Shockwave angioplasty device with valve perfusion

Abstract

The present invention discloses a shock wave forming device with valve blood flow perfusion, which relates to the field of medical device technology, including a catheter sheath, a shock wave forming balloon group, a shock wave generating component, a handle and a magnetic flexible mesh opening and closing structure; a guide wire is slidably arranged in the catheter sheath; the shock wave forming balloon group includes a plurality of shock wave balloons, one end of the shock wave balloon is connected to the end of the guide wire through a flexible mesh structure, and the other end is connected to the end of the catheter sheath through a flexible rod structure; the shock wave generating component includes an axial shock wave generating electrode pair and a circumferential shock wave generating electrode pair; the magnetic flexible mesh opening and closing structure is arranged between the end of the guide wire and the flexible mesh structure. The present invention can mechanically prop up or loosen a blood vessel; and through the axial shock wave generating electrode pair and the circumferential shock wave generating electrode pair, occluded plaques can be opened in the forward direction, and shock waves can be emitted in the circumferential direction to lyse or break up calcium deposits; and broken calcified plaques or aortic plaques and thrombi can also be captured.

Description

Technical Field

[0001] The present invention relates to the technical field of medical devices, and in particular to a shock wave shaping device with valve blood perfusion. Background Art

[0002] Vascular stenosis refers to the abnormal lipid metabolism in the human body's arteriovenous, coronary, peripheral, and intracranial blood vessels. The lipids in the blood are deposited on the originally smooth vascular endothelium, gradually accumulating into atherosclerotic lipid plaques. Over time, these plaques increase and even calcify, causing stenosis in the vascular lumen, obstructing blood flow, leading to ischemia of downstream blood vessels and the body, and producing corresponding clinical manifestations. If the stenosis occurs in the coronary arteries, it will cause palpitations, chest pain, dyspnea, and angina pectoris. In severe cases, it can lead to myocardial insufficiency or myocardial necrosis. If it occurs in the periphery, it will cause a decrease in skin epidermal temperature, muscle atrophy, intermittent claudication, and even necrosis or amputation of distal limbs. If it occurs intracranial, it can cause dizziness, syncope, and even brain tissue damage and brain dysfunction.

[0003] Existing angioplasty procedures involve inserting an expandable balloon into the blood vessels. The rapid expansion of the balloon creates mechanical stress that breaks up the calcifications. However, balloon angioplasty is only effective for large, centralized calcifications and cannot treat dispersed calcifications or those that extend deep into the ventricles. Consequently, calcium removal is inefficient and incomplete. Balloon angioplasty is less effective for patients with severe arterial calcification or long stenotic segments.

[0004] Rapid balloon expansion can cause a sudden change in pressure on the blood vessel wall, which can easily damage the blood vessel and even cause thrombosis. In addition, balloon expansion requires very high pressure (sometimes reaching 20 to 30 standard atmospheres, or even 40 standard atmospheres). Such pressures often lead to a significant increase in the probability of rebound stenosis, dissection, perforation, and rupture of the blood vessels. Such surgical events are particularly serious in cases of eccentric calcified lesions because the pressure of the balloon acts on soft tissue without calcification.

[0005] When the patient's intravascular plaque is hard and the stenosis is severe, the balloon may not be able to pass through the calcified area at all, let alone achieve any therapeutic effect. Therefore, a more effective medical device is needed to solve this problem. Summary of the Invention

[0006] In order to solve the above technical problems, the present invention provides a shock wave shaping device with valve blood perfusion, and the specific technical solution is as follows:

[0007] A shock wave shaping device with valve blood perfusion, comprising:

[0008] a catheter sheath, wherein a guide wire is slidably disposed in the catheter sheath;

[0009] A shock wave forming balloon assembly is provided at one end of the catheter sheath, comprising a plurality of shock wave balloons arranged circumferentially along the axis of the catheter sheath, one end of the shock wave balloon being connected to the end of the guide wire via a flexible mesh structure, and the other end being connected to the end of the catheter sheath via a flexible rod structure;

[0010] a shock wave generating assembly, disposed within the shock wave balloon, comprising an axial shock wave generating electrode pair and a circumferential shock wave generating electrode pair;

[0011] a handle provided at the other end of the catheter sheath, the handle being provided with a balloon assembly opening and closing control member, a balloon expansion and contraction control member, and a shock wave generation control member, the balloon assembly opening and closing control member being connected to the guide wire, the balloon expansion and contraction control member being connected to the shock wave balloon, and the shock wave generation control member being connected to the shock wave generation assembly;

[0012] A magnetic flexible mesh opening and closing structure is arranged between the guide wire end and the flexible mesh structure, and is used to control the opening and closing of the flexible mesh structure. The magnetic flexible mesh opening and closing structure includes a magnetic head and an electromagnet. The flexible mesh structure is connected to one end of the guide wire end to form a plurality of magnetic heads. The plurality of magnetic heads have the same polarity, and the guide wire end is provided with the electromagnet.

