Endoscope structure

Abstract

The endoscope structure comprises a connecting assembly, an optical assembly, an optical detector and a laser optical fiber assembly, the optical detector is arranged on the optical assembly, a second channel penetrating through the connecting assembly front and back is formed in the connecting assembly, and the optical assembly is detachably connected with the connecting assembly. A third channel penetrating through the optical assembly is formed in the optical assembly, and the laser optical fiber assembly is installed in the first channel. According to the scheme, the connecting assembly is detachably connected with the optical assembly. Therefore, the connecting assembly and the optical assembly can be disassembled and assembled according to conditions. For example, in the stage of laser calculus crushing, the connecting assembly can be connected with the optical assembly, so that the perfusate can be conveyed from the outside to the inside to reduce the temperature rise caused by laser. And in the stage that the lithotomy forceps are used for lithotomy, the connecting assembly can be detached, so that the user can make the lithotomy forceps go to a preset position through a third channel of the optical assembly to carry out lithotomy.

Description

Technical Field

[0001] The present disclosure relates to medical devices, and in particular to an endoscope structure. Background Art

[0002] Ureteroscopic lithotripsy is a minimally invasive, safe and effective treatment for upper urinary tract stones through the natural urinary cavity of the human body. It has become the preferred treatment for kidney stones with a diameter of less than 2 cm. At the same time, it has become a powerful tool and the "gold standard" for ureteroscopic lithotripsy when combined with a laser energy platform. From the perspective of design and application characteristics: rigid ureteroscopes are suitable for treating stones in the middle and lower ureters; flexible ureteroscopes are more suitable for treating stones in the upper ureters and kidneys.

[0003] Rigid ureteroscopes are easy to operate and inexpensive, but are only suitable for treating stones in the middle and lower ureteral segments, and cannot treat stones in the upper urinary tract with relatively curved cavities. Flexible ureteroscopes can treat stones in the upper ureteral segment and kidneys, but they are difficult to operate and have a long learning curve; flexible ureteroscopes are expensive and thin, easily damaged, and have high maintenance costs.

[0004] Specifically, if Figure 1 As shown, the lower part of the ureter is connected to the bladder 810, and the upper part of the ureter 820 is connected to the renal pelvis 830. The ureteroscope needs to pass through the bladder before reaching the ureter. However, since the ureter does not extend in a single direction, the rigid ureteroscope cannot be well placed in the upper part of the ureter, so a flexible ureteroscope is needed to treat stones in the upper part of the ureter.

[0005] Currently, there is no ureteroscope with a simple structure that can handle stones in the lower ureter, middle ureter, and upper ureter.

[0006] In addition, the existing soft endoscope is inconvenient to use hard stone removal forceps due to its curved structure. And the hard endoscope itself is difficult to reach the upper ureter. Therefore, how to deal with large stones in the upper ureter is also a relatively difficult problem. Summary of the invention

[0007] To solve at least one of the above-mentioned defects, the present disclosure provides an endoscope structure, which is convenient for inserting lithotripsy forceps therein.

[0008] The present disclosure provides an endoscope structure including a connecting component, an optical component, an optical detector, and a laser fiber component, wherein the optical detector is arranged on the optical component, and the connecting component is formed with a second channel that passes through the connecting component from front to back, wherein the optical component and the connecting component are detachably connected, wherein the optical component is formed with a third channel that passes through the optical component, and when the optical component and the connecting component are connected, the second channel is connected to the third channel to form the first channel, and the laser fiber component is installed on the connecting component, and the front end of the laser fiber component passes through the first channel to extend out of the optical component.

[0009] Optionally, the second channel is provided with a first sealing component, which forms a laser fiber through hole for the laser fiber assembly to pass through, and the first sealing component is tightly fitted to the laser fiber assembly to prevent the perfusion fluid in the second channel from flowing from one side of the laser fiber through hole to the other side of the laser fiber through hole.

[0010] Optionally, it also includes an outer sheath, which includes a sheath body and a sheath extension connected in sequence from back to front, the sheath body is connected to the optical component, the outer sheath is sleeved outside part or all of the connecting component and the optical component, and the outer diameter of the sheath extension is 2-10mm, the length of the sheath extension is 100-500mm, the laser fiber assembly is a bendable fiber assembly, so that the front end of the laser fiber assembly located outside the sheath extension can be bent relative to the sheath extension, wherein the sheath extension is a hard material, and a gap is formed between the sheath extension and the optical component, the gap is used to communicate with the suction assembly, and the outer sheath is formed with a lubricating layer.

[0011] Optionally, the optical component includes a first main body portion and a first extension portion connected in sequence from back to front, and the optical detector is arranged on the first extension portion, wherein the first main body portion and the front end portion of the connecting component are detachably connected, wherein the third channel is formed in the first main body portion and the first extension portion, and the third channel passes through the first main body portion and the first extension portion from front to back.

[0012] Optionally, the front end of the first extension portion extends forward to protrude out of the sheath extension portion, and a protrusion is formed on the side wall of the front end of the first extension portion.

[0013] Optionally, the laser fiber assembly is rotatably connected to the connecting assembly, so that the laser fiber assembly can rotate relative to the outer sheath tube.

[0014] Optionally, the connection component forms a water transfer channel, a water transfer opening formed at one end of the water transfer channel is located on the surface of the connection component, the other end of the water transfer channel is connected to the second channel, and the water transfer opening is used for external perfusion fluid to flow in.

[0015] Optionally, the sheath body and the optical component are detachably connected, and the sheath body and the optical component are relatively rotatable.

