CN221949889U - Ablation system - Google Patents

Abstract

The utility model belongs to the technical field of interventional medical instruments, and relates to a cutting system, which comprises a handle, a catheter arranged on the handle, a cutting device connected to the catheter and a protective cover, wherein the catheter is provided with a cutting device; the cutting device comprises a cutting assembly, the cutting assembly comprises a cutter, the protective cover is connected with the catheter or the cutting assembly, and the outer side of the protective cover is arc-shaped and can be covered on one side of the cutter. According to the excision system, the protection cover is arranged on the excision device, when an embolic material in a blood vessel is eccentric thrombus or plaque, a doctor can enable the protection cover to be located on the opposite side of the embolic material in operation, so that the cutter is isolated from the blood vessel wall on the opposite side of the embolic material, and the phenomenon that the cutter is accidentally scratched on the inner wall of the blood vessel on the opposite side when the cutter is used for excision of the eccentric thrombus or plaque is avoided.

Description

Resection system

Technical Field

The utility model relates to the technical field of interventional medical equipment, in particular to a resection system.

Background Art

Peripheral Arterial Disease (PAD), also known as Lower Extremity Atherosclerotic Occlusive Disease (LEAOD), mainly occurs in the arteries of the legs, feet and other lower limbs. It is a common vascular surgery disease caused by atherosclerotic plaques on the inner wall of the lower limb arteries, which leads to arterial stenosis and occlusion, restricting the normal flow of blood in the lower limbs, and eventually causing ischemic changes in the limbs, celiac arteries, carotid arteries and renal arteries. It is often manifested by symptoms such as intermittent claudication, cold lower limbs, cyanosis (bluish-purple skin) or pallor, rest pain, ulcers and gangrene.

At present, the treatment of peripheral arterial disease can adopt classic vascular bypass surgery to bypass the narrowed or occluded blood vessel segment by creating a new vascular channel, so that blood can flow back to the target area; it can also adopt the emerging lower extremity artery intravascular interventional treatment, that is, peripheral plaque rotational resection, which uses a resection device to intervene in the site of arterial lesions, directly removes thrombi, plaques and other embolic loads on the vessel wall, so that the lesion blood vessels have a larger lumen again, ensuring normal blood flow in the lesion. With the clinical practice and the continuous development of interventional treatment technology, peripheral plaque rotational resection has gradually become the first choice or preferred treatment for diseases such as femoral, popliteal and below-the-knee artery stenosis or occlusion.

However, in the prior art, when removing eccentric lesions in blood vessels, especially eccentric sclerotic plaques, the removal system has the problem that the cutter is easily offset during the removal operation. If the cutter is offset during the removal operation, it will not only reduce the removal efficiency, but in severe cases it may also cut the inner wall of the blood vessel on the opposite side of the eccentric lesion, causing damage to the inner wall of the blood vessel.

Utility Model Content

The purpose of the embodiment of the utility model is to solve the problem that when a cutting system is cutting an eccentric lesion in a blood vessel, the cutting knife may be offset and damage the contralateral blood vessel.

In order to solve the above technical problems, an embodiment of the utility model provides a resection system, which includes a handle, a catheter arranged on the handle, a resection device connected to the catheter and a protective cover; the resection device includes a cutting assembly, the cutting assembly includes a cutter, the protective cover is connected to the catheter or the cutting assembly, and the outer side surface of the protective cover is arranged in an arc shape and can be covered on one side of the cutter.

In some embodiments of the resection system of the present invention, the cutting assembly also includes a rotating shaft through which the catheter is passed, and the cutter is arranged on the distal side of the rotating shaft; when the protective cover is arranged on the cutter, the protective cover protrudes in a direction away from the cutter, and a protective groove for accommodating the cutter is formed on the side of the protective cover facing the cutter.

In some embodiments of the cutting system of the present invention, the cutting device further comprises a mounting tube disposed at the distal end of the catheter, the cutter is rotatably connected to the mounting tube, the proximal end of the protective cover is connected to the distal end of the mounting tube, and the axial length of the protective cover is greater than the axial length of the cutter extending out of the mounting tube;

The circumference of the protective cover is arranged in an arc shape, and the circumferential angle of the protective cover is 60 degrees to 180 degrees.

In some embodiments of the cutting system of the utility model, the groove wall of the protection groove is a closed structure, the groove wall of the protection groove is smoothly arranged; or the groove wall of the protection groove is arranged with a pattern.

In some embodiments of the cutting system of the present invention, at least a portion of the edge of the protective cover is in a serrated structure.

In some embodiments of the cutting system of the present invention, the mounting tube includes a sleeve and a tube claw fixedly connected to the distal end of the catheter, the cutter is rotatably connected to the tube claw, and the sleeve is sleeved on the outside of the tube claw and the cutter; a plurality of jaws are circumferentially spaced at the distal end of the tube claw, and limiting protrusions are provided on the inner walls of the plurality of jaws, and a limiting groove is circumferentially provided on the outer wall of the cutter, and the limiting protrusion is clamped in the limiting groove.

In some embodiments of the resection system of the present invention, the resection system also includes a bending adjustment component and a wire fixing component, a bending adjustment wire connected to the distal end of the catheter is arranged in the catheter, the wire fixing component is movably connected to the catheter and fixedly connected to the proximal end of the bending adjustment wire, the bending adjustment component is connected to the wire fixing component and the catheter, the bending adjustment component is used to drive the catheter to rotate circumferentially, and the bending adjustment component controls the distal bending of the catheter through the wire fixing component and the bending adjustment wire.

In some embodiments of the resection system of the present invention, the wire fixing assembly is movably sleeved on the catheter and is disposed within the bending adjustment assembly, and the bending adjustment assembly can independently drive the wire fixing assembly to move axially relative to the catheter or independently drive the wire fixing assembly to rotate synchronously with the catheter.

Compared with the prior art, the resection system provided by the embodiment of the utility model has the following beneficial effects:

The resection system is provided with a protective cover on the resection device, the protective cover is provided at the distal end of the mounting tube, and the radial clearance of the protective cover is provided on one side of the cutter, so as to cover the periphery of the cutter. During the operation, the protective cover can be located on the opposite side of the embolism to isolate the cutter and the blood vessel wall on the opposite side of the embolism, so that the doctor can safely resection the embolism multiple times under various circumstances, and a larger blood vessel cavity can be obtained at the lesion in one operation. At the same time, the cut embolism can also be fragmented under the relative rotation of the protective cover and the cutter in rotary cutting, which is conducive to the smoother discharge of the cut embolism from the body.

BRIEF DESCRIPTION OF THE DRAWINGS

In order to more clearly illustrate the scheme of the utility model, the following is a brief introduction to the drawings required for the description of the embodiments. Obviously, the drawings described below are some embodiments of the utility model or corresponding prior art. For ordinary technicians in this field, other drawings can be obtained based on these drawings without creative work. Among them:

FIG1 is a schematic diagram of the three-dimensional structure of the resection system in the first embodiment of the present invention; wherein the guide wire locking device is not shown in the figure;

FIG2 is a front view of the resection system in the first embodiment of the present invention; wherein the guide wire locking device is not shown in the figure, and a protective cover is added;

FIG3 is a three-dimensional exploded view of the cutting system in the first embodiment of the present invention; wherein the cutting knife is not shown in the figure;

FIG4 is a three-dimensional exploded view of a posture adjustment device in a resection system according to a first embodiment of the present invention;

Fig. 5 is a cross-sectional view of the A-A section in Fig. 1;

FIG6 is a schematic longitudinal cross-sectional view of a catheter of a resection system in Embodiment 1 of the present invention;

7 is a schematic diagram of the three-dimensional structure of the cutting assembly installed on the mounting cylinder in the first embodiment of the present invention;

8 is a three-dimensional exploded view of the cutter, sleeve and cylinder claw of the removal system in Example 1 of the present invention;

FIG9 is a schematic diagram of a state in which the distal end of the resection system in the first embodiment of the present invention is in a blood vessel; wherein, in this figure, the cutter has not reached the lesion;

FIG10 is a schematic diagram of another state of the distal end of the resection system in the first embodiment of the present invention in a blood vessel; wherein, in this figure, the cutter contacts the lesion;

11 is a schematic diagram of the three-dimensional structure of a first specific implementation of the protective cover in Example 1 of the present invention;

FIG12 is a side view of the protective cover in FIG11;

13 is a schematic diagram of the three-dimensional structure of a second specific implementation of the protective cover in Example 1 of the present invention;

14 is a schematic diagram of the three-dimensional structure of a third specific implementation of the protective cover in Example 1 of the present invention;

FIG15 is a top view of the protective cover in FIG14;

FIG. 16 is a schematic diagram of a three-dimensional structure of a fourth specific embodiment of the protective cover in Example 1 of the present invention.

