Multifunction integrated ultra-fine diameter bidirectional controllable bending endoscope

Abstract

The application discloses a multifunctional integrated ultra-fine diameter bidirectional controllable bending endoscope, which comprises a handle, a catheter, an adjusting unit and the like.

Description

Technical Field

[0001] This invention relates to the field of medical device technology, specifically to a multifunctional integrated ultra-fine diameter bidirectional controllable curved vascular endoscope. Background Technology

[0002] A vascular endoscope is a medical device that can directly observe lesions inside blood vessels. It obtains images of the inner wall of blood vessels in real time by inserting a miniature imaging probe into the lumen of the blood vessel. It is widely used in the diagnosis and interventional treatment of cardiovascular, cerebrovascular and peripheral vascular diseases. As interventional medicine develops towards precision and minimally invasive techniques, clinical practice has placed higher demands on the performance of vascular endoscopes, especially for small intracranial vessels, terminal branches of coronary arteries and areas of severe stenosis.

[0003] However, current vascular endoscopes still have the following shortcomings:

[0004] Firstly, in traditional endoscopes, a snake-like joint composed of multiple riveted metal rings is generally used to achieve angular deflection. To achieve sufficient bending flexibility and angular range, the snake-like segments usually need a certain axial length and radial wall thickness. Bending is generated by the relative rotation between the segments. However, this is only suitable for endoscopes or guide tubes with a diameter of about 2.5 mm or larger. When the diameter is reduced to the 1 mm level, it is difficult to achieve the segment ring cutting and riveting assembly within the 1 mm dimension. The processing accuracy and consistency cannot be guaranteed. Even if it is achieved, the wall thickness and riveting structure itself occupy a certain radial dimension. Within the 1 mm outer diameter, there is almost no remaining space to accommodate imaging, illumination, traction wires, and fluid channels.

[0005] Secondly, the guidewire channel and irrigation / flushing channel of traditional endoscopes are usually set as two independent cavities, each occupying an independent cross-sectional area. Under the premise of a fixed total cross-sectional area, the effective flow cross-sectional area of ​​each is compressed, and the double tube wall repeatedly occupies space, resulting in low cross-sectional utilization.

[0006] Therefore, due to the mutual constraints of multiple structures, the minimum outer diameter of traditional endoscopes is usually ≥1.5mm, making it difficult to enter the terminal blood vessels and distal branches of the coronary arteries with a diameter of less than 1.5mm in the intracranial cavity. During the operation, the only way to make an indirect judgment is to rely on X-ray angiography, which restricts the further improvement of surgical precision. Summary of the Invention

[0007] To address the shortcomings of existing technologies, this invention provides a multifunctional integrated ultra-fine diameter bidirectional controllable bending vascular endoscope, which solves the problem that existing vascular endoscopes cannot effectively reduce size.

[0008] According to an embodiment of the present invention, a multifunctional integrated ultra-fine diameter bidirectional controllable bending vascular endoscope includes:

[0009] handle;

[0010] The catheter has a bend control section and a fixed section. The fixed section is installed inside the handle and extends to one end of the handle. The bend control section extends to the other end of the handle. The bend control section is equipped with an imaging module and a side tube. The imaging module is located at the end of the bend control section. The side tube is arranged along the axial direction of the catheter and fits against the outer wall of the bend control section. It also has a guide channel that runs through both ends. The fixed section is also provided with an injection channel that runs through the outer wall of the bend control section.

[0011] An adjustment unit is located on the handle and connected to the bend control section of the catheter, used to drive the bend control section of the catheter to bend.

[0012] Preferably, the adjustment unit includes:

[0013] Two traction wires are inserted inside the conduit and arranged in a mirror image, with one end of each wire fixedly connected to the end of the bend control section.

[0014] The cable gathering wheel has a second mounting seat inside the handle. The cable gathering wheel is rotatably mounted on the second mounting seat and has two cable gathering grooves. The two cable gathering grooves are spaced apart along the axis of the cable gathering wheel. The other ends of the two traction wires pass through the fixed section of the guide tube and are wound in the two cable gathering grooves respectively, and the winding directions are opposite.

[0015] A locking element is located on the handle and is used to lock the cable reel.

[0016] Preferably, the locking element includes:

[0017] The worm gear is fixedly mounted on the end face of the wire feeder.

