CN217566230U - Interventional blood vessel volume reduction device - Google Patents

Abstract

The present application relates to an interventional vascular volume reduction device comprising: a sheath assembly including a sheath having a lumen; the bolt discharging assembly comprises a negative pressure suction mechanism, and the negative pressure suction mechanism is communicated with the lumen of the sheath tube; the rotary cutting assembly comprises a core shaft, a cutting piece and at least one propeller, the core shaft is arranged in the tube cavity along the axial direction, the cutting piece is connected with the far end of the core shaft outside the sheath tube, and the propeller is fixedly sleeved on the core shaft. The propeller sleeved on the mandrel rotates along with the mandrel in the rotary cutting process, and the pneumatic force generated in the rotation pushes the tissue removal objects in the tube cavity to be discharged towards the near end in an accelerating manner, so that the bolt removal efficiency is improved, the tissue removal objects are prevented from being accumulated and blocked in the sheath tube as much as possible, and then the risks of diseases and the risks of failure and even damage of equipment are reduced.

Description

Interventional blood vessel volume reduction device

Technical Field

The utility model relates to an intervene medical instrument, especially relate to an intervention formula blood vessel volume reduction device.

Background

Atherosclerosis in the vascular system can reduce or block blood flow through the blood vessels, resulting in narrowing or even occlusion of the blood vessels, thereby causing symptoms of low blood flow, such as leg pain (while walking or at rest), skin ulcers, angina (at rest or exertional), and the like. Aiming at the symptoms, an interventional blood vessel volume reduction device can be adopted at present, atherosclerosis formed in the blood vessel is removed in a rotary cutting mode and is taken out of the body, and therefore the treatment effect is achieved.

The interventional blood vessel volume reduction device can be divided into two types, namely a manual-containing type device and an active continuous-containing type device, when the manual-containing type device is used, a resection object flows into a containing cavity at the far end of a cutter head for temporary storage through the guiding of a rotary cutter head, and when the containing cavity is filled with the resection object, the rotary cutter device needs to be withdrawn from the body, manually cleaned by a surgeon and implanted into the body again for operation. The latter (active continuous embolectomy device) is used for sucking the excised material in real time by driving a embolectomy mechanism through a motor outside the body of the patient during rotary cutting. Compared with the former, the latter can continuously remove atheroma with higher efficiency, but due to the size limitation of the vascular interventional device, the sheath tube body for thrombus removal and sheath core protection needs to be smaller than the vascular lumen, even if the thrombus removal device provides enough negative pressure support, the thrombus removal efficiency (the efficiency of conveying the excision objects) is still lower, and the blood and excision objects in the sheath tube move at low speed, so that the device is easy to accumulate and block, and further the device is ineffective or damaged.

SUMMERY OF THE UTILITY MODEL

In order to solve the above technical problem or at least partially solve the above technical problem, the present application provides an interventional blood vessel volume reduction device comprising:

a sheath assembly including a sheath having a lumen;

the bolt discharging assembly comprises a negative pressure suction mechanism, and the negative pressure suction mechanism is communicated with the lumen of the sheath tube;

the rotary cutting assembly comprises a core shaft, a cutting piece and at least one propeller, the core shaft is arranged in the tube cavity along the axial direction, the cutting piece is connected with the far end of the core shaft outside the sheath tube, and the propeller is fixedly sleeved on the core shaft.

Preferably, the propeller comprises a hub fixed to the spindle and at least one blade attached to the hub.

Preferably, the rotary-cut assembly further comprises a spring tube fixedly sleeved on the mandrel; the spring tubes are axially spaced from the propeller.

Preferably, the rotary cutting assembly comprises at least one set of propellers, and the set of propellers comprises a plurality of propellers arranged at intervals along the axial direction.

Preferably, the propeller comprises a plurality of blades evenly spaced around the spindle.

