Delivery device and endoscopic surgical equipment

Abstract

The invention discloses a conveying device and endoscopic surgery equipment, and belongs to the technical field of medical instruments.In the conveying device, a conductive tube of a catheter assembly is arranged to comprise a soft section and a supporting section in the axial direction of the conductive tube, and the minimum bending radius of the soft section is smaller than the minimum bending radius of the supporting section; and the flexible section is connected with the electrode tip, so that the far-end part of the catheter assembly has better bending compliance. When the catheter assembly is propelled along a bent guide wire path in tissue, the soft far end can effectively fit the bent state of the guide wire, and the situation that the guide wire is ejected out of a target position due to the fact that the rigidity of the far end of the catheter assembly is too large is avoided; meanwhile, the supporting section at the near end can provide enough axial supporting force and torsion transmission capacity for pushing of the whole catheter assembly, and therefore on the premise that operation safety is guaranteed, smoothness and reliability of the instrument passing through a complex anatomical path are improved.

Description

Technical Field

[0001] This application relates to the field of medical device technology, and in particular to a delivery device and endoscopic surgical equipment. Background Technology

[0002] A delivery device is a medical instrument commonly used in endoscopic surgery. It typically includes a catheter, an electrode tip positioned distal to the catheter, and a drainage tube movably fitted over the outside of the catheter. During the procedure, the device is advanced along a guidewire to the target tissue location. The electrode tip is energized to establish a puncture channel, and the drainage tube is subsequently released and left in place for drainage.

[0003] During application, especially when the target path is tortuous, the guidewire is often in a bent state within the body cavity. However, when existing delivery devices advance along the tortuous guidewire, a strong interaction force is generated between the distal end of the catheter and the guidewire, which can easily cause the guidewire to accidentally dislodge from the target position or deviate from its path, thereby affecting the smooth progress of the surgery and increasing the operational risks. Summary of the Invention

[0004] This application provides a delivery device and an endoscope, which can effectively conform to the bending path of the guide wire to at least partially solve the above-mentioned technical problems.

[0005] To achieve the above objectives, according to a first aspect of this application, a conveying device is provided, comprising: Catheter assembly; An electrode tip is disposed at the distal end of the catheter assembly; The catheter assembly includes a conductive tube and a coating layer covering the outer periphery of the conductive tube; the conductive tube includes a flexible segment and a support segment arranged along its axial direction, the flexible segment being connected to the electrode head, and the support segment being closer to the proximal end of the catheter assembly than the flexible segment; wherein the minimum bending radius of the flexible segment is smaller than the minimum bending radius of the support segment.

[0006] In some embodiments, the minimum bending radius of the flexible segment is 5 mm to 50 mm.

[0007] In some embodiments, a perforated pattern is formed on the wall of the flexible segment.

[0008] In some embodiments, the perforated pattern extends in a spiral shape.

[0009] In some embodiments, the perforated pattern is an opening that penetrates the wall thickness of the conductive tube, or the perforated pattern is a groove that extends to the depth of a portion of the wall thickness of the conductive tube.

[0010] In some embodiments, the minimum bending radius of the conductive tube increases continuously or in a stepwise manner from its distal end to its proximal end.

[0011] In some embodiments, the conductive tube further includes a transition section located between the flexible section and the support section, wherein the minimum bending radius of the transition section is greater than the minimum bending radius of the flexible section and less than the minimum bending radius of the support section.

[0012] In some embodiments, the electrode head and the conductive tube are integrally formed; The electrode head includes a connecting portion connected to the flexible segment, wherein the minimum bending radius of the connecting portion is greater than the minimum bending radius of the flexible segment.

[0013] In some embodiments, the electrode head includes: The connecting part is fixedly connected to the flexible segment; At least two variable electrodes are arranged circumferentially at intervals along the connection portion and extend distally from the connection portion; The blade head is connected to the distal end of the variable electrode; The variable electrode is configured to be able to elastically switch between an expanded state and a contracted state in the radial direction.

[0014] In some embodiments, the delivery device further includes an inner liner disposed inside the electrode head and extending axially; the wall of the inner liner is configured to block the gap formed by the at least two variable electrodes being arranged circumferentially.

[0015] In some embodiments, the inner liner extends axially between the blade head and the conductive tube, with the distal end of the inner liner being axially opposite to the blade head and the proximal end of the inner liner being axially opposite to the conductive tube. When the cutter head is subjected to a force toward the proximal end, the inner liner can provide axial support between the cutter head and the conductive tube to limit the axial deformation of the variable electrode.

[0016] In some embodiments, the distal end of the inner liner is fixedly connected to the blade head, and the proximal end of the inner liner is used to movably abut against the conductive tube; or, The distal end of the inner liner tube is movably abutted against the blade head, and the proximal end of the inner liner tube is used for fixed connection with the conductive tube; or, The distal end of the inner liner tube is used to movably abut against the blade head, and the proximal end of the inner liner tube is used to movably abut against the conductive tube.

[0017] In some embodiments, the conveying device further includes a handle assembly, the handle assembly comprising: The handle body is connected to the proximal end of the conductive tube; A sealing structure is connected to the proximal end of the handle body; The handle assembly has a channel that passes through the handle body and the sealing structure. The channel is connected to the conductive tube, and the sealing structure is used to seal the channel.

[0018] In some embodiments, the sealing structure includes: A drive component is movably connected to the handle body, and a first channel is formed on the drive component; A seal is disposed between the drive member and the handle body, and a second channel is formed on the seal; The handle body has a third channel, and the first channel, the second channel and the third channel are connected and together form the channel. The drive element is configured to move relative to the handle body to axially compress the seal, causing radial deformation of the seal to seal the passage.

[0019] In some embodiments, the drive member is threadedly connected to the handle body, and the rotational motion of the drive member can be converted into axial movement relative to the handle body to compress the seal.

[0020] In some embodiments, the proximal end of the handle body is provided with an assembly cavity communicating with the third channel, the seal is disposed in the assembly cavity, and the second channel is aligned and communicates with the third channel; The drive component includes a pressing part extending into the assembly cavity and a rotating part connected to the outer periphery of the pressing part and sleeved on the proximal end of the handle body, wherein the first channel is formed in the pressing part; The rotating part is connected to the handle body by a thread to drive the extrusion part to move axially.

[0021] In some embodiments, the handle body is further provided with an injection port communicating with the channel.

[0022] In some embodiments, the conveying device further includes a handle assembly, the handle assembly comprising: The handle body is connected to the proximal end of the conductive tube; An adjustment structure, comprising a positioning element and an adjustment element, wherein the positioning element is connected to the distal end of the handle body, and the adjustment element is connected to the positioning element; The delivery device further includes an outer tube sleeved around the periphery of the conduit assembly, the outer tube being connected to the adjusting member; The adjusting member is configured to move axially relative to the positioning member, thereby driving the outer tube to move axially along the conduit assembly.

[0023] In some embodiments, the adjustment structure further includes a locking mechanism configured to lock the adjustment member at different axial positions of the positioning member.

[0024] In some embodiments, the locking mechanism includes: The toothed portion is provided on the positioning member; An elastic engagement portion is provided on the adjusting member; The elastic meshing part engages with the toothed part under the action of elastic force.

[0025] In some embodiments, the resilient engagement portion includes: Elastic components; A meshing member having meshing teeth for meshing with the toothed portion; The adjusting member is provided with a slot for inserting the engaging member and a limiting structure for limiting the engagement member. The engaging member is installed in the slot, and the elastic member is disposed between the adjusting member and the engaging member, and applies an elastic force to the engaging member to make it tend to engage with the toothed portion; The engaging member is configured to overcome the elastic force of the elastic member and move within the slot when pressed, so that the engaging teeth disengage from the toothed portion.

[0026] In some embodiments, the conveying device further includes a support wire configured to be inserted into the conductive tube to increase the rigidity of the conductive tube.

[0027] According to a second aspect of this application, an endoscopic surgical device is provided, comprising: The conveying device as described in any of the above embodiments, and, A drainage tube, which can be fitted around the periphery of the catheter assembly.

[0028] In some embodiments, the length of the flexible segment is L1, and the length of the drainage tube sleeved around the periphery of the catheter assembly is L2, satisfying: 1 / 4≤L1 / L2≤5.

[0029] In some embodiments, the electrode head of the delivery device includes at least two variable electrodes. When the variable electrodes are in the deployed state, the maximum outer diameter of the electrode head is smaller than the maximum outer diameter of the drainage tube sleeved around the periphery of the catheter assembly, and the difference between the two is 0.1 mm to 0.5 mm.

[0030] In some embodiments, the distance between the distal end of the drainage tube sleeved around the periphery of the catheter assembly and the proximal end of the electrode tip is 0 mm to 20 mm, or 0 mm to 5 mm.

[0031] In some embodiments, the drainage tube is provided with an ultrasound and / or X-ray imaging structure.

[0032] In the delivery device of this application embodiment, by configuring the conductive tube of the catheter assembly to include a flexible section and a support section along its axial direction, and by making the minimum bending radius of the flexible section smaller than that of the support section, and by connecting the flexible section to the electrode head, the distal portion of the catheter assembly can have better bending compliance. When advancing along the curved guidewire path within the tissue, the flexible distal end can effectively conform to the bending shape of the guidewire, reducing the possibility of the guidewire being pushed out of the target position due to excessive stiffness at the distal end of the catheter assembly; at the same time, the proximal support section can provide sufficient axial support force and torsional transmission capacity for the advancement of the entire catheter assembly, thereby improving the smoothness and reliability of the instrument passing through complex anatomical paths while ensuring operational safety.