[0013] Preferably, the shock wave forming balloon assembly further comprises an elastic skeleton, one end of which is connected to the end of the guide wire to form the flexible mesh structure, and the other end of which is connected to the end of the catheter sheath to form the flexible rod structure.

[0014] Preferably, the axial shock wave generating electrode pair comprises:

[0015] A first electrode inner sleeve is sleeved on the elastic frame;

[0016] A first electrode outer sleeve, sleeved on the outer side of the first electrode inner sleeve;

[0017] The first insulating sleeve is sleeved between the first electrode inner sleeve and the first electrode outer sleeve. The first insulating sleeve is retracted inward relative to one end of the first electrode outer sleeve to form an axial shock wave divergence cavity between the end of the first electrode outer sleeve and the first electrode inner sleeve.

[0018] Preferably, the circumferential shock wave generating electrode pair comprises:

[0019] A second electrode inner sleeve, sleeved on the elastic frame;

[0020] A second electrode outer sleeve is sleeved on the outside of the second electrode inner sleeve, and a shock wave diverging hole is provided on the side of the second electrode outer sleeve away from the axis of the catheter sheath;

[0021] The second insulating sleeve is sleeved between the second electrode inner sleeve and the second electrode outer sleeve. The second insulating sleeve is provided with an open groove relative to the shock wave diverging hole. Both ends of the open groove are retracted away from the shock wave diverging hole to form a circumferential shock wave diverging cavity between the shock wave diverging hole and the second electrode inner sleeve.

[0022] Preferably, the shock wave balloon is a compliant balloon, a semi-compliant balloon or a non-compliant balloon.

[0023] Preferably, a sliding sleeve is formed at the end of the flexible rod-shaped structure, and the sliding sleeve is fixedly connected to the end of the catheter sheath and is provided on the guide wire.

[0024] Preferably:

[0025] A catheter is further connected between the shock wave balloon and the catheter sheath, and the catheter is sleeved outside the flexible rod-shaped structure;

[0026] An anti-stress sheath is also provided between the catheter sheath and the handle.

[0027] Preferably:

[0028] The balloon expansion and contraction control member includes a liquid guide tube disposed in the catheter, one end of the liquid guide tube extending into the shock wave balloon, and the other end extending to the outside of the handle and connected to a liquid inlet connector;

[0029] The shock wave generation control component includes a wire arranged in the catheter, one end of the wire is connected to the shock wave generation component, and the other end extends to the outside of the handle and is connected to an electric control connector.

[0030] Preferably, it further comprises a limiting retaining ring arranged at the end of the guide wire, and the magnetic head is provided with a limiting notch matched with the limiting retaining ring at one end adjacent to the shock wave balloon.

[0031] The shock wave shaping device with valve blood perfusion provided by the present invention is configured by slidingly arranging a guidewire within a catheter sheath, and connecting the ends of the guidewire and the catheter sheath to a shock wave balloon via a flexible mesh structure and a flexible rod structure, respectively, so that pulling or pushing the guidewire can move multiple shock wave balloons away from or towards each other, thereby mechanically propping up or loosening the blood vessel; and by arranging an axial shock wave generating electrode pair and a circumferential shock wave generating electrode pair within the shock wave balloon, occluded plaques can be opened in the forward direction, the catheter can smoothly pass through lesions with a high degree of stenosis, and shock waves can be emitted circumferentially to lyse or break up calcium deposits; and multiple shock wave balloons can also be closed to capture broken calcified plaques, aortic plaques, thrombi, etc., providing immediate protection for medical surgery. BRIEF DESCRIPTION OF THE DRAWINGS

[0032] In order to more clearly illustrate the embodiments of the present invention or the technical solutions in the prior art, the following briefly introduces the drawings required for use in the embodiments or the description of the prior art. Obviously, the drawings described below are only some embodiments recorded in the present invention. For ordinary technicians in this field, other drawings can be obtained based on these drawings without paying any creative work.