Preferably, at least one propeller of a group of propellers comprises one blade, and the blades of all the propellers of the group of propellers are uniformly arranged around the core shaft on a projection plane perpendicular to the axial direction.

Preferably, the propeller comprises helical blades around a mandrel.

Preferably, the maximum radial length of the paddle is no more than 90% of the inner diameter of the lumen, and the degree of the paddle angle is in the range of 15-25 °.

Preferably, the sheath assembly further comprises a base with a central through hole, the base is fixedly connected with the distal end of the sheath and is communicated with the lumen of the sheath through the central through hole; the cutting member includes link, a plurality of cutting edges, is formed at two vicinities guiding gutter between the cutting edge, the link supports to lean on the base and is connected with the dabber drive, guiding gutter and central through-hole intercommunication, the cutting edge is the free end.

Preferably, the rotational atherectomy assembly further comprises a drive motor in driving communication with the proximal end of the mandrel.

Compared with the prior art, the technical scheme provided by the embodiment of the application has the following advantages: the propeller sleeved on the mandrel rotates along with the mandrel in the rotary cutting process, and the pneumatic force generated in the rotation pushes the tissue removal objects in the tube cavity to be discharged towards the near end in an accelerating manner, so that the bolt removal efficiency is improved, the tissue removal objects are prevented from being accumulated and blocked in the sheath tube as much as possible, and then the risks of diseases and the risks of failure and even damage of equipment are reduced.

Drawings

The accompanying drawings, which are incorporated in and constitute a part of this specification, illustrate embodiments consistent with the present invention and, together with the description, serve to explain the principles of the invention.

In order to more clearly illustrate the embodiments of the present invention or the technical solutions in the prior art, the drawings used in the embodiments or the technical solutions in the prior art will be briefly described below, and it is obvious for those skilled in the art that other drawings can be obtained according to the drawings without inventive labor.

In the drawings:

FIG. 1 is a schematic structural diagram of an interventional vascular reduction device according to a first embodiment of the present application;

FIG. 2 is a schematic view of a portion of the sheath of FIG. 1;

FIG. 3 is a schematic structural view of the sheath and the base of FIG. 1;

FIG. 4a is a schematic view of the cutter of FIG. 1 coupled to a mandrel;

FIG. 4b is a schematic view of the structure of the cutting element of FIG. 4 a;

FIG. 5 is a schematic illustration of an exemplary venting process of FIG. 1;

FIG. 6 is a schematic view of an exemplary propeller distribution of FIG. 1;

FIG. 7 is a cross-sectional schematic view of FIG. 6;

FIG. 8 is a schematic view of the structure of the motor assembly of FIG. 1;

FIG. 9 is a schematic view of a portion of an interventional vascular reduction device in accordance with a second embodiment of the present application;

FIG. 10 is a cross-sectional schematic view of FIG. 9;

fig. 11 is a schematic partial structure diagram of an interventional blood vessel volume reduction device according to a third embodiment of the present application.

Detailed Description

In order to clearly understand the technical features, objects, and effects of the present invention, embodiments of the present invention will be described in detail with reference to the accompanying drawings. In the following description, it should be understood that the directions or positional relationships indicated by "front", "back", "upper", "lower", "left", "right", "longitudinal", "horizontal", "vertical", "horizontal", "top", "bottom", "inner", "outer", "head", "tail", and the like are configured and operated in specific directions based on the directions or positional relationships shown in the drawings, and are only for convenience of description of the present technical solution, and do not indicate that the device or element referred to must have a specific direction, and thus, should not be construed as limiting the present invention.

It should also be noted that, unless expressly specified or limited otherwise, the terms "mounted," "connected," "secured," "disposed," and the like are to be construed broadly and encompass, for example, fixed connections as well as removable connections or integral parts; can be mechanically or electrically connected; either directly or indirectly through intervening media, either internally or in any other relationship. When an element is referred to as being "on" or "under" another element, it can be "directly" or "indirectly" on the other element or intervening elements may also be present. The terms "first", "second", "third", etc. are only for convenience in describing the present technical solution, and are not to be construed as indicating or implying relative importance or implicitly indicating the number of technical features indicated, whereby the features defined as "first", "second", "third", etc. may explicitly or implicitly include one or more of such features. The specific meaning of the above terms in the present invention can be understood according to specific situations by those skilled in the art.