[0033] This endoscopic surgical device includes the aforementioned delivery device, and therefore possesses all the technical features and beneficial effects of such a device, which will not be repeated here. Furthermore, this device combines the delivery device with a drainage tube that can be fitted around the periphery of its catheter assembly. The delivery device uses its electrode tip to establish a tissue channel and complete the delivery, while the drainage tube, as the delivered implant, can be left in place after release to perform functions such as drainage. This integrated device eliminates the need for multiple exchanges between the electrode and drainage tube instruments during a single surgery, thereby reducing the risk of tissue fluid leakage and loss of positioning due to repeated instrument entry and exit from body cavities, and helping to simplify surgical procedures and shorten surgical time.

[0034] Other features and advantages of this application will be described in detail in the following detailed description section. Attached Figure Description

[0035] To more clearly illustrate the technical solutions in the embodiments of this application, the accompanying drawings used in the description of the embodiments will be briefly introduced below. Obviously, the drawings described below are only some embodiments of this application. For those skilled in the art, other drawings can be obtained based on these drawings without creative effort.

[0036] To gain a more complete understanding of this application and its beneficial effects, the following description will be provided in conjunction with the accompanying drawings, wherein the same reference numerals in the following description denote the same parts.

[0037] Figure 1 This is a schematic diagram of the overall structure of the endoscopic surgical device provided in the embodiments of this application; Figure 2 This is a schematic diagram of the overall structure of the conveying device provided in the embodiments of this application; Figure 3 This is a schematic diagram of the bending structure of the flexible section of the conductive tube in the conveying device provided in the embodiments of this application; Figure 4 This is a schematic diagram of the structure of the conductive tube in a conveying device provided in one embodiment of this application; Figure 5 This is a schematic diagram of the structure of the conductive tube in the conveying device provided in another embodiment of this application; Figure 6 yes Figure 2 A magnified schematic diagram of the local structure of the O region; Figure 7 This is a schematic diagram of the endoscopic surgical device provided in the embodiments of this application from one side view. Figure 8 It is along Figure 7 Schematic diagram of the cross-sectional structure along line AA; Figure 9 yes Figure 8 Enlarged schematic diagram of a local structure in region A; Figure 10 This is a schematic diagram of the endoscopic surgical device provided in the embodiments of this application from another side view. Figure 11 It is along Figure 10 Schematic diagram of the cross-sectional structure of the middle BB line; Figure 12 yes Figure 11 A magnified schematic diagram of the local structure of region B in the middle; Figure 13 yes Figure 8 A magnified schematic diagram of the local structure of region C in the middle; Figure 14 It is along Figure 13 A partial cross-sectional view of the CC line; Figure 15 This is a flowchart illustrating an operation method of the endoscopic surgical device provided in the embodiments of this application; Figure 16 This is a flowchart illustrating another operating method of the endoscopic surgical device provided in the embodiments of this application.

[0038] Explanation of reference numerals in the attached figures: 10-Endoscopic surgical equipment; 100-Transport device; 110-Catheter assembly; 111-Conductive tube; 112-Covering layer; 1110-Soft section; 1113-Perforated pattern; 1111-Support section; 1112-Transition section; 120-Electrode head; 121-Connector; 122-Variable electrode; 123-Scalpel head; 124-Illuminating section; 130-Inner liner tube; 140-Handle assembly; 141-Handle body; 1410-Assembly cavity; 142-Sealing structure; 143-Driver; 1431-Compression section; 1432-Rotation. 144-Seal; 145-Adjusting structure; 146-Positioning component; 147-Adjusting component; 1471-Slot; 1472-Limiting structure; 148-Locking mechanism; 1480-Toothed part; 1481-Elastic engagement part; 1482-Elastic component; 1483-Engine; 1484-Engine tooth; 150-Outer tube; 170-Support wire; 171-Limiting head; 180-Channel; 181-First channel; 182-Second channel; 183-Third channel; 190-Injection port; 200-Drainage tube; 210-Developing structure. Detailed Implementation

[0039] The technical solutions of the embodiments of this application will be clearly and completely described below with reference to the accompanying drawings. Obviously, the described embodiments are only a part of the embodiments of this application, and not all of them. All other embodiments obtained by those skilled in the art based on the embodiments of this application without creative effort are within the protection scope of this application.

[0040] like Figure 1 and Figure 2 As shown, this application embodiment provides a delivery device 100. The delivery device 100 is used to deliver tubular implantable instruments, such as drainage tubes 200, during endoscopic surgery. It should be noted that the drainage tube 200, as an independent implantable instrument, can be used in conjunction with the delivery device 100. Its structure and size can be adapted to the delivery device 100. Before use, it can be fitted around the catheter assembly 110 of the delivery device 100, and during the surgery, the delivery device 100 delivers and places it at the target tissue location within the body.

[0041] Reference Figure 2 The delivery device 100 includes a catheter assembly 110 and an electrode head 120. The catheter assembly 110 constitutes the main tubular portion of the delivery device 100, and is generally an elongated tubular member with an inner lumen through which a guidewire can pass. In a specific application of the delivery drainage tube 200, the drainage tube 200 can be fitted around the outer periphery of the catheter assembly 110. The electrode head 120 is fixedly disposed at the distal end of the catheter assembly 110.

[0042] The catheter assembly 110 mainly consists of an internal conductive tube 111 and an external coating layer 112. The conductive tube 111, serving as the structural framework of the catheter assembly 110, is typically made of a metallic material and is conductive, used to introduce external current into the electrode tip 120. The conductive tube 111 is divided along its axial direction into segments with different mechanical properties, each segment possessing different bending mechanical properties. Specifically, the conductive tube 111 includes a flexible segment 1110 and a support segment 1111. Its distal portion is constructed as the flexible segment 1110 and is connected to the electrode tip 120. The support segment 1111 is located closer to the proximal end of the catheter assembly 110 than the flexible segment 1110. It can be understood that the proximal end refers to the end closer to the operator during operation, while the distal end refers to the end inserted into the body, typically farther from the operator.

[0043] The minimum bending radius of the flexible segment 1110 is configured to be smaller than that of the support segment 1111. This structural arrangement provides good compliance at the distal end of the catheter assembly 110 to accommodate tortuous paths, while the support segment 1111 near the proximal end provides sufficient pushing support.

[0044] The "minimum bending radius" mentioned here is defined as: under standard mechanical test conditions, for example... Figure 3 As shown, a force perpendicular to the axis of a conductive tube 111 sample is applied to one end to bend it, and the bending shape of its central axis is recorded. The minimum radius r of the bending trajectory that the central axis of the conductive tube 111 can reach before the material yields is determined. This minimum bending radius can be repeatedly measured and quantitatively compared using standard test methods, such as the three-point bending test.

[0045] The coating layer 112 can be made of an insulating polymer material. In a specific example, the coating layer 112 is tightly wrapped around the outer surface of the conductive tube 111 by a heat-shrink process. Its functions include at least: first, as an insulating layer, electrically isolating the conductive tube 111 from its surrounding area to ensure operational safety; second, limiting the axial stretching of the conductive tube 111, especially its distal end, which may have a flexible segment 1110 with a hollow structure. By wrapping it with the coating layer 112, excessive stretching of the conductive tube 111 under axial tension can be effectively limited, maintaining structural integrity; third, providing a smooth outer surface to reduce friction with the inner wall of the drainage tube 200.

[0046] By incorporating a flexible segment 1110 structure within the conductive tube 111 of the catheter assembly 110, the distal portion of the delivery device 100 possesses excellent flexibility and bending compliance. When the delivery device 100 is advanced along the naturally curved or coiled guidewire path within the patient's body, the distal flexible segment 1110 conforms to the guidewire's curvature, significantly reducing the risk of the guidewire being pushed out of the target position due to excessive rigidity at the distal end of the catheter assembly 110. Simultaneously, the proximal support segment 1111, due to its larger minimum bending radius (i.e., higher bending stiffness), provides stable and reliable axial support and torque transmission during long-distance propulsion through the body's natural cavities, effectively preventing unnecessary bending or instability of the catheter assembly 110 during the delivery process.

[0047] In some embodiments, such as Figure 3 As shown, the minimum bending radius r of the flexible segment 1110 is in the range of 5mm to 50mm. For example, it can be any value or a range between 5mm, 7mm, 10mm, 13mm, 16mm, 19mm, 22mm, 25mm, 28mm, 31mm, 34mm, 37mm, 40mm, 43mm, 46mm, 49mm, and 50mm. This range of values ​​is suitable for common guidewire bending patterns in target anatomical pathways within the human body, such as guidewire pathways through natural cavities to the gallbladder or pancreas region. Setting the upper limit of the minimum bending radius to 50mm ensures that the flexible segment 1110 has sufficient flexibility to closely conform to guidewires with various bending patterns, thereby maintaining excellent conformation even in more tortuous cavity segments and reducing the occurrence of guidewire protrusion. Setting the lower limit to 5mm ensures that the soft segment 1110 retains the necessary shape retention and compression resistance, preventing excessive axial compression when fitting the drainage tube 200, reducing fitting difficulty, and preventing ineffective bending or twisting due to excessive softness when pushed along a relatively gentle path, thus maintaining basic pushing efficiency.

[0048] By limiting the bending performance of the flexible segment 1110 to this specific range, the distal end of the conveying device 100 can adapt to various internal paths from sharp bends to gentle bends, ensuring extreme bending following ability while taking into account the overall controllability and efficiency of the pushing operation.