[0016] Optionally, the laser fiber assembly includes a control assembly, two or more traction wires, an optical fiber outer sheath tube, and a laser optical fiber. The laser optical fiber is installed in the optical fiber outer sheath tube, and the control assembly is used to control the two or more traction wires to control the bending of the front end of the optical fiber outer sheath tube, thereby driving the bending of the front end of the laser optical fiber.

[0017] Optionally, the laser fiber assembly includes a damping structure, the laser fiber is slidably installed in the optical fiber outer sheath tube so that the laser fiber can move forward and backward along the optical fiber outer sheath tube, and a fiber through hole is formed in the damping structure for the laser fiber to pass through, and the fiber through hole and the laser fiber are interference fit to provide damping for the movement of the laser fiber relative to the optical fiber outer sheath tube.

[0018] The endoscope structure disclosed herein has a connection component and an optical component that are detachably connected. Therefore, the connection component and the optical component can be connected or disassembled according to the situation. For example, in the laser stone treatment stage, the connection component can be connected to the optical component so that the perfusion fluid can be transported from the outside of the body to the inside of the body. In the stage of using lithotripsy forceps to remove stones, the connection component and the laser fiber component can be removed so that the user can use the lithotripsy forceps to remove stones through the third channel of the optical component.

[0019] In addition, the endoscope structure of the present invention has a hard sheath extension that can be extended into the middle and lower part of the ureter, and a gap is formed between the outer sheath and the optical component, so that the perfusion fluid can carry the crushed stones through the gap to flow back to the body to avoid remaining in the human body. BRIEF DESCRIPTION OF THE DRAWINGS

[0020] Figure 1 This is a schematic diagram of the structure of some internal organs of the human body.

[0021] Figure 2 It is a schematic structural diagram of the endoscope structure disclosed in the present invention.

[0022] Figure 3 for Figure 2 Exploded view of the endoscope structure.

[0023] Figure 4It is a partial structural cross-sectional view of the endoscope structure disclosed in the present invention.

[0024] Figure 5 It is a schematic diagram of the structure of the connection component and the temperature and pressure measuring optical fiber.

[0025] Figure 6 It is a cross-sectional view of the connection component and the temperature and pressure measuring optical fiber.

[0026] Figure 7 for Figure 2 Schematic diagram of the structure of the optical components.

[0027] Figure 8 for Figure 7 Cross-sectional view of the optical components in FIG.

[0028] Fig. 9 for Figure 7 Enlarged view of part A in .

[0029] Fig.10 and Fig.11 Schematic diagram of the structure of the first sealing component at different angles.

[0030] Fig.12 Schematic diagram of the structure of the outer sheath.

[0031] Fig.13 for Fig.12 Cross-sectional view of the outer sheath in FIG.

[0032] Fig.14 for Fig.12 Schematic diagram of the structure of the outer sheath at different angles.

[0033] Fig.15 This is a partial enlarged view of the endoscope structure.

[0034] Fig.16 for Figure 2 Schematic diagram of the partial structure of the laser fiber assembly.

[0035] Fig.17 for Fig.16 A partial cross-sectional view of a portion of the structure of the laser fiber assembly.

[0036] Fig.18 It is a cross-sectional view of the outer sheath of the optical fiber.

[0037] Markings in the figure:

[0038] 200, optical detector; 300, laser fiber assembly; 310, laser fiber; 320, handle; 321, second annular groove; 330, optical fiber outer sheath; 331, laser fiber channel; 340, control assembly; 341, rotating member; 342, rotating rod; 343, spur gear connecting rod; 344, gear; 345, first rack; 346, second rack; 360, damping structure; 400, connecting assembly; 410, second channel; 420, first sealing assembly; 422, first optical fiber mounting seat; 4221, through hole; 423, first elastic sealing member; 4231, laser fiber through hole; 430, water delivery channel; 440, solid Fixed ring; 450, optical fiber pipeline; 460, second sealing component; 470, sealing component pipeline; 500, optical component; 510, first main body; 511, first annular groove; 512, light beam channel; 520, first extension; 521, protrusion; 530, third channel; 540, wire harness channel; 541, first wire harness channel; 600, outer sheath; 610, sheath body; 611, first engaging member; 620, sheath extension; 621, mounting member; 6211, first through hole; 630, fourth channel; 640, suction channel; 700, temperature and pressure measuring optical fiber; 810, bladder; 820, ureter; 830, renal pelvis. DETAILED DESCRIPTION

[0039] It should be understood that the exemplary embodiments described herein should be considered only for descriptive purposes and not for limiting purposes. Descriptions of features or aspects in each exemplary embodiment should generally be considered applicable to similar features or aspects in other exemplary embodiments.

[0040] Figure 2 The schematic diagram of the structure of the endoscope disclosed in the present invention is shown. Figure 2-3 As shown in FIG. 1 , the endoscope structure includes a connection component 400, an optical component 500, an optical detector 200, and a laser fiber component 300. Figure 4-8 As shown, the optical detector 200 is arranged in the optical component 500, and the connecting component 400 is formed with a second channel 410 that passes through the connecting component 400 from front to back, wherein the optical component 500 and the connecting component 400 are detachably connected, wherein the optical component 500 is formed with a third channel 530 that passes through the optical component 500, when the optical component 500 is connected to the connecting component 400, the second channel 410 is connected to the third channel 530 to form a first channel, the laser fiber component 300 is installed in the connecting component 400, and the laser fiber component 300 is installed in the first channel.