In the description of the present application, it is noted that, in the field of interventional medical devices, the proximal end refers to the end closer to the operator, and the distal end refers to the end farther from the operator; axial refers to a direction parallel to the line connecting the center of the distal end and the center of the proximal end of the medical device, and circumferential is a direction perpendicular to the axial direction. The above definitions are for convenience of description only and should not be construed as limiting the present invention.

As shown in fig. 1-8, in a first embodiment of an interventional vascular reduction device of the present application, the interventional vascular reduction device includes a sheath assembly, a embolectomy assembly, and an atherectomy assembly. Wherein the sheath assembly comprises a sheath 11; the embolectomy component comprises a negative pressure suction mechanism 21, wherein the negative pressure suction mechanism 21 is communicated with the lumen 110 of the sheath tube 11; the rotary cutting assembly comprises a core shaft 31, a cutting piece 32 and at least one propeller 33, the core shaft 31 is arranged in the lumen 110 of the sheath tube 11 along the axial direction A, the cutting piece 32 is connected with the far end of the core shaft 31 outside the sheath tube 11, and the propeller 33 is fixedly sleeved on the core shaft 31.

In the interventional blood vessel volume reducing device, the cutting element 32 is driven by the mandrel 31 to rotate to carry out rotary cutting operation on atheroma, and the cut tissue 2a enters the lumen 110 of the sheath tube 11 and flows from the distal end to the proximal end of the sheath tube 11 under the action of the negative pressure suction mechanism 21 so as to be taken out of the body; meanwhile, the propeller 33 sleeved on the mandrel 31 rotates together with the mandrel 31 in the rotary cutting process, and the aerodynamic force generated in the rotation pushes the excised tissue 2a in the lumen 110 to accelerate and discharge towards the near end, so that the thrombus discharge efficiency is improved, the accumulation and blockage of the excised tissue 2a in the sheath tube 11 are avoided as much as possible, and the risks of diseases and the risks of equipment failure and even damage are reduced.

In addition, compared with the whole sheath tube 11, the volume of the propeller 33 dispersedly sleeved on the mandrel 31 is relatively small, and the propeller is only distributed on a very small section of the sheath tube 11, so that the bending performance of the sheath tube 11 is not affected, and the possibility that the vessel wall is easily damaged to form a new laceration or even a new interlayer when the sheath tube 11 is pushed in a tortuous blood vessel environment is avoided.

In addition, because the propellers 33 are not continuously arranged on the mandrel along the axial direction A, but can be separately and independently arranged, different combinations can be performed on the propellers 33, including various combinations of the shapes, the interval sizes, the number and the like of the propellers 33, so that the propellers are suitable for different blood vessels, are flexible in collocation and are wide in application range.

Specifically, the sheath 11 of the sheath assembly is a tubular structure along the axial direction a, and the sheath wall surrounds and forms an axial lumen 110, and the lumen 110 is communicated from the proximal end to the distal end of the sheath 11. The sheath 11 wall can be made of, for example, a multi-strand wound threaded tube and a pebax (block polyether amide resin) sleeve. The size of the sheath 11 generally matches the vessel for which it is intended, for example, if the interventional vascular reduction device of the present application is intended for use in a lower limb arterial vessel, the outer diameter of the sheath 11 is about 2mm (7F) and the thickness of the sheath 11 is about 0.1mm. If the matching is performed on other types of blood vessels, sheath tubes 11 with other adaptive sizes are selected, and the details are not repeated here. The sheath wall is provided with an opening (not shown) at the proximal end to communicate the lumen 110 with the outside, thereby leading out the tissue 2a excised from the lumen 110.