[0049] In some embodiments, please refer again Figure 4To form a flexible segment 1110 at the distal end of the conductive tube 111 and achieve the required flexibility at the distal end of the conductive tube 111, a specific perforated pattern 1113 can be formed on the wall of the flexible segment 1110 of the conductive tube 111. This perforated pattern 1113 can be formed by partially removing material from the wall of the conductive tube 111 through subtractive processing methods such as engraving, thereby locally reducing the bending stiffness of its structure. By controlling the distribution, shape, and size of the pattern, the overall bending mechanical properties of the flexible segment 1110 can be precisely controlled, ensuring that its minimum bending radius reaches a predetermined range.

[0050] Specifically, the aforementioned perforated pattern 1113 is constructed to extend spirally along the axial direction of the conductive tube 111. This spirally extending pattern forms a continuous, spring-like trajectory on the tube wall. When the conduit assembly 110 is subjected to bending stress, the spiral perforated portion allows for more coordinated elastic deformation and slight relative displacement of the tube wall material of the conductive tube 111, thereby distributing the bending stress more evenly across the entire length of the flexible section 1110, rather than concentrating it at a single point. This not only endows this section of the conductive tube 111 with excellent flexibility but also significantly improves its fatigue life. The parameters of the spiral pattern, such as the pitch, the width and depth of the spiral groove, can be controlled according to the target minimum bending radius.

[0051] There are at least two ways to implement the aforementioned hollow pattern 1113. The first way is that the hollow pattern 1113 is an opening that completely penetrates the wall thickness of the conductive tube 111. This through-hole design minimizes local stiffness, allowing the conductive tube 111 to achieve a smaller bending radius and extremely high flexibility. The second way is that the hollow pattern 1113 is a groove extending to a portion of the wall thickness of the conductive tube 111. This non-through groove reduces bending stiffness while retaining some continuous tube wall material, thus simultaneously ensuring flexibility and structural integrity.

[0052] In other embodiments, the hollow pattern 1113 is not limited to the spiral pattern described above, but can also take other forms. For example, multiple through holes or multiple grooves can be arranged regularly or irregularly on the tube wall to form the hollow pattern 1113.

[0053] In some embodiments, the overall mechanical properties of the conductive tube 111 from its distal end to its proximal end can be varied in at least two ways. Specifically, the minimum bending radius of the conductive tube 111 from its distal end to its proximal end can be increased continuously or in a stepwise manner.

[0054] When a continuously increasing variation mode is adopted, the bending stiffness of the conductive tube 111 begins at its distal, flexible segment 1110 and gradually increases smoothly and without abrupt changes along the axial direction towards the proximal end. This continuous stiffness variation can be achieved through various physical methods, such as changing the wall thickness of the conductive tube 111, or controlling the depth, width, or distribution density of the engraved patterns on the tube wall to gradually vary along the length of the conductive tube 111. This makes the curvature change of the conductive tube 111 more natural and smooth when bending, further optimizing stress distribution and improving fatigue resistance.

[0055] When a stepped increase in bending stiffness is adopted, the bending stiffness of the conductive tube 111 is divided along its length into several segments with different minimum bending radii. For example, the conductive tube 111 can consist of two, three, or four segments, with a clear difference in minimum bending radius between adjacent segments, while the minimum bending radius remains essentially consistent within the same segment. This stepped change can be achieved by using different material processing techniques or engraving parameters in different segments. Compared to continuous changes, stepped changes may be easier to manufacture and control while ensuring graded core mechanical properties.

[0056] Specifically, such as Figure 5 As shown, a transition section 1112 is added between the axial flexible section 1110 and the support section 1111 of the conductive tube 111. One end of the transition section 1112 is connected to the flexible section 1110, and the other end is connected to the support section 1111.

[0057] The transition segment 1112 is mechanically designed to fall between the flexible segment 1110 and the support segment 1111, with a minimum bending radius greater than that of the flexible segment 1110 and smaller than that of the support segment 1111. In other words, from the distal end to the proximal end of the conductive tube 111, the minimum bending radii of the three segments—flexible segment 1110, transition segment 1112, and support segment 1111—gradually increase. This allows the bending stiffness of the conductive tube 111 to change gradually from the distal end to the proximal end. This gradual stiffness distribution effectively disperses the stress generated inside the conductive tube 111 during bending and pushing, reducing the risk of fatigue damage or breakage due to repeated bending. Simultaneously, the smooth stiffness transition provides the doctor with a more consistent feel during the pushing operation, contributing to improved control precision.

[0058] In a specific example, the transition segment 1112 also uses a perforated pattern 1113 to control its minimum bending radius. The perforated pattern 1113 of the flexible segment 1110 is denser than that of the transition segment 1112, meaning that the flexible segment 1110 has more material reduction. The support segment 1111 may not have a perforated pattern 1113, or although it also has a perforated pattern 1113, its material reduction can be controlled to be less than that of the transition segment 1112, thus achieving a minimum bending radius greater than that of the transition segment 1112.

[0059] In some embodiments, the electrode head 120 and the conductive tube 111 are configured as separate structures and are connected together by welding.

[0060] Please refer to Figure 9 In some embodiments, the electrode head 120 and the conductive tube 111 are manufactured using an integral molding process, forming a continuous and complete single-unit structure, thereby eliminating assembly errors that may arise from separate connections. The electrode head 120 includes a connecting portion 121 that is directly and integrally connected to the flexible segment 1110 of the conductive tube 111. This connecting portion 121 serves as a mechanical transition region between the electrode head 120 and the main body of the conductive tube 111, and its structure is configured to have mechanical properties distinct from those of the flexible segment 1110. Specifically, its minimum bending radius is configured to be greater than the minimum bending radius of the flexible segment 1110 to which it is connected.

[0061] In other words, the mechanical properties do not simply continue to soften from the distal end of the conductive tube 111 towards the electrode head 120. Instead, in the connection region of the electrode head 120 adjacent to the flexible section 1110, its bending stiffness increases appropriately, exhibiting relatively higher rigidity. This structure can be achieved by employing different material processing techniques on the connection portion 121 during manufacturing, for example, keeping the tube wall material intact without hollowing it out, or performing localized heat treatment on this area to alter the material's microstructure.

[0062] By providing a more robust connecting portion 121 compared to the soft section 1110, a more stable base is provided for the electrode head 120, which reduces ineffective deformation and makes the structure more stable during puncture or electrocautery operations.

[0063] In some embodiments, the electrode head 120 is configured as a passively deformable elastic structure. Specifically, see [link to documentation]. Figure 6 The electrode head 120 mainly includes a connecting part 121, at least two variable electrodes 122, and a cutting head 123.

[0064] The connector 121 is fixed to the distal end of the conductive tube 111. At least two variable electrodes 122 are spaced apart from each other circumferentially along the connector 121 and extend from the connector 121 in a direction away from the catheter assembly 110. These variable electrodes 122 may be made of a material with excellent elasticity, such as a superelastic nickel-titanium alloy. At the extended end of the variable electrode 122, a blade head 123 is connected to form a tip for performing electrosurgical functions.

[0065] The variable electrode 122 is configured to be able to elastically switch between an expanded state and a contracted state in the radial direction.

[0066] In its natural state, the variable electrode 122, due to the elasticity of its material, maintains a radially outward-spreading position, i.e., it is in a state of... Figure 6 The electrode head 120 is shown in its deployed state, at which point it has a larger working outer diameter. During surgery, when a tubular implant (e.g., a drainage tube 200) already mounted on the catheter assembly 110 needs to be pushed forward, the inner wall of the drainage tube 200 will contact and slide axially over the deployed electrode head 120. During this process, the inner wall of the drainage tube 200 applies a compressive force to the variable electrode 122, forcing it to overcome its elastic potential energy and produce a radially inward elastic deformation towards the central axis. This results in a contraction of the entire electrode head 120's radial dimension, transforming it into a contracted state, allowing it to be housed and pass through the inner lumen of the drainage tube 200.

[0067] When it is necessary to release the drainage tube 200 from the delivery device 100, the electrode head 120 is disengaged from the distal opening of the drainage tube 200 by the relative axial movement between the catheter assembly 110 and the drainage tube 200, thereby releasing the drainage tube 200 from the delivery device 100. Once the outer radial constraint of the inner wall of the drainage tube 200 on the electrode head 120 is removed, the elastic potential energy stored in the variable electrode 122 is immediately released, driving it to automatically return to its initial radially outward unfolded state, preparing for possible subsequent puncture or positioning operations.

[0068] Figure 6 The structural layout of the variable electrode 122 in its deployed state and the connection relationships of its components are shown. This elastically deformable structure allows the electrode head 120 to achieve a safe and smooth transition between its state and that of the drainage tube 200 without the need for a complex external drive mechanism.

[0069] In some embodiments, the surface of the electrode head 120 is further provided with a imaging section 124 for imaging under ultrasound or X-ray, so as to facilitate the doctor's observation of the puncture location and status.

[0070] In some embodiments, the conveying device 100 further includes an inner liner 130. For example... Figures 6 to 9As shown, the inner liner tube 130 is disposed inside the electrode head 120 and extends approximately along the axial direction of the conduit assembly 110.

[0071] Combination Figure 6 Overall schematic diagram and Figure 9 As can be seen in the detailed cross-sectional view, the inner liner tube 130 is located within the internal space enclosed by the connecting portion 121, multiple variable electrodes 122, and the blade head 123. Its tubular body has a closed outer peripheral surface, meaning its tube wall is circumferentially closed, effectively shielding the gaps formed by the circumferential arrangement of adjacent variable electrodes 122. When the guidewire passes through the electrode head 120 region, its movement path is constrained within the inner cavity of the inner liner tube 130. Due to the shielding effect of the inner liner tube 130's wall, the guidewire is effectively isolated within the space enclosed by the variable electrodes 122, thus completely avoiding the risk of the guidewire head accidentally protruding laterally from the gaps between adjacent variable electrodes 122. Even when the variable electrodes 122 undergo elastic deformation or the device is in a bent state, the guidewire can always travel safely within the predetermined central channel, greatly improving the operational reliability and safety of the device.