FIG17 is a front view of the protective cover in FIG16;

18 is a schematic diagram of the three-dimensional structure of the fifth specific implementation of the protective cover in Example 1 of the present invention;

FIG19 is a top view of the protective cover in FIG18;

FIG20 is a side view of the protective cover in FIG18;

21 is a schematic diagram of the three-dimensional structure of the cutting system when the protective cover is not provided in the second embodiment of the present invention;

FIG22 is a schematic diagram of the three-dimensional structure of the cutting system in Embodiment 2 of the present invention when a second handle shell and a first cylinder shell are removed;

FIG23 is a three-dimensional exploded view of a cutting system from one viewing angle in the second embodiment of the present invention;

24 is a planar cross-sectional view of the guidewire locking device of the resection system in the second embodiment of the present invention and the gear with the shaft through the bearing;

FIG25 is a three-dimensional exploded view of the excision system from another perspective in the second embodiment of the present invention;

26 is a schematic diagram of a three-dimensional structure in which a push switch is installed in the first cylinder shell in Embodiment 2 of the present invention;

27 is a schematic diagram of the three-dimensional structure of the hollow limit shaft of the push switch in the second embodiment of the present invention;

28 is a schematic diagram of the three-dimensional structure of the second wire fixing slider of the wire fixing assembly in the second embodiment of the present invention;

29 is a schematic diagram of the three-dimensional structure of the clamp of the push switch in the second embodiment of the present invention;

30 is a schematic diagram of the three-dimensional structure of the latch plate of the push switch in the second embodiment of the present invention;

31 is a perspective exploded view of a driving device of a cutting system in a second embodiment of the present invention;

FIG32 is a three-dimensional exploded view of the removal system in Embodiment 3 of the present invention;

33 is a schematic diagram of the three-dimensional structure of the sliding key of the wire fixing assembly in Embodiment 3 of the present invention;

Figure 34 is a schematic diagram of the three-dimensional structure of the second cylinder shell of the adjustment cylinder in Example 3 of the present invention.

DETAILED DESCRIPTION

Unless otherwise defined, all technical and scientific terms used herein have the same meaning as commonly understood by technicians in the technical field of the present invention; the terms used in this specification are only for the purpose of describing specific embodiments and are not intended to limit the present invention. For example, the directions or positions indicated by the terms "length", "width", "up", "down", "left", "right", "front", "back", "vertical", "horizontal", "top", "bottom", "inside", "outside", etc. are based on the directions or positions shown in the drawings, which are only for the convenience of description and should not be understood as limitations on the present technical solution.

The terms "including" and "having" and any variations thereof in the specification and claims of the present invention and the above-mentioned drawings are intended to cover non-exclusive inclusions; the terms "first", "second", etc. in the specification and claims of the present invention or the above-mentioned drawings are used to distinguish different objects rather than to describe a specific order. "Multiple" means two or more, unless otherwise clearly and specifically defined.

In the specification and claims of the present invention and the above-mentioned drawings, when an element is referred to as being "fixed to" or "mounted on" or "disposed on" or "connected to" another element, it may be directly or indirectly located on the other element. For example, when an element is referred to as being "connected to" another element, it may be directly or indirectly connected to the other element.

In addition, reference to "embodiments" herein means that a particular feature, structure, or characteristic described in conjunction with the embodiments may be included in at least one embodiment of the present invention. The appearance of the phrase in various places in the specification does not necessarily refer to the same embodiment, nor is it an independent or alternative embodiment that is mutually exclusive with other embodiments. It is explicitly and implicitly understood by those skilled in the art that the embodiments described herein may be combined with other embodiments.

It should be noted that in the field of interventional medical devices, "proximal" and "distal" are customary terms. Among them, "proximal" refers to the end of the medical device implanted in the body that is close to the operator, and "distal" refers to the end that is away from the operator. The "proximal" and "distal" ends of any component of the medical device are defined based on this principle. "Axial" generally refers to the length direction of the medical device when it is transported, and "radial" generally refers to the direction of the medical device that is perpendicular to its "axial" direction. The "axial" and "radial" ends of any component of the medical device are defined based on this principle. "Middle section" generally refers to the part that distinguishes the two ends of any component of a medical device, and does not only refer to the part located in the middle of any component of a medical device.

An embodiment of the present invention provides a resection system 100, which is mainly used to resect emboli 300 formed by lesions in a blood vessel 200, such as thrombus or plaque tissue, including but not limited to being suitable for use in scenarios such as peripheral plaque rotational resection.

In general, the resection system 100 has various functions. Based on the principle of bending by the bending wire 21 of the existing products, the distal part of the resection device 3, such as the cutter 322, the head of the catheter 2, the protective cover 33, etc., can be precisely bent directly through the physical structure of the resection system 100, reducing the doctor's reliance on experience to push the handheld instrument and the human influence caused thereby, which is conducive to reducing the medical skills requirements for the surgeon; not only that, the catheter 2 can also be rotated 360 degrees, which is conducive to adjusting the head of the catheter 2 to a suitable bending direction and bending angle according to the size, location and shape of the lesion, so as to better and more thoroughly remove the embolism 300, and at the same time solves the problem that the existing products cannot realize the rotation of the catheter 2 when the bending is adjusted by wire drawing, and the bending wire 21 is easy to be entangled, and when the protective cover 33 of the cutter 322 is provided on the head of the catheter 2, the circumferential position of the protective cover 33 relative to the cutter 322 can be adjusted, and the guide wire (not shown) can pass through the entire resection system 100, which is convenient for pushing the resection device 3 and the catheter 2 to the lesion site.

As shown in Figures 1 to 3, the resection system 100 includes a handle 1, a catheter 2, a resection device 3 and a drive device 4. The handle 1 is a hollow shell structure. The catheter 2 and the drive device 4 are both arranged in the handle 1. Exemplarily, the proximal end of the catheter 2 is arranged in the handle 1 and the distal end is exposed outside the handle 1. The resection device 3 is partially exposed at the distal end of the catheter 2, and the main body of the drive device 4 is arranged in the handle 1.

In the embodiment of the present invention, as shown in FIG. 2 and FIG. 7 , the cutting device 3 includes a mounting tube 31 and a cutting assembly 32 driven to rotate by a driving device 4, wherein the cutting assembly 32 includes a rotating shaft 321 and a cutter 322, the rotating shaft 321 is sleeved with a catheter 2 and driven to rotate by the driving device 4, the cutter 322 is arranged at the distal end of the rotating shaft 321 to rotate with the rotating shaft 321, and the head of the cutter 322 is exposed at the distal end of the catheter 2 to achieve the removal of the embolic material 300 at the lesion. Specifically, to ensure the stability of the cutter 322 during use, the mounting tube 31 is arranged at the distal end of the catheter 2, the cutter 322 is rotatably mounted on the mounting tube 31, and the head is axially exposed at the mounting tube 31.

Exemplarily, the rotating shaft 321 is a torque shaft with a spiral structure, which is mainly fixed to the handle 1 by mechanical matching and welding. The cutter 322 is mainly fixed to the distal end of the rotating shaft 321 by laser welding, bonding, etc., and both the rotating shaft 321 and the cutter 322 can be made of stainless steel or nickel-titanium alloy. In addition, the driving device 4 is used to drive the rotating shaft 321 to rotate.

In an embodiment of the present invention, based on the bending adjustment by the bending adjustment wire 21, the catheter 2 is pre-buried with a bending adjustment wire 21 that can be pulled out at the distal side of the handle 1. Exemplarily, to achieve the pre-buried bending adjustment wire 21, as shown in Figures 5 and 6, the catheter 2 includes an outer tube 22, a braided layer 23, an inner tube 24, and a fixing ring 25 for fixing the bending adjustment wire 21, wherein, at the proximal side of the fixing ring 25, a wiring channel 26 is axially formed between the outer tube 22 and the braided layer 23, the distal end of the bending adjustment wire 21 is connected to the fixing ring 25, and the proximal end is pulled out of the catheter 2 along the wiring channel 26, and the outer tube 22 and the braided layer 23 are integrally formed by hot melting and other processes, so that the bending adjustment wire 21 can be pressed on the outside of the braided layer 23, so that when the bending adjustment wire 21 is pulled outside the outer tube 22, the head of the catheter 2 can be bent under the pulling action of the bending adjustment wire 21.

It should be noted that the mounting tube 31 is fixed to the distal end of the outer tube 22 of the catheter 2 by welding, bonding, etc. The outer tube 22 of the catheter 2 is usually made of soft materials because it needs to pass through the blood vessel 200. The mounting tube 31 can be made of hard materials such as stainless steel or nickel-titanium alloy. The fixing ring 25 can be made of tantalum alloy or platinum-iridium alloy, etc., so that it has a developing function and can show the direction of the distal end of the catheter 2, so that the bending of the tip of the catheter 2 can be identified with the help of the fixing ring 25.

In addition, in order to transfer the embolic material 300 removed by the cutter 322 to the outside of the body, a discharge cavity (not shown) communicating with the outside is formed in the handle 1. As shown in Figures 5 and 6, a transmission channel 27 communicating with the discharge cavity is also formed between the inner tube 24 of the catheter 2 and the rotating shaft 321. In the process of the rotating shaft 321 driving the cutter 322 to rotate and remove embolic materials 300 such as plaques, the cut thrombus or plaque can enter the transmission channel 27 from the gap between the cutter 322 and the mounting tube 31, and driven by the rotating shaft 321 with a spiral structure and rotation, it is transported to the discharge cavity toward the proximal end of the handle 1 so as to be discharged from the body.