[0018] The worm gear is located inside the handle and meshes with the worm wheel.

[0019] Preferably, the handle is further provided with a first mounting seat inside, the first mounting seat is rotatably provided with a driving gear, one end of the worm gear is provided with a driven gear, the driven gear meshes with the driving gear, and the outer side of the handle is provided with a pulsator, the shaft of the driving gear is connected to the pulsator.

[0020] Preferably, the bend control section of the catheter is provided with an alloy ring, and both traction wires are connected to the alloy ring.

[0021] Preferably, the second mounting base is also provided with a guide groove, and a partition is fixed in the middle of the guide groove to separate the two traction wires.

[0022] Preferably, the side of the side tube has a liquid outlet, which is connected to the liquid injection channel.

[0023] Preferably, both ends of the side tube are provided with guide slopes.

[0024] Preferably, the catheter comprises, from the inside out, a PTFE inner layer, a braided reinforcement layer, and a PEBAX outer layer, and the outer surface of the catheter has a hydrophilic coating.

[0025] Preferably, the first mounting base also has a glue-fixing port, through which the fixing section of the conduit passes.

[0026] Compared with the prior art, the present invention has the following beneficial effects:

[0027] In this design, firstly, the catheter includes a bending control section and a fixing section. The bending control section achieves bidirectional bending through an adjustment unit, eliminating the need to fabricate joints or other structures within a very small space. Simultaneously, the side tube is fitted to the outer wall of the bending control section rather than being built into the catheter, thus not occupying internal cross-sectional space and allowing other accessories to be rationally arranged within a 1mm outer diameter, achieving multi-functional integration. Secondly, the side tube, fitted to the outer wall of the bending control section, has a guiding channel running through both ends for guidewire insertion. The fixing section has an injection channel that extends through the outer wall of the bending control section, providing flushing functionality. The side tube and injection channel intersect and connect, enabling single-channel reuse; the same channel can be used for both guidewire passage and perfusion fluid delivery. Due to its ultra-fine outer diameter, this design effectively reduces friction and lateral stress on the vessel wall, allowing for smooth access to intracranial peripheral vessels, distal coronary branches, and other vascular regions. Attached Figure Description

[0028] Figure 1 This is a schematic diagram of the planar structure of the endoscope in an embodiment of the present invention.

[0029] Figure 2 for Figure 1 A magnified structural diagram of region A in the middle.

[0030] Figure 3 for Figure 1 A magnified structural diagram of region B in the middle.

[0031] Figure 4 for Figure 1 A magnified structural diagram of region C in the middle.

[0032] Figure 5 This is a three-dimensional structural diagram of the catheter tip in an embodiment of the present invention.

[0033] Figure 6 This is a three-dimensional structural diagram of the traction wire installed on the feeder wheel in an embodiment of the present invention.

[0034] In the above attached figures:

[0035] 1. Catheter; 101. Imaging module; 102. Alloy ring; 103. Traction wire; 104. Injection channel;

[0036] 2. Side tube; 201. Guide channel; 202. Liquid outlet; 203. Guide slope;

[0037] 3. Handle; 301. First mounting base; 302. Second mounting base; 303. Guide groove; 304. Spacer; 305. Glue opening;

[0038] 4. Worm gear;

[0039] 5. Cable feeder wheel; 501. Cable feeder trough;

[0040] 6. Impeller; 601. Drive gear;

[0041] 7. Worm gear; 701. Driven gear. Detailed Implementation

[0042] The technical solutions of the present invention will be further described below with reference to the accompanying drawings and embodiments.

[0043] This invention provides a multifunctional integrated ultra-fine diameter bidirectional controllable curved vascular endoscope, comprising:

[0044] Handle 3;

[0045] The catheter 1 has a bending control section and a fixing section. The fixing section is installed inside the handle 3 and extends to one end of the handle 3. The bending control section extends to the other end of the handle 3. The bending control section is provided with an imaging module 101 and a side tube 2. The imaging module 101 is located at the end of the bending control section. The side tube 2 is arranged along the axial direction of the catheter 1 and fits against the outer wall of the bending control section. It also has a guide channel 201 that runs through both ends. The fixing section is also provided with an injection channel 104 that runs through the outer wall of the bending control section.

[0046] An adjustment unit is located on the handle 3 and connected to the bending control section of the conduit 1, used to drive the bending control section of the conduit 1 to bend.