[0041] In the present disclosure, in addition to the laser fiber assembly 300 passing through, the first channel is likely to be used for the circulation of perfusion fluid. Therefore, a sealing structure is provided in the first channel to seal the first channel to prevent the perfusion fluid from flowing through the gap between the laser fiber assembly 300 and the first channel and leaking out. However, it will also make it difficult for the stone removal forceps to pass through the first channel. Therefore, the endoscope structure provided by the present disclosure has a detachable connection between the connecting component 400 and the optical component 500. Therefore, when laser is used to crush stones, the connecting component 400 and the optical component 500 are still connected, and the laser fiber assembly 300 extends out of the first channel to treat the stones. At the same time, the perfusion fluid can also reach the lesion area through the first channel to cool the lesion area and control the lesion area to be in a suitable temperature range. When the stone crushing is completed, the connecting component 400 and the optical component 500 can be removed, and the user passes the stone removal forceps through the third channel 530 to complete the stone removal. It should be noted that, since the optical component 500 is provided with an optical detector 200, the user can still observe the situation of the lesion area according to the optical detector 200 to complete the stone removal.

[0042] It should be noted that perfusion fluid generally refers to liquid injected in medical surgery or scientific research experiments to maintain the activity of organs, tissues or cells, clean them or for specific treatment purposes. In the present disclosure, the perfusion fluid can be saline, glucose solution or mannitol solution, which is mainly used to flush and clean the surgical area to make the surgical area clear, prevent thermal damage caused by laser, and allow small particles after lithotripsy to be discharged from the body with the help of saline flow.

[0043] Optional, such as Figure 5 , Fig. 9 as well as Fig.10As shown, the second channel 410 is provided with a first sealing component 420, and the first sealing component 420 forms a laser fiber through hole 4231 for the laser fiber assembly 300 to pass through, and the first sealing component 420 and the laser fiber assembly 300 are tightly fitted to prevent the perfusion liquid in the second channel 410 from flowing from one side of the laser fiber through hole 4231 to the other side of the laser fiber through hole 4231. Specifically, the first sealing component 420 includes a first fiber mounting seat 422 and a first elastic seal 423, and through holes are formed on the first fiber mounting seat 422 and the first elastic seal 423 for the laser fiber assembly 300 to pass through, and these through holes are interference fit or size match with the laser fiber assembly 300 to better prevent the leakage of the perfusion liquid. Specifically, the first fiber mounting seat 422 and the first elastic seal 423 are both fixed to the rear end of the second channel 410. Therefore, when the laser fiber assembly 300 enters from the rear end of the second channel 410 to pass through the first channel (i.e., the second channel 410 and the third channel 530) from back to front, the laser fiber assembly 300 will fit tightly with the first fiber mounting seat 422 and the first elastic seal 423 to prevent leakage of the perfusion fluid.

[0044] As described in the background technology, the existing ureteroscopes are divided into two types, one is a hard ureteroscope and the other is a soft ureteroscope. The front end of the hard ureteroscope is a hard structure, which makes it difficult to penetrate into the upper part of the ureter 820 after entering the ureter 820. The front end of the soft ureteroscope is a flexible structure, which can be input into the upper part of the ureter 820 to treat the stones in the upper part of the ureter 820. However, the operation of the soft mirror is relatively complicated and expensive. When using the soft mirror, the soft mirror must first be passed through the bladder 810 to enter the ureter 820. Then, the zebra guide wire is inserted into the guide wire channel of the soft mirror until the guide wire is placed in the predetermined position. Then, the soft mirror is taken out, and the sheath is placed in the predetermined position under the guidance of the guide wire. Finally, the soft mirror is moved along the sheath to the predetermined position, and then the stone is treated by laser. It is not difficult to find that the operation of the soft mirror is relatively complicated, which requires higher operating skills of the operator, and there is a risk of further damage or infection to the patient due to multiple steps.

[0045] It should be noted that when treating stones with a soft endoscope, the stones are crushed and flow along the ureter 820 to the bladder 810 and other locations, which may affect the bladder 810. Therefore, in addition to guiding the soft endoscope to a specific location, the sheath also has the function of guiding the stones out of the human body.

[0046] In addition, since the entire front end of the ureteroscope needs to be bent together, more factors need to be considered during design. For example, in order to achieve a better bending effect, most will adopt a snake bone design to facilitate the precise swing of the ureter 820, but it will also lead to an increase in production costs. Secondly, since the entire front end of the ureteroscope can be bent, there are specific requirements for the internal material, which is not conducive to production.

[0047] To this end, the present disclosure needs to provide a new endoscope structure to solve the above problems. Specifically, the endoscope structure also includes an outer sheath 600, the outer sheath 600 includes a sheath body 610 and a sheath extension 620 connected in sequence from back to front, the sheath body 610 is connected to the optical component 500, the outer sheath 600 is sleeved outside the partial or entire connection component 400 and the optical component 500, and the outer diameter of the sheath extension 620 is 2-10mm, the length of the sheath extension 620 is 100-500mm, the laser fiber assembly 300 is a bendable fiber assembly, so that the front end of the laser fiber assembly 300 can be bent relative to the sheath extension 620, wherein the sheath extension 620 is a hard material, and the outer sheath 600 is formed with a lubricating layer, wherein the front end of the laser fiber assembly 300 is located in front of the sheath extension 620, and its bending is not limited by the limitation of the sheath extension 620.

[0048] When it is necessary to crush the stones in the lower middle section of the ureter 820, the user can pass the endoscope structure through the bladder 810 and insert the sheath extension 620 into the lower middle section of the ureter 820. Then, according to the image fed back by the optical detector 200, the user can manipulate the laser fiber assembly 300 to bend to crush the stones. At the same time, the perfusion fluid can be delivered to the lesion area through the first channel for cooling. The perfusion fluid carrying the crushed small stones can flow out of the patient's body through the gap between the outer sheath 600 and the optical assembly 500.

