Adjustable bendable microcatheter for neurointervention

Abstract

The application discloses a kind of adjustable bending microcatheter for nerve intervention, including main catheter, traction assembly and handle;Main catheter has distal end and proximal end, is sequentially provided with bending section, support section and twist control section;Bending section both ends are respectively provided with first developing ring and second developing ring, bending section can be bent under the traction of traction assembly;Twist control section includes hypotube layer, hypotube layer is the metal tube layer with a plurality of cutting openings arranged on the surface spiral;The inner wall of the opposite two sides of main catheter is provided with the passage for traction assembly to pass through;Traction assembly is arranged in the passage, one end of traction assembly is fixed with first developing ring, the other end is connected with handle;Handle is connected with the proximal end of main catheter, for controlling the bending of bending section by traction assembly and controlling the swing of bending section by transmitting torque to twist control section.The application is convenient for doctor to control the multi-angle deflection of microcatheter distal end in patient's body by external operation, with the characteristics of simple operation and accurate control.

Description

Technical Field

[0001] This invention relates to the field of medical device technology, and in particular to an adjustable bendable microcatheter for neurointervention. Background Technology

[0002] Since the advent of hand-brain angiography in 1927, the treatment of various head and neck diseases has undergone a revolutionary change with the intervention of endovascular surgery. Treatments for aneurysms, arteriosclerosis, stroke, and other conditions involve inserting a catheter into the vascular system through a small incision in the skin. This catheter can reach the pathological areas of the neurovascular system, and other medical devices or therapeutic drugs can be delivered through the catheter's lumen for targeted treatment. Through these minimally invasive procedures, patients can benefit from faster and more effective recovery times and less discomfort.

[0003] However, for interventional physicians, the following problems with current microcatheter products used in interventional procedures urgently need to be addressed:

[0004] (1) Interventional physicians cannot directly observe the treatment site and can only be guided by fluoroscopic images, which may lead to a lack of coordination between vision and actual operation.

[0005] (2) The degree of freedom and feedback of catheter insertion instruments are limited. When the traditional catheter used for neurovascular surgery is in the patient’s body, the control of the tip of the interventional instrument is limited. When guided in the vascular system, the tip of the traditional catheter is generally fixed and has an unchangeable curvature, making it difficult to select branches in vascular networks with different curvatures. At this time, it is necessary to remove or replace the catheter, which increases the operation time and the difficulty of the doctor’s operation.

[0006] (3) For the treatment of intracranial aneurysms, the tip of the interventional device (usually a microcatheter) needs to be pre-shaped to reach the target position and deliver the coil into the aneurysm. However, the pre-shaping of the microcatheter increases the interventional procedure time and the difficulty of the doctor's operation. Sometimes, it may be necessary to perform multiple shaping operations to reach the target position. The control of these catheters is highly dependent on the interventional physician's operating skills and requires a very high level of operation.

[0007] Therefore, it is crucial to introduce new, more intuitive, and more effective microcatheter control methods. There is an urgent need for a tip-operated microcatheter that allows interventional physicians to control the distal end's deflection angle within the patient's body via external manipulation, providing more precise control and resolving the issue of frequent catheter changes and reshaping during procedures. Summary of the Invention

[0008] To overcome the shortcomings of existing technologies, this invention provides an adjustable bendable microcatheter for neurointervention, which allows doctors to control the distal end of the microcatheter to deflect at multiple angles within the patient's body through external manipulation. It features simple operation and precise control.

[0009] The present invention provides an adjustable bendable microcatheter for neurointervention, comprising a main guide tube, a traction component and a handle;

[0010] The main tube has a distal end and a proximal end. From the distal end to the proximal end, the main tube is sequentially provided with a bending section, a support section, and a torsion control section. The bending section has a first developing ring and a second developing ring at each end, with the first developing ring positioned closer to the distal end and the second developing ring positioned closer to the proximal end. The bending section can be bent under the pull of the traction assembly. The support section provides primary support. The torsion control section includes a sodium hydroxide tube layer, which is a metal tube layer with a plurality of spirally arranged cuts on its surface. The inner walls of the opposite sides of the main tube are provided with channels through which the traction assembly can pass.