Referring to fig. 3, the sheath assembly further comprises a base 12 having a central through hole 120, the base 12 being fixedly connected to the distal end of the sheath 11 and communicating with the lumen 110 of the sheath 11 through the central through hole 120. By the communication of both, the excised tissue 2a can enter the lumen 110 of the sheath 11 from the base 12.

The embolectomy assembly further comprises a receiving mechanism 23 and a hose 22, wherein the negative pressure suction mechanism 21 is communicated with the receiving mechanism 23 through the hose 22, and is simultaneously communicated with the lumen 110 of the sheath 11 through the hose 22, for example, the opening of the sheath 11 is connected to communicate with the lumen 110 through the hose 22, so that the tissue 2a cut in the lumen 110 can be sucked into the receiving mechanism 23 through the hose 22 to be stored under the negative pressure suction effect.

The rotational atherectomy assembly includes a mandrel 31, a cutting member 32, and at least one propeller 33. The mandrel 31 is disposed in the lumen 110 of the sheath 11 along the axial direction a, the distal end of the mandrel 31 is fixedly connected to the rotary-cut cutting element 32, for example, the mandrel 31 can be welded and fixed, so as to mainly play a role in transmission, and the mandrel 31 rotates to drive the cutting element 32 connected thereto to rotate, thereby realizing the rotary-cut of the atheroma. To ensure a stable rotation speed and torque of the rotary-cut cutting member 32, the connecting core 31 may be a stainless steel wire rope woven by multiple strands, for example, a stainless steel wire rope woven by 24 strands, and the diameter of the core 31 is about 0.6mm.

Referring to fig. 4a and 4b, the cutting element 32 includes a connecting end (not shown), a plurality of blades 321, and a guiding groove 322 formed between two adjacent blades 321, wherein there are 4 blades 321, and of course, the number of blades 321 may be 3 or other, and the blades 321 are axially distributed, preferably axially spirally distributed, so that the guiding groove 322 formed between the adjacent blades 321 is also axially distributed, or preferably axially spirally distributed. The direction of the cutting edge 321 is matched with the rotary cutting direction, so that atheroma in a tube cavity can be conveniently cut; in addition, the guide groove 322 is arranged in the axial direction, so that the cut tissue can smoothly flow into the lumen of the sheath tube. The person of ordinary skill in the art can select any suitable cutting member structure based on the utility model of this application, for example can select other cutting edge structures, only need can realize to the rotary-cut of congee form hard piece and water conservancy diversion organize the thing can.

Specifically, the connecting end of the cutting element 32 abuts against the base 12, the base 12 can limit the rotary cutting element 32 to ensure the stability of the cutting element 32 during working, and the connecting end is in driving connection with the mandrel 31, so that rotary cutting can be performed under the driving of the mandrel 31; the guide grooves 322 are substantially axially distributed and communicate with the central through hole 120, so that the cut-off tissue 2a can enter the lumen 110 of the sheath 11 via the guide grooves 322 and the central through hole 120; the blade 321 is free and is disposed beyond the distal end of the sheath 11 to effect atherectomy of atheroma.

In a specific embodiment of this embodiment, the propeller 33 of the rotary-cut assembly includes a hub 331 fixedly secured to the core shaft 31, and at least one blade 332 connected to the hub 331; the blades 332 may be airfoils, one end connected to the hub 331 and the other end being a free end of rotation. The hub 331 and the blades 332 connected with the hub 331 are driven to rotate in the rotation process of the mandrel 31, and in the rotation process of the blades 332, on one hand, the aerodynamic force generated in the rotation pushes the excised tissue 2a in the lumen 110 to accelerate and discharge towards the proximal end, so that the thrombus discharging efficiency is improved; on the other hand, the blades 332 can crush the excised tissue 2a in the lumen 110 during the rotation process, so as to reduce the size of the tissue 2a, and the reduced size of the tissue 2a is more beneficial to the flow in the lumen 110, so as to avoid the blockage of the tissue 2a in the sheath as much as possible, thereby ensuring the stable operation of the interventional blood vessel volume reduction device and reducing the risks in the operation; on the other hand, the blades 332 of the propeller 33 do not need to be attached to the inner wall of the sheath tube 11 during the rotation process, so that the contact area between the core shaft 31 and the sheath tube 11 and the mechanism (such as the propeller 33) arranged on the core shaft 31 is effectively reduced, the friction and the energy loss caused by the friction are reduced, and the safety and the stability of the rotary cutting piece 32 are guaranteed.

