CN115886706A - Vibrating device and vibration anti-blocking ureteroscope - Google Patents

Abstract

The utility model discloses a vibrating device prevents stifled formula ureteroscope with vibration, wherein, prevent stifled formula ureteroscope is prevented in vibration includes: the tube lens comprises a tube lens main body with a front end part and a rear end part, an operation part coupled to the rear end part of the tube lens main body, and a vibration device arranged on the tube lens main body. The vibrating device comprises a vibrating rod arranged in the suction channel of the tube lens main body, the vibrating rod is driven to vibrate in a direction which is a preset included angle with the radial direction set by the tube lens main body in a working state, so as to drive the crushed calculi in the suction channel to reciprocate in the non-radial direction of the tube lens main body, and the calculi in the suction channel are guided in a non-radial direction in a linear arrangement manner and are guided through the suction channel.

Description

Vibrating device and vibration anti-blocking type ureteroscope

Technical Field

The application relates to the field of medical equipment, in particular to a vibrating device, a vibrating anti-blocking ureteroscope and a method for guiding out calculus by using the ureteroscope.

Background

The ureteroscope is a medical instrument which can extend into a ureter or a kidney from a urethral orifice, and can be widely applied to treatment of urinary calculus diseases. For example, ureteroscopy is used to treat kidney stones.

The existing ureteroscope can treat kidney stones by matching perfusion flushing with negative pressure suction. Specifically, in the treatment of renal stones using a ureteroscope, first, the ureteroscope is inserted into the kidney, then stones in the renal pelvis are crushed, and then the crushed stones are discharged out of the body through a discharge passage by the action of perfusion flushing and negative pressure suction.

However, in practical applications, in the process of discharging the crushed stones out of the body through the discharge channel by the action of irrigation and negative pressure suction, the crushed stones are easily blocked in the discharge channel and are difficult to be discharged out of the body of the patient, and the problem of low stone discharge rate occurs. The unextracted calculus may form a stone street in the ureter to block the ureter, and the calculus disease is recurrent.

Therefore, a new ureteroscope is needed to avoid the blockage of the calculus in the discharge channel as much as possible, and to improve the calculus removal efficiency.

Disclosure of Invention

One advantage of the present application is that a vibration device and vibration anti-blocking ureteroscope are provided, wherein, vibration anti-blocking ureteroscope can change and be beaten garrulous calculus and be in the radial ascending distribution that vibration anti-blocking ureteroscope set for to destroy and be beaten garrulous calculus and be in radial ascending pile up, and then avoid being beaten garrulous calculus and take place to block up in attracting the passageway.

Another advantage of this application lies in providing a vibrating device and vibration prevent stifled formula ureteroscope, wherein, prevent stifled formula ureteroscope in the vibration can drive the lithangiuria of being hit in attracting the passageway and be reciprocating motion on the nonradial direction of vibration prevent stifled formula ureteroscope, in order to guide attract the interior lithangiuria that takes place to block up of passageway and arrange on nonradial direction is linear, passes through under the impact of rivers attract the passageway progressively remove external, and then improve the lithangiuria and derive efficiency.

To achieve at least one of the advantages described above, according to one aspect of the present application, there is provided a vibration anti-blocking ureteroscope comprising:

an operation section;

a tube lens body having a front end and a rear end, comprising: a tube structure body, at least one perfusion channel extending within the tube structure body from the rear end to the front end, a suction channel extending within the tube structure body from the front end to the rear end, the suction channel having a suction port at the front end, the operating portion being coupled to the rear end of the tube scope body; and

set up in the vibrating device of tube mirror main part, vibrating device including set up in attract the vibrating arm in the passageway, the vibrating arm is driven under operating condition with the tube mirror main part sets up radially become the direction vibration of predetermineeing the contained angle, in order to drive attract the interior garrulous calculus of being hit of passageway to be in be reciprocating motion in the non-radial direction of tube mirror main part, through such mode guide is in attract the interior calculus of passageway to be in linear arrangement on the non-radial direction passes through under the impact of rivers attract the passageway to remove gradually externally.

In the vibration anti-blocking ureteroscope according to the application, the vibration rod comprises a rod body and at least one protrusion portion which is protrudingly arranged on the peripheral side surface of the rod body.

In the vibration block-resistant ureteroscope according to the present application, the leading end of the protrusion is adjacent to the suction port.

In the vibration anti-blocking ureteroscope according to the present application, the vibration rod extends forward to the suction port in the axial direction set by the scope main body.

In the vibration anti-blocking ureteroscope according to the present application, the tube structure main body has a front end surface, and the suction port is formed in the front end surface.

In the vibration block-resistant ureteroscope according to the present application, the tube structure main body further has an outer peripheral surface, and the leading end surface extends obliquely forward from a first side of the outer peripheral surface to a second side opposite to the first side in an axial direction set by the scope main body.