[0011] The traction component is inserted into the channel, with one end of the traction component fixed to the first developing ring and the other end extending out from the end of the channel and connected to the handle;

[0012] The handle is connected to the proximal end of the main tube and is used to control the bending of the bending section through the traction assembly and to control the oscillation of the bending section by transmitting torque to the torque control section.

[0013] In a preferred embodiment, the cut is a hexagonal slit with a width of 0.03-0.05 mm.

[0014] In a preferred embodiment, the cut density decreases from the proximal end to the distal end; the distance between two adjacent cuts near the proximal end is 0.13 mm.

[0015] In a preferred embodiment, the bending section further includes a first inner tube layer and a first outer tube layer, with a plurality of bending joints provided between the first inner tube layer and the first outer tube layer. The bending joints have through holes formed on opposite sides for the traction component to pass through. The bending is achieved by the density difference between the bending joints on opposite sides of the bending section caused by the traction component.

[0016] In a preferred embodiment, the support section includes a second inner tube layer and a second outer tube layer, with a first spring layer and a second spring layer disposed between the second inner tube layer and the second outer tube layer. Both the first spring layer and the second spring layer are made of woven or wound metal wires. The channel for the traction assembly to pass through is disposed between the first spring layer and the second spring layer.

[0017] In a preferred embodiment, the handle is connected to the torque control section via a stress-relieving tube;

[0018] The handle includes a housing assembly and a bending adjustment structure. The bending adjustment structure is disposed inside the housing assembly and is connected to the traction assembly. It is used to control the curvature of the bending section by pulling the traction assembly.

[0019] In a preferred embodiment, the housing assembly has an internal mounting cavity, one end of the housing assembly is connected to the main guide tube, the other end is provided with a detachable cap, and the side of the housing assembly is provided with an expansion window.

[0020] In a preferred embodiment, the housing assembly has a first control port and a second control port on opposite sides; the inner sides of the first control port and the second control port form an annular sliding groove; the axis of the annular sliding groove is consistent with the length direction of the housing assembly.

[0021] In a preferred embodiment, the bending adjustment structure is disposed within the mounting cavity. The bending adjustment structure includes a drive structure, a transmission structure, and a winding wheel. The drive structure includes a dial wheel and a transmission wheel, with an internal gear ring formed within the dial wheel that meshes with the transmission wheel. The dial wheel is disposed within the annular sliding groove, and its outer circumferential surface protrudes from the first control port and the second control port. The drive structure is linked to the winding wheel via the transmission structure. The winding wheel has a winding groove formed circumferentially, and the winding groove is connected to the traction assembly.

[0022] The dial is rotated by the first control port and / or the second control port, which drives the transmission wheel to rotate. The transmission wheel transmits torque to the winding wheel, thereby causing the winding wheel to rotate and pulling the traction wire, thus controlling the curvature of the bending section.

[0023] In a preferred embodiment, the transmission structure includes a drive shaft and a set of meshing worm gears, the worm gears being connected to the drive wheel via the drive shaft; the turbine is rotatably connected within the mounting cavity, and the end of the turbine is connected to the worm wheel.

[0024] Compared with the prior art, the beneficial effects of the present invention are as follows:

[0025] 1. The adjustable bendable microcatheter for neurointervention of the present invention has an adjustable bend section set at the distal end of the main tube, and the curvature of the adjustable bend section is controlled by the handle through the traction component, so that it can bend the tip of the catheter for overselection, avoiding the doctor from overselecting the target position by using different other interventional instruments during the operation, thereby improving the efficiency and effect of the operation.