[0049] When it is necessary to crush stones in the upper section of the ureter 820, the user can insert part of the endoscope structure (for example, the sheath extension 620, the laser fiber assembly 300 and the first extension) into the middle and lower section of the ureter 820. Then, move the laser fiber assembly 300 to the upper section of the ureter 820. Then manipulate the laser fiber assembly 300 to bend to treat the stones in the upper section of the ureter 820. At the same time, the perfusion fluid can be delivered to the lesion area through the first channel for cooling. The perfusion fluid carrying the crushed small stones can flow out of the patient's body through the gap between the outer sheath 600 and the optical assembly 500.

[0050] Therefore, it is not difficult to see that the endoscope structure disclosed in the present invention can effectively and quickly treat stones in the entire ureter 820, has a wider treatment range (including the upper section of the ureter 820) than the existing rigid ureteroscope, and is more convenient and quicker to operate than the existing flexible ureteroscope, which is conducive to users using it according to the situation.

[0051] In addition, it should be noted that a lubricating layer is formed on the outer side of the outer sheath tube 600. Specifically, the lubricating layer is formed by depositing self-lubricating diamond-like nanoparticles onto the outer sheath tube 600 by vapor deposition. Of course, in addition to being obtained by vapor deposition of self-lubricating diamond-like nanoparticles, the lubricating layer can also be a ceramic-based diamond composite coating, a molybdenum disulfide coating, and the like.

[0052] The above solution reduces the friction coefficient of the outer sheath by the lubricating layer, thereby reducing the damage to the ureteral mucosa when the outer sheath moves in the ureter. In addition, the outer sheath 600 disclosed in the present invention can replace the ureteral sheath in the prior art, further reducing the cost of use for patients.

[0053] Optional, such as Figure 7-9 As shown, the optical component 500 includes a first main body portion 510 and a first extension portion 520 connected in sequence from back to front, and the optical detector 200 is arranged on the first extension portion 520, wherein the first main body portion 510 and the front end portion of the connecting component 400 are detachably connected, wherein the third channel 530 is formed in the first main body portion 510 and the first extension portion 520, and the third channel 530 passes through the first main body portion 510 and the first extension portion 520 front to back.

[0054] Specifically, see Figure 2 , the rear end of the first body part 510 and the front end of the connecting assembly 400 are detachably connected through a fixing ring 440. A fixing pin is provided on the fixing ring 440. When the button on the fixing ring 440 is pressed, the fixing pin is inserted into the fixing hole of the first body part 510 and the connecting assembly 400, so that the first body part 510 and the connecting assembly 400 are connected to each other. In addition, it should be noted that there are various ways to connect the first body part 510 and the connecting assembly 400, and the present disclosure does not make specific restrictions.

[0055] In addition, a harness channel portion 540 is formed on the first main body portion 510, a first harness channel 541 is formed on the harness channel portion 540, an eyepiece cover is arranged at the rear end of the first harness channel 541, one end of the harness is connected to the eyepiece cover, and the other end is connected to the optical detector 200 at the front end of the first extension portion 520 through the first harness channel 541 and the first extension portion 520 (a second harness channel is formed in the first extension portion 520 for the harness to pass through). When in use, the image obtained by the optical detector 200 can be imaged on a monitor by connecting the eyepiece cover to an image processing system.

[0056] In addition, a light source channel portion is formed on the first main body portion 510, and a light source channel is formed in the light source channel portion, and its function is to allow the guide light beam to pass through. Specifically, the light beam channel 512 is connected with the third channel 530, and the guide light beam can extend to the front of the endoscope structure through the light beam channel 512 and the third channel 530 to provide a light source for the user's observation.

[0057] Continue to refer Figure 6 In some optional embodiments, the connection component 400 forms a water delivery channel 430, and a water delivery opening formed at one end of the connection component 400 is located on the surface of the connection component 400, and the other end of the water delivery channel 430 is connected to the second channel 410. More specifically, the water delivery channel 430 cooperates with the second channel 410 and the third channel 530 to form a whole channel for delivering the perfusion liquid. The perfusion liquid can enter from the water delivery opening of the water delivery channel 430 and then be delivered to the second channel 410 and then reach the third channel 530, and finally be ejected from the front end of the third channel 530. At the same time, the first channel composed of the second channel 410 and the third channel 530 can also be used for the laser fiber assembly 300 to pass through. It should be noted that the shell of the laser fiber assembly 300 is made of tetrafluoroethylene, and the perfusion liquid cannot penetrate into the laser fiber assembly 300 through the tetrafluoroethylene.

[0058] More specifically, the connection assembly 400 is provided with two water delivery channels 430, and each water delivery channel 430 is provided with a Luer interface to communicate with an external perfusion waterway. In addition, a water inlet valve is provided in each water delivery channel 430 to control the opening and closing of the water delivery channel 430.

[0059] It should be noted that, for the endoscope structure of the ureter 820, water pressure can be used to flush the opening of the ureter 820 in the bladder 810. In addition, the endoscope structure of this solution has a laser fiber 310, which will generate high temperature when it emits laser light to interact with stones. Therefore, by setting a water delivery channel 430 and connecting the water delivery channel 430 with the second channel 410 and the third channel 530, the perfusion fluid can also be delivered to the lesion area through the water delivery channel 430, the second channel 410 and the third channel 530 to cool the lesion area and control the lesion area to be in a suitable temperature range.