In an embodiment of the present invention, the resection system 100 also includes a posture adjustment structure arranged on the handle 1 for adjusting the distal part of the catheter 2. Exemplarily, it is mainly used to adjust the posture of the catheter 2 and/or the cutter 322, such as adjusting the bending angle of the catheter 2 and/or the cutter 322, or driving the catheter 2 to rotate. When a protective cover 33 is provided at the distal end of the catheter 2, the direction of the protective cover 33 can also be adjusted circumferentially.

Specifically, as shown in Figures 2 to 4, the resection system 100 includes a wire fixing component 5 and a bending adjustment component 6, wherein the wire fixing component 5 is movably connected to the bending adjustment component 6 and fixedly connected to the proximal end of the bending adjustment wire 21. The bending adjustment component 6 is disposed on the handle 1 and is sleeved with the catheter 2, and is mainly used to adjust the traction force of the bending adjustment wire 21 by controlling the axial sliding of the wire fixing component 5, thereby adjusting the bending angle of the catheter 2.

Understandably, under the control of the bending adjustment component 6, the wire fixing component 5 can move forward and backward along the axial direction of the catheter 2. Since the length of the bending adjustment wire 21 is fixed, the proximal end of the bending adjustment wire 21 moves forward when the wire fixing component 5 moves forward, which is equivalent to reducing the traction force and releasing the bending adjustment wire 21 to reduce the bending angle of the head of the catheter 2; conversely, when moving backward, it is equivalent to increasing the traction force and pulling the bending adjustment wire 21 to increase the bending angle of the head of the catheter 2. In this way, the bending angle of the head of the catheter 2 is adjusted by controlling the sliding distance of the wire fixing component 5 to achieve the adjustment of the bending angle of the cutter 322. Exemplarily, the cutting system 100 can realize the bending adjustment function of the catheter 2 to adjust 0° to 45° based on the current state.

In addition, the bending component 6 can also be used to control the rotation of the catheter 2, so that the doctor can choose the appropriate direction for bending according to the size, position and shape of the embolus 300, which is conducive to flexibly and accurately controlling the bending direction and/or bending angle of the catheter 2, so as to pass through the bend of the blood vessel and control the direction of the cutter 322, so that the doctor can better and faster deal with the eccentric calcified embolus 300.

Compared with the method of relying on the doctor's hands to perform rotation, turning and other pushing operations to drive the entire handle 1 to adjust together, the resection system 100 uses its own physical structure to bend and rotate, which is accurate and stable, and can greatly reduce the doctor's medical skills requirements and human influence, which is conducive to reducing surgical risks.

In the embodiment of the present invention, in order to prevent the bending adjustment wire 21 from being entangled when the catheter 2 is rotated, when the bending adjustment component 6 is rotatably arranged on the handle 1, the wire fixing component 5 can be rotated synchronously with the catheter 2. It can be understood that when the bending adjustment component 6 is rotated, the catheter 2 and the wire fixing component 5 can rotate together with the bending adjustment component 6, so the bending adjustment wire 21 fixed to the wire fixing component 5 can remain relatively still with the catheter 2 in the circumferential direction to avoid entanglement.

For example, since both the bending adjustment component 6 and the wire fixing component 5 are covered with the catheter 2, in order to simplify the overall structure, the posture adjustment device only needs to limit the circumferential rotation of the wire fixing component 5 through the bending adjustment component 6, so that the wire fixing component 5 only slides axially relative to the bending adjustment component 6, which can ensure that when the bending adjustment component 6 rotates, the wire fixing component 5 rotates circumferentially together with the bending adjustment component 6 to achieve synchronous rotation with the catheter 2 fixedly connected to the bending adjustment component 6. Of course, other methods can also be used to achieve synchronous rotation of the wire fixing component 5 and the catheter 2.

In an embodiment of the present invention, as shown in FIG2 , the removal device 3 may further include a protective cover 33, wherein the protective cover 33 is disposed at the distal end of the mounting tube 31 and is spaced to cover one side of the cutter 322. Specifically, the protective cover 33 and the cutter head 322 are both axially exposed to the mounting tube 31, and the protective cover 33 is located on one side of the cutter 322, so that one side of the cutter 322 is isolated from the wall of the blood vessel 200 by the protective cover 33, and the other side is radially exposed to the protective cover 33 to remove the embolism 300 in the blood vessel 200. Exemplarily, the protective cover 33 is fixed to the distal end of the mounting tube 31 by welding, bonding or hot melting, and the material of the protector is preferably stainless steel or nickel-titanium alloy.

Also exemplarily, for eccentric stenosis in the blood vessel 200, in clinical use, as shown in FIG9, the cutting device 3 is extended into the lesion position of the blood vessel 200, and the cutter 322 is close to the embolus 300 but does not contact the embolus 300. As shown in FIG10, when the cutter 322 is pushed to contact the embolus 300 and gradually axially penetrates the embolus 300, under the control of the driving device 4, the rotating shaft 321 rotates to drive the cutter 322 to rotate relative to the catheter 2, the mounting tube 31 and the protective cover 33 to cut the eccentric embolus 300 in the blood vessel 200. When the cutter 322 is rotary cut, because the protective cover 33 is fixed and is located between the non-lesion side of the blood vessel 200 and the cutter 322 to separate the cutter 322, the risk of the blood vessel 200 wall on the opposite side of the embolus 300 being scratched or perforated by the cutter 322 can be greatly reduced, so as to better adapt to a variety of different conditions and improve the versatility of the cutting system 100.

Specifically, even if the cutter 322 deflects during rotary cutting due to accidental deflection, excessive pushing speed or poor alignment with the blood vessel 200, under the protection of the protective cover 33, the cutter 322 will not directly contact the wall of the blood vessel 200 on the opposite side of the embolus 300, which allows the doctor to safely perform multiple resections of the embolus 300 around the embolus 300, ensuring that most or even all of the embolus 300 can be removed in one operation, thereby reducing the amount of residual embolus 300 after surgery, trying to obtain a larger blood vessel 200 cavity at the lesion site, reducing the requirements for the doctor's medical skills, and ensuring the surgical effect.

In addition, as shown in FIG. 2 , in the radial direction, a gap is set between the protective cover 33 and the cutter 322. In this way, on the one hand, interference with the cutter 322 can be avoided, and the size of the gap between the cutter 322 and the mounting tube 31 can be ensured not to be reduced due to the provision of the protective cover 33. On the other hand, it is conducive to reducing the cost of surgery and shortening the duration of surgery. Specifically, after the cut embolic material 300 falls on the protective cover 33, it will be broken up by the relative rotation between the cutter 322 and the protective cover 33 during the rotary cutting at the radial gap between the protective cover 33 and the cutter 322 and its vicinity, which is conducive to the smoother discharge of the cut embolic material 300 from the body, reducing the risk of distal embolism of the blood vessel 200, and reducing the frequency of using the distal protective umbrella separately, thereby helping to reduce the difficulty and cost of surgery and shorten the duration of surgery.

It can be understood that the above-mentioned embodiment can at least adjust the circumferential position of the protective cover 33. Specifically, since the protective cover 33 is arranged on the mounting tube 31 connected to the catheter 2, when the above-mentioned bending adjustment component 6 rotates, the protective cover 33 can rotate driven by the bending adjustment component 6 to adjust its circumferential position, that is, the protective cover 33 can realize 360° rotation together with the catheter 2 to circumferentially adjust the direction of the protective cover 33 so that it is located on the opposite side of the lesion in the blood vessel 200 during resection, so as to isolate and protect the wall of the blood vessel 200 on the opposite side of the lesion.

In other embodiments, the protective cover 33 can be arranged on the catheter 2 or on the cutting device 3. For example, the protective cover 33 is movably connected to the mounting tube 31, and the protective cover 33 can be retracted into the mounting tube 31. Specifically, an axially movable control line (not shown) is passed through the catheter 2, and the proximal end of the protective cover 33 is connected to the control line. In the initial state, the protective cover 33 is retracted inside the mounting tube 31. When the protective cover 33 is required to cover the cutter 322, the control line is pushed to the distal end to make the protective cover 33 extend from the mounting tube 31. Through the above embodiment, the protective cover 33 can be retracted inside the mounting tube 31 when the catheter 2 passes through the curved part of the blood vessel, so as to avoid the protective cover 33 affecting the passability of the distal end of the catheter 2.