The number of propellers 33 may be one or more, for example 2, 3 or more, not to mention here. In one embodiment of this embodiment, the rotary cutting assembly includes 3 propellers 33a, 33b, and 33c spaced along the axial direction a, for example, uniformly spaced apart, as shown in fig. 5. The plurality of propellers 33a, 33b, and 33c rotate simultaneously, improving the pushing effect, and then improving the bolt discharging efficiency. In addition, the plurality of spaced propellers can sequentially crush the tissue 2a in the lumen 110 to have a size as small as possible, thereby preventing the tissue 2a from being blocked in the sheath as much as possible. For example, in the direction of embolus removal (arrow B), tissue 2a1 is first crushed by propeller 33a and becomes smaller tissue 2a2, second crushed by propeller 33B and becomes smaller tissue 2a3, and third crushed by propeller 33c and becomes smaller, and so on. Meanwhile, the propellers 33 are arranged at intervals, so that the bending performance of the sheath tube 11 is not affected, and the possibility that the vessel wall is easily damaged to form a new laceration or even an interlayer when the sheath tube 11 is pushed in a tortuous vessel environment is avoided.

Of course, the arrangement of the plurality of propellers 33 may be various, the propellers 33 may be arranged in groups, the plurality of propellers 33 are arranged in one group of propellers 33, and parameters of each group of propellers 33 may be independently set, such as the number of blades of the propellers 33, the shape of the blades, the size of the blades, the blade angle, the pitch between the propellers, and the like. The spacing between one set of propellers 33 and another set of propellers 33 may be set according to the actual vessel adaptation.

For example, the hub 331 and the blades 332 may be integrally formed, or may be separately formed and then connected together, and the hub 331 is connected and fixed with the core shaft 31 through integral injection molding or bonding, hot melting, fastening, or other methods; the blades 332 are preferably made of a polymer or metal material of 80D or more, the maximum diameter of the blades 332 should be not more than 90% of the inner diameter of the sheath 11, the thickness of the blades 332 should be not more than 10% of the maximum diameter of the blades 332, and the blade angle (blade 332 angle) is preferably 15-25 °. The paddles 332 are not in the same plane as the circumferential direction but are angled with respect to the circumferential direction to effectively urge tissue toward the direction of the embolus.

The number of the blades 332 of each propeller 33 may be 1-5, preferably, a plurality of blades 332 may be uniformly arranged around the mandrel 31, although the pushing efficiency is higher as the number of the blades is larger, due to the size limitation of the sheath 11, the area of a single blade is reduced as the number of the blades 332 is too large, the processing difficulty is increased, the space between the blades is reduced, and the risk of blockage is caused. However, if the propeller 33 has only one blade 332, there is a risk of instability of the spindle 31 during rotation, for which purpose it may be provided that at least one propeller 33 of a group of propellers 33 comprises one blade 332, the blades 332 of all propellers 33 of the group of propellers 33 being evenly spaced around the spindle 31 on a plane of projection perpendicular to the axial direction a. For example, referring to fig. 6 and 7, each propeller 33 of the set of propellers 33 comprises one blade 332, all blades 332 being uniformly arranged around the core axis 31 on a plane of projection perpendicular to the axial direction a, the angle between the blades 332 and the blades 332 on the plane of projection being preferably between 30 ° and 120 °. Through the combination, the problem that the rotation of the mandrel 31 is unstable due to the fact that the number of the paddles 332 is small is solved, and the preparation process is simplified due to the fact that the number of the paddles 332 is small, the preparation cost is reduced, and the preparation difficulty is reduced.