[0060] In some optional embodiments, the connection assembly 400 is provided with a temperature and pressure measuring optical fiber 700, which is used to measure the external temperature and pressure, thereby ensuring that the urinary tract pressure is kept within a normal range (below 40 mmhg) and the urinary tract water environment temperature is lower than the thermal damage value (42°C). Specifically, the temperature and pressure measuring optical fiber 700 can be a temperature-pressure composite Fabry-Perot optical fiber.

[0061] In some embodiments, a temperature sensor and / or a pressure sensor may be separately provided to measure external conditions. For example, a temperature sensor with a temperature-sensitive resistor and a pressure sensor with a pressure-sensitive resistor may be provided to perform measurements.

[0062] More specifically, the connection assembly 400 is provided with an optical fiber conduit 450 for the temperature and pressure measuring optical fiber 700 to pass through. The connection assembly 400 is formed with a sealing assembly conduit 470, in which a second sealing assembly 460 is provided to tightly fit the temperature and pressure measuring optical fiber 700 to prevent the perfusion liquid from leaking from the gap between the temperature and pressure measuring optical fiber 700 and the sealing assembly conduit 470. The second sealing assembly 460 includes a second optical fiber mounting seat and a second elastic seal, and the second optical fiber mounting seat and the second elastic seal are installed in the sealing assembly conduit 470, and the second optical fiber seat is connected to the optical fiber conduit 450. Therefore, the front end of the temperature and pressure measuring optical fiber 700 can pass through the second elastic seal, the second optical fiber mounting seat and the optical fiber conduit 450 in sequence until it reaches the front end of the endoscope structure. It should be noted that the second elastic seal and the second optical fiber mounting seat are tightly fitted to the temperature and pressure measuring optical fiber 700 to prevent the perfusion liquid from flowing out of the gap between the temperature and pressure measuring optical fiber 700 and the second elastic seal and / or the second optical fiber mounting seat. The inner diameter of the optical fiber tube 450 is substantially the same as the temperature and pressure measuring optical fiber 700 so as to allow the temperature and pressure measuring optical fiber 700 to be inserted.

[0063] refer to Figure 1 and Figure 12-14 Optionally, the sheath body 610 is detachably connected to the optical assembly 500, and the sheath body 610 and the optical assembly 500 can rotate relative to each other. Specifically, the rear end of the sheath body 610 is detachably connected to the front end of the first body 510. A first annular groove 511 is formed at the front end of the first body 510, and a first limiting hole is formed at the rear end of the sheath body 610 and a first engaging member 611 is provided. The first engaging member 611 can partially protrude from the first limiting hole to cooperate with the first annular groove 511 so that the rear end of the sheath body 610 is detachably connected to the front end of the first body 510, wherein the aperture of the first limiting hole is smaller than the maximum size of the first engaging member 611, thereby limiting the first engaging member 611 from being separated from the first limiting hole. Optionally, the first engaging member 611 is a spherical structure. When the sheath body 610 and the optical assembly 500 are installed, the optical assembly 500 can be inserted into the sheath body 610 with force, so that the first engaging member 611 engages with the first annular groove 511. And because the first annular groove 511 is an annular groove and the first engaging member 611 is a spherical structure, the sheath body 610 and the optical assembly 500 can rotate relative to each other around the first annular groove 511.

[0064] In some embodiments, a plurality of first limiting holes are formed at the rear end of the sheath body 610 and a plurality of first engaging members 611 are provided, and the first engaging members 611 correspond to the first limiting holes one by one.

[0065] The above design ensures that the optical component 500 can rotate freely 360° in the outer sheath 600, ensuring that the user can adjust the position of the optical component 500 at any time for observation according to the situation, while preventing the outer sheath 600 from rotating and pulling the ureteral 820 mucosa, causing perforation, detachment, and rupture of the ureteral 820 mucosa.

[0066] It should be noted that, in some optional embodiments, the outer diameter of the sheath extension 620 is 13.5Fr, and the effective working length is 370mm. The outer diameter of the first extension 520 is 8.1Fr, and the effective working length is 423mm. The third channel 530 of the optical component 500 is an irregular circle with an inner diameter of about 6.6Fr. In addition, the first engaging member 611 can be an annular structure or other shapes, which can be inserted into the first annular groove 511 and rotate around the first annular groove 511.

[0067] Continue reading Figure 12-14 The fourth channel 630 of the outer sheath 600 is formed in the sheath body 610 and the sheath extension 620, and the fourth channel 630 penetrates the sheath body 610 and the sheath extension 620 from front to back. When the optical assembly 500 is installed on the outer sheath 600, the first extension 520 of the optical assembly 500 can be inserted into the fourth channel 630, and the front end of the first body 510 can also be inserted into the fourth channel 630, so that the first annular groove 511 located at the front end of the first body 510 cooperates with the first engaging member 611 in the fourth channel 630, thereby allowing the first body 510 to be rotatably connected with the sheath body 610.

[0068] During assembly, the connection assembly 400 is inserted into the optical assembly 500 from the back to the front, and the outer sheath 600 is sleeved outside the optical assembly 500 from the front to the back, so that the sheath extension 620 is sleeved outside part or all of the first extension 520, forming a layer of protection. More specifically, when the optical assembly 500 is inserted into the outer sheath 600, the first extension 520 of the optical assembly 500 passes through the sheath body 610 through the fourth channel 630 to be inserted into the sheath extension 620, and the first body 510 of the optical assembly 500 cooperates with the first engaging member 611 at the rear end of the sheath body 610 through the first annular groove 511 at the front end to achieve engagement.