In summary, compared with the prior art, the resection system 100 has at least the following beneficial effects:

Among them, the wire fixing component 5 is movably sleeved on the catheter 2 and fixedly connected to the proximal end of the bending adjustment wire 21 whose distal end is pre-buried in the catheter 2. The bending adjustment component 6 is arranged on the handle 1 and sleeved with the catheter 2, so that the axial sliding of the wire fixing component 5 can be controlled by operating the bending adjustment component 6. Since the pulling length of the bending adjustment wire 21 is fixed, the traction force of the bending adjustment wire 21 is adjusted. When the axial position of the catheter 2 remains unchanged, it is equivalent to adjusting the bending radius of the catheter 2 by releasing or pulling the bending adjustment wire 21, so that the catheter 2 is offset in a predetermined direction, thereby adjusting the bending angle of the catheter 2, and then adjusting the direction of the cutter 322. When the bending component 6 is rotatably arranged on the handle 1, the catheter 2 can also be controlled to rotate with the bending component 6. In this way, on the one hand, it is convenient for the doctor to directly operate the resection system 100 to accurately and stably perform bending and rotation; on the other hand, it is convenient for the doctor to select a suitable direction for bending according to the specific conditions of the lesion location, etc., which is conducive to flexibly and accurately controlling the bending direction and/or bending angle of the catheter 2, so that it can better and faster pass through the curved part of the blood vessel, and adjust the direction of the cutter 322 to deal with the eccentric calcified embolism 300. Therefore, the resection system 100 can be accurately, flexibly and stably adjusted from different angles, has multiple functions, good surgical effects, good versatility, and greatly reduces the medical skills requirements for the surgeon.

In addition, the resection system 100 can also selectively set a protective cover 33 on the resection device 3. By setting the protective cover 33 at the distal end of the mounting tube 31 and setting the radial gap of the protective cover 33 on one side of the cutter 322 to cover the periphery of one side of the cutter 322, the protective cover 33 is located on the opposite side of the embolus 300 during the operation to isolate the cutter 322 and the wall of the blood vessel 200 on the opposite side of the embolus 300, so that the doctor can safely resect the embolus 300 multiple times under various circumstances, and a larger blood vessel 200 cavity can be obtained at the lesion site in one operation. The cut embolus 300 can also be fragmented under the relative rotation of the protective cover 33 and the cutter 322 during the rotary cutting, so that it can be discharged more smoothly from the body, thereby reducing the risk of distal embolism of the blood vessel 200 and the frequency of additional use of the distal protective umbrella. Therefore, the resection system 100 can further reduce the difficulty of the operation, improve the operation effect, reduce the cost of the operation, shorten the operation time, and has a simple and reliable structure.

Embodiment 1 of the resection system 100 of the present invention

In order to enable those skilled in the art to better understand the solution of the present invention, the technical solution in Embodiment 1 of the present invention will be clearly and completely described below in conjunction with Figures 1 to 20.

Regarding the structure of the mounting cylinder 31 of the cutting device 3, in the first embodiment of the present invention, as shown in FIG. 7 and FIG. 8, the mounting cylinder 31 includes a sleeve 311 and a cylinder claw 312, wherein the sleeve 311 is fixedly connected to the distal end of the catheter 2, the cylinder claw 312 is rotatably connected to the cutter 322, and the sleeve 311 and the catheter 2 are fixedly sleeved on the cylinder claw 312 at the connection between the two.

The outer diameter of the cylinder claw 312 is less than or equal to the inner diameter of the sleeve 311, the distal end of the cylinder claw 312 is axially inserted into the sleeve 311, and the cylinder claw 312 is fixedly connected to the sleeve 311 by welding, bonding, etc.; the portion of the cylinder claw 312 extending out of the proximal end of the sleeve 311 is inserted into the distal end of the catheter 2, and is fixedly connected to the inner tube 24 of the catheter 2 by UV curing, adhesive, etc. In addition, the proximal end of the sleeve 311 can be fixedly connected to the distal end of the outer tube 22 of the catheter 2 by welding, bonding, etc.

In this embodiment, the barrel claw 312 is inserted into the connection between the sleeve 311 and the catheter 2 from the inner side of the catheter 2, and the barrel claw 312 is fixedly connected to the sleeve 311 and the catheter 2, so that the barrel claw 312 supports the sleeve 311 and the catheter 2, and the sleeve 311 is not only directly fixedly connected to the catheter 2, but also can be fixedly connected to the catheter 2 again through the barrel claw 312, so as to effectively enhance the connection strength and reliability between the sleeve 311 and the catheter 2, which is conducive to improving the safety of the operation.

In some specific implementations of Example 1 of the present invention, as shown in Figure 8, in order to rotatably connect the cutter 322 to the mounting cylinder 31, a plurality of jaws 3121 are circumferentially spaced apart at the distal end of the cylinder claw 312, and a limiting protrusion 3122 is provided on the inner wall of the plurality of jaws 3121. Correspondingly, a limiting groove 3221 is circumferentially provided on the outer wall of the cutter 322, wherein when the limiting groove 3221 and the limiting protrusion 3122 are matched in a concave-convex manner, the cutter 322 is clamped by the plurality of jaws 3121 radially constrained by the sleeve 311 so as to be rotatably connected to the cylinder claw 312.

It should be noted that when the limiting protrusion 3122 and the limiting groove 3221 are matched, the length of the cutter 322 exposed from the mounting tube 31 can be maintained within a certain range, preventing the cutter 322 from being recessed into the sleeve 311 or further jumping out of the sleeve 311, which is beneficial to improving the stability of the rotary cutting action of the cutter 322, thereby ensuring the surgical effect and reducing the surgical risk.

As shown in Figures 3 and 4, the wire fixing assembly 5 includes a hollow first wire fixing slider 51 fixed with the bending wire 21. Exemplarily, as shown in Figure 4, the first wire fixing slider 51 is provided with a first wire threading hole 511, and the proximal end of the bending wire 21 can be wound around the first wire fixing slider 51 after passing through the first wire threading hole 511, so as to be fixedly connected to the first wire fixing slider 51.

As shown in Figures 2 to 4, the bending adjustment assembly 6 includes a mounting seat 61 and a bending adjustment knob 62, wherein the mounting seat 61 is arranged on the handle 1, and a rotation limiting structure 6121 is provided at the far end of the mounting seat 61; the bending adjustment knob 62 is rotatably connected to the mounting seat 61, and the interior of the bending adjustment knob 62 is threadedly connected to the first wire fixing slider 51, so that a screw structure is formed through the cooperation of the rotation limiting structure 6121 during rotation, so that the first wire fixing slider 51 moves axially.

Exemplarily, the bending adjustment knob 62, the first wire fixing slider 51 and the mounting seat 61 are all sleeved on the catheter 2, thereby saving internal space. The bending adjustment knob 62 is rotatably sleeved on the distal end of the mounting seat 61, and the bending adjustment wire 21 passes through the bending adjustment knob 62 and is fixed to the first wire fixing slider 51 in the bending adjustment knob 62. The first wire fixing slider 51 cannot rotate relative to the bending adjustment knob 62 due to the restriction of the rotation limiting structure 6121. Therefore, when the bending adjustment knob 62 is rotated to rotate relative to the mounting seat 61, the rotation of the bending adjustment knob 62 can be converted into the axial movement of the first fixed slider along the catheter 2, so as to realize the bending of the catheter 2 by adjusting the traction force of the bending adjustment wire 21.

As shown in Figures 3 and 4, the rotation limiting structure 6121 is a slide groove for radially limiting the first wire fixing slider 51, wherein the first wire fixing slider 51 is axially slidably inserted into the slide groove in the bending knob 62. For example, the slide groove can be formed by a radial gap enclosed by a limiting plate (not shown) protruding from the far end of the mounting seat 61.

In the first embodiment of the present invention, in order to realize the rotation of the catheter 2 on the basis of being able to bend, as shown in Figures 2 to 4, the mounting seat 61 includes a fixed seat 611 and a rotating knob 612, wherein the fixed seat 611 is clamped on the handle 1 and is sleeved with the catheter 2; the rotating knob 612 is rotatably connected to the distal end of the fixed seat 611, is fixedly sleeved on the catheter 2 and has a rotation limiting structure 6121 at the distal end, which is mainly used to drive the bending knob 62, the first fixed wire slider 51 and the catheter 2 to rotate synchronously during rotation.

Exemplarily, the catheter 2 is fixedly connected to the bending knob 62 by welding, bonding, etc., and the fixing seat 611 is installed at the distal end of the handle 1. For example, as shown in Figures 1 to 3, the handle 1 includes two first handle shells 11 that overlap radially, and a mounting hole 111 is axially opened at the distal end of the first handle shell 11 in the handle 1, and a mounting groove 6111 is opened on the fixing seat 611. The fixing seat 611 can be clamped on the handle 1 through the concave-convex cooperation between the mounting groove 6111 and the shell ribs forming the mounting hole 111. Among them, the axial depth of the mounting groove 6111 is greater than the thickness of the hole wall of the mounting hole 111, that is, there is a gap between the mounting groove 6111 and the hole wall of the mounting hole 111, so that the fixing seat 611 can move axially by the distance of the preset gap.

In addition, in order to achieve damped rotation of the rotating knob 612 , a first damping tooth 6122 is disposed at the proximal end of the rotating knob 612 , and a tooth structure meshing with the first damping tooth 6122 is disposed at the distal end of the fixing seat 611 .