In the vibration anti-blocking ureteroscope according to the application, the vibrating rod is located in the suction channel.

In the vibration anti-blocking ureteroscope according to the application, the vibration frequency of the vibration rod is 20 Hz to 40 Hz.

In the vibration anti-blocking ureteroscope according to the application, the vibrating rod drives the broken calculus in the suction channel to reciprocate in the axial direction set by the ureteroscope main body when being driven to vibrate.

In the vibration anti-blocking ureteroscope according to this application, the vibrating device further including be coupled in the power supply of vibrating arm, the power supply is configured as the drive the vibrating arm vibrates with the preset direction.

In the vibration anti-blocking ureteroscope according to the present application, the scope body further includes a stone striking channel for allowing a stone striking mechanism to pass through, the stone striking channel extending from the front end portion to the rear end portion within the tube structure body.

In accordance with another aspect of the present application, there is also provided a method of using a ureteroscope to deliver stones, comprising:

the laser emitted by the stone-hitting mechanism hits and breaks stones;

guiding the crushed stone into a suction channel; and

the broken stones in the suction channel are guided by the vibration device to be linearly arranged in the non-radial direction of the tube lens main body, and are gradually removed from the body through the suction channel under the impact of water flow.

In a method of ureteroscopically deriving a stone according to the application, a crushed stone guided in the aspiration channel by a vibrating device is linearly aligned in a non-radial direction of the scope body, comprising: a vibrating rod that drives the vibrating device to vibrate in a non-radial direction of the tube lens main body; impacting the crushed stone by a projection of the vibration device; and driving the crushed stones to reciprocate in the non-radial direction of the tube lens main body.

According to yet another aspect of the present application, there is also provided a vibrating device for a ureteroscope comprising: a vibration rod including a rod body and a protrusion protrudingly provided at an outer circumferential side of the rod body; and a power source coupled to the vibration rod and configured to drive the vibration rod to vibrate in a preset direction.

Further objects and advantages of the present application will become apparent from an understanding of the ensuing description and drawings.

These and other objects, features and advantages of the present application will become more fully apparent from the following detailed description, the accompanying drawings and the claims.

Drawings

The above and other objects, features and advantages of the present application will become more apparent by describing in more detail embodiments of the present application with reference to the attached drawings. The accompanying drawings are included to provide a further understanding of the embodiments of the application and are incorporated in and constitute a part of this specification, illustrate embodiments of the application and together with the description serve to explain the principles of the application. In the drawings, like reference numbers generally represent like parts or steps.

Fig. 1 illustrates a schematic view of a vibrating anti-blocking ureteroscope according to an embodiment of the present application.

Fig. 2 illustrates a schematic cross-sectional view of a scope body of a vibrating anti-blocking ureteroscope according to an embodiment of the present application.

Fig. 3A illustrates one of the partial schematic views of the body of a vibrating block-resistant ureteroscope according to an embodiment of the present application.

Fig. 3B illustrates a second partial schematic view of the body of a vibrating block-resistant ureteroscope according to an embodiment of the present application.

Fig. 3C illustrates a third schematic view of a portion of the scope body of a vibrating anti-blocking ureteroscope according to an embodiment of the present application.

Fig. 3D illustrates four of a partial schematic view of a tube lens body of a vibrating anti-blocking ureteroscope according to embodiments of the present application.

FIG. 4 illustrates a partial schematic view of a vibration device according to an embodiment of the present application.

FIG. 5 illustrates a schematic diagram of a vibration device according to an embodiment of the present application.

FIG. 6 illustrates another schematic view of a vibration device according to an embodiment of the present application.

Fig. 7A illustrates one of the schematic working process diagrams of the vibrating anti-blocking ureteroscope according to the embodiments of the present application.

Fig. 7B illustrates a second schematic operation of the vibrating anti-blocking ureteroscope according to an embodiment of the present application.

Fig. 7C illustrates a third schematic operation process of the vibration anti-blocking ureteroscope according to the embodiment of the present application.

Figure 8 illustrates a flow diagram of a method of using a ureteroscope to derive stones according to an embodiment of the present application.

Detailed Description

Hereinafter, example embodiments according to the present application will be described in detail with reference to the accompanying drawings. It should be understood that the described embodiments are only some embodiments of the present application and not all embodiments of the present application, and that the present application is not limited by the example embodiments described herein.

Summary of the application

As described above, in practical applications, in the process of discharging the crushed stone out of the body through the discharge channel by the action of perfusion flushing and negative pressure suction, the crushed stone is easily blocked in the discharge channel, and is difficult to be discharged out of the body of the patient, so that the problem of low stone discharge rate occurs.