[0033] Figure 1 A front view of a shock wave shaping device with valve blood perfusion provided in an embodiment of the present invention;

[0034] Figure 2 A three-dimensional diagram of the hidden structure of the shock wave forming balloon assembly provided in an embodiment of the present invention;

[0035] Figure 3 for Figure 2 A partial enlarged view of part A;

[0036] Figure 4 A sectional front view of a shock wave shaping balloon assembly provided in an embodiment of the present invention;

[0037] Figure 5 for Figure 4 A partial enlarged view of part B;

[0038] Figure 6 for Figure 4 A partial enlarged view of part C in the middle;

[0039] Figure 7 for Figure 4 A partial enlarged view of part D in the middle;

[0040] Figure 8 A front cross-sectional view of an open flexible mesh structure in a shock wave forming balloon assembly provided in an embodiment of the present invention.

[0041] The reference numerals are: 1-catheter sheath; 11-guidewire; 12-limiting retaining ring; 2-shock wave forming balloon group; 21-shock wave balloon; 22-flexible mesh structure; 23-flexible rod structure; 231-sliding sleeve; 24-elastic skeleton; 25-catheter; 3-shock wave generating assembly; 31-axial shock wave generating electrode pair; 311-first electrode inner sleeve; 312-first electrode outer sleeve; 313-first insulating sleeve; 314-axial shock wave diverging cavity; 32-circumferential shock wave generating electrode pair; 32 1-Second electrode inner sleeve; 322-Second electrode outer sleeve; 3221-Shock wave divergence hole; 323-Second insulating sleeve; 3231-Opening slot; 324-Circumferential shock wave divergence cavity; 4-Handle; 41-Balloon assembly opening and closing control member; 42-Balloon expansion and contraction control member; 421-Liquid guide tube; 422-Liquid inlet connector; 43-Shock wave generation control member; 431-Electrical control connector; 5-Magnetic flexible mesh opening and closing structure; 51-Magnetic head; 511-Limiting notch; 52-Electromagnet; 6-Anti-stress sheath. DETAILED DESCRIPTION

[0042] In order to enable those skilled in the art to better understand the technical solution of the present invention, the present invention is described in detail below with reference to the accompanying drawings. The description in this part is only exemplary and explanatory and should not have any limiting effect on the scope of protection of the present invention.

[0043] It should be noted that similar reference numerals denote similar items in the following drawings, and therefore, once an item is defined in one drawing, it does not need to be further defined or explained in the subsequent drawings.

[0044] It should be noted that the terms "center," "upper," "lower," "left," "right," "vertical," "horizontal," "inner," and "outer" and the like indicate positions or locations based on the positions shown in the accompanying drawings, or the positions or locations in which the inventive product is typically placed when in use. These terms are intended solely to facilitate and simplify the description of the present invention and are not intended to indicate or imply that the devices or components referred to must have a specific orientation, be constructed, or operate in a specific orientation. Therefore, they should not be construed as limitations on the present invention. Furthermore, the terms "first," "second," and the like are used solely for distinction and should not be construed as indicating or implying relative importance.

[0045] Furthermore, terms such as "horizontal," "vertical," and "overhanging" do not necessarily imply that a component must be absolutely horizontal or overhanging, but rather that it can be slightly tilted. For example, "horizontal" simply means that its direction is more horizontal than "vertical," and does not mean that the structure must be completely horizontal, but rather that it can be slightly tilted.

[0046] In the description of the present invention, it should also be noted that, unless otherwise expressly specified or limited, the terms "disposed," "installed," "connected," and "connected" should be understood in a broad sense. For example, they may refer to fixed connections, detachable connections, or integral connections; they may refer to mechanical connections or electrical connections; they may refer to direct connections or indirect connections through an intermediate medium; and they may refer to internal communication between two components. Those skilled in the art will understand the specific meanings of the above terms in the present invention based on the specific circumstances.

[0047] See Figures 1 to 8 This embodiment provides a shock wave shaping device with valve blood perfusion, including a catheter sheath 1, a shock wave shaping balloon group 2, a shock wave generating component 3, a handle 4 and a magnetic flexible mesh opening and closing structure 5.

[0048] A guide wire 11 is slidably disposed in the catheter sheath 1 .