[0072] In some embodiments, the inner liner 130, in addition to guiding the guidewire and preventing it from protruding, also provides mechanical support to the electrode head 120. For example... Figure 9 As shown in the cross-sectional view, the inner liner tube 130 extends axially between the cutter head 123 and the conductive tube 111. The distal end of the inner liner tube 130 is positioned axially opposite to the cutter head 123, and the proximal end of the inner liner tube 130 is positioned axially opposite to the conductive tube 111. When the cutter head 123 is subjected to a force toward the proximal end, the inner liner tube 130 can provide axial support between the cutter head 123 and the conductive tube 111 to limit the axial deformation of the variable electrode 122.

[0073] Specifically, when the blade head 123 of the electrode head 120 punctures or contacts tissue and experiences a reaction force from the tissue proximally, this force is transmitted throughout the entire electrode head 120 structure. In this case, the distal end of the liner tube 130 remains in contact with the inner side or adjacent structure of the blade head 123, while its proximal end remains in contact with the conductive tube 111. Through this arrangement, the liner tube 130 forms contact points with the blade head 123 and the conductive tube 111 at its axial ends, respectively. When the electrode head 120 punctures, the blade head 123 experiences pressure proximally, which is directly transmitted to the conductive tube 111 through the liner tube 130. Since the conductive tube 111 is constrained by the handle, this force is effectively converted into an axial compressive load on the liner tube 130. The liner tube 130, by virtue of its own axial compressive strength, bears this load, thereby axially restricting further relative proximity between the blade head 123 and the conductive tube 111. This restriction directly reduces the axial compressive deformation that the variable electrode 122 between the connecting head 123 and the connecting part 121 needs to withstand, preventing the variable electrode 122 from undergoing plastic deformation or breakage due to excessive compression, and protecting the structural integrity and reusability of the electrode head 120.

[0074] Optionally, the specific installation and engagement of the inner liner 130 in the device can have different implementations. For example, in one specific example, the distal end of the inner liner 130 is fixedly connected to the blade head 123 by welding, bonding, or interference fit. Simultaneously, the proximal end of the inner liner 130 is configured to movably abut against the conductive tube 111. That is, the contact surfaces between the proximal end and the conductive tube 111 are allowed to separate. In particular, when the variable electrode 122 is squeezed by the drainage tube 200, it contracts radially and elongates axially, during which the distance between the proximal end of the inner liner 130 and the conductive tube 111 also increases. In another example, the distal end of the inner liner 130 and the blade head 123 form a movable abutment, allowing them to move away from each other when the variable electrode 122 elongates axially. The proximal end of the inner liner 130 is then fixedly connected to the conductive tube 111. Alternatively, in other examples, the two ends of the inner liner tube 130 are not connected to the cutter head 123 and the conductive tube 111, and the cutter head 123 and the conductive tube 111 are engaged with the inner liner tube 130 in a movable abutment manner.

[0075] In some embodiments, the conveying device 100 also integrates a handle assembly 140 to facilitate precise control by the operator. Figure 1 , Figure 2 Overall schematic diagram and Figure 7 , Figure 8 , Figure 10 and Figure 11 The handle assembly 140 is located at the proximal end of the catheter assembly 110.

[0076] like Figure 11 and Figure 12 As shown, the handle assembly 140 mainly includes a handle body 141 and a sealing structure 142. The handle body 141 forms the part that the operator holds, and it is connected to the proximal end of the conduit assembly 110, specifically to the conductive tube 111. The sealing structure 142 is connected to the proximal end of the handle body 141, that is, the end away from the conduit assembly 110.

[0077] from Figure 8 , Figure 11 and Figure 12 The cross-sectional view clearly shows that a through-hole 180 is provided inside the entire handle assembly 140. This through-hole 180 starts at the proximal end of the sealing structure 142, passes through the sealing structure 142 and the handle body 141 sequentially, and finally communicates with the inner cavity of the conductive tube 111, thus forming a continuous channel from the proximal end of the handle to the distal end of the device. This through-hole 180 is used for the passage of guidewires and support wires 170, or as a pathway for liquid infusion or aspiration when needed. The sealing structure 142 is used to open and close the through-hole 180 as needed. When the through-hole 180 needs to remain open to allow instrument passage or liquid flow, the sealing structure 142 is in the open state; when it is necessary to prevent blood, bile, or other bodily fluids from backflowing along the through-hole 180, the sealing structure 142 can be activated to close the through-hole 180, achieving a seal.

[0078] In some embodiments, the sealing structure 142 mainly includes a drive member 143 and a seal member 144. The drive member 143 is movably connected to the handle body 141. A channel, referred to as a first channel 181, is machined internally within the drive member 143. The seal member 144 is disposed on the handle body 141 and located between the drive member 143 and the handle body 141. The seal member 144 can be made of an elastic material, such as rubber or silicone, and also has a channel internally, referred to as a second channel 182. A third channel 183 is machined internally within the handle body 141. The first channel 181, the second channel 182, and the third channel 183 are axially aligned and interconnected, forming a complete channel 180 extending from the proximal end of the handle assembly 140 to the inner cavity of the catheter assembly 110. This allows the instrument to pass unobstructed through the entire handle assembly 140.

[0079] The drive element 143 is configured to move axially along the handle assembly 140. When the drive element 143 is driven toward the handle body 141, its end abuts against and axially compresses the seal 144 located in front. After being axially compressed, the seal 144 undergoes radial expansion deformation due to the properties of its elastic material and the constraints of its structure. This radial expansion causes the inner wall of the seal 144, i.e., the channel wall of the second channel 182, to contract inward until it tightly embraces an instrument such as a guide wire or support wire 170 passing through it, or completely seals the channel section when no instrument is present, thereby achieving a fluid seal for the entire channel 180.

[0080] In some embodiments, the drive member 143 is connected to the handle body 141 via a threaded connection. Specifically, matching threads are machined on the outer surface of the handle body 141 and the inner surface of the drive member 143 that mates with the outer surface. Alternatively, matching threads are machined on the inner surface of the handle body 141 and the outer surface of the drive member 143 that mates with the inner surface. The drive member 143 is mounted on the handle body 141 by means of this threaded structure. When the operator rotates the drive member 143, the interaction of the threaded pair converts the rotational motion of the drive member 143 into its linear axial movement relative to the handle body 141. For example, rotating the drive member 143 in one direction causes it to move towards the distal end, i.e., towards the seal 144, while rotating it in the opposite direction causes it to move towards the proximal end. Through this conversion from rotational to linear motion, the drive member 143 can precisely control the magnitude and stroke of the axial compressive force applied to the seal 144, thereby achieving stable and adjustable control of the sealing state. The use of threaded connections helps to provide a clear operating feel and reliable self-locking force.

[0081] Please refer to it again. Figure 12 In one specific example, the handle body 141 has a mounting cavity 1410 at its proximal end. This mounting cavity 1410 communicates with a third channel 183 formed inside the handle body 141. A seal 144 is received and positioned within this mounting cavity 1410. In the assembled state, the second channel 182 formed on the seal 144 and the third channel 183 remain axially aligned and communicated to ensure continuous flow. The drive member 143 includes a pressing portion 1431 and a rotating portion 1432. The pressing portion 1431 extends into the aforementioned mounting cavity 1410. The rotating portion 1432 is connected to the outer periphery of the pressing portion 1431 and is fitted onto the proximal outer side of the handle body 141. A first channel 181 is formed inside the pressing portion 1431.

[0082] To achieve stable and controllable drive, the rotating part 1432 is connected to the handle body 141 via a threaded structure. When the operator rotates the rotating part 1432, the threaded engagement converts the rotational motion into axial movement of the rotating part 1432 and the connected pressing part 1431 relative to the handle body 141. The axial movement of the pressing part 1431 directly acts on the seal 144 within the assembly cavity 1410, thereby achieving precise control over the pressing stroke of the seal 144. This structure combines the convenience of rotary operation with the precision of axial drive and provides reliable mechanical self-locking for sealing operations.

[0083] Optionally, the thread of the handle body 141 can be provided on the outer side of its proximal end, i.e., an external thread, while the thread of the drive member 143 is provided on the inner surface of the rotating part 1432, i.e., an internal thread; or, the thread of the handle body 141 can be provided on the inner wall of its assembly cavity 1410, i.e., an internal thread, while the thread of the drive member 143 is provided on the outer surface of the pressing part 1431, i.e., an external thread.

[0084] In some embodiments, the handle assembly 140 further integrates an infusion function. Specifically, please refer to... Figure 8 and Figure 11 A liquid injection port 190 is provided on the handle assembly 140. This port 190 communicates with a channel 180 passing through the handle assembly 140. The port 190 can also be located on the handle body 141, with its interface leading to a third channel 183 formed inside the handle body 141, thus communicating with the entire continuous channel 180 formed by the first channel 181, the second channel 182, and the third channel 183 connected in series. Through this port 190, the operator can connect an external syringe or other fluid device.

[0085] The operator can connect a syringe through this injection port 190 for negative pressure aspiration. For example, in biliary tract surgery, once the distal end of the device reaches a suspected location, aspiration can be used to observe whether bile is being drawn out, thus helping to determine whether the electrode tip 120 has accurately entered the target bile duct. On the other hand, the injection port 190 can also be used to inject fluids such as saline into the target area for flushing, or to inject contrast agents for X-ray imaging. This integrated structure avoids the need to establish a separate fluid channel outside the instrument, simplifying the surgical procedure and improving the convenience and efficiency of the operation.