In particular, for inserting the ureteroscope into the ureter, the radial dimension of the ureteroscope is limited, and the discharge channel for discharging the crushed stones is constrained by the radial dimension of the ureteroscope, which likewise has limited radial space. When more crushed stones enter the discharge passage at the same time, a large amount of crushed stones are attracted by negative pressure and move in the same direction, so that blockage is easy to occur, other crushed stones are prevented from entering or passing through the discharge passage, the crushed stones are difficult to discharge, the stone discharge efficiency is low, and the operation time is long.

The idea of the inventor of the present application to solve the above problems is: a vibration device is arranged in a channel for leading out the crushed stone to avoid the crushed stone from being blocked in the channel, so that the crushed stone is smoothly discharged. Specifically, the stones in the channel for leading out the crushed stones are driven by the vibration device to reciprocate in the non-radial direction of the ureteroscope, and the distribution of the crushed stones in the radial direction set by the ureteroscope is changed, so that the stacking of the crushed stones in the radial direction is damaged, and the crushed stones are prevented from being blocked in the channel.

Based on this, the application provides a vibration prevents stifled formula ureteroscope, and it includes: the tube lens comprises a tube lens main body with a front end part and a rear end part, an operation part coupled to the rear end part of the tube lens main body, a stone striking mechanism arranged on the tube lens main body and a vibration device arranged on the tube lens main body. The tube lens main body includes: the suction channel is provided with a suction port at the front end. The vibrating device comprises a vibrating rod arranged in the suction channel, the vibrating rod is driven to vibrate in a direction which is a preset included angle with the radial direction set by the tube lens main body in a working state so as to drive crushed stones in the suction channel to do reciprocating motion in the non-radial direction of the tube lens main body, and the stones in the suction channel are guided to be linearly arranged in the non-radial direction in such a way and are gradually removed from the body through the suction channel under the impact of water flow.

Exemplary ureteroscope

As shown in fig. 1 to 7C, a vibration block-resistant ureteroscope 100 according to an embodiment of the present application is illustrated. The vibrating anti-blocking ureteroscope 100 may be used in the treatment of kidney stones. Specifically, the vibration block resistant ureteroscope 100 may be used to examine the condition of the kidney, break up stones within the renal pelvis, and guide the broken stones out. In the embodiment of the present application, the vibration anti-blocking ureteroscope 100 includes: the tube lens comprises a tube lens body 10 with a front end part 110 and a back end part 120, an operation part 20 operatively coupled to the back end part 120 of the tube lens body 10, and a vibration device 40 arranged on the tube lens body 10.

In practical applications, the tube lens main body 10 as the insertion portion of the vibration anti-blocking ureteroscope 100 may extend from the urethra into the kidney, and an image collecting device 300 and a light source 400 may be disposed on the tube lens main body 10 to collect images of the kidney and stones in the kidney. Preferably, the tube lens body 10 has a smooth outer surface, or the outer surface of the tube lens body 10 is smooth after entering the patient, so that the tube lens body 10 can smoothly enter the kidney. The operation portion 20, as a bridge of the vibration anti-blocking ureteroscope 100 connected to an external device, can be communicably connected to an image output device (e.g., a computer communicably connected to the image acquisition device 300) to acquire an image of the kidney and the stone in the kidney, thereby facilitating medical workers to observe the condition of the stone in the renal pelvis. Further, the operable member (e.g., the stone striking mechanism 200, the guide mechanism, the liquid injection device, the suction device) can perform other functional operations by the operation portion 20. For example, the operation unit 20 operates the stone striking mechanism 200 provided in the scope body 10 to strike a stone. The stone striking mechanism 200 may be implemented as a holmium laser, or other laser mechanism that strikes the stone, or other mechanism that can be used to strike the stone. The vibration device 40 is used to drive the crushed stones in the suction channel 13 to move, so as to prevent the crushed stones from blocking in the suction channel 13.

Specifically, the tube mirror body 10 includes a tube structure body 11, an irrigation passage 12, and a suction passage 13, as shown in fig. 2. The priming channel 12 extends within the tube structure body 11 from the rear end 120 to the front end 110, and the suction channel 13 extends within the tube structure body 11 from the front end 110 to the rear end 120. Also, preferably, the perfusion channel 12 and the suction channel 13 are isolated from each other, so that directing fluid through the perfusion channel 12 into the kidney to impact the crushed stone, drawing fluid carrying the crushed stone to the suction channel 13 can be done simultaneously, and avoiding interference between impacting the stone and drawing the stone.