[0049] The shock wave forming balloon group 2 is arranged at one end of the catheter sheath 1, including multiple shock wave balloons 21 arranged along the axis and circumference of the catheter sheath 1. One end of the shock wave balloon 21 is connected to the end of the guide wire 11 through a flexible mesh structure 22, and the other end is connected to the end of the catheter sheath 1 through a flexible rod structure 23.

[0050] The shock wave generating assembly 3 is disposed in the shock wave balloon 21 and includes an axial shock wave generating electrode pair 31 and a circumferential shock wave generating electrode pair 32 .

[0051] The handle 4 is provided at the other end of the catheter sheath 1, and is provided with a balloon group opening and closing control component 41, a balloon expansion and contraction control component 42 and a shock wave generation control component 43. The balloon group opening and closing control component 41 is connected to the guide wire 11, the balloon expansion and contraction control component 42 is connected to the shock wave balloon 21, and the shock wave generation control component 43 is connected to the shock wave generation component 3.

[0052] The magnetic flexible mesh opening and closing structure 5 is arranged between the end of the guide wire 11 and the flexible mesh structure 22, and is used to control the opening and closing of the flexible mesh structure 22. The magnetic flexible mesh opening and closing structure 5 includes a magnetic head 51 and an electromagnet 52. The flexible mesh structure 22 is connected to one end of the guide wire 11 to form multiple magnetic heads 51. The multiple magnetic heads 51 have the same polarity, and an electromagnet 52 is provided at the end of the guide wire 11.

[0053] Among them, the number of shock wave balloons 21 can be 3, 4 or 5, and the balloon group opening and closing control component 41 can be used to control the guide wire 11 to slide in the catheter sheath 1. When the guide wire 11 is pulled, the guide wire 11 slides toward the proximal end of the catheter sheath 1, and the end of the guide wire 11 and the end of the catheter sheath 1 approach each other, so that the flexible mesh structure 22 and the flexible rod-shaped structure 23 push the shock wave balloon 21 outward, so that the shock wave forming balloon group 2 opens, so that the shock wave balloon 21 contacts the inner wall of the blood vessel. At this time, liquid is injected into the shock wave balloon 21 through the balloon expansion and contraction control component 42, and a certain pressure is applied to fill the shock wave balloon 21. At least a portion of the outer surface of the balloon contacts the blood vessel wall and the vascular calcification lesion area, and then the shock wave generation control component 43 is used to control the shock wave generation component 3 to generate shock waves. The shock wave generated by the electrode pair is radially transmitted to the balloon surface through the liquid inside the balloon, and then transmitted to the calcification lesion through the surface of the balloon. When the shock wave is transmitted to the calcified lesion, the compressive stress of the shock wave will cause the calcified tissue inside the calcified lesion to soften, lyse or break the calcium deposits. Shock waves of appropriate intensity can satisfy the need to destroy the calcified tissue without placing additional burden on the soft tissue surrounding the calcified tissue. The axial shock wave generating electrode pair 31 can generate shock waves along the axial direction of the guidewire 11, which can open the occluded plaque forward, allowing the catheter to pass smoothly through the lesion with a higher degree of stenosis; the circumferential shock wave generating electrode pair 32 can generate shock waves along the radial direction of the guidewire 11, lyse or break the calcium deposits. An axial shock wave generating electrode pair 31 and multiple circumferential shock wave generating electrode pairs 32 can be arranged side by side in a shock wave balloon 21 to make it easier to rupture the calcified plaque along the length of the blood vessel. The operator can select a certain electrode to send the shock wave, or can stimulate the electrode pairs in sequence, or can stimulate all the electrode pairs at the same time, which greatly facilitates the operator's operation during the operation. After the calcified plaque ruptures, the shockwave balloon 21 can be controlled to shrink by the balloon expansion and contraction control member 42, pushing the guidewire 11 so that the end of the guidewire 11 and the end of the catheter sheath 1 are separated from each other, thereby causing the flexible mesh structure 22 and the flexible rod structure 23 to pull the shockwave balloon 21 inward, closing the shockwave forming balloon assembly 2, thereby capturing the broken calcified plaque or aortic plaque and thrombus. Because the opening and closing of the shockwave forming balloon assembly 2 is achieved by the flexible mesh structure 22 and the flexible rod structure 23 pushing or pulling the shockwave balloon 21, when the blood vessel is propped up during the valvular plastic expansion surgery, the blood flow to the valve will not be blocked.