[0069] More specifically, the axis of the sheath extension 620 extends in the front-to-back direction, the axis of the first extension 520 extends in the front-to-back direction, the fourth channel 630 also extends in the front-to-back direction, and the axes of the sheath extension 620, the first extension 520 and the fourth channel 630 coincide, and the first annular groove 511 is circumferentially arranged on the first body portion 510, and the first body portion 510 cooperates with the first engaging member 611 through the first annular groove 511 to be connected to the sheath body portion 610 to rotate around the axis of the first extension portion 520. Therefore, when the sheath body portion 610 rotates relative to the first body portion 510, it will rotate around the axis of the first extension portion 520, and at the same time, the sheath extension 620 will also rotate around the axis of the first extension portion 520 relative to the first extension portion 520, so that when the first body portion 510 can rotate relative to the sheath body portion 610, it will also drive the entire connection assembly 400 to rotate relative to the outer sheath 600 along the axis of the first extension portion 520.

[0070] In addition, the sheath body 610 is formed with a suction channel 640, and a gap is formed in the radial direction between the sheath extension 620 and the first extension 520, and the suction channel 640 is connected to the gap. More specifically, there is a gap in the radial direction between the portion of the fourth channel 630 at the sheath extension 620 and the first extension 520, and since the gap is connected to the suction channel 640, when the external suction structure performs suction at the suction channel 640, the perfusion liquid can be transported from the front end of the endoscope structure to the rear end of the endoscope structure through the gap, and then the perfusion liquid is sucked out. The gap is about 0.7 mm, which can discharge the powdered stones in the entire urinary cavity.

[0071] And, optionally, Fig.13 As shown, the front end of the first extension portion 520 extends forward to protrude out of the sheath extension portion 620 , and a protrusion 521 is formed on the side wall of the front end of the first extension portion 520 .

[0072] In addition, in some optional embodiments, such as Fig.13 As shown, the front end of the sheath extension 620 is provided with a mounting member 621, and the mounting member 621 is provided with a mounting through hole for mounting the first extension 520. Specifically, the first extension 520 can pass through the fourth channel 630 to reach the front end of the sheath extension 620 to be inserted into and pass through the mounting through hole, thereby fixing the front end of the first extension 520. Moreover, in some embodiments, a protrusion 521 is formed on the side wall of the front end of the first extension 520, so the mounting through hole is also formed with a groove corresponding to the protrusion 521 for the first extension 520 to pass through.

[0073] The mounting member 621 is formed in a conical shape to reduce the damage to the urethra and ureter 820 when the endoscope structure enters the human body. Optionally, the material of the mounting member 621 is a hard structure.

[0074] When the endoscope is extended into the patient's body, since the side wall at the front end of the first extension part 520 is formed with a protrusion 521, the user can use the protrusion 521 on the first extension part 520 to lift the upper lip of the ureter 820 to smoothly enter the ureter 820. Specifically, the endoscope can be delivered to the orifice of the ureter 820 along the zebra guidewire, and then the user can lift the endoscope and gently and continuously push it, then slowly flatten the endoscope and use the protrusion 521 to lift the upper lip of the ureter 820.

[0075] It should be noted that in the structure with the mounting member 621, the mounting member 621 may be provided with three first through holes 6211, and the perfusion liquid located in front of the endoscope structure may enter the gap between the sheath extension portion 620 and the first extension portion 520 through the first through holes 6211, and finally be sucked out of the patient's body by the suction assembly. More specifically, the suction assembly is disposed at one end of the suction channel 640, and the sucked perfusion liquid first enters the fourth channel 630 through the first through hole 6211, and then successively passes through the fourth channel 630 and the suction channel 640 and finally enters the suction assembly. The suction assembly may be a device having the function of negative pressure suction perfusion liquid, such as a negative pressure aspirator and a manual negative pressure suction bottle.

[0076] Secondly, the cross-sectional area of ​​the gap and the suction channel 640 is larger than the cross-sectional area of ​​the water delivery channel 430 and the first channel, and the gap and the suction channel 640 are connected to the suction assembly. When the lithotripsy channel is established, some small fragments of stones or powder can be directly sucked out of the body through the hard endoscope sheath connected to the negative pressure, reducing the escape of stones. Some slightly larger fragments that are not easy to crush can also be taken out of the body by lithotripsy forceps, "clamps" "net basket sleeves", etc., to achieve a higher stone removal rate.

[0077] For easier understanding, see Figure 6 and Figure 8 It is not difficult to find that the second channel 410 and the third channel 530 extend from front to back, and the water delivery channel 430 is perpendicular to the second channel 410. After the connection component 400, the optical component 500 and the outer sheath 600 are assembled, the laser fiber component 300 can be inserted from back to front into the rear end of the connection component 400 and connected to the connection component 400.

[0078] In addition, optional Figure 14-16As shown, the laser fiber assembly 300 includes a control assembly 340, two or more traction wires, an optical fiber outer sheath tube 330, and a laser optical fiber 310. The laser optical fiber 310 is installed in the optical fiber outer sheath tube 330, and the control assembly 340 is used to control the two or more traction wires to control the front end bending of the optical fiber outer sheath tube 330, thereby driving the front end bending of the laser optical fiber 310.

[0079] Optionally, the laser fiber assembly 300 includes a damping structure 360, and the laser fiber 310 is slidably installed in the optical fiber outer sheath tube 330 so that the laser fiber 310 can move forward and backward along the optical fiber outer sheath tube 330, and an optical fiber through hole is formed in the damping structure 360 ​​for the laser fiber 310 to pass through, and the optical fiber through hole and the laser fiber 310 are interference-fitted to provide damping for the movement of the laser fiber 310 relative to the optical fiber outer sheath tube 330. Specifically, the optical fiber outer sheath tube 330 is formed with a laser fiber channel 331, and the laser fiber 310 can move along the laser fiber channel 331. Since the laser fiber 310 is slidably installed in the optical fiber outer sheath tube 330, the user can adjust the front and rear position of the laser fiber 310 according to the situation, for example, the laser fiber 310 can be extended or retracted to align with the stone.