More specifically, the perfusion channel 12 has at least one perfusion port 121 at the front end portion 110 and at least one first operation port 122 in communication with the at least one perfusion port 121, and fluid can reach the kidney from the perfusion port 121 and impact crushed stones in the kidney. The suction channel 13 has a suction port 131 at the distal end portion 110 and a second operation port 132 communicating with the suction port 131, and when the fluid carrying the crushed stone reaches the vicinity of the suction port 131, the fluid is sucked to the suction port 131 and enters the suction channel 13 from the suction port 131 to form a water return loop. That is, the crushed stones can enter the suction channel 13 from the suction port 131 by the water backflow loop to be guided out through the suction channel 13.

Accordingly, the operation part 20 includes an operation body 21, a first operation end 22 (not shown) provided to the operation body 21 and communicating with the perfusion channel 12, and a second operation end 23 (not shown) provided to the operation body 21 and communicating with the suction channel 13. The operation portion 20 communicates with the perfusion channel 12 through the first operation end 22 communicating with the first operation port 122, and communicates with the suction channel 13 through the second operation end 23 communicating with the second operation port 132. The first operative end 22 is adapted to connect to a priming device and allow the priming device to inject fluid through the perfusion channel 12 into the renal pelvis to impact the crushed stones, and the second operative end 23 is adapted to connect to a suction device (e.g., an air pump) and allow the suction device to suck fluid and crushed stones near the suction channel 13 through the suction channel 13. As shown in fig. 1, in order to control the negative pressure in the suction passage 13, in one embodiment of the present application, the operating portion 20 further includes a negative pressure regulator 27, and the negative pressure regulator 27 is configured to regulate the pressure in the suction passage 13.

It should be understood that the roles of the first operating end 22 and the second operating end 23 are not intended to limit the present application. The first operating end 22 and the second operating end 23 are also adapted to allow other devices to perform other functional operations. For example, the first manipulation end 22 is adapted to allow a guide mechanism 600 to pass through the perfusion channel 12 and guide the scope body 10 to a target location. It should also be understood that the operating portion 20 may include other operating ends to allow other devices to perform other functional operations.

In some embodiments of the present application, the tube lens body 10 further includes a stone-hitting channel 14 (not shown) extending from the rear end portion 120 to the front end portion 110, and configured to allow the stone-hitting mechanism 200 to pass through, and accordingly, the stone-hitting mechanism 200 may be disposed in the stone-hitting channel 14. The stone hitting channel 14 may be connected to the suction channel 13, or may be isolated from the suction channel 13, which is not limited in the present application. When the stone hitting channel 14 is communicated with the suction channel 13, the stone hitting mechanism 200 can extend out from the suction port 131 to hit stones. When the stone striking channel 14 and the suction channel 13 are isolated from each other, the stone striking channel 14 has a fiber opening at the front end portion 110 and a third operation port at the rear end portion 120, and the stone striking mechanism 200 can protrude from the fiber opening to strike a stone.

In a specific example of the present application, the stone striking channel 14 communicates with the suction channel 13. The stone striking channel 14 includes a main body section and a communication section extending between the main body section and the suction channel 13, the communication section having the communication port communicating with the suction channel 13 and communicating with the suction channel 13 via the communication port, and the communication section extending obliquely upward from the main body section to the suction channel 13 along a predetermined direction. In this particular example, the angle between the preset extension direction and the central axis of the suction channel 13 is 45 °. Accordingly, an included angle between a central axis of the communicating section and a central axis of the suction passage 13 is 45 °, and the stone striking mechanism 30 can extend into the suction port 131 along the communicating section in a direction inclined by an angle of 45 ° with respect to the central axis of the suction passage 13. It will be appreciated that the steeper the communication section is, the closer the central axis thereof coincides with the central axis of the suction passage 13, and the faster the stone striking mechanism passes through the suction passage 13 and protrudes out of the suction port 131. The angle between the communicating section and the central axis of the suction channel 13 may be other angles, for example, 30 °,60 °, and is not limited in this application.

The stone striking mechanism 200 may be fixed in the stone striking channel 14, or may be movably installed in the stone striking channel 14, which is not limited in this application. In a specific example of the present application, the stone striking mechanism 200 is telescopically disposed in the stone striking channel 14, and the stone striking mechanism 200 can be extended or retracted from the stone striking channel opening or the suction port 131 in the stone striking channel 14. In another specific example of the present application, the stone striking mechanism 200 is movable with respect to the central axis of the suction port 131, and is movable in the stone striking channel 14 in a direction close to the central axis of the suction port 131, or movable in the stone striking channel 14 in a direction away from the central axis of the suction port 131.

Accordingly, in some embodiments of the present application, the operation portion 20 further includes a third operation end 24 (not shown) disposed on the operation body 21 and communicated with the stone striking channel 14. The operation portion 20 communicates with the stone striking passage 14 through the third operation end 24 thereof communicating with the third operation port 142. The third operative end 24 is adapted to allow the stone striking mechanism 200 to pass through and extend into the stone striking channel 14.