[0086] In some embodiments, the handle assembly 140 also integrates an adjustment structure 145 for finely adjusting the axial position of the delivered tubular implant (e.g., drainage tube 200). Please refer to... Figure 7 , Figure 8 , Figure 10 , Figure 11 and Figure 13The adjustment structure 145 mainly includes a positioning element 146 and an adjusting element 147. The positioning element 146 is connected to the distal end of the handle body 141, that is, the end near the connection of the conduit assembly 110. The adjusting element 147 is connected to the positioning element 146 in an axially movable manner, for example, through a sliding sleeve engagement, so that the adjusting element 147 can slide back and forth relative to the positioning element 146 in the axial direction of the device.

[0087] like Figure 13 As shown, the positioning member 146 is constructed as a generally tubular structure, a portion of the adjusting member 147 is axially movably disposed within the positioning member 146, with its distal end extending outside the tubular structure of the positioning member 146, and the conduit assembly 110 is axially disposed through the adjusting member 147. In other embodiments, the positioning member 146 may be constructed as other non-tubular support structures, for example, its main body extending axially on both sides of the adjusting member 147 to achieve assembly and guidance of the adjusting member 147.

[0088] In addition, the delivery device 100 includes an outer tube 150 for mechanical transmission. The outer tube 150 is sleeved around the conduit assembly 110, forming an annular gap between the outer tube 150 and the conduit assembly 110. The proximal end of the outer tube 150 is fixedly connected to the adjusting member 147.

[0089] When the operator manually drives the adjusting member 147 to move axially relative to the positioning member 146, this movement is directly transmitted to the outer tube 150. Since the outer tube 150 is fitted outside the conduit assembly 110 and there is a gap between the outer tube 150 and the conduit assembly 110, the axial movement of the adjusting member 147 will drive the entire outer tube 150 to slide axially in the same direction along the outer surface of the conduit assembly 110.

[0090] When a tubular implant such as a drainage tube 200 is fitted around the periphery of the catheter assembly 110, the distal end of the outer tube 150 can contact or be in a movable position with the proximal end of the drainage tube 200. Therefore, when the outer tube 150 is driven distally by the adjusting member 147, its distal end will push the drainage tube 200 fitted on the catheter assembly 110 distally as well. Through this mechanical transmission method, the operator can fine-tune the axial position of the drainage tube 200 along the catheter assembly 110 by manipulating the adjusting member 147 on the handle without directly contacting the catheter assembly 110 or the drainage tube 200. This allows for precise control of the position of the drainage tube 200 relative to the electrode tip 120, for example, making it closer to the proximal end of the electrode tip 120 to optimize the sealing effect after puncture.

[0091] In some embodiments, the process of fitting the drainage tube 200 from the distal end to the periphery of the catheter assembly 110 is as follows: When the inner wall of the drainage tube 200 contacts the electrode head 120 in its deployed state and continues to advance proximally, an axial compressive force is applied to the electrode head 120. Due to the significant flexibility of the catheter assembly 110, especially the flexible segment 1110 at the distal end of its conductive tube 111, this compressive force causes a certain degree of axial elastic compression of the entire catheter assembly 110, particularly the distal portion. After the drainage tube 200 has completely passed the electrode head 120 and is fitted into the predetermined position, the electrode head 120 extends from the distal end of the drainage tube 200, and the axial compressive force it experiences suddenly disappears. At this time, the previously elastically compressed catheter assembly 110 will return to its original length due to the resilience of its material, causing the electrode head 120 and the distal end of the catheter assembly 110 to extend outward by an unexpected, excessive distance relative to the distal end of the drainage tube 200. If this is not compensated for, at least two problems may arise: First, during subsequent punctures, the excessively long exposed catheter assembly 110 segment may be too soft, affecting the accuracy and force of the puncture; second, after the puncture establishes the channel, the distal end of the drainage tube 200 may not be tightly attached to the proximal end of the electrode head 120, causing bile to leak prematurely from the large gap between the electrode head 120 and the port of the drainage tube 200 during the withdrawal of the electrode head 120.

[0092] To address this issue, this embodiment incorporates the aforementioned adjustment structure 145. After loading the drainage tube 200 and allowing the catheter assembly 110 to return to its natural length, the operator can use the driving adjustment element 147 to move the outer tube 150 distally along the axial direction of the catheter assembly 110. This movement of the outer tube 150 pushes the drainage tube 200 in front of it distally, thereby delivering the drainage tube 200 to a predetermined position closer to the proximal end of the electrode tip 120. This fine-tuning eliminates redundant length caused by the elastic compression and recovery of the catheter assembly 110, maintaining a smaller distance between the drainage tube 200 port and the electrode tip 120. This provides stable support for the puncture procedure and allows the drainage tube 200 port to effectively adhere to the tissue immediately after puncture, minimizing bile leakage and thus improving the safety and effectiveness of the entire surgical procedure.

[0093] In a specific example, when the drainage tube 200 is fitted around the periphery of the catheter assembly 110, the position of the drainage tube 200 relative to the electrode tip 120 can be adjusted by operating the adjustment structure 145, so that the proximal distance between the drainage tube 200 and the electrode tip 120 is 0 mm to 20 mm, optimizing the puncture seal. Optionally, the preferred distance between the distal end of the drainage tube 200 and the proximal end of the electrode tip 120 is 0 mm to 5 mm to further improve the seal and minimize leakage.

[0094] In some embodiments, the adjustment structure 145 also integrates a locking mechanism 148 to improve operational stability and position retention reliability. The locking mechanism 148 reliably locks the adjustment member 147 to multiple different axial positions on the positioning member 146, thereby preventing unintended displacement of the drainage tube 200 due to accidental contact or internal stress of the device itself after the operator has completed fine-tuning of the drainage tube 200.

[0095] Specifically, please refer to Figure 13 and Figure 14 As shown, the locking mechanism 148 mainly comprises two cooperating parts. One part is a toothed portion 1480 disposed on the positioning member 146. The toothed portion 1480 can be configured as grooves, protrusions, or other textured structures with periodic undulations arranged along the axial direction. The other part is an elastic engagement portion 1481 disposed on the adjusting member 147. The elastic engagement portion 1481 includes an engaging component and a component that provides elastic force.

[0096] In its natural state, the elastic engagement portion 1481, under the action of elastic force, keeps its engagement component engaged with the toothed portion 1480 on the positioning member 146. This engagement generates mechanical interference, effectively preventing the adjusting member 147 from sliding freely axially relative to the positioning member 146, thereby firmly locking it in its current position.

[0097] When the operator needs to readjust the position of the drainage tube 200, a force sufficient to overcome its inherent elasticity must be applied to the elastic engagement part 1481. This operation can be achieved by pressing or flicking. Under the action of the external force, the elastic engagement part 1481 is displaced, causing its engaging component to disengage from the toothed portion 1480 of the positioning member 146. Once disengaged, the mechanical interference is released, and the adjusting member 147 can move freely axially on the positioning member 146 to push the drainage tube 200 to a new target position. After reaching the new position, the external force is removed, and the elastic engagement part 1481 automatically resets under the action of the elasticity, and its engaging component re-engages with the toothed portion 1480 in the new axial position, thereby achieving relocking.

[0098] Specifically, the elastic engagement portion 1481 mainly includes an elastic element 1482 and an engagement element 1483.

[0099] The engaging member 1483, as a movable component, is machined with engaging teeth 1484 for engaging with the toothed portion 1480 on the positioning member 146. For example... Figure 14As shown, the meshing teeth 1484 are disposed on the side of the main body of the meshing member 1483, facing towards the meshing teeth 1484. The adjusting member 147 is provided with a slot 1471 for receiving and guiding the meshing member 1483, and a limiting structure 1472 for limiting the movement range of the meshing member 1483 within the slot 1471. The limiting structure 1472 can be a snap-fit ​​structure provided on the side wall of the slot 1471 or within the slot 1471. Correspondingly, the meshing member 1483 is also provided with a snap-fit ​​structure that cooperates with the snap-fit ​​structure. The meshing member 1483 is installed in the slot 1471 of the adjusting member 147 and can slide a certain distance within the slot 1471 in a direction perpendicular to the axial direction.

[0100] The elastic element 1482 can be a compression spring or similar elastic element, which is disposed between the adjusting member 147 and the engaging member 1483. In its natural state, the elastic element 1482 is under pressure or preload, thereby continuously applying a spring force to the engaging member 1483. The direction of this spring force is set to cause the engaging member 1483 to be in the engaged position, where the engaging teeth 1484 on it are tightly engaged with the teeth 1480 on the positioning member 146, thereby achieving stable locking without external force intervention.

[0101] When unlocking is required to adjust the position, the operator applies a pressing force directly or indirectly to the engaging member 1483, the direction of which is opposite to the direction of the elastic force. When the pressing force is greater than the elastic force provided by the elastic member 1482, the engaging member 1483 overcomes the elastic force and moves within the slot 1471. This movement causes the engaging teeth 1484 on it to disengage from the toothed portion 1480 of the positioning member 146, thereby releasing the engagement between the two. Then, the adjusting member 147 can move freely axially relative to the positioning member 146. When the adjustment is in place and the pressing force is removed, the elastic force of the elastic member 1482 will push the engaging member 1483 back to its original position, causing its engaging teeth 1484 to re-engage with the toothed portion 1480 in a new axial position, achieving relocking.