[0026] 2. The adjustable microcatheter for neurointervention of the present invention significantly improves the catheter's maneuverability and torsional control by setting a thiopancreatography (THB) layer at the proximal end, achieving high-efficiency torque transmission and thus controlling the degree of oscillation of the adjustable segment. Under the precise control of the handle, combined with the control of the degree of bending of the adjustable segment, it achieves all-round precise control of the distal end. It has greater advantages, especially for situations requiring multi-angle, high-precision, and high-frequency control. It increases the angle when releasing the coil, reduces the difficulty of releasing the coil during surgery, and allows the doctor to remotely operate through the handle during the operation to achieve the appropriate position to complete the release and delivery of other instruments and drugs, improving the efficiency and effectiveness of the operation.

[0027] 3. The adjustable microcatheter for neurointervention of the present invention, by setting a first contrast ring and a second contrast ring in the bending section respectively, has a double contrast ring structure that makes it easier for doctors to determine the location during the operation with the support of a computer-controlled digital subtraction angiography (DSA) system, thus facilitating the surgical procedure. Attached Figure Description

[0028] Figure 1 This is a schematic diagram showing the usage of the adjustable bendable microcatheter for neurointervention according to the present invention.

[0029] Figure 2 This is a schematic diagram of the adjustable bendable microcatheter for neurointervention of the present invention;

[0030] Figure 3 This is a cross-sectional view of the support segment of the adjustable bendable microcatheter for neurointervention of the present invention.

[0031] Figure 4 This is a cross-sectional view of the support segment of an adjustable bendable microcatheter for neurointervention, according to another embodiment of the present invention.

[0032] Figure 5 This is a schematic diagram of the thiopancreatic tube layer of the adjustable bendable microcatheter for neurointervention of the present invention;

[0033] Figure 6 This is a schematic diagram of the incision structure for nerve intervention according to the present invention;

[0034] Figure 7 This is a schematic diagram of the handle of the adjustable bendable microcatheter for neurointervention of the present invention.

[0035] Figure 8 This is a schematic diagram of the internal structure of the handle of the adjustable bendable microcatheter for neurointervention of the present invention.

[0036] Figure 9This is a cross-sectional view of the handle of the adjustable bendable microcatheter for neurointervention of the present invention.

[0037] In the diagram: 100, main tube; 110, bending section; 111, first developing ring; 112, second developing ring; 120, support section; 121, second inner tube layer; 122, second outer tube layer; 123, first spring layer; 124, second spring layer; 130, torsion control section; 131, sodium hypochlorite tube layer; 132, cutting opening; 200, traction assembly; 210, traction wire; 220, covering tube; 300, handle; 310, housing assembly; 311, cap; 312, expansion window; 313, first control port; 314, second control port; 315, annular sliding groove; 320, bending structure; 321, dial wheel; 322, transmission wheel; 323, turbine; 324, worm gear; 325, transmission shaft; 326, winding wheel. Detailed Implementation

[0038] The invention will now be further described with reference to the accompanying drawings and specific embodiments. It should be noted that, without conflict, the various embodiments or technical features described below can be arbitrarily combined to form new embodiments. Unless otherwise specified, the materials and equipment used in this embodiment are commercially available. Examples of the embodiments are shown in the accompanying drawings, wherein the same or similar reference numerals denote the same or similar elements or elements having the same or similar functions throughout. The embodiments described below with reference to the accompanying drawings are exemplary and are only used to explain this application, and should not be construed as limiting this application.

[0039] In the description of this application, it should be understood that the terms "upper," "lower," "front," "rear," "vertical," "horizontal," "top," "bottom," "inner," and "outer," etc., indicate the orientation or positional relationship based on the orientation or positional relationship shown in the accompanying drawings, and are only for the convenience of describing this application and simplifying the description, and do not indicate or imply that the device or element referred to must have a specific orientation, or be constructed and operated in a specific orientation, and therefore should not be construed as a limitation on this application. In the description of this application, "a plurality of" means two or more, unless otherwise precisely specified.

[0040] In the description of this application, it should be noted that, unless otherwise expressly specified and limited, the terms "connected," "linked," and "connected" should be interpreted broadly. For example, they can refer to a fixed connection, a connection through an intermediary, or a connection within two elements or an interaction between two elements. Those skilled in the art can understand the specific meaning of the above terms in this application according to the specific circumstances.