During surgery, the stone striking mechanism 200 (e.g., holmium laser) may pass through the scope body 10 into the kidney and strike the stone. During the stone breaking up of the stone by the stone breaking mechanism, the irrigation channel 12 may direct fluid to exit from the irrigation port 121 to impact the stone and entrain the movement of the broken up stone. The internal pressure of the suction channel is in a negative pressure state, so when the fluid carries the crushed stones to move to a position close to the suction port 131, the fluid and the crushed stones are sucked to the suction channel 13.

It is worth mentioning that the radial dimension of the vibration anti-blocking ureteroscope 100 is limited, and the radial space of the suction channel 13 is also limited due to the constraint of the radial dimension of the vibration anti-blocking ureteroscope 100. When a large number of crushed stones enter the suction channel 13 at the same time, the large number of crushed stones move in the same direction, and the crushed stones located in the suction channel 13 are stacked in the radial direction set by the tube lens body 10, easily block the suction channel 13, and are difficult to move backward. Thus, not only the crushed stones blocked in the blocked section of the suction channel 13 are difficult to be discharged, but also the crushed stones located in front of the blocked section of the suction channel 13 are blocked in the suction channel 13 or outside the suction channel 13 due to the blocking of at least one section of the suction channel 13, and more crushed stones are deposited in the suction channel 13 to form a stone street, which is difficult to be discharged, resulting in low stone discharge efficiency and long operation time.

In particular, in the present embodiment, the vibration block-resistant ureteroscope 100 is provided with the vibration device 40. The vibrating device 40 comprises a vibrating rod 41 arranged in the suction channel 13, the vibrating rod 41 is driven to vibrate in a direction forming a preset included angle with the radial direction set by the tube lens main body 10 in a working state, so as to drive the broken stones in the suction channel 13 to reciprocate in the non-radial direction of the tube lens main body 10, and the broken stones are broken down to be stacked in the radial direction set by the tube lens main body 10, and the gaps among the broken stones in the non-radial direction are changed in such a way, so as to guide the stones in the suction channel 13 to be linearly arranged in the non-radial direction, so that the broken stones are prevented from being blocked in the channel, and then the stones are led out through the suction channel 13.

Specifically, as shown in fig. 2 and 4, the vibration rod 41 includes a rod body 411 and at least one protrusion 412 protrudingly disposed on an outer circumferential side of the rod body 411. When the vibration rod 41 is driven to move in the operating state, the vibration rod 41 vibrates in the suction channel 13 in a direction forming a preset included angle with the radial direction set by the borescope main body 10, that is, the vibration rod 41 vibrates in the suction channel 13 in a non-radial direction. When the crushed stones hit the protrusion 412, the crushed stones are hit off the protrusion 412, then fall back to the protrusion 412, then bounce off by the protrusion 412, then fall back to the protrusion 412 again, and so on. In this way, the stack of the crushed stones in the radial direction is destroyed and the gaps of the crushed stones in the non-radial direction, in which they are linearly arranged, are changed. The process is like screening sand, and the arrangement mode among the sand changes when the sand is repeatedly raised and falls, so that the sand is screened out through the gauze. The oscillating rod 41 prevents the crushed stones from being blocked in the suction channel 13 as much as possible, so that the crushed stones can be more quickly discharged through the suction channel 13, and the stone discharge efficiency is improved.

Preferably, the vibrating rod 41 vibrates in the axial direction set by the tube lens main body 10 when driven to vibrate, so as to drive the broken stones in the suction channel 13 to reciprocate in the axial direction set by the tube lens main body 10, as shown in fig. 7A to 7C.

It will be appreciated that the frequency of vibration of the vibrating rod affects the effect of the vibrating rod in directing the crushed stones. When the vibration frequency of the vibrating bar is too high, the crushed stones at the suction port are easy to pop out of the suction channel, and when the vibration frequency of the vibrating bar is lower, the popping amplitude of the crushed stones is small, the adjusting speed is slow, and even the crushed stones can be popped up by law. In the embodiment of the application, the vibration frequency of the vibration rod is 20 Hz to 40 Hz.

It should be noted that the protrusion 412 of the oscillating rod 41 may penetrate the entire suction passage 13 in the axial direction set by the scope body 10, that is, the protrusion 412 extends from the front end of the suction passage 13 to the rear end of the suction passage 13. The protrusion 412 of the oscillating rod 41 may be provided only in a partial region of the suction channel 13 in the axial direction set by the tube lens body 10, for example, only in a front stage of the suction channel 13, which is not intended to limit the present invention. The at least one protrusion 412 may extend continuously in the suction channel 13 or may extend at intervals in the suction channel 13, which is not limited by the present application.