[0054] The operator can adjust the polarity of the electromagnet 52 through the control device. When the catheter is inserted into the blood vessel, the polarity of the electromagnet 52 is opposite to that of the magnetic head 51, so that the magnetic head 51 is firmly adsorbed on the electromagnet 52. When it is necessary to capture calcified plaques or aortic plaques and thrombi, the polarity of the electromagnet 52 can be adjusted to make the polarity of the electromagnet 52 the same as that of the magnetic head 51, so that the magnetic head 51 is moved away from the electromagnet 52, and the flexible mesh structure 22 is opened. Figure 8 As shown, it is convenient to capture calcified plaques or aortic plaques and thrombi. After the capture is completed, the polarity of the electromagnet 52 can be adjusted again so that the polarity of the electromagnet 52 is opposite to the polarity of the magnetic head 51. Since the flexible mesh structure 22 itself has elasticity, it can force the magnetic head 51 to be adsorbed in the direction close to the electromagnet 52, thereby preventing the calcified plaques or aortic plaques and thrombi from being detached after capture.

[0055] The shock wave shaping device with valve blood flow perfusion provided in this embodiment is configured by slidingly setting a guidewire 11 within a catheter sheath 1, and connecting the ends of the guidewire 11 and the ends of the catheter sheath 1 to a shock wave balloon 21 via a flexible mesh structure 22 and a flexible rod structure 23, respectively. Pulling or pushing the guidewire 11 can move the multiple shock wave balloons 21 away from or closer to each other, thereby mechanically propping up or loosening the blood vessel. Furthermore, by setting an axial shock wave generating electrode pair 31 and a circumferential shock wave generating electrode pair 32 within the shock wave balloon 21, occluded plaques can be opened in the forward direction, the catheter can smoothly pass through the lesion site with a high degree of stenosis, and shock waves can be emitted circumferentially to lyse or break up calcium deposits. Furthermore, the multiple shock wave balloons 21 can be closed to capture broken calcified plaques, aortic plaques, and thrombi, thereby providing immediate protection for medical surgery.

[0056] Further, see Figure 2 The shock wave forming balloon assembly 2 further includes an elastic skeleton 24 , one end of which is connected to the end of the guide wire 11 to form a flexible mesh structure 22 , and the other end is connected to the end of the catheter sheath 1 to form a flexible rod-shaped structure 23 .

[0057] Specifically, the elastic skeleton 24 can be a stone retrieval basket, the grid portion of the stone retrieval basket forms a flexible mesh structure 22, and the edge of the stone retrieval basket forms multiple strips extending toward the catheter sheath 1 to form a flexible rod-shaped structure 23.

[0058] Further, see Figure 5 The axial shock wave generating electrode pair 31 includes a first electrode inner sleeve 311 , a first electrode outer sleeve 312 and a first insulating sleeve 313 .

[0059] The first electrode inner sleeve 311 is sleeved on the elastic skeleton 24 .

[0060] The first electrode outer sleeve 312 is sleeved on the outside of the first electrode inner sleeve 311 .

[0061] The first insulating sleeve 313 is sleeved between the first electrode inner sleeve 311 and the first electrode outer sleeve 312. The first insulating sleeve 313 is retracted inward relative to one end of the first electrode outer sleeve 312 to form an axial shock wave divergence cavity 314 between the end of the first electrode outer sleeve 312 and the first electrode inner sleeve 311.

[0062] Specifically, the first insulating sleeve 313 separates the first electrode inner sleeve 311 from the first electrode outer sleeve 312, allowing the liquid in the shock wave balloon 21 to flow into the gap between the first electrode inner sleeve 311 and the first electrode outer sleeve 312. The electrode pair applies a transient high voltage to generate an arc, which generates a shock wave accompanied by the expansion and collapse of the bubble generated by the arc. Under the guidance of the axial shock wave divergence cavity 314, the shock wave diverges axially toward the guide wire 11. The principle of shock wave generation is the electrohydraulic effect. Generating shock waves through the electrohydraulic effect is a conventional technical means in the field and is therefore not described in detail in this embodiment.

[0063] For further information, please see Figure 5 The circumferential shock wave generating electrode pair 32 includes a second electrode inner sleeve 321 , a second electrode outer sleeve 322 and a second insulating sleeve 323 .

[0064] The second electrode inner sleeve 321 is sleeved on the elastic frame 24 .