[0047] like Figure 1 , Figure 2 , Figure 4 and Figure 5As shown, in this embodiment, the handle 3 is hollow inside to accommodate the fixed section of the conduit 1 and the related transmission components of the adjustment unit. In terms of shape, it can be set as an ergonomic non-slip grip structure, which makes it easy for the operator to hold it stably with one hand. For catheter 1, catheter 1 has a bending control section and a fixing section. The fixing section extends from one end of the handle 3, and the bending control section extends from the other end of the handle 3. The two are fixed relative to each other and are used to anchor catheter 1 inside the handle 3. The bending control section is a flexible section that can be actively bent. Its hardness is designed with a gradual change. The distal wall is thinner and more flexible, while the proximal support section has increased hardness, which takes into account both distal compliance and overall pushing support force. It is used to bend in a directional manner under the control of the operator to guide it into the target blood vessel branch. Preferably, catheter 1 includes a PTFE inner layer, a braided reinforcement layer and a PEBAX outer layer from the inside to the outside. The outer surface of catheter 1 has a hydrophilic coating. The PTFE inner layer provides a low-friction inner surface. The braided reinforcement layer is made of stainless steel wire or nickel-titanium wire and provides anti-torsion performance and axial support force to prevent lumen collapse. The PEBAX outer layer provides moderate flexibility, while the hydrophilic coating can reduce the frictional resistance of catheter 1 when it is pushed into the blood vessel.

[0048] The imaging module 101 is located at the distal end of the bending section of the conduit 1, at the very front of the entire endoscope. Compared to traditional fiber optic illumination, which suffers from poor fiber optic bending resistance, leading to fiber breakage after repeated bending and resulting in dark spots in the field of view, and because the fiber bundle occupies a large cross-sectional space, limiting the endoscope's outer diameter to at least 1.5mm, this embodiment uses a micro CMOS image sensor chip, an optical lens, and a matching flexible signal cable. The outer diameter of the CMOS image sensor chip is controlled to be within 0.5mm, with a resolution of at least 720P and an imaging frame rate of at least 6. The system operates at 0fps and employs wafer-level packaging or micro-ceramic substrate packaging. The optical lens is positioned at the front end of the CMOS chip, featuring a wide-angle lens design with a field of view of at least 120°. It focuses the optical image of the blood vessel wall onto the CMOS photosensitive surface. One end of the flexible signal cable is electrically connected to the CMOS chip's pads, while the other end extends backward along the inside of catheter 1 to the handle 3 and connects to the image transmission interface. The outer diameter of the flexible signal cable does not exceed 0.35mm, and it utilizes a micro-coaxial or ultra-fine flexible circuit board structure to ensure signal transmission stability during repeated bending in the controlled bending section. Because fiber optic light experiences significant attenuation after long-distance fiber transmission, the light intensity reaching the head end is far lower than the light source's output intensity. Furthermore, the smaller the fiber bending radius and the more bends, the greater the light attenuation and the unstable image quality. Therefore, in this embodiment, the LED chip is directly mounted on the head end, allowing the conversion of electrical energy to light energy to occur at the illumination position. This eliminates light energy loss during fiber optic transmission, resulting in stable image brightness, accurate color reproduction, and image quality that does not fluctuate with bending control operations.

[0049] As for the side tube 2, the side tube 2 is a slender tubular structure with a guide channel 201 running through both ends along the axis inside. The diameter of the guide channel 201 is adapted to the diameter of the clinical standard microguidewire. The side tube 2 is also made of nickel-titanium alloy material. At the same time, the side tube 2 has a certain degree of flexibility and can adapt to the bending of the control section. The injection channel 104 is located inside the fixed section of the catheter 1. Its proximal end has a connection port for connecting to an external flushing device. It extends along the axial direction of the catheter 1, and its distal end penetrates the outer wall of the control bend section. It can intersect and communicate with the guide channel 201 of the side tube 2 within the fixed section, so that the flushing fluid injected by the injection channel 104 can flow into the guide channel 201 and be transported to the distal end of the side tube 2 through the guide channel 201. Alternatively, it can be located on the side of the side tube 2. Specifically, the side of the side tube 2 has an outlet 202, which is connected to the injection channel 104 and is inclined towards the imaging module 101. After the flushing fluid is transported to the distal end through the guide channel 201, it is sprayed out directionally from the outlet 202 and sprayed into the blood vessel lumen in front of the imaging module 101, thereby dispersing the blood in front of the imaging module 101 and forming a clear field of view.