[0080] Specifically, the control assembly 340 includes a rotating member 341, a rotating rod 342, a spur gear connecting rod 343, a gear 344, a first rack 345, and a second rack 346. The user can rotate the rotating member 341 relative to the handle 320 to drive the rotating rod 342 to rotate and drive the spur gear connecting rod 343 to move. The movement of the spur gear connecting rod 343 will drive the first rack 345 to move, and the first rack 345 drives the second rack 346 to move through the gear 344, and finally the first rack 345 and the second rack 346 form opposite movements. At the same time, the first rack 345 and the second rack 346 are respectively connected to two traction lines, which can drive the optical fiber outer sheath tube 330 and the optical fiber located in the optical fiber outer sheath tube 330 to bend. More specifically, the front ends of the two traction wires are respectively located on the left and right sides of the optical fiber outer sheath tube 330, and the rear ends of the two traction wires are respectively connected to the first rack 345 and the second rack 346. Therefore, when the first rack 345 and the second rack 346 move forward and backward, one of the traction wires will be tightened and the other traction wire will be relaxed, thereby causing the optical fiber outer sheath tube 330 to bend to the left or right.

[0081] It should be noted that since the present invention only needs to bend the laser fiber and the optical fiber outer sheath 330 sleeved outside the laser fiber, the bending control structure of the laser fiber assembly 300 of the present invention is relatively simple and does not require additional snake bones to complete, which makes the production cost relatively low and the manufacturing difficulty relatively simple.

[0082] Optionally, the laser fiber assembly 300 is rotatably connected to the connecting assembly 400, so that the laser fiber assembly 300 can rotate relative to the outer sheath 600. More specifically, the front end of the handle 320 of the laser fiber assembly 300 is formed with a second annular groove 321, and the rear end of the second channel 410 of the connecting assembly 400 is formed with a second limiting hole and provided with a second clamping piece, and the second clamping piece can partially protrude from the second limiting hole to cooperate with the second annular groove 321 so that the rear end of the connecting assembly 400 and the front end of the handle 320 can be detachably connected, wherein the aperture of the second limiting hole is smaller than the maximum size of the second clamping piece, thereby limiting the second clamping piece from being separated from the second limiting hole. Optionally, the second clamping piece is a spherical structure. When the rear end of the connecting assembly 400 is installed with the front end of the handle 320, the front end of the handle 320 can be inserted into the connecting assembly 400 with force, so that the second clamping piece is engaged with the second annular groove 321. Furthermore, since the second annular groove 321 is an annular groove and the second engaging member is a spherical structure, the connecting assembly 400 and the laser optical fiber assembly 300 can rotate relative to each other.

[0083] When using the endoscope structure of the present invention, first, the outer sheath 600, the optical component 500, the connecting component 400, the temperature and pressure measuring components, etc. need to be connected as shown in FIG. Figure 2 Assemble as shown, connect external equipment, put the patient into anesthesia, put him in surgical position, and prepare for treatment.

[0084] Secondly, connect the perfusion water circuit to the two Luer connectors of the connection assembly 400, and adjust the perfusion pressure to between 30 and 40 cmH20.

[0085] Next, connect a hose with one end connected to the opening of the suction channel 640 of the outer sheath 600 and the other end connected to the negative pressure suction bottle. Set the negative pressure suction pressure of the suction component to -60 to -90 kPa so that the suction component can suck the crushed stones and perfusion fluid through the negative pressure suction bottle.

[0086] Then, the optical assembly 500 is connected to the light guide, and by connecting the eyepiece cover to the image processing system, the image obtained by the optical detector 200 is imaged on the monitor.

[0087] Next, the outer sheath 600 and the mounting member 621 are coated with medical lubricant, and the endoscope structure is inserted into the bladder 810 through the urethra under direct vision of the imaging device.

[0088] Next, the irrigation water circuit and the negative pressure suction bottle are opened; the opening of the ureter 820 in the bladder 810 is flushed open with water pressure, and a zebra guidewire is inserted. Then, the endoscope structure enters the ureter 820 under the guidance of the zebra guidewire, and enters the lesion position corresponding to the ureter 820.

[0089] Then, the direction of the adjustable laser fiber 310 catheter is adjusted to guide the laser fiber 310 to the location of the stone. The laser fiber 310 excites energy to crush the stone into small fragments or powder, and the small fragments and powder of the stone are sucked out through the suction component.

[0090] Furthermore, the temperature and pressure measuring optical fiber 700 sensor is used to monitor the pressure of the ureter 820, and timely feedback and adjustment parameters are provided to avoid the occurrence of related complications.

[0091] Finally, after checking that there is no residual stone in the entire ureter 820, the operation is ended while withdrawing the endoscope and observing the damage to the ureteral 820 mucosa.

[0092] This solution provides a bendable laser fiber 310, but does not make the front end of the endoscope structure bendable as a whole, so that the entire design is relatively simple and convenient, which reduces costs and reduces the difficulty of production. Secondly, through the cooperation between the bendable laser fiber 310 and the outer sheath 600, the laser fiber 310 of the endoscope structure disclosed in the present invention can be extended into various parts of the entire urinary cavity to crush and recover stones in the entire urinary cavity, including the urethra, bladder 810, lower section of ureter 820, middle section of ureter 820 and upper section of ureter 820, and is compatible with the functions of ureteroscope soft and ureteroscope hard, and has a relatively simple structure and is easy to operate.