Accordingly, in some embodiments of the present application, the rod 411 extends from the front end 110 to the rear end 120 within the suction channel 13, and the protrusion 412 extends from the front end 110 to the rear end 120 within the suction channel 13. In other embodiments of the present application, the protrusion 412 extends from a first predetermined area to a second predetermined area of the suction channel 13 in the suction channel 13, and can drive the crushed stones in the first predetermined area and the second predetermined area to move back and forth in the non-radial direction, so as to dredge the stones in the suction channel 13 and avoid the crushed stones from being blocked in the suction channel 13 as much as possible.

The position of the protrusion 412 may be designed according to practical applications, for example, when the crushed stones are easy to block in the middle of the suction channel 13, the protrusion 412 may be provided only in the middle of the suction channel 13; when the crushed stones are likely to be clogged at the front section of the suction passage 13, the protrusion 412 may be provided only at the front section of the suction passage 13, which is not a limitation of the present application.

In one specific example of the present application, the vibrating rod 41 is designed to be telescopically disposed in the suction channel 13, such that the position of the protrusion 412 in the suction channel 13 can be adjusted according to practical application to dredge and guide the crushed stones in the region where the blockage occurs. In other specific examples, the vibration rod 41 is designed to be non-telescopically disposed in the suction channel 13, and the application is not limited thereto.

In a specific example of the present application, the front end of the protrusion 412 is adjacent to the suction port 131. Specifically, the rod body 411 extends forward to the suction port 131 in the axial direction set by the tube lens body 10, the protrusion 412 extends forward to the suction port 131 in the axial direction set by the tube lens body 10, and the leading end of the protrusion 412 is located at the suction port 131 in the axial direction set by the tube lens body 10. In this embodiment, the pipe structural body 11 has a front end face 1101 and an outer peripheral surface 1102, the suction port 131 is formed in the front end face 1101, and the front end of the projection 412 is flush with the front end face 1101.

In this specific example, the front end face 1101 of the pipe structural body 11 is designed to: extends obliquely forward from a first side of the outer peripheral surface 1102 to a second side opposite to the first side in an axial direction set by the tube lens body 10. For example, the front end surface 1101 of the tube structure body 11 extends obliquely forward from a lower side set by the outer peripheral surface 1102 to an upper side opposite to the lower side in the axial direction set by the tube mirror body 10, as shown in fig. 3A.

Specifically, the front end surface 1101 may be designed as a convex slope, a concave slope, a wave slope, and other types of slopes formed between the first side and the second side of the outer peripheral surface 1102, which is not limited in this application. In one embodiment of the present application, the front end surface 1101 is designed as a wave-shaped inclined surface depressed in the middle between the first side and the second side of the outer peripheral surface 1102.

It should be understood that, in other embodiments, the front end face 1101 of the tubular main body 11 may also be designed such that the front end face 1101 of the tubular main body 11 extends flush along the axial direction set by the mirror main body 10 from a first side of the outer peripheral surface 1102 to a second side opposite to the first side (i.e., an end of the front end face 1101 close to the first side of the suction channel 13 is flush with an end thereof close to the second side of the suction channel 13 in the axial direction), and this is not a limitation of the present application.

Further, the suction port 131 formed in the distal end surface 1101 extends obliquely forward in the axial direction set by the tube lens body 10 from a first side of the suction passage 13 to a second side opposite to the first side, wherein the first side of the outer peripheral surface 1102 corresponds to the first side of the suction passage 13, and the second side of the outer peripheral surface 1102 corresponds to the second side of the suction passage 13.

It is worth mentioning that when the front end surface 1101 is designed to extend obliquely forward in the axial direction set by the tube mirror body 10 from the first side to the second side of the outer peripheral surface 1102, a relatively larger distribution space can be provided for the suction ports 131 than when the front end surface 1101 of the tube structure body 11 extends flush in the axial direction set by the tube mirror body 10 from the first side of the outer peripheral surface 1102 to the second side opposite to the first side, and accordingly, the size of the suction ports 131 is relatively increased, so that more crushed stones can be allowed to pass through the suction passage 13, blocking of the suction ports 131 by the crushed stones is avoided, and the stone derivation efficiency is improved.

In some embodiments of the present application, the infusion port 121 and the suction port 131 are located on two different faces, respectively. The pouring port 121 is formed on a first surface of the front end portion 110, and the suction port 131 is formed on a second surface having a predetermined angle with the first surface.