[0065] The second electrode outer sleeve 322 is sleeved on the outside of the second electrode inner sleeve 321 . A shock wave diverging hole 3221 is provided on the side of the second electrode outer sleeve 322 away from the axis of the catheter sheath 1 .

[0066] The second insulating sleeve 323 is sleeved between the second electrode inner sleeve 321 and the second electrode outer sleeve 322. An open groove 3231 is provided on the second insulating sleeve 323 relative to the shock wave diverging hole 3221. Both ends of the open groove 3231 are retracted away from the shock wave diverging hole 3221 to form a circumferential shock wave diverging cavity 324 between the shock wave diverging hole 3221 and the second electrode inner sleeve 321.

[0067] Specifically, the second insulating sleeve 323 separates the second electrode inner sleeve 321 and the second electrode outer sleeve 322, so that a gap is formed on the second electrode outer sleeve 322 relative to the inner wall of the shock wave divergence hole 3221, the inner wall of the opening groove 3231 and the surface of the first electrode inner sleeve 311. The liquid in the shock wave balloon 21 can flow into the gap, and the electrode pair applies an instantaneous high voltage to generate an arc. The bubble generated by the arc expands and collapses, and shock waves are generated, which diverge radially along the guide wire 11 under the guidance of the circumferential shock wave divergence cavity 324 and the shock wave divergence hole 3221.

[0068] The first electrode inner sleeve 311 and the second electrode inner sleeve 321 can be an integrated electrode sheet, and the axial shock wave generating electrode pair 31 and the circumferential shock wave generating electrode pair 32 can be integrated into a single electrode pair, thereby reducing the layout volume. A limiting ring can also be provided on the elastic skeleton 24, abutting the inner sidewalls of the first electrode inner sleeve 311 and / or the second electrode inner sleeve 321 to limit the displacement of the electrode inner sleeves.

[0069] Furthermore, the shock wave balloon 21 can be a compliant, semi-compliant, or non-compliant balloon. Compliant balloons offer excellent expansion, expansion, and insulation properties. Compliant balloons do not require folding, significantly reducing the difficulty of catheter distal manipulation. Semi-compliant or non-compliant balloons can apply high pressure (10-30 ATM), expanding the area of vascular calcification.

[0070] Furthermore, a sliding sleeve 231 is formed at the end of the flexible rod-shaped structure 23, and the sliding sleeve 231 is fixedly connected to the end of the catheter sheath 1 and is provided on the guide wire 11. This makes it easier for the guide wire 11 to slide in the catheter sheath 1.

[0071] Furthermore, a catheter 25 is connected between the shock wave balloon 21 and the catheter sheath 1 . The catheter 25 is sleeved outside the flexible rod-shaped structure 23 to protect the components on the flexible rod-shaped structure 23 .

[0072] An anti-stress sheath 6 is further provided between the catheter sheath 1 and the handle 4 to prevent damage to the connection between the catheter sheath 1 and the handle 4 .

[0073] Furthermore, the balloon expansion and contraction control member 42 includes a liquid guide tube 421 disposed in the catheter 25 . One end of the liquid guide tube 421 extends into the shock wave balloon 21 , and the other end extends to the outside of the handle 4 and is connected to a liquid inlet connector 422 .

[0074] The shock wave generation control component 43 includes a wire disposed in the catheter 25 , one end of the wire is connected to the shock wave generation assembly 3 , and the other end extends to the outside of the handle 4 and is connected to an electric control connector 431 .

[0075] Further, see Figure 7 .

[0076] Furthermore, a retaining ring 12 is provided at the end of the guidewire 11, and a retaining notch 511 is provided at the end of the magnetic head 51 adjacent to the shock wave balloon 21, which cooperates with the retaining ring 12. When the magnetic head 51 is attracted to the electromagnet 52, the retaining notch 511 can fit into the retaining ring 12. The cooperation between the retaining ring 12 and the retaining notch 511 can prevent the magnetic head 51 from shifting at the end of the guidewire 11.