[0050] The adjustment unit is used to drive the bending section of the conduit 1 to bend.

[0051] Specifically, the structure of the adjustment unit is deeply optimized, and the adjustment unit includes:

[0052] Two traction wires 103 are inserted inside the conduit 1 and arranged in a mirror image, with one end of each wire fixedly connected to the end of the bending section.

[0053] The cable gathering wheel 5 has a second mounting base 302 inside the handle 3. The cable gathering wheel 5 is rotatably mounted on the second mounting base 302. The cable gathering wheel 5 has two cable gathering grooves 501. The two cable gathering grooves 501 are spaced apart along the axial direction of the cable gathering wheel 5. The other ends of the two traction wires 103 pass through the fixed section of the guide tube 1 and are respectively wound in the two cable gathering grooves 501, and the winding directions are opposite.

[0054] A locking element is provided on the handle 3 and is used to lock the cable reel 5.

[0055] like Figure 3 and Figure 6As shown, the two traction wires 103 are arranged symmetrically at 180° on the radial section of the catheter 1 to ensure that the bending moment applied to the bending control section is equal in magnitude and opposite in direction, thereby achieving stable bidirectional bending control. In the installation of the traction wires 103, their ends are fixed to the ends of the bending control section. Preferably, the bending control section of the catheter 1 is provided with an alloy ring 102, and both traction wires 103 are connected to the alloy ring 102. In interventional procedures involving distal small blood vessels, the radiographic images are often not clear enough due to factors such as overlapping blood vessels, contrast agent dilution, or blood flow scouring, making it difficult to accurately distinguish the precise position and bending direction of the tip in the blood vessel lumen. The alloy ring 102 is made of a medical alloy material with high radioactivity, and its radiographic intensity under X-ray fluoroscopy is much higher than that of nickel-titanium alloy. As a high-contrast radiographic marker, it can still accurately determine the spatial orientation of the distal end of the bending control section in the blood vessel, while also serving as the anchoring point for the traction wires 103, facilitating welding.

[0056] After the proximal ends of the two traction wires 103 pass through the fixed section of the conduit 1, they are guided into the two cable trays 501 respectively and wound around the two cable trays 501 respectively. One traction wire 103 is wound in the corresponding cable tray 501 in a clockwise direction, and the other traction wire 103 is wound in the corresponding cable tray 501 in a counterclockwise direction. When the cable tray wheel 5 rotates around its axis, the two cable trays 501 rotate synchronously. One of the two traction wires 103 is further wound and tightened, and the other is released synchronously, thereby realizing the pull and release movement mode of the two traction wires 103, which in turn drives the bending control section to bend in the corresponding direction. Preferably, the second mounting base 302 is further provided with a guide groove 303, and a partition 304 is fixedly provided in the middle of the guide groove 303 to separate the two traction wires 103. After the two traction wires 103 pass through the fixed section of the guide tube 1, they pass through both sides of the partition 304 in the guide groove 303 respectively, and are guided to the two cable trays 501 respectively, so as to prevent the two traction wires 103 from getting tangled or interfering with each other during the movement, and to ensure that the two traction wires 103 run independently.

[0057] After the above adjustments and bending control, the device can be locked in place using a locking mechanism.

[0058] It is worth noting that during use, when the endoscopic endoscope is pushed to the bifurcation site along the pre-placed microguidewire, if the bending control segment is directly bent, the bending deformation of the control segment may cause displacement of the side tube 2 and the microguidewire inside, thereby generating an unexpected traction force on the distally implanted microguidewire. Therefore, when the endoscope needs to be bent at the bifurcation site, the microguidewire in the guide channel 201 of the side tube 2 should first be retracted proximally, so that the distal end of the microguidewire is retracted to the guide channel 201 of the side tube 2. Inside channel 201, the microguidewire no longer penetrates the bending deformation area of ​​the control segment. The control segment is driven to bend towards the target branch by the adjustment unit. Since the microguidewire has retreated to a safe position, the bending deformation of the control segment will not exert a pulling or squeezing effect on the microguidewire, thereby avoiding damage to the vessel wall by the microguidewire. After the control segment bends to the target angle and locks, the microguidewire is pushed forward from the guide channel 201, so that it extends out of the distal end of the side tube 2 again and is implanted forward along the target branch vessel to the distal target position.