[0093] Obviously, the above embodiments of the present disclosure are merely examples for clearly illustrating the present disclosure, and are not intended to limit the implementation methods of the present disclosure. For those of ordinary skill in the art, other different forms of changes or modifications can be made based on the above description. It is not necessary and impossible to list all implementation methods here. Any modifications, equivalent substitutions, improvements, etc. made within the spirit and principles of the present disclosure shall be included in the protection scope of the claims of the present disclosure.

[0094] Obviously, the above embodiments of the present disclosure are merely examples for clearly illustrating the present disclosure, and are not intended to limit the implementation methods of the present disclosure. For those of ordinary skill in the art, other different forms of changes or modifications can be made based on the above description. It is not necessary and impossible to list all implementation methods here. Any modifications, equivalent substitutions, improvements, etc. made within the spirit and principles of the present disclosure shall be included in the protection scope of the claims of the present disclosure.

Claims

1. An endoscope structure, characterized in that: The invention comprises a connecting component (400), an optical component (500), an optical detector (200), and a laser fiber component (300), wherein the optical detector (200) is arranged on the optical component (500), the connecting component (400) is formed with a second channel (410) which passes through the connecting component (400) from front to back, wherein the optical component (500) and the connecting component (400) are detachably connected, wherein the optical component (500) is formed with a third channel (530) which passes through the optical component (500), and when the optical component (500) and the connecting component (400) are connected, the second channel (410) and the third channel (530) are connected to form the first channel, and the laser fiber component (300) is installed on the connecting component (400), and the front end of the laser fiber component (300) passes through the first channel to extend out of the optical component (500).

2. The endoscope structure according to claim 1, characterized in that: The second channel (410) is provided with a first sealing component (420), and the first sealing component (420) forms a laser fiber through hole (4231) for the laser fiber assembly (300) to pass through, and the first sealing component (420) is tightly fitted with the laser fiber assembly (300) to prevent the perfusion liquid in the second channel (410) from flowing from one side of the laser fiber through hole (4231) to the other side of the laser fiber through hole (4231).

3. The endoscope structure according to claim 1, characterized in that: The optical device further comprises an outer sheath tube (600), wherein the outer sheath tube (600) comprises a sheath tube main body (610) and a sheath tube extension part (620) connected in sequence from the back to the front, the sheath tube main body (610) is connected to the optical component (500), the outer sheath tube (600) is sleeved outside part or all of the connecting component (400) and the optical component (500), the outer diameter of the sheath tube extension part (620) is 2-10 mm, and the length of the sheath tube extension part (620) is 1 00-500mm, the laser fiber assembly (300) is a bendable fiber assembly, so that the front end of the laser fiber assembly (300) located outside the sheath extension (620) can be bent relative to the sheath extension (620), wherein the sheath extension (620) is made of a hard material, and a gap is formed between the sheath extension (620) and the optical assembly (500), and the gap is used to communicate with the suction assembly, and the outer sheath (600) is formed with a lubricating layer.

4. The endoscope structure according to claim 3, characterized in that: The optical component (500) comprises a first main body portion (510) and a first extension portion (520) which are connected in sequence from back to front, the optical detector (200) is arranged on the first extension portion (520), wherein the first main body portion (510) and the front end portion of the connecting component (400) are detachably connected, wherein the third channel (530) is formed on the first main body portion (510) and the first extension portion (520), and the third channel passes through the first main body portion (510) and the first extension portion (520) from front to back.

5. The endoscope according to claim 4, characterized in that The front end of the first extension portion (520) extends forward to protrude outside the sheath extension portion (620), and a protrusion is formed on the side wall of the front end of the first extension portion (520).

6. The endoscope structure according to claim 3, characterized in that: The laser optical fiber assembly (300) is rotatably connected to the connecting assembly (400), so that the laser optical fiber assembly (300) can rotate relative to the outer sheath tube (600).

7. The endoscope structure according to claim 3, characterized in that: The connection component (400) forms a water delivery channel (430), a water delivery opening formed at one end of the water delivery channel (430) is located on the surface of the connection component (400), and the other end of the water delivery channel (430) is connected to the second channel (410), and the water delivery opening is used for external perfusion liquid to flow in.

8. The endoscope according to claim 3, characterized in that: The sheath tube body (610) and the optical component (500) are detachably connected, and the sheath tube body (610) and the optical component (500) are relatively rotatable.

9. The endoscope structure according to claim 3, characterized in that: The laser fiber assembly (300) includes a control assembly (340), two or more traction wires, an optical fiber outer sheath tube (330), and a laser optical fiber (310). The laser optical fiber (310) is installed in the optical fiber outer sheath tube (330), and the control assembly (340) is used to control the two or more traction wires to control the bending of the front end of the optical fiber outer sheath tube (330), thereby driving the bending of the front end of the laser optical fiber (310).

10. The endoscope structure according to claim 9, characterized in that: The laser fiber assembly (300) includes a damping structure (360), the laser fiber (310) is slidably installed in the optical fiber outer sheath tube (330) so that the laser fiber (310) can move forward and backward along the optical fiber outer sheath tube (330), and a fiber through hole is formed in the damping structure (360) for the laser fiber (310) to pass through, and the fiber through hole and the laser fiber (310) are interference fit to provide damping for the movement of the laser fiber (310) relative to the optical fiber outer sheath tube (330).

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