Understandably, when the rotating knob 612 is rotated to rotate relative to the fixed seat 611, the rotating knob 612 can simultaneously drive the bending knob 62, the first wire fixing slider 51 and the catheter 2 to rotate together because the bending knob 62 rotates and sleeves the rotating knob 612 connected to the mounting seat 61, and is limited by the circumferential rotation of the above-mentioned rotation limiting structure 6121, so that the bending knob 612 can be driven to rotate together with the first wire fixing slider 51, and the circumferential position of the catheter 2 and the protective cover 33 can be adjusted, and the winding of the bending wire 21 can be avoided. And the damping tooth structure at the connection between the rotating knob 612 and the fixed seat 611 is engaged, so that the fixing of the rotating knob 612 after any angle is realized.

As shown in FIGS. 2 to 4 , in order to ensure the installation and rotation stability of the catheter 2, the mounting seat 61 further includes a rod seat 613 and a buffer elastic member 614 located in the handle 1, wherein a rotation groove 6131 is provided on the outer wall of the rod seat 613, and a rotation hole 112 is provided in the first handle shell 11, and the rod seat 613 can be rotatably installed in the handle 1 through the concave-convex cooperation between the rotation groove 6131 and the shell rib forming the rotation hole 112. In addition, the rod seat 613 is fixedly sleeved on the catheter 2 by bonding or the like, and a buffer elastic member 614 is provided between the rod seat 613 and the fixing seat 611, so as to radially support the middle section of the catheter 2 through the rod seat 613, and to tension the rotating knob 612 through the buffer elastic member 614.

Specifically, the buffer elastic member 614 is a compression spring, and the catheter 2 is fixedly connected to the rod seat 613 and the bending knob at the same time. Since the fixed seat 611 is clamped and fixed to the handle 1 and has an axial movement gap with the mounting hole 111 of the handle 1, the compression spring arranged between the fixed seat 611 and the rod seat 613 can press the fixed seat 611 and the rotating knob 612 to achieve circumferential positioning of the rotating knob 612.

In addition, in embodiment 1 of the present invention, as shown in Figures 1 to 3, in order to make the catheter 2 pushed along the guide wire more smoothly, the resection system 100 also includes a guide wire locking device 7 arranged at the proximal end of the handle 1, wherein the rotating shaft 321 is axially opened with a wire hole 3211 for the guide wire to pass through, and the guide wire locking device 7 is mainly used to fix the guide wire that passes through the guide wire locking device 7 from the outside and enters the wire hole 3211.

Exemplarily, the guide wire locking device 7 includes a screw cap 71 and a sealing gasket 72 (see Figure 3), and a locking thread 3212 is provided on the outer wall of the rotating shaft 321 (see Figure 1), wherein the sealing gasket 72 is inserted into the stepped hole of the rotating shaft 321 from the proximal end of the rotating shaft 321, and the screw cap 71 is threadedly sleeved on the proximal end of the rotating shaft 321 through the locking thread 3212, and can axially abut against the sealing gasket 72 in the rotating shaft 321, and the guide wire can pass through the screw cap 71 and the sealing gasket 72 in turn from the outside, and enter the wire feeding hole 3211 of the rotating shaft 321, so that the guide wire can pass axially through the handle 1 as a whole, which is convenient for pushing the catheter 2 into the lesion site more smoothly. When the screw cap 71 is tightened, the sealing gasket 72 can be axially squeezed inside the screw cap 71, so that the aperture of the sealing gasket 72 shrinks and locks the guide wire to fix the guide wire and prevent the guide wire from rotating with the cutter 322 during the operation and damaging the blood vessel 200, while also sealing the proximal end of the handle 1.

As shown in FIG. 2 and FIG. 3 , in order to realize the rotation of the cutting assembly 32, the driving device 4 includes a motor 41, a battery 43, a Y-type valve 46, a gear pair 47 and a mounting shaft 49 arranged in the handle 1, wherein the Y-type valve 46 includes a main valve pipe and a waste discharge pipe. In the handle 1, the motor 41 is electrically connected to the battery 43 through an electric wire, and the output shaft of the motor 41 is connected to the driving wheel of the gear pair 47; the proximal end of the rotating shaft 321 of the cutting assembly 32 is inserted into the mounting shaft 49 in the main valve pipe of the Y-type valve 46 and is fixedly connected to the mounting shaft 49 by welding or the like, and the distal end of the mounting shaft 49 is rotatably mounted in the main valve pipe of the Y-type valve 46 through a bearing, and the mounting shaft 49 is fixedly connected to the driven wheel of the gear pair 47. After the switch is turned on, when the battery 43 is powered, the motor 41 can be operated to drive the rotating shaft 321 to rotate, thereby realizing the rotary cutting function of the cutter 322.

Regarding the specific structure of the protective cover 33, in embodiment 1 of the present invention, as shown in Figures 9 to 11, 13, 14, 16 and 18, the protective cover 33 is recessed with a protective groove 331 for accommodating the cutter 322 on the side close to the cutter 322, and the cutter 322 is partially exposed from the protective groove 331 away from the protective cover 33.

Exemplarily, in the blood vessel 200, the protective cover 33 needs to be located on the opposite side of the blood vessel 200 wall where the embolus 300 is located during the operation, and the notch of the protective groove 331 faces the embolus 300, and a portion of the cutter 322 is accommodated in the protective groove 331, and the cutter 322 and the blood vessel 200 wall on the opposite side of the embolus 300 are isolated by the protective cover 33, and a portion of the cutter 322 is radially exposed to the protective groove 331 toward the embolus 300, so as to remove the embolus 300. Of course, in other embodiments, the protective cover 33 can also be a structure in which the outer wall surface (i.e., the side away from the cutter 322) is adapted to the blood vessel 200 wall, and the inner wall surface (i.e., the side facing the cutter 322) is a structure of other suitable shapes.

As shown in Figures 2, 9 and 10, the proximal end of the protective cover 33 is arranged at the distal end of the mounting tube 31, and the axial length L1 of the protective cover 33 is greater than the length L2 of the cutter 322 axially exposed from the mounting tube 31, that is, the distal end of the protective cover 33 axially extends out of the distal end of the cutter 322, which is beneficial to improving the centering of the torque shaft and the cutter 322. Specifically, on the distal side of the cutter 322, the protective cover 33 can be used to pre-correct the blood vessel 200 at the distal end of the cutter 322, so that the blood vessel 200 at the distal end of the cutter 322 is arranged in advance along the axial direction of the protective cover 33, so as to ensure that the cutting assembly 32 is kept parallel to the blood vessel 200 where the embolus 300 is located, which is beneficial to reduce the risk of scratching or perforation of the blood vessel 200, and is more convenient for multiple removal of the embolus 300 in the diseased blood vessel 200 in one operation.

On the other hand, the protective cover 33 can catch the cut embolic material 300 at the distal side of the cutter 322, so that the cut embolic material 300 is concentrated near the cutter 322 to prevent it from escaping to the distal end, thereby reducing the risk of distal embolism.

Exemplarily, the circumference of the protective cover is arranged in an arc shape, and the circumferential angle of the protective cover is 60 degrees to 180 degrees, so as to adapt to eccentric thrombi or plaques with different degrees of embolism.

The proximal end of the protective cover 33 is fixed to the distal end of the sleeve 311 of the mounting tube 31 by welding or bonding, and the bottom of the protective groove 331 smoothly transitions with the inner wall of the distal end of the mounting tube 31, and the outer wall of the protective cover 33 is flush with the outer wall of the mounting tube 31 and smoothly transitions to ensure that the cut embolic material 300 smoothly enters the transmission channel 27, avoids blockage at the cutter 322, and reduces the risk of thrombosis at the distal end of the cutter 322.

As shown in Figures 11, 13, 14, 16 and 18, the cross-section of the protective cover 33 is concave arc-shaped, that is, the protective cover 33 as a whole is a tile-like structure, so as to adapt to the shape of the inner wall of the blood vessel, and the groove wall of the protective groove 331 is a closed structure or a hollow structure, so that the cover wall of the protective cover 33 is used to isolate the cutter 322 and the wall of the blood vessel 200.

In addition, in some specific embodiments, in order to allow the cut embolus 300 to be discharged from the body more smoothly, at least a portion of the edge of the protective cover 33 may have a serrated structure 335, so that the embolus 300 on the wall of the blood vessel 200 can be squeezed by the protective cover 33 to loosen the embolus 300 in advance, which is conducive to the cutter 322 to remove the embolus 300 more quickly.

The specific structure of the protective cover 33 will be described in detail below through several specific implementations:

In a first specific embodiment of the protective cover 33, the groove wall of the protective groove 331 of the protective cover 33 is a closed structure. For example, as shown in FIG11 and FIG12, the groove wall of the protective groove 331 is smoothly arranged, that is, the groove wall surface of the protective groove 331 is a smooth concave arc surface. Alternatively, the groove wall of the protective groove 331 of the protective cover 33 is a closed structure, and the groove wall of the protective groove 331 is concave and convex. In addition, a serrated structure can be selectively arranged at the edge of the protective cover 33.