Referring to fig. 8, the interventional vascular reduction device further includes a handle assembly 40, the handle assembly 40 including: a housing 41, a motor 42, a power supply 43, a knob 44, a hemostatic valve 45, and the like. It should be understood that not all of the components of the handle assembly 40 are shown, such as a circuit assembly, etc., and that one of ordinary skill in the art may select a suitable handle structure based on the inventive concepts of the present application. The motor 42 of the handle assembly 40 can directly drive the spindle 31 to rotate, thereby rotating the cutter 32 via the rotation of the spindle 31.

The hemostatic valve 45 may be a luer connector for preoperative deflation, which is communicated with the above-mentioned opening of the lumen 110 of the sheath 11, and the flexible tube 22 of the embolectomy assembly is connected to the luer connector during operation, and after the device is started, the vacuum negative pressure suction mechanism 21 of the embolectomy assembly provides continuous negative pressure to the embolectomy flexible tube 22, so that the cutting member 32 cuts the wall-attached tissue (such as porridge-like hard mass) in the blood vessel by rotary cutting, and the cut tissue 2a is discharged out of the body through the lumen 110 of the sheath 11 and flows into the accommodating mechanism 23. Of course, the negative pressure suction mechanism 21 and the housing mechanism 23 may be replaced by a vacuum container to perform the functions of negative pressure and waste liquid collection.

Referring to fig. 9 and 10, the interventional vascular reduction device according to the second embodiment of the present application differs from the interventional vascular reduction device of the first embodiment in that the propeller 33 comprises helical blades 33a surrounding the mandrel 31. The paddle 33a is a spiral continuous structure that spirals at least one turn around the mandrel 31, and the paddle 33a is shown as making multiple turns around the mandrel 31. Preferably, the maximum thickness of the blade is not more than 10% of the maximum diameter, in this case, in order to reduce the influence of the helical blades 33a on the flexibility of the mandrel 31, a polymer material with 25D-50D hardness is preferred, and the axial length of the blades 33a is set appropriately.

Referring to fig. 11, compared to the interventional vascular reduction device in the first embodiment, the interventional vascular reduction device in accordance with the third embodiment of the present application is different in that the atherectomy assembly further includes a spring tube 35 fixedly sleeved on the mandrel 31; spring tubes 35 are spaced axially a from propeller 33. The spring tube 35 is added to be matched with the propeller 33, so that the stability of the rotating mandrel 31 can be improved in the rotary cutting process while the bolt removing efficiency is ensured.

The spring tube 35 can be fixed on the mandrel 31 by welding or injection molding, the spring tube 35 can be made of metal or high polymer material, the outer diameter of the spring tube 35 is approximately attached to the inner wall of the sheath tube 11, namely, the outer diameter is 90-95% of the inner diameter of the sheath tube 11, and the helical angle of the spring tube 35 is not less than 35 degrees. The spring tube 35 placement area and the blade 332 placement area have no fore-aft order requirements and no length requirements for the spring tube 35 placement area, but a relatively short spring tube 35 may be selected as is typical for cooperation with the propeller 33, e.g., the length of the spring tube 35 may preferably be 5mm-100mm. The lower the bolt arranging efficiency of the arrangement area of the spring tube 35 is compared with that of the propeller 33, the flexibility of the tube body of the sheath tube 11 is reduced, and the rotation stability of the core shaft 31 can be better protected.