[0041] The terms "first," "second," etc., in the specification, claims, and accompanying drawings of this application are used to distinguish similar objects and are not necessarily used to describe a specific order or sequence. Furthermore, the terms "comprising" and "having," and any variations thereof, are intended to cover non-exclusive inclusion; for example, a process, method, system, product, or apparatus that comprises a series of steps or units is not necessarily limited to those steps or units explicitly listed, but may include other steps or units not explicitly listed or inherent to such process, method, product, or apparatus.

[0042] Please refer to Figure 1-9 As shown, this embodiment provides an adjustable bendable microcatheter for neurointervention. The overall effective length of the adjustable bendable microcatheter in this embodiment is preferably 130-160cm, including a main tube 100, a traction component 200 and a handle 300.

[0043] The main tube 100 is a slender tubular structure with an overall length preferably of 110cm-125cm, accounting for about 2 / 3-3 / 4 of the total effective length. The main tube 100 has a distal end and a proximal end, both of which have flat openings. The proximal end is used to connect with the handle 300. The inner diameter of the distal end is preferably 0.43mm-0.54mm, and the outer diameter of the main tube 100 is 0.70mm-0.80mm.

[0044] The main tube 100 is provided with a bending section 110, a support section 120 and a torsion control section 130 in sequence from the distal end to the proximal end; the bending section 110 is provided with a first imaging ring 111 and a second imaging ring 112 at its two ends respectively. The first imaging ring 111 is located near the distal end of the bending section 110, that is, the first imaging ring 111 is located at the distal end of the main tube 100, and the second imaging ring 112 is located near the proximal end of the bending section 110. The structure of the double imaging rings can make it easier for doctors to determine the position during the operation and facilitate the surgical operation.

[0045] The bending section 110 can be bent under the pull of the traction assembly 200; specifically, the bending section 110 includes a first inner tube layer and a first outer tube layer. A plurality of bending joints are provided between the first inner tube layer and the first outer tube layer, and through holes for the traction assembly 200 to pass through are formed on opposite sides of each bending joint; bending is achieved by creating a density difference between the bending joints on opposite sides of the bending section 110 through the pulling action of the traction assembly 200, and the curvature of the bending section 110 is adjusted according to different degrees of pull. The specific structure of the bending joints is well known to those skilled in the art and will not be described in detail here.

[0046] The support section 120 provides primary support. In this embodiment, the support section 120 includes a second inner tube layer 121 and a second outer tube layer 122. A first spring layer 123 and a second spring layer 124 are disposed between the second inner tube layer 121 and the second outer tube layer 122. Both the first spring layer 123 and the second spring layer 124 are made of woven or wound metal wire. A channel for the traction assembly 200 to pass through is formed between the first spring layer 123 and the second spring layer 124, or it can be formed within the first spring layer 123 and the second spring layer 124. In this embodiment, both the second inner tube layer 121 and the first inner tube layer are made of PTFE material, thereby creating a flat and lubricated inner cavity, facilitating the passage of other instruments. The second outer tubular layer 122 comprises a nylon or PEBAX-type polymer composite material, which is fused with the second inner tubular layer 121, the first spring-wound layer 123, and the second spring-wound layer 124 through rheological technology, making it a whole and further improving the performance of the tube. This allows it to conform to the complex tortuous paths of blood vessels within the body, making it easier for doctors to push and withdraw. The first spring-wound layer 123 and the second spring-wound layer 124 are preferably made of nickel-titanium alloy or stainless steel wires woven or wound, thus providing mechanical reinforcement to the tube and making it more resistant to bending and deformation.

[0047] refer to Figure 5-6 As shown, the torsion control section 130 includes a sodium hypochlorite tube layer 131, which is a metal tube layer with a plurality of cuts 132 spirally arranged on its surface. The torsion control section 130 is connected to the support section 120 by hot melting and adhesive bonding processes. By setting a sodium hypochlorite tube reinforcement structure at the near end, it is beneficial to better transmit the torque input from the main tube 100 to the far end of the main tube 100, thereby increasing the torsion controllability of the main tube 100.