Exemplarily, when the groove wall of the protection groove 331 is arranged in a concave-convex manner, a protrusion may be convexly arranged on the groove wall of the protection groove 331, and/or a groove may be concavely arranged, so that the inner wall of the protection cover 33 is uneven, but the outer wall is a closed wall.

Understandably, the uneven inner wall of the protective cover 33 can increase the friction between the cutter 322 and the protective cover 33 on the cut embolic material 300, so that the cut embolic material 300 is broken into finer particles by the relative rotation between the cutter 322 and the protective cover 33 during rotary cutting, which is conducive to the cut embolic material 300 being discharged from the body more smoothly.

In a second specific embodiment of the protective cover 33 , as shown in FIG13 , the groove wall of the protective groove 331 of the protective cover 33 is a hollow structure. Specifically, the groove wall of the protective groove 331 is provided with a plurality of crushing holes 332 , and the gaps between the plurality of crushing holes 332 are distributed throughout the groove wall of the protective groove 331 .

Exemplarily, the crushing hole 332 is a through hole, so that the protective cover 33 is covered with meshes as a whole, forming a hollow mesh cover, so that the cut embolic material 300 can be crushed into finer particles by the cutter 322 and the hollow mesh cover during rotary cutting, which is conducive to the smoother discharge of the cut embolic material 300 from the body. In addition, the shape of the crushing hole 332 includes but is not limited to regular holes such as round holes, and can also be irregular holes.

In the third specific embodiment of the protective cover 33, as shown in Figures 14 and 15, a serrated through hole 333 extending axially is provided from the distal end of the protective cover 33, and a plurality of serrated through holes 333 are provided on the protective cover 33, and the plurality of serrated through holes 333 are arranged at intervals, and the serrated through holes 333 can also allow the cut embolic material 300 to be crushed into finer particles by the cutter 322 and the protective cover 33 in the rotary cutting, which is conducive to the smoother discharge of the cut embolic material 300 from the body. In addition, the edge of the protective cover 33 can also be provided with a serrated structure 335, so as to facilitate the cutter 322 to remove the embolic material 300 more quickly.

In a fourth specific embodiment of the protective cover 33, as shown in Figures 16 and 17, the groove wall of the protective groove 331 is a hollow structure, and the protective cover 33 includes a plurality of inserts 334 that are circumferentially spaced and connected at the proximal ends, wherein the hollow gap structure formed between adjacent inserts 334 can also allow the cut embolic material 300 to be crushed into finer particles by the cutter 322 and the protective cover 33 during rotary cutting, thereby facilitating the cut embolic material 300 to be discharged from the body more smoothly.

In addition, the distal ends of the plurality of inserts 334 may be flush with each other; or, the projections of the plurality of inserts 334 on the horizontal axis plane of the protective cover 33 are arranged in the shape of a convex arc 3341 at the distal end, that is, as the inserts 334 are radially closer to the embolic object 300, the length of the inserts 334 axially extending out of the cutter 322 becomes shorter, so that the distal ends of the plurality of inserts 334 are arranged along the route of the convex arc 3341, so as to guide the cut embolic object 300 to the vicinity of the cutter 322 as quickly as possible, thereby reducing the probability of its escape to the distal end of the cutter 322.

In a fifth specific embodiment of the protective cover 33, as shown in Figures 18 to 20, the protective cover 33 includes a cover body 335 and a plurality of inserts 334, wherein the cover body 335 is opposite to the cutter 322, and the groove wall corresponding to the cover body 335 is a closed structure or a hollow structure; the plurality of inserts 334 are circumferentially spaced at the far end of the cover body 335.

For example, as shown in Figures 18 to 20, the inner wall of the cover body 335 is a closed structure, and the inner wall of the cover body 335 is convexly provided with a plurality of protrusions 3351, and the plurality of protrusions 3351 are arranged at intervals, which can be arranged in an array. In addition, the axial length of the cover body 335 is greater than or equal to the length of the cutter 322 exposed from the mounting cylinder 31.

Understandably, the plurality of inserts 334, the hollow gap structure formed between the inserts 334, and the concave-convex structure formed by the plurality of protrusions 3351 can cause the cut embolic material 300 to be crushed into finer particles by the cutter 322 and the protective cover 33 during rotary cutting, thereby facilitating the cut embolic material 300 to be discharged from the body more smoothly.

Embodiment 2 of the resection system 100 of the present invention

As shown in FIG. 21 to FIG. 31 , the main technical features of the second embodiment are substantially the same as those of the first embodiment described above, and the main difference between the second embodiment and the first embodiment lies in the specific structures of the bending adjustment component 6 and the line fixing component 5 .

As shown in FIGS. 21 to 23 , a wire fixing component 5 and a bending adjustment component 6 are provided on the handle 1, and a bending adjustment wire 21 is provided in the catheter 2. The distal end of the bending adjustment wire 21 is fixedly connected to the distal end of the catheter 2, and the proximal end of the bending adjustment wire 21 is connected to the wire fixing component 5. The wire fixing component 5 is movably connected to the bending adjustment component 6 and is fixedly connected to the proximal end of the bending adjustment wire 21. The bending adjustment component 6 is provided on the handle 1 and sleeved outside the catheter 2, and is mainly used to adjust the traction force of the bending adjustment wire 21 by controlling the axial sliding of the wire fixing component 5, thereby adjusting the bending angle of the catheter 2.

Under the control of the bending adjustment component 6, the wire fixing component 5 can move forward and backward along the axial direction of the catheter 2. Since the length of the bending adjustment wire 21 is fixed, the proximal end of the bending adjustment wire 21 moves toward the distal end when the distal end of the wire fixing component 5 moves, which is equivalent to reducing the traction force and releasing the bending adjustment wire 21 to reduce the bending angle of the head of the catheter 2; conversely, when moving toward the proximal end, it is equivalent to increasing the traction force and pulling the bending adjustment wire 21 to increase the bending angle of the head of the catheter 2. In this way, the bending angle of the head of the catheter 2 is adjusted by controlling the sliding distance of the wire fixing component 5, so that it passes through the curved part in the blood vessel.

The bending adjustment component 6 includes an adjustment cylinder 63, wherein the adjustment cylinder 63 is connected to the handle body and sleeved on the catheter 2. The wire fixing component 5 is axially slidably arranged in the adjustment cylinder 63 by pressing the switch 64 in the adjustment cylinder 63.

The proximal end of the adjusting cylinder 63 is connected to the distal end of the handle 1 and communicates with the inner cavity of the handle 1, and the main parts of the fixing wire component 5 and the push switch 64 are all arranged in the adjusting cylinder 63; the adjusting cylinder 63, the fixing wire component 5 and the push switch 64 are all sleeved on the catheter 2, and the catheter 2 and the adjusting cylinder 63 are fixedly connected by bonding, welding, etc., so that when the adjusting cylinder 63 rotates, it can drive the catheter 2 to rotate.

In addition, a stress diffusion tube 123 is provided at the distal end of the bending adjustment component 6. The stress diffusion tube 123 is sleeved on the catheter 2 and fixedly connected to the distal end of the adjustment tube 63 to prevent the catheter 2 from being bent due to stress concentration at the connection with the adjustment tube 63.

To adjust the bending angle of the catheter 2, the wire fixing assembly 5 includes a hollow second wire fixing slider 52, which is sleeved on the catheter 2 and used to fix the proximal end of the bending adjustment wire 21 and pull the bending adjustment wire 21 through axial movement.

25 to 28, the wire fixing assembly 5 further includes a fixed wire pin 53, and an axial second wire threading hole 521 and a fixed wire hole 522 which is in communication with the second wire threading hole 521 and extends radially are provided on the outer wall of the second wire fixing slider 52. The bending wire 21 led out from the catheter 2 passes through the second wire threading hole 521 and enters the fixed wire hole 522, and the fixed wire pin 53 is inserted into the fixed wire hole 522 through which the bending wire 21 is passed, so that the bending wire 21 can be fixed on the second wire fixing slider 52.

As shown in FIG21 , the push switch 64 includes a push button 641, which is axially slidably disposed on the outer wall of the adjustment tube 63. Specifically, as shown in FIG23 , the adjustment tube 63 includes two first tube shells 631, which are relatively covered on the left and right sides to enclose the adjustment tube 63. A first key groove 6311 is concavely disposed on the outer wall of the adjustment tube 63, and the push button 641 is accommodated in the first key groove 6311 and can slide axially along the first key groove 6311, and the sliding of the push button 641 drives the second wire fixing slider 52 to slide.

25 and 26 , a hollow limit shaft 642 and a clamping member 643 are also provided in the adjusting cylinder 63. The hollow limit shaft 642 is arranged along the axial direction of the adjusting cylinder 63. The second wire fixing slider 52 is slidably sleeved on the hollow limit shaft 642, thereby guiding the axial sliding of the second wire fixing slider 52.

