c. A limiting boss 131 cooperating with the cutter head slot 113 is provided at the distal end of the limiting seat 13. Among them, the limiting seat 13 is sleeved on the outer periphery of the rotary cutting cutter head 11 and its limiting boss 131 is clamped in the cutter head slot 1130, so that the rotary cutting cutter head 11 can be axially and radially limited. A part of the sleeve 12 is sleeved on the outer periphery of the limiting seat 13 to limit the limiting seat 13, and the other part is sleeved on the outer periphery of the rotary cutting cutter head 11 to protect and shield the cutter head 11. Among them, the first cutting portion 11a is exposed to the sleeve 12, and the second cutting portion 11b is located in the sleeve 12. In the actual operation process, for example, when the diseased tissue of the blood vessel wall is removed, the first cutting portion 11a is used for initial cutting to remove the diseased tissue from the blood vessel wall. The removed diseased tissue will enter the sleeve 12 and be located in the gap between the sleeve 12 and the second cutting portion 11b as the rotary cutting cutter head 11 rotates. Due to the restriction of the sleeve 12 on the diseased tissue, the second cutting portion 11b will further cut the diseased tissue located in the gap so that the diseased tissue is separated from each other and broken into smaller pieces of diseased tissue. As the rotary cutting cutter head 11 rotates, the diseased tissue will enter the catheter 20. Since the outer side of the spiral shaft 75 has a threaded structure, as the spiral shaft 75 rotates, the threaded structure will transport the diseased tissue from the distal end of the catheter to the proximal end and to the three-way joint cavity 822a of the three-way joint 822, and finally be discharged from the discharge pipe 84.

[0060] Second embodiment

[0061] The intravascular resection device in this embodiment is substantially the same as that in the first embodiment, except that the rotary cutting blade head and the spiral shaft are connected in a different manner. Unlike the first embodiment in which the spiral shaft and the rotary cutting blade head are connected in an inseparable manner, in this embodiment, the rotary cutting blade head and the spiral shaft are connected in a quick-change manner for easy replacement.

[0062] See also Fig.16 As shown, the rotary cutting cutter head 110 includes a first cutting portion 111 and a second cutting portion 112, wherein the outer structure of the first cutting portion 111 and the second cutting portion 112 is substantially the same as that in the first embodiment, and will not be described in detail herein. A connecting portion 751 is provided on the distal side of the spiral shaft 750, and a clamping joint 752 arranged at intervals along the circumferential direction is provided on the outer periphery of the connecting portion 751. In this embodiment, the clamping joint 752 is a spherical protrusion, and the number thereof is two and they are symmetrically arranged along the circumferential direction. In other embodiments, the number of the clamping joints 752 may also be three or more, which are evenly or unevenly arranged at intervals along the circumferential direction on the outer periphery of the connecting portion 751.