[0048] In this embodiment, the material of the hypoecho tube layer 131 is preferably a nickel-titanium tube, with an overall length preferably of 297-303 mm. The resulting hypoecho tube has an outer diameter of 0.335 mm and a single-sided wall thickness of 0.06 mm. The surface cutouts 132 of the hypoecho tube layer 131 are hexagonal narrow slits with a width of 0.03-0.05 mm. A single cut is used, and several cutouts 132 are arranged at intervals on the surface of the hypoecho tube layer 131. The hexagonal cuts of the hypoecho tube ensure that the torsion control section 130 can conform to the curvature of the blood vessel, while facilitating torque transmission, reducing efficiency loss, and efficiently transmitting torque to the torsion control section 130 to make it oscillate, thereby improving the operation feedback rate. Furthermore, the density of the cut 132 decreases from the proximal end to the distal end; it can be a density gradient, or the sodium hypochlorite tube layer 131 can be divided into three segments, including a first segment, a second segment, and a third segment. The length of the first segment is preferably 167-171 mm, the length of the second segment is preferably 60-62 mm, and the length of the third segment is preferably 68-72 mm. The density of the cut 132 in the first segment is the first density, the density of the cut 132 in the second segment is the second density, and the density of the cut 132 in the third segment is the third density. The relationship between the first density, the second density, and the third density is: first density > second density > third density. The distance between two adjacent cuts 132 near the proximal end (i.e., the rib width) is 0.13 mm. After cutting, the sodium hypochlorite tube layer 131 is acid-washed to passivate its surface and avoid scratching the vascular tissue. By segmenting the density of the cut 132, the torque control section 130 has different hardness segments, which improves torque transmission efficiency while ensuring compliance and support.

[0049] The traction assembly 200 is inserted into the channel, with one end fixed to the first developing ring 111 at the distal end of the main guide tube 100 and the other end extending from the end of the channel and connected to the handle 300. The handle 300 controls the curvature of the bending section 110 by the degree of traction of the traction assembly 200. In this embodiment, the traction assembly 200 includes a traction wire 210 and a covering tube 220, with the covering tube 220 on the surface of the traction wire 210. The traction wire 210 is manufactured by twisting, typically requiring 3 to 10 wires to be simultaneously wound together using equipment to form a twisted structure, thus giving it superior bending resistance and tensile strength compared to round wires of the same outer diameter. By covering the surface of the traction wire 210 with the covering tube 220, the smoothness of the traction wire 210 during stretching is improved, while preventing the traction wire 210 from deforming due to the influence of adjacent layer structures.

[0050] In this embodiment, the length of the handle 300 is preferably 11-13cm. The handle 300 can be connected to the torque control section 130 through the stress relief tube. The handle 300 controls the curvature of the bending section 110 through the traction component 200 and controls the swing of the bending section 110 by transmitting torque to the torque control section 130.

[0051] Specifically, the handle 300 includes a housing assembly 310 and a bending structure 320. The bending structure 320 is disposed inside the housing assembly 310 and is connected to the traction assembly 200. It is used to control the curvature of the bending section 110 by pulling the traction wire 210.

[0052] Specifically, the housing assembly 310 has a polygonal prism structure, which is more convenient for applying torsional force and adjusting the angle compared to the commonly used cylindrical structure. The housing assembly 310 includes an upper housing and a lower housing that interlock, forming a mounting cavity between the upper and lower housings. One end of the housing assembly 310 forms a connection port, through which the handle 300 is connected to the main tube 100. The other end of the housing assembly 310 is provided with a detachable cap 311, and the side of the housing assembly 310 is provided with an expansion window 312. The detachable cap 311 and the expansion window 312 enable the expansion of the end or side of the main tube 100. The end or side of the main tube 100 can be opened by the detachable cap 311 or the expansion window 312, or it can be connected to other devices to achieve more expansion operation functions.

[0053] The housing assembly 310 has a first control port 313 and a second control port 314 on opposite sides; the inner sides of the first control port 313 and the second control port 314 form an annular sliding groove 315; the axis of the annular sliding groove 315 is consistent with the length direction of the housing assembly 310.