The clamping member 643 is sleeved on the outer side of the second wire fixing slider 52, the clamping member 643 is connected to the pressing key 641, and can be slidably connected to the second wire fixing slider 52 in the radial direction, and a rack 6421 is provided on the hollow limiting shaft 642, and the rack 6421 is provided on the other side of the hollow limiting shaft 642 relative to the pressing key 641. A clamping tooth plate 6432 corresponding to the rack 6421 is provided on the clamping member 643, and a return spring 644 is provided between the clamping member 643 and the second wire fixing slider 52, and the return spring 644 is used to drive the clamping member 643 to move toward the direction of the pressing key 641, and in a natural state, the rack 6421 and the clamping tooth plate 6432 are engaged under the drive of the return spring 644, so that the pressing key 641 and the hollow limiting shaft 642 are relatively fixed in the axial direction.

When the push button 641 is pressed, the return spring 644 is compressed, and the rack 6421 is separated from the latch tooth 6432. At this time, the push button 641 can move axially, thereby driving the second wire fixing slider 52 to move axially, and then driving the distal end of the catheter 2 to bend through the bending wire 21.

A thread hole 6422 is axially provided on the distal end of the hollow limit shaft 642, and the bending wire 21 enters the fixed wire hole 522 from the thread hole 6422 and the second thread hole 521 in sequence for fixing, as shown in Figure 28. The clamping member 643 includes a fixedly connected clamp 6431, and a clamping tooth plate 6432 is arranged on the clamp 6431.

Specifically, as shown in FIGS. 26 to 30 , the clamp 6431 is provided with a positioning groove 64311, and the clamping plate 6432 is provided with a positioning protrusion 64322 on the side facing the hollow limit shaft 642. The clamp 6431 passes through the radial groove 612 on the second wire fixing slider 52 and is engaged with the clamping plate 6432. The clamp 6431 and the clamping plate 6432 are fixed by the positioning groove 64311 and the positioning protrusion 64322. Thus, the clamp 643 is sleeved on the second wire fixing slider 52, and the clamp 643 can move radially relative to the radial groove 612 on the second wire fixing slider 52.

The tooth plate 6432 is provided with a tooth gap 64321, and the rack 6421 on the outer wall of the hollow limiting shaft 642 is engaged with the tooth gap 64321 on the tooth plate 6432. The second wire fixing slider 52 is also provided with an avoidance hole 523, wherein the tooth gap 64321 of the clamping member 643 can enter the cavity of the second wire fixing slider 52 through the avoidance hole 523 to be engaged with the rack 6421 on the hollow limiting shaft 642.

The push button 641 is fixedly connected to the top of the clamp 6431 by bonding, welding, etc. The return spring 644 is arranged between the second wire fixing slider 52 and the clamp 6431. The side of the clamp 6431 facing the second wire fixing slider 52 is provided with a mounting column 64312, and the return spring 644 is assembled on the mounting column 64312.

According to the above embodiment, in the initial state, the return spring 644 will push up the clamp 6431, so that the tooth gap 64321 on the clamping plate 6432 is engaged with the rack 6421 on the hollow limit shaft 642, so as to axially fix the second wire fixing slider 52. When the pressing key 641 is pressed, the clamping plate 6432 will be pushed out to make the tooth gap 64321 separate from the rack 6421, and then the pressing key 641 is axially pushed to achieve the bending of the catheter 2. For example, by moving the pressing key 641 proximally, the second wire fixing slider 52 can move toward the proximal end under the drive of the clamp 6431, so as to increase the traction force on the bending wire 21, so as to bend the head of the catheter 2, and achieve the bending function.

In order to realize the positioning of the catheter 2 after rotation, there is a large damping between the adjustment cylinder 63 and the handle 1, so that the adjustment cylinder 63 can be stationary relative to the handle 1 without external force. When the doctor rotates the adjustment cylinder 63, the adjustment cylinder 63 can rotate relative to the handle 1, and synchronously drive the second fixed line slider 52 to rotate by pressing the switch 64, so as to avoid the bending wire 21 and the internal structure of the handle 1 from being entangled when the adjustment cylinder 63 rotates. When the doctor operates the press switch 64, the pressing key 641 can drive the fixed line assembly 5 to move axially, so as to bend the distal end of the catheter 2.

Specifically, as shown in FIG. 26 , since the catheter 2 is fixedly connected to the adjustment cylinder 63, and the clamp 6431 of the push switch 64 is connected to the second wire fixing slider 52 and the hollow limit shaft 642 of the wire fixing assembly 5, the hollow limit shaft 642 is fixedly arranged on the first cylinder shell 631 of the adjustment cylinder 63, and is movably sleeved on the catheter 2. Therefore, when the adjustment cylinder 63 is rotated and the push button 641 is not subjected to a pressing force, the entire push switch 64 can rotate together with the adjustment cylinder 63 and the catheter 2. When the push button 641 is subjected to a pressing force to release the axial limit of the second wire fixing slider 52, the push button 641, the clamping member 643, the second wire fixing slider 52 and the catheter 2 of the push switch 64 can also rotate together with the adjustment cylinder 63. In this way, the second wire fixing slider 52 and the catheter 2 can rotate synchronously with the adjustment cylinder 63, and the bending wire 21 can be prevented from being entangled with the catheter 2.

As shown in Figures 21 to 23, in order to achieve the damped rotation of the adjustment cylinder 63 relative to the handle 1, the handle 1 includes a second handle shell 12, on which a damping rib position 121 is convexly provided, and a convex rib 6312 is also circumferentially provided on the proximal end of the first cylinder shell 631 of the adjustment cylinder 63, and a damping hole 63121 is axially opened on the convex rib 6312, wherein, when the proximal end of the adjustment cylinder 63 is rotated and inserted into the distal end of the handle 1, the convex rib 6312 is inside the handle 1 and is located on the proximal side of the damping rib position 121, so that the ball 122 inserted into the damping hole 63121 is abutted against the damping rib position 121, so as to achieve the damping effect when the adjustment cylinder 63 rotates.

As shown in combination with FIG. 22 and FIG. 31 , in order to realize the rotation of the cutting assembly 32, the driving device 4 includes a motor 41, a wire 42, a battery 43, a driving switch 44, a Y-type valve 46, a gear pair 47, a bearing 48 and a mounting shaft 49 arranged in the handle 1, and also includes a switch key 45 arranged on the outer wall of the handle 1 and connected to the driving switch 44, wherein the Y-type valve 46 includes a main valve pipe and a waste discharge pipe, and in the handle body, the motor 41 is electrically connected to the battery 43 and the driving switch 44 through the wire 42, and the output shaft of the motor 41 is connected to the driving wheel of the gear pair 47; the cutting assembly The proximal end of the rotating shaft 321 of the component 32 is inserted into the mounting shaft 49 in the main valve tube of the Y-type valve 46 and is fixedly connected to the mounting shaft 49 by welding or the like. The distal end of the mounting shaft 49 is rotatably mounted in the main valve tube of the Y-type valve 46 through a bearing 48. The mounting shaft 49 is fixedly connected to a driven wheel of a gear pair 47, and the proximal end is mounted in the cylinder seat 73 through another bearing 48. When the battery 43 is energized, the drive switch 44 is started by operating the switch key 45 to enable the motor 41 to work, so as to drive the rotating shaft 321 to rotate, thereby realizing the rotary cutting function of the cutter 322.

The Y-shaped valve 46 is communicated with the transmission channel 27 of the catheter 2 and extends obliquely out of the handle body along the direction of removing the embolic material 300 so as to discharge the removed embolic material 300 as quickly as possible.

In other embodiments, the rotation speed and torque of the rotating shaft 321 can be adjusted by different transmission ratios between the driving wheel and the driven wheel in the gear pair 47, so as to meet the needs of removing emboli 300 of different hardness. For example, in the normal removal state, the high speed gear can be selected to facilitate rapid removal and shorten the operation time; when encountering special situations such as eccentric calcified lesions, the low speed gear can be selected to avoid the cutter 322 from getting stuck.

As shown in Figures 22 to 24, the guide wire locking device 7 includes a screw cap 71, a sealing gasket 72 and a cartridge seat 73, wherein the cartridge seat 73 is fixedly mounted on the proximal end of the handle body, the proximal end of the mounting shaft 49 of the drive device 4 is rotatably mounted in the stepped hole at the distal end of the cartridge seat 73 through the bearing 48, the sealing gasket 72 is inserted into the cartridge seat 73 from the proximal end of the cartridge seat 73, the screw cap 71 is threadedly sleeved on the proximal end of the cartridge seat 73, and can axially abut against the sealing gasket 72 in the cartridge seat 73, the guide wire can pass through the screw cap 71, the sealing gasket 72, the cartridge seat 73 and the mounting shaft 49 in sequence from the outside to enter the rotating shaft 321, so as to realize the overall axial penetration of the guide wire through the handle body, making it convenient and smoother to push the catheter 2 into the lesion site. When the screw cap 71 is tightened, the sealing gasket 72 in the cylinder seat 73 can be axially squeezed to shrink the aperture of the sealing gasket 72 and lock the guide wire to fix the guide wire and prevent the guide wire from rotating with the cutter 322 during the operation and damaging the blood vessel 200. At the same time, the proximal end of the handle body is also sealed.