As shown in fig. 3A to 3D, in this specific example, the pouring port 121 is provided in the outer peripheral surface 1102 of the pipe structure body 11, the pouring port 121 formed in the outer peripheral surface 1102 of the pipe structure body 11 mainly occupies the axial dimension of the pipe structure body 11, and the suction port 131 formed in the front end surface 1101 of the pipe structure body 11 mainly occupies the radial dimension of the pipe structure body 11. In this way, without coordinating the space ratio occupied by the pouring ports 121 and the suction ports 131 in the radial direction of the tube structure body 11 under the condition that the radial dimension of the tube structure body 11 is limited, the sizes of the suction ports 131 and the pouring ports 121 can be relatively increased, and the design flexibility of the shape, number, and ratio design of the suction ports 131 and the pouring ports 121 is relatively improved. Through the reasonable arrangement of the perfusion opening 121 and the suction opening 131, the sizes of the suction opening 131 and the perfusion opening 121 can be relatively increased, so that crushed stones can more easily pass through to prevent the crushed stones from blocking the vibration anti-blocking ureteroscope 100, and the liquid outlet amount of the perfusion opening 121 of the perfusion channel 12 is ensured.

When the liquid output of the pouring opening 121 is large, on one hand, the range of the fluid emitted from the pouring opening 121 is relatively prolonged, the impact force on the crushed stones is relatively increased, and the leading-out efficiency of the crushed stones is relatively improved. On the other hand, a larger liquid outlet amount can be realized under relatively lower irrigation, and the risk of pressure rise in the renal pelvis is reduced.

As shown in fig. 2, in this specific example, the vibration rod 41 is provided suspended in the suction passage 13, that is, the vibration rod 41 is not in contact with the inner peripheral wall of the suction passage 13. Moreover, preferably, the protrusions 412 are distributed on each side of the outer peripheral side of the rod body 411, so as to fully exert the guiding and dredging functions of the vibrating rod 41, so that the vibrating rod 41 drives the crushed stones on each side around the vibrating rod 41 to move in the non-radial direction, thereby achieving the dredging function.

Further, the vibration bar 41 is located at a middle region of the suction passage 13. Here, the central region of the suction passage 13 refers to a region of the suction passage 13 formed around the central axis thereof. Preferably, the vibration rod 41 is disposed coaxially with the suction channel 13, i.e., a central axis of the vibration rod 41 and a central axis of the suction channel 13 coincide. In this way, the crushed stones are relatively uniformly distributed around the vibrating rod 41, so that the crushed stones can be guided out relatively quickly by making full use of the vibration dredging effect of the protrusion 412, thereby improving the stone guiding efficiency.

It will be appreciated by those skilled in the art that the closer the distance from the protrusion 412, the greater the force of the protrusion 412 on the crushed stone, and the further the distance from the protrusion 412, the less the force of the protrusion 412 on the crushed stone. When the gap between the protrusion 412 and the inner peripheral wall of the suction passage 13 is larger than the maximum acting distance of the protrusion 412, the crushed stones are difficult to be carried. When the gap between the protrusion 412 and the inner circumferential wall of the suction passage 13 is smaller than the maximum acting distance of the protrusion 412, the space between the protrusion 412 and the inner circumferential wall of the suction passage 13 may not be fully utilized. When the gap between the protrusion 412 and the inner peripheral wall of the suction channel 13 is too small, it is difficult for crushed stones to smoothly pass through the suction channel 13.

Accordingly, the gap between the protrusion 412 and the inner peripheral wall of the suction channel 13 will affect the guiding and dredging function of the vibration rod 41 for the crushed stones in the suction channel 13. The gap between the protrusion 412 and the inner circumferential wall of the suction passage 13 may be designed according to the actual circumstances.

As shown in fig. 2 and 5, in the embodiment of the present application, the vibration device 40 further includes a power source 42 coupled to the vibration rod 41, and the power source 42 is configured to drive the vibration rod 41 to vibrate. In the embodiment of the present application, the power source 42 is implemented as an ultrasonic transducer, and the power source 42 may also be implemented as other devices capable of providing kinetic energy to the vibration rod 41, which is not limited in the present application.

The power source 42 is fluidly isolated from the fluid so as not to interfere with the proper operation of the power source 42. In a specific example of the present application, the vibration blockage prevention ureteroscope 100 further includes a sealing member 17 disposed between the scope body 10 and the power source 42 to prevent fluid in the channel of the scope body 10 from flowing into the power source 42 and affecting the function of the vibration device 40.

In the embodiment of the present application, the vibration device 40 is installed between the tube lens body 10 and the operation portion 20. Specifically, the vibration device 40 may be fixedly attached between the tube lens body 10 and the operation portion 20, or may be detachably attached between the tube lens body 10 and the operation portion 20.