[0077] Principle description:

[0078] The number of shock wave balloons 21 can be 3, 4 or 5. The balloon group opening and closing control component 41 can be used to control the guide wire 11 to slide in the catheter sheath 1. When the guide wire 11 is pulled, the guide wire 11 slides toward the proximal end of the catheter sheath 1, and the end of the guide wire 11 and the end of the catheter sheath 1 approach each other, so that the flexible mesh structure 22 and the flexible rod-shaped structure 23 push the shock wave balloon 21 outward, causing the shock wave forming balloon group 2 to open, so that the shock wave balloon 21 contacts the inner wall of the blood vessel. At this time, liquid is injected into the shock wave balloon 21 through the balloon expansion and contraction control component 42, and a certain pressure is applied to fill the shock wave balloon 21. At least a portion of the outer surface of the balloon contacts the blood vessel wall and the vascular calcification lesion area, and then the shock wave generation control component 43 is used to control the shock wave generation component 3 to generate shock waves. The shock wave generated by the electrode pair is radially transmitted to the balloon surface through the liquid inside the balloon, and then transmitted to the calcification lesion through the surface of the balloon. When the shock wave is transmitted to the calcified lesion, the compressive stress of the shock wave will cause the calcified tissue inside the calcified lesion to soften, lyse or break the calcium deposits. Shock waves of appropriate intensity can satisfy the need to destroy the calcified tissue without placing additional burden on the soft tissue surrounding the calcified tissue. The axial shock wave generating electrode pair 31 can generate shock waves along the axial direction of the guidewire 11, which can open the occluded plaque forward, allowing the catheter to pass smoothly through the lesion with a higher degree of stenosis; the circumferential shock wave generating electrode pair 32 can generate shock waves along the radial direction of the guidewire 11, lyse or break the calcium deposits. An axial shock wave generating electrode pair 31 and multiple circumferential shock wave generating electrode pairs 32 can be arranged side by side in a shock wave balloon 21 to make it easier to rupture the calcified plaque along the length of the blood vessel. The operator can select a certain electrode to send the shock wave, or can stimulate the electrode pairs in sequence, or can stimulate all the electrode pairs at the same time, which greatly facilitates the operator's operation during the operation. After the calcified plaque ruptures, the shockwave balloon 21 can be controlled to shrink by the balloon expansion and contraction control member 42, pushing the guidewire 11 so that the end of the guidewire 11 and the end of the catheter sheath 1 are separated from each other, thereby causing the flexible mesh structure 22 and the flexible rod structure 23 to pull the shockwave balloon 21 inward, closing the shockwave forming balloon assembly 2, thereby capturing the broken calcified plaque or aortic plaque and thrombus. Because the opening and closing of the shockwave forming balloon assembly 2 is achieved by the flexible mesh structure 22 and the flexible rod structure 23 pushing or pulling the shockwave balloon 21, when the blood vessel is propped up during the valvular plastic expansion surgery, the blood flow to the valve will not be blocked.

[0079] It should be noted that, in this article, the terms "comprises", "includes" or any other variations thereof are intended to cover non-exclusive inclusion, so that a process, method, article or apparatus that includes a series of elements includes not only those elements, but also includes other elements not explicitly listed, or also includes elements that are inherent to such process, method, article or apparatus.

[0080] This article uses specific examples to illustrate the principles and implementation methods of the present invention. The description of the above embodiments is only used to help understand the method of the present invention and its core ideas. The above is only a preferred implementation method of the present invention. It should be pointed out that due to the limitations of textual expression, there are objectively infinite specific structures. For ordinary technicians in this technical field, without departing from the principles of the present invention, they can make several improvements, modifications or changes, and can also combine the above technical features in an appropriate manner; these improvements, modifications, changes or combinations, or the direct application of the inventive concept and technical solution to other occasions without improvement, should be regarded as the scope of protection of the present invention.

Claims

1. A shock wave shaping device with valve blood perfusion, characterized in that: include: A catheter sheath (1), wherein a guide wire (11) is slidably arranged inside the catheter sheath (1); A shock wave forming balloon group (2) is provided at one end of the catheter sheath (1), comprising a plurality of shock wave balloons (21) arranged along the axis of the catheter sheath (1) in a circumferential direction, wherein one end of the shock wave balloon (21) is connected to the end of the guide wire (11) via a flexible mesh structure (22), and the other end is connected to the end of the catheter sheath (1) via a flexible rod structure (23); A shock wave generating assembly (3) is provided in the shock wave balloon (21), comprising an axial shock wave generating electrode pair (31) and a circumferential shock wave generating electrode pair (32); A handle (4) is provided at the other end of the catheter sheath (1), and a balloon assembly opening and closing control component (41), a balloon expansion and contraction control component (42), and a shock wave generation control component (43) are provided on the handle (4), wherein the balloon assembly opening and closing control component (41) is connected to the guide wire (11), the balloon expansion and contraction control component (42) is connected to the shock wave balloon (21), and the shock wave generation control component (43) is connected to the shock wave generation component (3); A magnetically attracted flexible mesh opening and closing structure (5) is provided between the end of the guide wire (11) and the flexible mesh structure (22) and is used to control the opening and closing of the flexible mesh structure (22). The magnetically attracted flexible mesh opening and closing structure (5) comprises a magnetic head (51) and an electromagnet (52). The flexible mesh structure (22) is connected to one end of the guide wire (11) to form a plurality of magnetic heads (51). The plurality of magnetic heads (51) have the same polarity. The electromagnet (52) is provided at the end of the guide wire (11).