Embodiment 3 of the resection system 100 of the present invention

As shown in FIG. 32 to FIG. 34 , the main technical features of the third embodiment are substantially the same as those of the second embodiment described above, and the main difference between the third embodiment and the second embodiment lies in the specific structures of the bending adjustment component 6 and the line fixing component 5 .

The bending adjustment component 6 includes an adjustment cylinder 63 , wherein the adjustment cylinder 63 is connected to the handle 1 and sleeved on the catheter 2 , and the wire fixing component 5 is axially slidably arranged on the adjustment cylinder 63 to adjust the bending angle of the catheter 2 .

The proximal end of the adjustment cylinder 63 is connected to the distal end of the handle 1 and communicates with the inner cavity of the handle 1, and the main body of the wire fixing component 5 is located in the adjustment cylinder 63, and the adjustment cylinder 63 and the wire fixing component 5 are respectively sleeved on the catheter 2. In addition, the wire fixing component 5 can be movably connected to the catheter 2, and the adjustment cylinder 63 and the catheter 2 are fixedly connected by bonding, welding, etc.

As shown in Figures 32 to 34, in order to realize the axial sliding of the wire fixing component 5 set on the adjustment cylinder 63, the wire fixing component 5 includes a sliding key 54, and the sliding key 54 includes a sliding shaft 541, a fixing frame 542 and a sliding key 543, wherein the sliding shaft 541 is movably sleeved on the catheter 2, and the fixing frame 542 is radially arranged on the outer wall of the sliding shaft 541 for fixing the bending wire 21; the sliding key 543 is connected to the end of the fixing frame 542 away from the sliding shaft 541, and is axially damped and slidably arranged on the outer wall of the adjustment cylinder 63.

As shown in FIG. 32 and FIG. 33 , a second keyway 6321 is recessed on the outer wall of the adjusting cylinder 63, and the sliding key 543 is accommodated in the second keyway 6321 and can slide axially along the second keyway 6321. In order to realize the fixing and bending adjustment functions of the sliding key 54. A third threading hole 5421 is axially opened on the fixing frame 542, wherein the bending adjustment wire 21 passes through the third threading hole 5421 and then is wound on the fixing frame 542, so that the bending adjustment wire 21 can be fixed on the fixing frame 542. And because the entire sliding key 54 is axially movable and sleeved on the catheter 2, when the sliding key 543 is damped in the axial sliding in the second keyway 6321, the sliding key 543 can drive the fixing frame 542 and the sliding shaft 541 connected thereto to slide axially relative to the catheter 2, thereby adjusting the traction force of the bending adjustment wire 21 and realizing the adjustment of the bending angle of the catheter 2.

As shown in FIG34 , in order to achieve damped axial sliding of the sliding key 543, the adjusting cylinder 63 includes two second cylinder shells 632, which are relatively covered up and down to enclose the adjusting cylinder 63. The inner wall of the second cylinder shell 632 is provided with a second damping tooth 6322. Correspondingly, an elastic hook 5422 is provided on the fixing frame 542, wherein when the sliding key 543 slides axially, the hook 5422 can be engaged with the second damping tooth 6322 at the corresponding position, thereby achieving the damping effect of the axial sliding of the sliding key 543.

The bending adjustment assembly 6 also includes a guide cylinder 645. The adjustment cylinder 63 is rotatably arranged on the handle 1. The guide cylinder 645 is fixedly connected to the catheter 2. When the adjustment cylinder 63 rotates relative to the handle 1, the guide cylinder 645 rotates synchronously with the adjustment cylinder 63. In order to realize the guiding function of the guide cylinder 645 and ensure that the sliding key 54 rotates together with the adjustment cylinder 63, the sliding shaft 541 is movably sleeved on the guide cylinder 645. The guide cylinder 645 supports the sliding shaft 541 from the inside of the sliding shaft 541. The outer wall of the guide cylinder 645 is provided with a guide rib 6451. The inner wall of the sliding shaft 541 is provided with a sliding hole 5411. The guide rib 6451 extends along the axial direction of the guide cylinder 645. The guide rib 6451 is slidably connected with the sliding hole 5411. Therefore, the sliding shaft 541 can slide along the axial direction of the guide cylinder 645, while being relatively stationary in the circumferential direction.

Through the above structure, when the adjusting cylinder 63 is rotated, the sliding key 54 arranged on the adjusting cylinder 63 and the catheter 2 fixedly connected to the adjusting cylinder 63 will rotate together with the adjusting cylinder 63, so as to realize the rotation of the catheter 2 while avoiding the entanglement of the bending wire 21.

In this embodiment, the handle 1 includes two third handle shells 13, which are overlapped with each other up and down to enclose the handle 1, and the proximal end of the second cylinder shell 632 of the adjusting cylinder 63 is connected to the distal damping rotation of the third handle shell 13 of the handle 1 through friction.

The above description is only a preferred embodiment of the present invention and is not intended to limit the present invention. For those skilled in the art, the present invention may have various modifications and variations. Any modification, equivalent substitution, improvement, etc. made within the spirit and principle of the present invention should be included in the scope of the claims of the present invention.

Claims (10)

1. A cutting system, characterized in that the cutting system comprises a handle, a catheter arranged on the handle, a cutting device connected with the catheter and a protective cover; the cutting device comprises a cutting assembly, the cutting assembly comprises a cutter, the protective cover is connected with the catheter or the cutting assembly, and the outer side of the protective cover is arc-shaped and can be covered on one side of the cutter.

2. The ablation system of claim 1, wherein the cutting assembly further comprises a rotating shaft threaded through the catheter, the cutter being disposed on a distal side of the rotating shaft; when the protective cover is covered on the cutter, the protective cover protrudes towards the direction away from the cutter, and a protective groove for accommodating the cutter is formed on one side of the protective cover facing the cutter.

3. The ablation system of claim 2, wherein the ablation device further comprises a mounting barrel disposed at a distal end of the catheter, the cutter is rotatably coupled to the mounting barrel, the proximal end of the protective shield is coupled to the distal end of the mounting barrel, and an axial length of the protective shield is greater than a length of the cutter extending axially out of the mounting barrel;

The circumference of the protective cover is arranged in an arc shape, and the circumferential angle of the protective cover is 60-180 degrees.

4. The ablation system of claim 2, wherein the walls of the protective slot are of a closed configuration, the walls of the protective slot being smoothly disposed; or the groove wall of the protection groove is provided with patterns.

5. The excision system according to claim 2, wherein the wall of the protection groove is in a hollowed-out structure, and a plurality of crushing holes are formed in the wall of the protection groove and are arranged in a clearance mode;

Or the protecting cover is provided with sawtooth-shaped through holes which axially extend from the far end, and the plurality of sawtooth-shaped through holes are arranged at intervals;

or the protective cover comprises a plurality of cutting bars which are circumferentially arranged at intervals and are connected at the proximal end;

Or the protective cover comprises a cover body and a plurality of cutting bars arranged at the far end of the cover body at intervals, and the groove wall corresponding to the cover body is of a closed structure or a hollow structure.

6. The ablation system of claim 5, wherein when the protective cap comprises a plurality of slips, distal ends of the plurality of slips are flush; or the distal ends of the projections of the plurality of cutting bars on the horizontal axial plane of the protective cover are arc-shaped.

7. The ablation system of claim 4 or 5, wherein the edge of the protective cap is at least partially serrated.

8. The ablation system of claim 3, wherein the mounting barrel comprises a sleeve fixedly attached to the distal end of the catheter and a barrel jaw, the cutter is rotatably attached to the barrel jaw, and the sleeve is sleeved outside the barrel jaw and the cutter; the distal end circumference interval of section of thick bamboo claw is provided with a plurality of clamping jaws, the inner wall of a plurality of clamping jaws is provided with spacing arch, the spacing groove has been seted up to the outer wall circumference of cutter, spacing protruding joint in the spacing inslot.

9. The ablation system of claim 1, further comprising a bend-adjusting assembly and a wire-fixing assembly, wherein a bend-adjusting wire connected to the distal end of the catheter is disposed in the catheter, the wire-fixing assembly is movably connected to the catheter and fixedly connected to the proximal end of the bend-adjusting wire, the bend-adjusting assembly is connected to the wire-fixing assembly and the catheter, the bend-adjusting assembly is used for driving the catheter to circumferentially rotate, and the bend-adjusting assembly controls the distal end of the catheter to bend through the wire-fixing assembly and the bend-adjusting wire.

10. The ablation system of claim 9, wherein the wire-fixing assembly is movably sleeved in the catheter and is arranged in the bending-adjusting assembly, and the bending-adjusting assembly can independently drive the wire-fixing assembly to axially move relative to the catheter or independently drive the wire-fixing assembly to synchronously rotate with the catheter.