[0054] The bending structure 320 is disposed within the mounting cavity. The bending structure 320 includes a drive structure, a transmission structure, and a winding wheel 326. The drive structure includes a dial wheel 321 and a transmission wheel 322. An internal gear ring is formed within the dial wheel 321 that meshes with the transmission wheel 322. The dial wheel 321 is disposed within the annular sliding groove 315 to improve the connection stability of the dial wheel 321. The axis of the dial wheel 321 is arranged along the length direction of the housing assembly 310, and the outer peripheral surface of the dial wheel 321 protrudes from the first control port 313 and the second control port 314. The transmission structure includes a set of meshing turbines 323 and worm gears 324. The worm gears 324 are connected to the transmission wheel 322 via a transmission shaft 325. The turbines 323 are linked with the winding wheel 326. The winding wheel 326 has a winding groove formed circumferentially. The inner wall of the winding groove is roughened to make it non-slip. The winding groove is connected to the traction assembly 200.

[0055] In use, the dial 321 is turned by moving the portion of its outer surface protruding from the first control port 313 and / or the second control port 314. The current design allows the surgical operator to grip the half of the housing assembly 310 near the detachable cap 311 with their palm, middle finger, ring finger, and little finger, while simultaneously using their thumb and index finger to turn the dial 321 on both sides. Compared to existing dials with only one protruding outer shell, this design allows the operator to use only their thumb, resulting in a better tactile feel. The dial 321 drives the transmission wheel 322 to rotate, which in turn drives the worm gear 324 via the transmission shaft 325. This, in turn, drives the turbine 323 meshing with the worm gear 324 to rotate, thereby causing the rotating wheel 326 to rotate and pulling the traction wire 210, thus controlling the curvature of the bending section 110. Through testing, the control ratio between the curvature deflection angle of the bending segment 110 and the rotation of the dial 321 was determined to be such that for every 1° deflection of the bending segment 110, the required angular displacement of the dial 321 is 0.5-0.8 turns. In other words, for every 1° deflection of the bending segment 110, the surgeon's thumb and forefinger need to rotate the dial approximately 2 to 3 times. This control ratio demonstrates the advantage of accurately transmitting angular displacement while ensuring finger comfort and preventing fatigue. Furthermore, the outer surface of the dial 321 is slightly smooth, unlike the friction-textured dials known in the prior art. This design has two advantages: firstly, it allows for better sliding cooperation with the annular sliding groove 315; secondly, it provides a sliding buffer during rotation by the surgeon, meaning that each rotation of the dial 321 by the forefinger and thumb will result in a suitable amount of slippage, preventing less experienced surgeons from causing the bending segment 110 to deflect too quickly due to tension. Adjusting the bend angle too quickly or controlling the proportion improperly can cause sudden changes in blood flow in the blood vessels at the location of the interventional device, potentially leading to patient discomfort. Adjusting too slowly will not cause this problem; however, the aforementioned "too slow" should be understood within the reasonable scope of a person skilled in the art.

[0056] The traction component 200 can be traction controlled by multiple sets of winding wheels 326. The two traction wires 210 arranged opposite each other are in a master-slave relationship. By pulling one of the traction wires 210 or the adjacent traction wires 210 to make them wrap around the surface of the winding wheel 326, the curvature of the bending section 110 can be controlled.

[0057] The current operating handle 300 integrates multiple control functions, generally using buttons or push-pull mechanisms. When multiple functions are integrated into the same handle 300, accidental touches or interference are prone to occur, and errors may occur in emergency situations due to blind control or inertia. This embodiment sets the axis of the dial 321 along the length of the housing assembly 310, and controls it by flicking it left and right, distinguishing it from the current button or push-pull methods. This avoids errors caused by inertia. When it is integrated with other function buttons in the same control module, it can also be distinguished by touch and control method, effectively avoiding accidental touches and improving surgical efficiency. In this embodiment, the dial 321 can be rotated by flicking the first control port 313 or the first control port 313 on either side of the dial 321. It can also be controlled by pinching the first control port 313 and the first control port 313 on opposite sides of the dial 321 with two fingers. Controlling from both sides can improve the stability of the doctor's hand adjustment and the ability to control the curvature and speed. This provides multiple control methods, making the operation more flexible and adaptable to different needs during use.