Further, the rotary-cut assembly may include a plurality of sets of propellers 33, each set of propellers 33 including a plurality of propellers 33, and one set of propellers 33 being spaced apart from another set of adjacent propellers 33 by spring tubes 35. Wherein the propeller 33 having a significant thrust effect can raise the carrying speed of the fluid in the sheath tube 11; the adherent spring tubes 35 arranged in the intervals ensure the centering and the stability of the central spindle 31 in the arrangement area of the propeller 33 on the premise of not influencing the transportation of the excised tissue, and provide a stable environment for the safe operation of the blades 332.

Specifically, the pitch between the spring tube 35 and the propeller 33 and the pitch between the propeller 33 and the propeller 33 may be independently set, respectively, i.e., the pitches may be non-equidistant. For example, when the device needs to establish a channel by mountain-turning (entering from a femoral artery on one side, ascending through an abdominal aorta and then descending into an iliac artery on the other side), a longer region in the middle of the sheath 11 is in a bent state for a long time, and the region can be designed as a spring tube 35 arrangement region and other regions can be set as a propeller 33 arrangement region according to the general requirements of a user group in the application scene, so that the sheath 11 and the mandrel 31 are better protected, and the occurrence rate of faults is reduced. Similarly, the distribution ratio of the spring tube 35 arrangement area and the blade 332 arrangement area can be adjusted according to different diseases and use scenes, so that the pumping efficiency is improved on the premise of ensuring safety and stability.

It should be understood that the above examples only represent the preferred embodiments of the present invention, and the description thereof is more specific and detailed, but should not be construed as limiting the scope of the present invention; it should be noted that, for those skilled in the art, the above technical features can be freely combined, and 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; therefore, all changes and modifications that come within the meaning and range of equivalency of the claims are to be embraced within their scope.

Claims (10)

1. An interventional vascular reduction device, comprising:

a sheath assembly comprising a sheath having a lumen;

a embolus discharging assembly comprising a negative pressure suction mechanism in communication with the lumen of the sheath;

the rotary cutting assembly comprises a core shaft, a cutting piece and at least one propeller, the core shaft is arranged in the tube cavity along the axial direction, the cutting piece is arranged outside the sheath tube and connected with the far end of the core shaft, and the propeller is fixedly sleeved on the core shaft.

2. The interventional vessel reduction device of claim 1, wherein the propeller comprises a hub fixedly sleeved on the mandrel and at least one blade connected to the hub.

3. The interventional vascular reduction device of claim 1, wherein the rotational atherectomy assembly further comprises a spring tube secured to the mandrel; the spring tubes and the propellers are arranged at intervals along the axial direction.

4. The interventional vessel reduction device of any of claims 1-3, wherein the rotational atherectomy assembly comprises at least one set of propellers, the set of propellers comprising a plurality of propellers spaced apart along the axial direction.

5. The interventional vascular reduction device of claim 4, wherein the propeller comprises a plurality of blades evenly spaced about the mandrel.

6. The interventional vascular reduction device of claim 4, wherein at least one propeller of the set of propellers comprises one blade, the blades of all propellers of the set of propellers being evenly arranged around the mandrel on a projection plane perpendicular to the axial direction.

7. The interventional vascular reduction device of claim 1, wherein the propeller comprises a helical blade surrounding the mandrel.

8. The interventional vascular reduction device of claim 2, wherein the maximum diametric length of the paddle is no greater than 90% of the inner diameter of the lumen and the degree of paddle angle is in the range of 15 ° -25 °.

9. The interventional vascular reduction device of claim 1, wherein the sheath assembly further comprises a base having a central through-hole, the base being fixedly connected to the distal end of the sheath and communicating with the lumen of the sheath through the central through-hole; the cutting member includes link, a plurality of cutting edge, is formed at two adjacent guiding gutter between the cutting edge, the link support lean on the base, and with the dabber drive is connected, the guiding gutter with central through-hole intercommunication, the cutting edge is the free end.

10. The interventional vascular reduction device of claim 1, wherein the rotational atherectomy assembly further comprises a drive motor in driving connection with the proximal end of the mandrel.

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