[0102] In one alternative configuration, the elastic element 1482 can be a spring or other component with suitable elasticity. The elastic element 1482 can be installed within a mounting cavity formed by the corresponding structures on the engaging element 1483 and the adjusting element 147, with the resulting elastic force direction approximately perpendicular to the axial direction of the handle assembly 140. The slot 1471 extends in a direction perpendicular to the axial direction. A pressure block for easy application of force can be provided on the engaging element 1483. During operation, pressing this pressure block causes the engaging element 1483 to overcome the elastic force of the elastic element 1482 and move towards the bottom of the slot 1471. This movement causes the engaging teeth 1484 on the engaging element 1483 to disengage from the teeth 1480 on the positioning element 146, thereby releasing the lock on the adjusting element 147. Subsequently, the operator can axially push the adjusting element 147 to adjust the position of the drainage tube 200. Once the adjustment is in place, the pressure on the engaging element 1483 is released. At this point, the elastic force of the elastic element 1482 will push the engaging element 1483 to move outward and reset, causing its engaging teeth 1484 to re-engage with the toothed portion 1480, thereby locking the adjusting element 147 in a new axial position. This process realizes a rapid cycle of unlocking, adjusting, and relocking.

[0103] In a delivery device 100, the handle assembly 140 can simultaneously possess both the sealing structure 142 and the adjustment structure 145, meaning it simultaneously provides both sealing of the channel 180 and adjustment of the position of the tubular implant. Alternatively, the handle assembly 140 may only possess one of the sealing structure 142 and the adjustment structure 145. For example, only the sealing structure 142 is provided without the adjustment structure 145, thus integrating the sealing function of the channel 180; or, for example, only the adjustment structure 145 is provided without the sealing structure 142, thus integrating the adjustment function of the position of the tubular implant. The specific choice can be made according to the needs of the surgery.

[0104] In some embodiments, the conveying device 100 is also equipped with an optional support wire 170 to expand its functional applicability. For example... Figure 8 , Figure 9 and Figure 12 As shown, the support wire 170 is a slender, solid, rigid wire with a diameter set to match the inner cavity of the conductive tube 111, allowing it to be selectively inserted into the internal channel of the conductive tube 111.

[0105] When the support wire 170 is fully inserted and positioned within the conductive tube 111, it significantly increases the overall structural rigidity of the catheter assembly 110. Specifically, the support wire 170 provides built-in skeletal support for the catheter assembly 110. This makes the catheter assembly 110 more axially straight and enhances its bending resistance.

[0106] To facilitate the insertion and removal of the support wire 170, a feature such as... is provided at the end of the support wire 170. Figure 12 The limit head 171 is shown.

[0107] The support wire 170 can be used in at least two types of applications. The first type is during the loading of the drainage tube 200. As previously explained, when the drainage tube 200 is fitted onto the catheter assembly 110 from distal to proximal, the compression of the electrode tip 120 by the drainage tube 200 can cause axial compression of the flexible catheter assembly 110. Therefore, the support wire 170 is pre-inserted into the catheter assembly 110 before loading, providing additional stiffness to help resist this axial compressive force and reduce the compressed length of the catheter assembly 110. The second type of application is in specific surgical procedures. For example, when the target tissue is closely attached to the puncture initiation point (such as the wall of a pancreatic pseudocyst and the gastric wall), there is a clinical need for a direct puncture technique, i.e., without pre-positioning a guidewire, directly using the electrode tip 120 of the delivery device 100 for electrocautery puncture. In this mode, the catheter assembly 110, which has a certain degree of flexibility under normal conditions, may not easily provide sufficient advancement stability. At this point, inserting the support wire 170 temporarily transforms the entire catheter assembly 110 and electrode tip 120 assembly into a more rigid puncture instrument, which can assist in the stable and precise establishment of the initial channel. The support wire 170 eliminates the need for guidewire insertion, improving surgical efficiency.

[0108] Accordingly, this application also provides an endoscopic surgical device 10, which is a complete system that can be directly used for specific clinical surgeries. For example... Figure 1 As shown, the device mainly consists of the aforementioned two parts: a conveying device 100 and a drainage pipe 200.

[0109] The delivery device 100 is the structure described in detail in any of the foregoing embodiments of this application, and it features a catheter assembly 110, a retractable and deployable electrode head 120, and a multi-functional handle assembly 140. The drainage tube 200 is an independent implantable medical device, and its structure and size are configured to fit and be fitted around the catheter assembly 110 of the delivery device 100. The endoscopic surgical device 10 can be equipped with one or more drainage tubes 200 according to the specific surgical needs.

[0110] The delivery device 100 is responsible for a series of active operations, including establishing the channel and positioning the device. The drainage tube 200, acting as the delivered load, is released and left in place at the target location to perform its final therapeutic functions, such as drainage and support. During the procedure, the surgeon does not need to repeatedly exchange between the traditional, separate electrode instruments and the drainage tube 200. This effectively reduces problems such as tissue fluid leakage, loss of target location, and prolonged operation time that may be caused by repeated insertion and removal of instruments from the patient's body cavity.

[0111] In some embodiments, please refer again Figure 1 and Figure 2 As shown, the length of the flexible section 1110 of the delivery device 100 is L1, and the length of the drainage tube 200 to be delivered, which is sleeved on the outer periphery of the conduit assembly 110, is L2. The two satisfy the relationship: 1 / 4 ≤ L1 / L2 ≤ 5. That is, the length of the flexible section 1110 is 1 / 4 to 5 times the length of the drainage tube 200 to be delivered. For example, the length of the flexible section 1110 can be 1 / 4, 2 / 5, 1 / 2, 2 / 3, 3 / 4, 4 / 5, 5 / 6, 6 / 7, 7 / 8, etc., of the length of the drainage tube 200 to be delivered, or the two can be equal, or the length of the flexible section 1110 can be 2, 3, 4, 5, etc., of the length of the drainage tube 200 to be delivered.

[0112] By setting the length relationship between the two within the aforementioned range, a sufficiently long soft area is provided to continuously perform its function of compliantly tracking the guidewire path during the process of the drainage tube 200 being pushed to the target position and released, ensuring the accuracy of the push.

[0113] For example, for a common drainage tube 200 with a length of 70mm to 200mm, the length of the flexible segment 1110 of the matching catheter assembly 110 can be set to 17.5mm to 1000mm accordingly. This setting allows the flexible segment 1110 to fully conform to various curved paths and adapt to the length requirements of internal cavities.

[0114] In some embodiments, to improve surgical outcomes and prevent leakage, such as Figure 9As shown, in the deployed state where the variable electrode 122 of the electrode head 120 is radially outward, the maximum outer diameter D1 of the electrode head 120 is set to be smaller than the maximum outer diameter D2 of the drainage tube 200 to be delivered. This maximum outer diameter D2 is the position with the maximum outer diameter of the tissue portion to be implanted at the distal end of the drainage tube 200, and the diameter difference between the two is controlled within the range of 0.1 mm to 0.5 mm. For example, it can be any value among 0.1 mm, 0.2 mm, 0.3 mm, 0.4 mm, and 0.5 mm, or a range between any two values. When the electrode head 120 is energized to cut tissue, the diameter of the channel it forms on the target tissue is approximately equal to the maximum outer diameter of the electrode head 120 itself. Because this outer diameter is slightly smaller than the maximum outer diameter of the drainage tube 200, the subsequently pushed drainage tube 200 will slightly expand the tissue channel to pass through, thereby forming a tight fit with the tissue after implantation and generating a certain radial pressure. This effectively prevents tissue fluid from leaking along the gap between the outer wall of the drainage tube 200 and the tissue channel. Meanwhile, setting the upper limit of the difference to 0.5mm ensures that the channel is not too small to obstruct the smooth passage of the drainage tube 200 or cause excessive damage to the tissue; setting the lower limit of the difference to 0.1mm ensures the sealing effect after the drainage tube 200 is implanted, reducing the risk of sealing failure due to excessive gap.

[0115] In some embodiments, the maximum outer diameter D1 of the electrode head 120 in its unfolded state is greater than the inner diameter D3 of the drainage tube 200. Specifically, the drainage tube 200 is a tubular structure with a certain wall thickness, typically 0.4 mm to 0.6 mm. Its inner diameter D3 is necessarily smaller than its maximum outer diameter D2, and the inner diameter D3 is 0.8 mm to 1.2 mm smaller than the maximum outer diameter D2. The fact that the maximum outer diameter D1 of the electrode head 120 is greater than the inner diameter D3 of the drainage tube 200 allows the electrode head 120 to be compressed by the inner wall of the drainage tube 200 and undergo radial contraction when the drainage tube 200 passes over the unfolded electrode head 120 again, thereby achieving relative movement between the two.

[0116] In some embodiments, a imaging structure 210 is also provided on the drainage tube 200. See also Figure 1 The imaging structure 210 is typically disposed on the wall of the drainage tube 200 in the form of dots, rings, or other regular patterns. Common placement locations include the distal and proximal ends of the drainage tube 200. The imaging structure 210 is made of a material capable of generating high-contrast signals under medical imaging; for example, for ultrasound imaging, a coating containing microbubbles or a special polymer material may be used; for X-ray imaging, barium rings or metal markers may be embedded.

[0117] During the procedure, once the drainage tube 200 is released by the delivery device 100 and placed in the target tissue, the doctor can observe it using real-time imaging equipment such as ultrasound and X-ray. At this time, the imaging structure 210 on the drainage tube 200 will be clearly displayed in the image, thereby helping the doctor to accurately determine the actual positions of both ends of the drainage tube 200 and confirm whether it is fully deployed and located in the predetermined area.

[0118] This application embodiment also provides an operation method for the above-described endoscopic surgical device 10. This operation method is used to transport the drainage tube 200 using the delivery device 100 of any of the foregoing embodiments. It enables the reusability of a single delivery device 100 to efficiently complete the sequential placement of multiple drainage tubes 200.