[0058] The transmission is achieved through the meshing of the internal gear ring of the dial wheel 321 and the transmission wheel 322, which can provide a larger transmission ratio and perform the first speed adjustment of the traction speed of the dial wheel 321 on the traction wire 210. The second speed adjustment of the traction speed is achieved through the transmission of the worm gear 324 and the worm 323. The third speed adjustment is achieved through the transmission of the worm gear 323 and the winding wheel 326. Through multiple speed adjustments, the traction speed of the dial wheel 321 on the traction wire 210 can be controlled at a lower speed, which slows down the curvature change rate of the bending section 110 and allows for more precise fine-tuning control. In addition to achieving a large transmission ratio and reversing, the transmission of the worm gear 323 and the winding wheel 326 has a self-locking function, which can avoid stress feedback during operation. By roughening the inner wall of the winding groove, the friction coefficient between the surface of the winding groove and the surface of the traction wire is kept constant and controllable when it comes into contact with the traction wire 210, so as to achieve more precise control.

[0059] When using this adjustable microcatheter, carefully inspect it for kinks, knots, or other damage. If necessary, use the included shaping needle to shape the adjusting segment 110 according to the shaping requirements. Connect the syringe filled with heparinized saline to the adjustable microcatheter and flush the lumen of the main tube 100. Push the adjustable microcatheter through the microguidewire to the vicinity of the vessel or aneurysm requiring superselection. Remove the microguidewire and use the adjustable microcatheter handle 300 to control the bending and swinging of the adjusting segment 110 to complete vessel superselection and reach the target position. Release the coil to complete the operation. If there is no microguidewire guidance, the adjustable microcatheter can be used directly to control the bending segment 110 and push it to the vessel requiring superselection. During superselection, adjust the distal bending and swinging appropriately to avoid entering the false lumen. Finally, remove the adjustable microcatheter for subsequent processing.

[0060] The adjustable-bend microcatheter for neurointervention in this embodiment features a bendable section 110 at the distal end of the main tube 100. The curvature of this bendable section 110 is controlled by the handle 300 through the traction component 200, allowing for tip-bend adjustment and superselective catheterization. This avoids the need for frequent switching of different catheters or instruments during surgery, improving surgical efficiency and effectiveness. Furthermore, this adjustable-bend microcatheter can be shaped without altering the tip-bend and can be advanced to the target location using a "painting" method, reducing the difficulty of superselective vessel selection, lowering surgical risks, and shortening surgical time. The adjustable-bend microcatheter for neurointervention in this embodiment significantly improves the catheter's maneuverability and torsional control by incorporating a hypotube layer 131 at the proximal end. This enables highly efficient torque transmission and control over the oscillation of the bend section 110. With precise control of the handle 300, combined with the control of the bend section 110's degree of bending, it achieves comprehensive and precise control of the distal end. This is particularly advantageous for cases requiring multi-angle, high-precision, and high-frequency control, such as coil filling for aneurysms. It increases the angle during coil release, reduces the difficulty of coil release during surgery, and improves surgical efficiency and effectiveness. Furthermore, the adjustable-bend microcatheter for neurointervention in this embodiment incorporates a first contrast-enhancing ring 111 and a second contrast-enhancing ring 112 in the bend section 110. This dual-ring structure allows surgeons to more easily determine the location of the coil during surgery with the support of a computer-controlled digital subtraction angiography (DSA) system. This facilitates the delivery of the coil to the aneurysm location and allows for coil release to complete the "painting" action, thus treating aneurysms and simplifying the surgical procedure.

[0061] The above embodiments are merely preferred embodiments of the present invention and should not be construed as limiting the scope of protection of the present invention. Any non-substantial changes and substitutions made by those skilled in the art based on the present invention shall fall within the scope of protection claimed by the present invention.