2. The shock wave shaping device with valve blood perfusion according to claim 1, characterized in that: The shock wave forming balloon assembly (2) further comprises an elastic skeleton (24), one end of which is connected to the end of the guide wire (11) to form the flexible mesh structure (22), and the other end of which is connected to the end of the catheter sheath (1) to form the flexible rod structure (23).

3. The shock wave shaping device with valve blood perfusion according to claim 2, characterized in that: The axial shock wave generating electrode pair (31) comprises: A first electrode inner sleeve (311) is sleeved on the elastic skeleton (24); A first electrode outer sleeve (312) is sleeved on the outside of the first electrode inner sleeve (311); The first insulating sleeve (313) is sleeved between the first electrode inner sleeve (311) and the first electrode outer sleeve (312), and one end of the first insulating sleeve (313) is retracted inward relative to the end of the first electrode outer sleeve (312) to form an axial shock wave divergence cavity (314) between the end of the first electrode outer sleeve (312) and the first electrode inner sleeve (311).

4. The shock wave shaping device with valve blood perfusion according to claim 2, characterized in that: The circumferential shock wave generating electrode pair (32) comprises: A second electrode inner sleeve (321) is sleeved on the elastic skeleton (24); A second electrode outer sleeve (322) is sleeved on the outside of the second electrode inner sleeve (321), and a shock wave diverging hole (3221) is provided on the second electrode outer sleeve (322) on a side away from the axis of the catheter sheath (1); The second insulating sleeve (323) is sleeved between the second electrode inner sleeve (321) and the second electrode outer sleeve (322); an opening groove (3231) is provided on the second insulating sleeve (323) at a position relative to the shock wave diverging hole (3221); both ends of the opening groove (3231) are retracted in a direction away from the shock wave diverging hole (3221), so that a circumferential shock wave diverging cavity (324) is formed between the shock wave diverging hole (3221) and the second electrode inner sleeve (321).

5. The shock wave shaping device with valve blood perfusion according to claim 1, characterized in that: The shock wave balloon (21) is a compliant balloon, a semi-compliant balloon or a non-compliant balloon.

6. The shock wave shaping device with valve blood perfusion according to claim 2, characterized in that: A sliding sleeve (231) is formed at the end of the flexible rod-shaped structure (23); the sliding sleeve (231) is fixedly connected to the end of the catheter sheath (1) and is arranged on the guide wire (11).

7. The shock wave shaping device with valve blood perfusion according to any one of claims 1 to 6, characterized in that: A catheter (25) is further connected between the shock wave balloon (21) and the catheter sheath (1), and the catheter (25) is sleeved outside the flexible rod-shaped structure (23); An anti-stress sheath (6) is further provided between the catheter sheath (1) and the handle (4).

8. The shock wave shaping device with valve blood perfusion according to claim 7, characterized in that: The balloon expansion and contraction control member (42) comprises a liquid guide tube (421) disposed in the catheter (25), one end of the liquid guide tube (421) extending into the shock wave balloon (21), and the other end extending to the outside of the handle (4) and connected to a liquid inlet connector (422); The shock wave generation control component (43) comprises a wire disposed in the catheter (25), one end of the wire being connected to the shock wave generation assembly (3), and the other end extending to the outside of the handle (4) and being connected to an electric control connector (431).

9. The shock wave shaping device with valve blood perfusion according to claim 1, characterized in that: It also includes a limiting retaining ring (12) arranged at the end of the guide wire (11), and a limiting notch (511) that matches the limiting retaining ring (12) is provided at one end of the magnetic head (51) adjacent to the shock wave balloon (21).

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