[0063] See also Figure 17-18 As shown, a connecting hole 113 is provided on the second cutting portion 112, and two radially opposite mounting grooves 114 are provided on the inner wall of the connecting hole 113 along the circumferential direction. In other embodiments, three or more mounting grooves can also be provided on the inner wall of the connecting hole 113 along the circumferential direction, and the number of the mounting grooves is the same as that of the clamp joint 752 and the shapes match, so that each clamp joint 752 can be embedded in the corresponding mounting groove. For each mounting groove 114, it includes an introduction groove 114a extending in the axial direction and a limiting groove 114b provided at the bottom (distal end) of the introduction groove 114a and connected to the introduction groove 114a. Among them, the introduction groove 114a and the limiting groove 114b are mutually offset in the circumferential direction, and the shape of the limiting groove 114b matches the shape of the clamp joint 752, and the depth matches the axial length of the clamp joint 752. In this embodiment, when the clamping joint 752 is a spherical protrusion, the cross-sectional shape of the introduction groove 114a is square, and the limiting groove 114b is set as a spherical protrusion structure that can accommodate the clamping joint 752, and its cross-sectional shape is arc-shaped. Among them, there is a transition portion 115 at the connection between the introduction groove 114a and the limiting groove 114b, and the transition portion 115 is a radially inward protruding protrusion structure between the introduction groove 114a and the limiting groove 114b. When the spiral shaft 750 is concentrically connected to the rotary cutting cutter head 110, that is, the spiral shaft 750 is concentrically inserted into the connecting hole 113, in the vertical and axial cross-sections, the minimum distance between the transition portion 115 and the center of the connecting hole 113 is less than the maximum distance between the clamping joint 752 and the center of the connecting hole 113. Therefore, the clamping joint 752 will abut against the clamping joint 752 to limit its rotation. See. Figure 19a-19b, the installation process of the spiral shaft 750 and the rotary cutting cutter head 110 is described. When the rotary cutting cutter head 110 and the spiral shaft 750 need to be assembled, the connection hole 113 of the rotary cutting cutter head 110 is aligned with the spiral shaft 750 so that the distal end of the spiral shaft 750 is inserted into the connection hole 113. During the insertion process, the clamping joint 752 slides along the introduction groove 114a to its bottom. At this time, the clamping joint 752 is located in the introduction groove 114a and adjacent to the limit groove 114b, as shown in FIG. Fig.19a As shown. As shown by the arrow in Figure 19b, the spiral shaft 750 rotates counterclockwise relative to the rotary cutting cutter head 110. During the rotation process, the clamping joint 752 will squeeze the transition part 115 to deform the transition part 115 and / or the clamping joint 752. The squeezing effect will make the clamping joint 752 get rid of the limiting effect of the transition part 115, and the clamping joint 752 will rotate from the bottom of the introduction groove 114a to the limiting groove 114b. After the clamping joint 752 enters the limiting groove 114b, the transition part 115 and / or the clamping joint 752 will restore their shape due to deformation. At this time, the transition part 115 continues to limit the clamping joint 752 to prevent it from entering the introduction part 114a from the limiting groove 114b. In this embodiment, by providing the transition portion 115, the clamping joint 752 can be limited in the introduction groove 114a or the limiting groove 114b. Only after the clamping joint 752 is deformed relative to the transition portion 115 by external force, can the restraint of the transition portion 115 be overcome and the clamping joint 752 can be switched back and forth between the introduction groove 114a and the limiting groove 114b. When the excision is actually performed, the spiral shaft 750 rotates in the counterclockwise direction, and the clamping joint 752 applies a driving force F to the inner wall of the limiting groove 114b. The driving force F applies a torque to the rotary cutting head 110 to rotate in the counterclockwise direction, thereby driving the rotary cutting head 110 to rotate in the counterclockwise direction with it through the spiral shaft 750. Since the driving force F applied by the clamping joint 752 acts on the inner wall of the limiting groove 114b instead of the transition portion 115, it can be prevented that the clamping joint 752 is separated from the limiting groove 114b during the rotation process.

[0064] Since the rotary cutting blade 110 and the spiral shaft 750 in this embodiment are detachably connected, different types of rotary cutting blades 110 can be selected according to surgical requirements. The rotary cutting blade 110 can include multiple types. In this embodiment, the rotary cutting blade 110 includes a blade head with few blades 110a, a blade head with multiple blades 110b, and a blade head with full blades 110c.

[0065] See also Figure 20a-20bAs shown, for the blade head 110a with few blades and the blade head 110b with many blades, their external structure is roughly the same as that of the rotary cutting blade head in the first embodiment. Specifically, the blade head 110a with few blades or the blade head 110b with many blades includes, from the distal end to the proximal end, a first cutting portion 111a and a second cutting portion 112a which are connected to each other, and a blade retaining groove 113 is provided between the first cutting portion 111a and the second cutting portion 112a. The first cutting portion 111a has a plurality of first cutting edges 111 which are arranged opposite to each other in the radial direction, and the second cutting portion 112a has a plurality of second cutting edges 112 which are arranged at intervals in the circumferential direction. In this embodiment, two first cutting edges 111 are provided, and four second cutting edges 112 are provided. In addition, an annular blade retaining groove 113 is also provided on the outer periphery of the second cutting edge 112. For the few-edged cutter head 110a, cutting teeth 1111 are provided on a partial area of ​​the first cutting edge 111 or no cutting teeth 1111 are provided on the first cutting edge 112; for the multi-edged cutter head 110b, cutting teeth 1111 are provided on the entire area of ​​the first cutting edge 111, that is, the cutting teeth 1111 cover the entire first cutting edge 111. Therefore, in this embodiment, a few-edged cutter head is provided with no cutting teeth or with cutting teeth on a partial area of ​​the first cutting edge 111, and a multi-edged cutter head is provided with cutting teeth on the entire area of ​​the first cutting edge 111.

[0066] See also Fig.20c For the full-edge cutter head 110c, it also includes a first cutting portion 111c and a second cutting portion 112c connected to each other from the distal end to the proximal end. The first cutting portion 111c has a plurality of first cutting edges 113 arranged opposite to each other in the radial direction. The first cutting edges 113 can be arranged in two pieces, and no cutting teeth are arranged on the first cutting edges 113. Different from the multi-edge cutter head 110b and the few-edge cutter head 110a, the second cutting edge 114 of the second cutting portion 111c of the full-edge cutter head 110c is spiral-shaped, extending spirally in the axial direction, and the second cutting edge 114 is provided with cutting teeth 1141 in the entire area.