[0119] Figure 15 The flowchart clearly shows the steps and loops involved in this operation method.

[0120] During the delivery preparation phase, the drainage tube 200 is first loaded into the delivery device 100. Specifically, during the surgical preparation phase, the operator (such as a doctor or nurse) manually places a drainage tube 200 around the periphery of the catheter assembly 110 of the delivery device 100. During loading, the drainage tube 200 can be inserted from the distal end of the catheter assembly 110 and pushed axially along the catheter assembly 110 to a predetermined starting position near the handle assembly 140 (see the description of the adjustment structure 145 above).

[0121] During delivery, the operator manipulates the delivery device 100 to deliver and release the drainage tube 200: In this step, the operator holds the handle assembly 140 of the delivery device 100 and inserts it into the body through the working channel of the endoscope. Inside the body, the device can be guided along a pre-placed guidewire to the target tissue area, or in some cases, directly through puncture using its electrode tip 120 to establish a channel. The outer tube 150 is pushed by the adjustment structure 145 on the handle assembly 140, which in turn pushes the drainage tube 200, which is fitted onto the catheter assembly 110, distally. When the drainage tube 200 reaches the target location, for example, crossing the established puncture channel, with part of it inside the cavity and part outside, the tube 200 is then withdrawn from the distal end of the drainage tube 200 by retracting the catheter assembly 110 and the electrode tip 120, leaving the drainage tube 200 in place in the tissue, thus completing the release.

[0122] Withdrawal of delivery device 100 and indwelling drainage tube 200: After confirming that the drainage tube 200 is released and secured, the operator keeps the drainage tube 200 in place while withdrawing the entire delivery device 100 from the patient's body through the endoscope's working channel. After this step, the delivery device 100 is completely removed from the body, while the first drainage tube 200 is left alone and stably in place at the target location within the body.

[0123] After completing the first loading, delivery, release, and withdrawal cycle, the delivery device 100 is now in an idle state outside the body. At this point, another drainage tube 200 can be loaded. That is, the operator attaches a second, brand-new drainage tube 200 to the periphery of the same catheter assembly 110 of the same delivery device 100 in the same manner. Subsequently, the delivery device 100 is operated again to deliver and release the second drainage tube 200, placing it at the same or different target location as the first tube, and then the delivery device 100 is withdrawn again. This loading, delivery, release, and withdrawal cycle can be repeated multiple times as needed clinically.

[0124] Using this method, a single delivery device 100 can serve as a reusable, universal delivery platform, assisting surgeons in sequentially implanting multiple drainage tubes 200 into the body during a single surgery. This not only avoids the need to prepare and use a separate, entirely new delivery instrument for each drainage tube 200, significantly saving on consumable costs, but more importantly, it eliminates the risks of time delays, increased tissue trauma, and accumulated positioning errors associated with repeatedly inserting and removing different instruments completely from the body cavity when placing multiple drainage tubes 200, as is done in traditional methods.

[0125] This application embodiment also provides another operating method for the endoscopic surgical device 10 described above, which is also based on the delivery device 100 of any of the foregoing embodiments. Unlike the foregoing operating methods, this method involves a single intervention into the body cavity to continuously deliver and release multiple drainage tubes 200.

[0126] Figure 16 The flowchart clearly illustrates the loop of steps involved in this method.

[0127] and Figure 15 The operating methods shown are different. Figure 16 The procedure shown involves pre-loading at least two drainage tubes 200 sequentially onto the delivery device 100 during the delivery preparation phase. Before the surgery begins, the operator manually and coaxially loads at least two drainage tubes 200 onto the periphery of the catheter assembly 110 of the delivery device 100. For example, the first drainage tube 200 is pushed to an initial position near the distal end of the catheter assembly 110, the second drainage tube 200 is then loaded into a position closer to the proximal end, and so on. This pre-loading ensures that multiple implants are in place before the delivery device 100 enters the body.

[0128] Initial delivery and release of the first drainage tube 200: The operator inserts the delivery device 100, which has been loaded with multiple drainage tubes 200, into the body through the endoscopic channel in one go and guides it to the target area. By operating the handle assembly 140, the device delivers the first drainage tube 200 (i.e., the most distal one) to the first position in the target tissue and releases it by actions such as retracting the catheter assembly 110, leaving it in place at that position. At this time, the main body of the delivery device 100 remains in the body, and the subsequent drainage tubes 200 are still attached to the catheter assembly 110.

[0129] Without withdrawing the delivery device 100, subsequent drainage tubes 200 are continuously delivered and released: after the first drainage tube 200 is released, the operator does not need to withdraw the delivery device 100 from the body cavity. Instead, by continuing to operate the adjustment structure 145 of the handle assembly 140, the outer tube 150 can be driven to push the second drainage tube 200 distally, allowing it to move relative to the catheter assembly 110 and be delivered to a different point in the same target tissue, or to another adjacent target tissue location, before being released and left in place. This push, positioning, and release process can be repeated according to the number of pre-loaded drainage tubes 200 until all drainage tubes 200 have been released.

[0130] After all releases are completed, the delivery device 100 is removed: After all drainage tubes 200 have been successfully released and left in place, the operator removes the entire delivery device 100 from the patient's body.

[0131] This method compresses the placement of multiple drainage tubes 200, which traditionally required multiple entry and exit cycles, into a single interventional procedure. This significantly reduces the total operative time and minimizes the risk of tissue irritation, trauma, and potential complications caused by repeated instrument entry and exit. It provides a smoother, faster, and less invasive solution for clinical situations requiring the placement of multiple drainage tubes 200.

[0132] Corresponding to Figure 15 The operation method shown in this application embodiment also provides a delivery method for delivering the drainage tube 200, which includes the following steps: S101. Loading step: Fit a single drainage tube 200 onto the outer periphery of the catheter assembly 110 of a delivery device 100, wherein the delivery device 100 includes the catheter assembly 110 and an electrode head 120 disposed at its distal end. S102. Stoma and / or dilation procedure: Operate the delivery device 100 to establish a puncture channel at the target tissue using its electrode head 120; S103. Release and retention steps: Advance the drainage tube 200 along the catheter assembly 110 to insert the drainage tube 200 into the puncture channel established in the aforementioned steps and reach the target position; by retracting the catheter assembly 110 and the electrode head 120, the electrode head 120 is dislodged from the distal end of the drainage tube 200, leaving the drainage tube 200 in place at the target position in the tissue; S104. Withdrawal procedure: Withdraw the delivery device 100 from the endoscope instrument channel.

[0133] For surgeries requiring the implantation of multiple drainage tubes 200, the delivery method also includes: S105. Repeat the steps: For the subsequent drainage tube 200, repeat the above steps until withdrawal, i.e., steps S101 to S104, to deliver the subsequent drainage tube 200 to the same or different target tissue locations.

[0134] In some embodiments, after fitting the drainage tube 200 to the periphery of the catheter assembly 110 of the delivery device 100, the delivery method further includes pushing the drainage tube 200 distally so that the drainage tube 200 and the electrode tip 120 meet a target distance. The target distance can be a distance of 0 mm to 20 mm between the proximal end of the drainage tube 200 and the electrode tip 120. This allows the drainage tube 200 to promptly conform to the puncture channel during the stoma and / or dilation steps, reducing the possibility of leakage.

[0135] The outer tube 150 of the delivery device 100 can be moved to the distal end by operating the handle assembly 140 of the delivery device 100 and using the adjustment structure 145 on the handle assembly 140, thereby advancing the drainage tube 200 along the conduit assembly 110.

[0136] For some surgeries, at least one of the following methods can be used to determine whether the drainage tube 200 has reached the appropriate position: bile aspiration or contrast agent preparation.

[0137] Of course, experienced operators can determine the position of the drainage tube 200 directly based on their experience, without having to use methods such as aspirating bile or creating contrast agents.

[0138] Bile or contrast agent can be drawn through the injection port 190 on the handle assembly 140 via the channel 180. Before drawing bile or contrast agent, the channel 180 can be sealed distally by the sealing structure 142 on the handle assembly 140.

[0139] In some surgeries, the drainage tube 200 can also be visualized by ultrasound or X-ray to determine whether the drainage tube 200 has reached the appropriate position.

[0140] Corresponding to Figure 16The present application embodiment also provides a conveying method for conveying the drainage tube 200, which differs from the aforementioned conveying method. This conveying method includes the following steps: S201. Preloading step: At least two drainage tubes 200 are sequentially fitted onto the outer periphery of the catheter assembly 110 of a delivery device 100, wherein the delivery device 100 includes the catheter assembly 110 and an electrode head 120 disposed at its distal end. S202. Stoma and / or dilation procedure: Operate the delivery device 100 to establish a puncture channel at a first location in the target tissue using its electrode head 120; S203. Initial release and placement steps: Advance the drainage tube 200 along the catheter assembly 110 so that the first drainage tube 200 is inserted into the puncture channel established in the aforementioned steps and reaches the target position; by retracting the catheter assembly 110 and the electrode head 120, the electrode head 120 is dislodged from the distal end of the first drainage tube 200, leaving the first drainage tube 200 in the first position; S204. Continuous delivery and release step: Without withdrawing the delivery device 100, continue to operate the delivery device 100 to sequentially advance and release the subsequent drainage tubes 200 at the same or different positions of the target tissue; S205. Withdrawal procedure: After all drainage tubes 200 have been released, withdraw the delivery device 100 from the endoscopic instrument channel.