[0059] Specifically, the structure of the locking component is optimized in depth, such as... Figure 1 As shown, the locking element includes:

[0060] Worm gear 4 is fixedly mounted on the end face of the wire feeder 5;

[0061] The worm 7 is rotatably located inside the handle 3 and meshes with the worm wheel 4.

[0062] The worm gear 4 is fixedly mounted on the end face of the wire feeder 5. The worm gear 4 and the wire feeder 5 are coaxially fixedly connected and rotate synchronously. Simply rotating the worm 7 will drive the worm gear 4 to rotate the wire feeder 5 to adjust the bending angle. After releasing the worm 7, the wire feeder 5 will be automatically locked in the current position due to the self-locking effect, without the need for additional locking operations, making it convenient to use.

[0063] Moreover, as Figure 1 As shown, the handle 3 is also provided with a first mounting base 301 inside, the first mounting base 301 is rotatably provided with a drive gear 601, one end of the worm gear 7 is provided with a driven gear 701, the driven gear 701 meshes with the drive gear 601, the outer side of the handle 3 is rotatably provided with a pulsator 6, and the shaft of the drive gear 601 is connected to the pulsator 6.

[0064] By rotating the impeller 6, the drive gear 601 rotates synchronously with the impeller 6. The drive gear 601 drives the driven gear 701 to rotate the worm 7. The worm 7 then drives the worm wheel 4 to rotate the wire feeding wheel 5, ultimately realizing the winding or unwinding of the traction wire 103. Through gear reduction transmission, the small-amplitude movement applied to the impeller 6 can be converted into a smooth pulling force output to the traction wire 103, achieving fine adjustment. Moreover, an angle scale mark can be set on the side of the impeller 6. By using the scale value corresponding to the current pointing position of the impeller 6, the approximate bending angle of the current bending section can be determined, improving the predictability of the operation.

[0065] Specifically, such as Figure 5 As shown, both ends of the side tube 2 are provided with guide bevels 203. If the port of the side tube 2 is a sharp right angle and the port comes into contact with the blood vessel wall, it may cause scratches and friction damage on the blood vessel intima. The smooth contour of the guide bevel 203 effectively disperses the contact stress between the port of the side tube 2 and the blood vessel wall, avoids mechanical cutting of the blood vessel intima by the right angle edge, and effectively reduces the risk of blood vessel damage during the operation.

[0066] Specifically, such as Figure 1 As shown, the first mounting base 301 also has a bonding port 305. The fixed section of the conduit 1 passes through the bonding port 305. The first mounting base 301 simultaneously achieves circumferential and axial fixation of the fixed section of the conduit 1 through the bonding port 305. During assembly, after the fixed section of the conduit 1 passes through the bonding port 305 and is adjusted to the preset axial position, adhesive is injected into the injection hole of the bonding port 305 through the injection needle. The adhesive fills the gap between the inner wall of the bonding port 305 and the outer wall of the conduit 1. After being irradiated by ultraviolet light or cured naturally, the fixation is completed. The entire assembly process is simple to operate.

[0067] In summary, during use, the fixed section of catheter 1 is connected to the imaging host, LED driver power supply, and external flushing device. The microguidewire is pushed to the distal target position of the target blood vessel and stably placed. Then, holding handle 3, the microguidewire is smoothly inserted into the guide channel 201. The endoscope is pushed into the blood vessel along the guidewire. When the vessel bifurcates and bending is required, the microguidewire is first retracted proximally so that its distal end is inside the guide channel 201. The pulsator 6 on the outside of handle 3 is turned. Power is transmitted to the filament collecting wheel 5 through the driving gear 601, driven gear 701, worm 7, and worm wheel 4. When the filament collecting wheel 5 rotates, the two traction wires 103 wound in opposite directions in the two filament collecting grooves 501 are pulled and released, driven by the alloy ring 102. The control section bends in the target direction. After releasing the wave wheel 6, the self-locking properties of the worm gear 4 and worm 7 lock the wire pulley 5 in the current position. After locking, the microguidewire is pushed into the branch vessel along the bending direction to the distal target position. If blood removal is required, the guidewire is withdrawn, and saline is injected through the injection channel 104. The liquid is delivered to the distal end of the side tube 2 through the guide channel 201 and sprayed out directionally from the outlet 202, dispersing the blood in front of the imaging module 101 to form a clear field of view. If instrument replacement is required, the microguidewire is left in place, and the endoscope is withdrawn along the guidewire. Subsequent instruments are pushed into the target position along the same guidewire without the need to reconstruct the access. After the operation is completed, the wave wheel 6 is reversed to reset the control section to straight, and the endoscope and guidewire are withdrawn from the body simultaneously.