[0067] For the rotary cutting cutter head 110, whether it is a cutter head with few blades 110a, a cutter head with many blades 110b or a cutter head with full blades 110c, the first cutting portion is exposed on the outside of the sleeve 12, while the second cutting portion is inside the sleeve 12. The first cutting portion is used for the first cutting, which cuts the diseased tissue from the blood vessel wall and separates it from the blood vessel wall, while the second cutting portion is used for the second cutting, which further cuts and crushes the diseased tissue into smaller tissues to facilitate subsequent transportation and discharge. For the first cutting edge, its main function is to cut the diseased tissue from the blood vessel wall. For the cutting teeth, there are many of them and they are small in size, and they are mainly used to crush the diseased tissue. For the cutter head with few blades 110a and the cutter head with many blades 110b, the more cutting teeth there are on the first cutting edge, the stronger the crushing function of the first cutting portion on the diseased tissue. For example, for the multi-blade cutter head 110b, since the cutting teeth 1111 cover the entire first cutting edge 111, the first cutting portion 111a can break up the diseased tissue while cutting it off from the blood vessel wall, and can cut smaller diseased tissue than the few-blade cutter head 110a.

[0068] See also Figures 21a-21c As shown, in actual use, different types of rotary cutting heads 110 can be matched with different speed adjustment gears according to surgical requirements.

[0069] Specifically, see Fig.21a As shown, when facing a fresh thrombus, since the hardness of the thrombus is low and the difficulty of removal is small, a few-edged blade head 110a can be used in combination with a high-speed gear to quickly and efficiently remove the thrombus.

[0070] See also Figure 21b As shown, for subacute thrombus and thrombus plaque mixed lesions, the multi-blade cutter head 1012 is used with the medium speed gear to stably and effectively remove them. For subacute thrombus and thrombus plaque mixed lesion tissue, it is more difficult to break than fresh thrombus. Therefore, compared with the removal of fresh thrombus, at this time, cutting teeth are added and a multi-blade cutter head is used, and the rotation speed is reduced to increase the cutter head torque.

[0071] See also Fig.21c As shown, when facing hard calcified plaque lesions, the full-edge blade head 111c is used with a low speed gear to increase the torque, increase the cutting area, and directly crush the plaque. Since the hard calcified plaque is hard and the crushing is the most difficult, the first cutting part is used to cut it off from the blood vessel wall, and then the spiral second cutting edge with cutting teeth is used to crush the hard calcified plaque to ensure smooth cutting.

[0072] In summary, the excision device in this embodiment has a variety of rotary cutting heads that can adapt to different types of stenotic lesions in blood vessels. For harder stenotic lesions, a head with sharp cutting edges and a large number of cutting edges (such as a full-edge head or a multi-edge head) can be selected for processing, and the handle switch can be controlled to perform stepless speed regulation to reduce the head speed and increase the head cutting force to solve stubborn and difficult-to-remove lesions; for softer stenotic lesions, a rotary cutting head with fewer cutting edges (such as a few-edge head) can be selected for processing to reduce the risk of vascular damage, and the handle switch can be controlled to perform stepless speed regulation to increase the head speed, quickly capture the softer material cut off, and improve cutting efficiency; at the same time, for different types of stenotic lesions in blood vessels, a set of products can be applicable to multiple types of lesions, and doctors can replace multiple types of heads during surgery to provide convenience for surgery.

[0073] Third embodiment

[0074] The intravascular resection device in this embodiment is substantially the same as that in the second embodiment, except that the rotary cutting blade head and the spiral shaft are connected quickly by snap-fit, in this embodiment, the rotary cutting blade head and the spiral shaft are connected by threads.

[0075] See also Figure 22-23 As shown, the rotary cutter head 210 includes a first cutting portion 211 and a second cutting portion 212, a connecting hole 213 is provided on the second cutting portion 212, and a connecting internal thread 214 is provided on the inner wall of the connecting hole 213. The distal side of the spiral shaft 850 has a connecting external thread 851 that cooperates with the connecting internal thread 214, and the threaded connection between the two can be achieved by screwing the distal end of the spiral shaft 850 into the rotary cutter head 210. In addition, in order to prevent the threaded connection from loosening during the rotation of the rotary cutter head 210 driven by the spiral shaft 850, the design in this embodiment makes the tightening direction of the threaded connection the same as the working rotation direction of the rotary cutter head 210. For example, when the rotary cutter head 210 rotates counterclockwise during operation, the tightening direction of the spiral shaft 850 relative to the rotary cutter head 210 is also counterclockwise. Through the above arrangement, when the spiral shaft 850 drives the rotary cutter head 210 to rotate, the threaded connection will only become tighter and tighter, and will not loosen. When the rotary cutting blade 210 needs to be replaced, it is only necessary to loosen the threaded connection by twisting it in the opposite direction.