[0141] In some embodiments, after fitting at least two drainage tubes 200 to the periphery of the catheter assembly 110 of the delivery device 100, the delivery method further includes pushing the drainage tubes 200 distally so that the first drainage tube 200 and the electrode tip 120 meet a target distance. The target distance can be a distance of 0 mm to 20 mm between the first drainage tube 200 and the proximal end of the electrode tip 120. This allows the drainage tubes 200 to promptly conform to the puncture channel during the stoma and / or dilation steps, reducing the possibility of leakage.

[0142] The outer tube 150 of the delivery device 100 can be moved to the distal end by operating the handle assembly 140 of the delivery device 100 and using the adjustment structure 145 on the handle assembly 140, thereby advancing the drainage tube 200 along the conduit assembly 110.

[0143] For some surgeries, at least one of the following methods can be used to determine whether the drainage tube 200 has reached the appropriate position: bile aspiration or contrast agent preparation.

[0144] Of course, experienced operators can determine the position of the drainage tube 200 directly based on their experience, without having to use methods such as aspirating bile or creating contrast agents.

[0145] Bile or contrast agent can be drawn through the injection port 190 on the handle assembly 140 via the channel 180. Before drawing bile or contrast agent, the channel 180 can be sealed distally by the sealing structure 142 on the handle assembly 140.

[0146] In some surgeries, the drainage tube 200 can also be visualized by ultrasound or X-ray to determine whether the drainage tube 200 has reached the appropriate position.

[0147] In the description of this application, the terms "first" and "second" are used for descriptive purposes only and should not be construed as indicating or implying relative importance or implicitly specifying the number of technical features indicated. Therefore, a feature defined as "first" or "second" may explicitly or implicitly include one or more features. In the description of this application, "multiple" means two or more, unless otherwise explicitly specified.

[0148] In the above embodiments, the descriptions of each embodiment have different focuses. For parts not described in detail in a certain embodiment, please refer to the relevant descriptions in other embodiments.

[0149] The embodiments, implementation methods, and related technical features of this application can be combined and substituted for each other without conflict.

[0150] The above are merely preferred embodiments of this application and are not intended to limit this application in any way. Any simple modifications, equivalent changes, and alterations made to the above embodiments based on the technical essence of this application without departing from the scope of the technical solution of this application shall still fall within the scope of the technical solution of this application.

Claims

1. A conveying device, characterized in that, include: Catheter assembly; An electrode tip is disposed at the distal end of the catheter assembly; The catheter assembly includes a conductive tube and a coating layer covering the outer periphery of the conductive tube; the conductive tube includes a flexible segment and a support segment arranged along its axial direction, the flexible segment being connected to the electrode head, and the support segment being closer to the proximal end of the catheter assembly than the flexible segment; wherein the minimum bending radius of the flexible segment is smaller than the minimum bending radius of the support segment.

2. The conveying device according to claim 1, characterized in that, The minimum bending radius of the flexible segment is 5 mm to 50 mm.

3. The conveying device according to claim 1, characterized in that, The flexible section has a hollowed-out pattern formed on its tube wall.

4. The conveying device according to claim 3, characterized in that, The hollowed-out pattern extends in a spiral shape.

5. The conveying device according to claim 3, characterized in that, The hollow pattern is an opening that penetrates the thickness of the conductive tube wall, or the hollow pattern is a groove that extends to the depth of a portion of the conductive tube wall thickness.

6. The conveying device according to claim 1, characterized in that, The minimum bending radius of the conductive tube increases continuously or in a stepwise manner from its distal end to its proximal end.

7. The conveying device according to claim 1, characterized in that, The conductive tube further includes a transition section located between the flexible section and the supporting section, wherein the minimum bending radius of the transition section is greater than the minimum bending radius of the flexible section and less than the minimum bending radius of the supporting section.

8. The conveying device according to any one of claims 3 to 7, characterized in that, The electrode head and the conductive tube are integrally formed. The electrode head includes a connecting portion connected to the flexible segment, wherein the minimum bending radius of the connecting portion is greater than the minimum bending radius of the flexible segment.

9. The conveying device according to claim 1, characterized in that, The electrode head includes: The connecting part is fixedly connected to the flexible segment; At least two variable electrodes are arranged circumferentially at intervals along the connection portion and extend distally from the connection portion; The blade head is connected to the distal end of the variable electrode; The variable electrode is configured to be able to elastically switch between an expanded state and a contracted state in the radial direction.

10. The conveying device according to claim 9, characterized in that, The conveying device further includes an inner liner tube disposed inside the electrode head and extending axially; the wall of the inner liner tube is configured to block the gap formed by the at least two variable electrodes being arranged at intervals in the circumferential direction.

11. The conveying device according to claim 10, characterized in that, The inner liner extends axially between the blade head and the conductive tube, with the distal end of the inner liner being axially opposite to the blade head and the proximal end of the inner liner being axially opposite to the conductive tube. When the cutter head is subjected to a force toward the proximal end, the inner liner can provide axial support between the cutter head and the conductive tube to limit the axial deformation of the variable electrode.

12. The conveying device according to claim 11, characterized in that, The distal end of the inner liner is fixedly connected to the blade head, and the proximal end of the inner liner is used to movably abut against the conductive tube; or, The distal end of the inner liner tube is movably abutted against the blade head, and the proximal end of the inner liner tube is used for fixed connection with the conductive tube; or, The distal end of the inner liner tube is used to movably abut against the blade head, and the proximal end of the inner liner tube is used to movably abut against the conductive tube.

13. The conveying device according to claim 1, characterized in that, The conveying device further includes a handle assembly, the handle assembly comprising: The handle body is connected to the proximal end of the conductive tube; A sealing structure is connected to the proximal end of the handle body; The handle assembly has a channel that passes through the handle body and the sealing structure. The channel is connected to the conductive tube, and the sealing structure is used to seal the channel.

14. The conveying device according to claim 13, characterized in that, The sealing structure includes: A drive component is movably connected to the handle body, and a first channel is formed on the drive component; A seal is disposed between the drive member and the handle body, and a second channel is formed on the seal; The handle body has a third channel, and the first channel, the second channel and the third channel are connected and together form the channel. The drive element is configured to move relative to the handle body to axially compress the seal, causing radial deformation of the seal to seal the passage.

15. The conveying device according to claim 14, characterized in that, The drive unit is threadedly connected to the handle body, and the rotational motion of the drive unit can be converted into axial movement relative to the handle body to compress the seal.

16. The conveying device according to claim 14, characterized in that, The handle body has a proximal end with an assembly cavity communicating with the third channel, the seal is disposed in the assembly cavity, and the second channel is aligned and communicates with the third channel; The drive component includes a pressing part extending into the assembly cavity and a rotating part connected to the outer periphery of the pressing part and sleeved on the proximal end of the handle body, wherein the first channel is formed in the pressing part; The rotating part is connected to the handle body by a thread to drive the extrusion part to move axially.

17. The conveying device according to claim 13, characterized in that, The handle body is also provided with an injection port that communicates with the channel.

18. The conveying device according to claim 1, characterized in that, The conveying device further includes a handle assembly, the handle assembly comprising: The handle body is connected to the proximal end of the conductive tube; An adjustment structure, comprising a positioning element and an adjustment element, wherein the positioning element is connected to the distal end of the handle body, and the adjustment element is connected to the positioning element; The delivery device further includes an outer tube sleeved around the periphery of the conduit assembly, the outer tube being connected to the adjusting member; The adjusting member is configured to move axially relative to the positioning member, thereby driving the outer tube to move axially along the conduit assembly.

19. The conveying device according to claim 18, characterized in that, The adjustment structure also includes a locking mechanism configured to lock the adjustment member at different axial positions of the positioning member.

20. The conveying device according to claim 19, characterized in that, The locking mechanism includes: The toothed portion is provided on the positioning member; An elastic engagement portion is provided on the adjusting member; The elastic meshing part engages with the toothed part under the action of elastic force.

21. The conveying device according to claim 20, characterized in that, The elastic engagement portion includes: Elastic components; A meshing member having meshing teeth for meshing with the toothed portion; The adjusting member is provided with a slot for inserting the engaging member and a limiting structure for limiting the engagement member. The engaging member is installed in the slot, and the elastic member is disposed between the adjusting member and the engaging member, and applies an elastic force to the engaging member to make it tend to engage with the toothed portion; The engaging member is configured to overcome the elastic force of the elastic member and move within the slot when pressed, so that the engaging teeth disengage from the toothed portion.

22. The conveying device according to claim 1, characterized in that, The conveying device also includes a support wire, which is configured to be inserted into the conductive tube to increase the rigidity of the conductive tube.

23. An endoscopic surgical device, characterized in that, include: The conveying device as described in any one of claims 1 to 22, and, A drainage tube, which can be fitted around the periphery of the catheter assembly.

24. The endoscopic surgical device according to claim 23, characterized in that, The length of the flexible segment is L1, and the length of the drainage tube sleeved around the periphery of the catheter assembly is L2, satisfying: 1 / 4≤L1 / L2≤5.

25. The endoscopic surgical device according to claim 23, characterized in that, The electrode head of the delivery device includes at least two variable electrodes. When the variable electrodes are in the deployed state, the maximum outer diameter of the electrode head is smaller than the maximum outer diameter of the drainage tube sleeved on the outer periphery of the catheter assembly, and the difference between the two is 0.1 mm to 0.5 mm.

26. The endoscopic surgical device according to claim 23, characterized in that, The distance between the distal end of the drainage tube, which is fitted around the periphery of the catheter assembly, and the proximal end of the electrode tip is 0 mm to 20 mm, or 0 mm to 5 mm.

27. The endoscopic surgical device according to claim 23, characterized in that, The drainage tube is equipped with an ultrasound and / or X-ray imaging structure.

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