[0068] Finally, it should be noted that the above embodiments are only used to illustrate the technical solutions of the present invention and are not intended to limit it. Although the present invention has been described in detail with reference to preferred embodiments, those skilled in the art should understand that modifications or equivalent substitutions can be made to the technical solutions of the present invention without departing from the spirit and scope of the technical solutions of the present invention, and all such modifications or substitutions should be covered within the scope of the claims of the present invention.

Claims

1. A multifunctional integrated ultra-fine diameter bidirectional controllable curved vascular endoscope, characterized in that, include: Handle (3); The catheter (1) has a bending section and a fixing section. The fixing section is installed inside the handle (3) and extends to one end of the handle (3). The bending section extends to the other end of the handle (3). The bending section is provided with an imaging module (101) and a side tube (2). The imaging module (101) is located at the end of the bending section. The side tube (2) is arranged along the axial direction of the catheter (1) and fits against the outer wall of the bending section. It also has a guide channel (201) that runs through both ends. The fixing section is also provided with an injection channel (104). The injection channel (104) runs through the outer wall of the bending section. An adjustment unit is provided on the handle (3) and connected to the bending section of the conduit (1) for driving the bending section of the conduit (1) to bend.

2. The vascular endoscope according to claim 1, characterized in that, The adjustment unit includes: Two traction wires (103) are inserted inside the conduit (1) and arranged in a mirror image, with one end of each wire fixedly connected to the end of the bending section. The cable gathering wheel (5) has a second mounting seat (302) inside the handle (3). The cable gathering wheel (5) is rotatably mounted on the second mounting seat (302). The cable gathering wheel (5) has two cable gathering grooves (501). The two cable gathering grooves (501) are spaced apart along the axial direction of the cable gathering wheel (5). The other ends of the two traction wires (103) pass through the fixed section of the guide tube (1) and are respectively wound in the two cable gathering grooves (501) in opposite directions. A locking element is provided on the handle (3) for locking the cable pulley (5).

3. The vascular endoscope according to claim 2, characterized in that, The locking element includes: Worm gear (4), the worm gear (4) is fixedly disposed on the end face of the wire feeder (5); The worm (7) is rotatably disposed inside the handle (3) and meshes with the worm wheel (4).

4. The vascular endoscope according to claim 3, characterized in that, The handle (3) is also provided with a first mounting seat (301), the first mounting seat (301) is rotatably provided with a drive gear (601), one end of the worm (7) is provided with a driven gear (701), the driven gear (701) meshes with the drive gear (601), the outer side of the handle (3) is rotatably provided with a pulsator (6), and the shaft of the drive gear (601) is connected to the pulsator (6).

5. The vascular endoscope according to any one of claims 2-4, characterized in that, The conduit (1) has an alloy ring (102) in the bend control section, and both of the two traction wires (103) are connected to the alloy ring (102).

6. The vascular endoscope according to claim 5, characterized in that, The second mounting base (302) is also provided with a guide groove (303), and a partition (304) is fixedly provided in the middle of the guide groove (303) to separate the two traction wires (103).

7. The vascular endoscope according to claim 1, characterized in that, The side tube (2) has a liquid outlet (202) on its side, and the liquid outlet (202) is connected to the liquid injection channel (104).

8. The vascular endoscope according to claim 1 or 7, characterized in that, Both ends of the side tube (2) are provided with guide slopes (203).

9. The vascular endoscope according to claim 1, characterized in that, The catheter (1) comprises, from the inside out, a PTFE inner layer, a braided reinforcement layer and a PEBAX outer layer, and the outer surface of the catheter (1) has a hydrophilic coating.

10. The vascular endoscope according to claim 4, characterized in that, The first mounting base (301) also has a glue-fixing port (305), through which the fixed section of the conduit (1) passes.

Images