Claims

1. An adjustable-bend microcatheter for neurointervention, characterized in that, Includes the main tube, traction assembly, and handle; The main tube has a distal end and a proximal end. From the distal end to the proximal end, the main tube is sequentially provided with a bending section, a support section, and a torsion control section. The bending section has a first developing ring and a second developing ring at each end, with the first developing ring positioned closer to the distal end and the second developing ring positioned closer to the proximal end. The bending section can be bent under the pull of the traction assembly. The support section provides primary support. The torsion control section includes a sodium hydroxide tube layer, which is a metal tube layer with a plurality of spirally arranged cuts on its surface. The inner walls of the main tube on opposite sides have channels through which the traction assembly can pass. The traction assembly is inserted into the channel, with one end of the traction assembly fixed to the first developing ring and the other end extending out from the end of the channel and connected to the handle; the traction assembly includes a traction wire and a covering tube. The handle is connected to the proximal end of the main tube and is used to control the bending of the bending section through the traction assembly and to control the swing of the bending section by transmitting torque to the torque control section. The handle includes a housing assembly and a bending adjustment structure. The bending adjustment structure is disposed inside the housing assembly and is connected to the traction assembly. It is used to control the curvature of the bending section by pulling the traction assembly. The housing assembly has an internal mounting cavity, and one end of the housing assembly is connected to the main guide tube; The housing assembly has a first control port and a second control port on opposite sides; an annular sliding groove is formed inside the first and second control ports; the axis of the annular sliding groove is consistent with the length direction of the housing assembly; the bending structure is disposed in the mounting cavity, and the bending structure includes a drive structure, a transmission structure, and a winding wheel; the drive structure includes a dial wheel and a transmission wheel, and an internal gear ring that meshes with the transmission wheel is formed inside the dial wheel; the dial wheel is disposed in the annular sliding groove, and the outer peripheral surface of the dial wheel protrudes from the first and second control ports; the drive structure is linked with the winding wheel through the transmission structure; a winding groove is formed circumferentially on the winding wheel, and the winding groove is connected to the traction assembly; The dial is rotated by the first and second control ports, which drives the transmission wheel to rotate. The transmission wheel transmits torque to the winding wheel, thereby driving the winding wheel to rotate and pulling the traction wire, thus controlling the curvature of the bending section. The transmission structure includes a transmission shaft and a set of meshing worm gears, the worm gears being connected to the transmission wheel via the transmission shaft; the turbine is rotatably connected within the mounting cavity, and the end of the turbine is connected to the worm wheel.

2. The adjustable bendable microcatheter for neurointervention according to claim 1, characterized in that, The cut is a hexagonal narrow slit with a width of 0.03-0.05 mm.

3. The adjustable bendable microcatheter for neurointervention according to claim 2, characterized in that, The kerf density decreases from the proximal end to the distal end; the distance between two adjacent kerfs near the proximal end is 0.13 mm.

4. The adjustable bendable microcatheter for neurointervention according to claim 1, characterized in that, The bending section further includes a first inner tube layer and a first outer tube layer. A plurality of bending joints are provided between the first inner tube layer and the first outer tube layer. Through holes are formed on opposite sides of the bending joints so that the traction component can pass through. The bending section is bent by creating a density difference between the bending joints on opposite sides through the traction component.

5. The adjustable bendable microcatheter for neurointervention according to claim 1, characterized in that, The support section includes a second inner tube layer and a second outer tube layer. A first spring layer and a second spring layer are provided between the second inner tube layer and the second outer tube layer. Both the first spring layer and the second spring layer are made of woven or wound metal wire. The channel for the traction assembly to pass through is provided between the first spring layer and the second spring layer.

6. The adjustable bendable microcatheter for neurointervention according to claim 1, characterized in that, The handle is connected to the torsion control section via a stress-relieving tube.

7. The adjustable bendable microcatheter for neurointervention according to claim 6, characterized in that, The other end of the housing assembly is provided with a detachable cap, and the side of the housing assembly is provided with an expansion window.

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