[0076] The above-mentioned embodiments only express several implementation methods of the present invention, and the description is relatively specific and detailed, but it cannot be understood as limiting the scope of the invention patent. It should be pointed out that for ordinary technicians in this field, several modifications and improvements can be made without departing from the concept of the present invention, which all belong to the protection scope of the present invention. The protection scope of the patent of the present invention shall be based on the attached claims.

Claims

1. An intravascular resection device, characterized in that: include: A handle housing, wherein the handle housing has a receiving portion; A catheter extends axially, with a proximal end rotatably connected to the handle housing and a rotary cutting head disposed at a distal end; A bending adjustment component, which includes a sliding rod, a wire drawing ring, a button and a bending adjustment wire. The sliding rod is rotatably arranged in the accommodating portion, the sliding rod has a sliding rod inner cavity, the catheter passes through the sliding rod inner cavity and is fixedly connected to the sliding rod, the wire drawing ring can slide axially relative to the sliding rod but cannot be rotatably mounted on the sliding rod relative to the sliding rod, the button is rotatably mounted on the wire drawing ring, the distal end of the bending adjustment wire is fixed to the distal side of the catheter, and the proximal end is fixed to the wire drawing ring.

2. The intravascular resection device according to claim 1, characterized in that: It also includes a catheter connector, which is rotatably connected to the proximal end side of the housing; The catheter passes through the catheter connector and is fixedly connected thereto, and the distal end of the slide rod is fixedly connected to the proximal end of the catheter connector.

3. The resection device according to claim 1, characterized in that: The outer periphery of the slide rod is provided with a first limiter extending in the axial direction, and the inner wall of the wire drawing ring is provided with a second limiter cooperating with the first limiter. The first limiter can slide relative to the second limiter but cannot rotate.

4. The resection device according to claim 1, characterized in that The button comprises a button ring, and the button ring is rotatably sleeved on the wire drawing ring.

5. The resection device according to claim 4, characterized in that The button also includes a button body connected to the button ring, and the button body is connected to a limiting unit; a limiting plate extending along the axial direction is arranged in the handle shell, and the limiting unit is slidably connected to the limiting plate, and a plurality of limiting protrusions for limiting the movement of the limiting unit are arranged at intervals along the axial direction on the limiting plate.

6. The resection device according to claim 1, characterized in that The distal side wall of the slide rod is provided with a slide rod through-groove communicated with the inner cavity of the slide rod. After the proximal end of the bending wire extends out from the tube wall of the catheter, it passes through the slide rod through-groove and is fixedly connected with the wire drawing ring.

7. The resection device according to claim 6, characterized in that A wire drawing ring limiting portion is also provided on the outer periphery of the slide rod, and the wire drawing ring limiting portion has a notch groove, and the wire drawing ring can abut against the wire drawing ring limiting portion, and the proximal end of the bending wire passes through the notch groove and is fixedly connected to the wire drawing ring.

8. The resection device according to claim 1, characterized in that A spiral shaft is inserted into the catheter, a power assembly is arranged in the receiving portion, the distal end of the spiral shaft is fixedly connected to the rotary cutting cutter head, and the proximal end is connected to the power assembly.

9. The resection device according to claim 8 is characterized in that a three-way joint is arranged in the receiving portion, the three-way joint includes a main tube having a three-way joint cavity, the spiral shaft passes through the three-way joint cavity, and the proximal side of the sliding rod is rotatably sealed and connected to the distal side of the main tube.

10. The resection device according to claim 9, characterized in that The outer circumference of the spiral shaft has a spiral structure, and the spiral structure extends axially from the distal end side of the spiral shaft to the three-way joint cavity.

11. The resection device according to claim 9, characterized in that: It also includes a connecting tube, the proximal end of which is sealed and connected to the main tube, and the distal end of the connecting tube is provided with an enlarged section, and the enlarged section is rotatably and sealedly connected to the proximal end of the slide rod.

12. The resection device according to claim 9, characterized in that It also includes a transmission sealing shell arranged in the accommodating portion, the transmission sealing shell has a sealed cavity, the power component includes a power transmission component, the power transmission component is arranged in the sealed cavity, and the spiral shaft extends from the three-way joint cavity into the sealed cavity and is connected to the power transmission component.

13. The resection device according to claim 12, characterized in that The transmission sealing shell further includes a motor mounting portion, and the power assembly further includes a motor having a motor shaft. The motor is mounted in the motor mounting portion, and the motor shaft is connected to the power transmission assembly.

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