Accordingly, as shown in fig. 6, the vibration device 40 further includes a mounting carrier 43, the power source 42 is mounted on the mounting carrier 43, and the mounting carrier 43 is mounted on the operation portion 20 to mount the vibration device 40 between the tube mirror body 10 and the operation portion 20. The mount carrier 43 may be fixedly attached to the operation portion 20 such that the vibration device 40 is fixedly attached between the tube mirror main body 10 and the operation portion 20, and the mount carrier 43 may be detachably attached to the operation portion 20 such that the vibration device 40 is detachably attached between the tube mirror main body 10 and the operation portion 20. In a specific example of the present application, the vibration device 40 is detachably mounted between the tube lens main body 10 and the operation portion 20 through the mounting carrier 43, and the mounting carrier 43 includes at least one connection structure 431.

It is worth mentioning that the fluid may be disturbed by the attraction force in the attraction channel 13 during the impact of the crushed stone, and the attraction disturbance to the fluid can be reduced by adjusting the relative position relationship between the perfusion opening 121 and the attraction opening 131 and controlling the flow direction of the fluid.

In the present embodiment, the pouring port 121 and the suction port 131 are oriented differently. The perfusion port 121 of the perfusion channel 12 has a first orientation for allowing fluid to be injected into the renal pelvis along the perfusion channel 12 from the perfusion port 121 in a first direction directed in the first orientation, and the suction port 131 of the suction channel 13 has a second orientation at a preset angle to the first orientation for allowing the fluid to be sucked from the suction port 131 into the suction channel 13 in a second direction directed in the second orientation after being diverted within the renal pelvis to form a fluid loop.

The second orientation is different from the first orientation, the first direction is the same as the first orientation, and the second orientation is opposite to the second orientation, so that an included angle between the first direction and the second direction is not 0 ° or 180 °, that is, the first direction and the second direction are different from each other and are not opposite to each other. In this way, the fluid emitted from the pouring port 121 along the first direction is deflected and then flows back along the second direction having an included angle with the first direction, so as to form a vortex-type fluid loop, and the fluid can be prevented from flowing back to the suction port 131 facing the same direction as the pouring port 121 along the opposite direction of the first direction after being emitted from the pouring port 121 along the first direction, so that the interference of the suction force on the fluid can be reduced.

In the embodiment of the present application, an included angle between the first direction and the second direction is greater than or equal to 90 ° and less than 180 °. In a specific example, the second direction is parallel to or infinitely close to the axial direction set by the tube lens body 10, the angle between the first direction and the axial direction set by the tube lens body 10 is greater than 0 ° and less than or equal to 90 °, and correspondingly, the angle between the first direction and the second direction is greater than or equal to 90 ° and less than or equal to 180 °. In another specific example, the first direction is parallel to or infinitely close to an axial direction set by the tube lens body 10, the second direction has an angle greater than 0 ° and equal to or less than 90 ° with respect to the axial direction, and accordingly, the first direction has an angle greater than or equal to 90 ° and less than 180 ° with respect to the second direction.

In the embodiment of the present application, the perfusion opening 121 and the suction opening 131 are not flush with each other in the axial direction set by the scope body 10, so that the distance between the perfusion opening 121 and the suction opening 131 and the movement path of the fluid can be extended, which not only can reduce the interference of the negative pressure in the suction channel 13 with the suction of the fluid, but also can improve the calculus removing efficiency because the area range through which the fluid flows is wider and the fluid can carry relatively more gravels on the movement path of the fluid.

Here, the fact that the perfusion opening 121 and the suction opening 131 are not flush with each other in the axial direction set by the tube lens body 10 means that there is a difference in height between the perfusion opening 121 and the suction opening 131, and the distances between the perfusion opening 121 and the suction opening 131 and the front end point located at the foremost position of the tube lens body 10 are different. In a specific example, the distance between the infusion port 121 and the front end point of the tube lens body 10 is greater than the distance between the suction port 131 and the front end point of the tube lens body 10, that is, the suction port 131 is located axially forward of the infusion port 121, and the suction port 131 is closer to the front end point of the tube lens body 10 than the infusion port 121. In another specific example, the distance between the perfusion port 121 and the front end point of the tube mirror body 10 is smaller than the distance between the suction port 131 and the front end point of the tube mirror body 10, that is, the perfusion port 121 is located axially in front of the suction port 131, and the perfusion port 121 is closer to the front end point of the tube mirror body 10 than the suction port 131.

In a modified embodiment of the present application, the perfusion port 121 and the suction port 131 may be flush with each other in the axial direction set by the tube lens body 10, which is not intended to limit the present application.

In this specific example, the perfusion port 121 is formed in the outer peripheral surface 1102 so as to be open in the lateral direction, the suction port 131 is formed in the front end surface so as to be open in the front direction, and the fluid is injected into the renal pelvis in the first direction from the perfusion port 121 formed in the outer peripheral surface 1102 of the tube structure body 11, and is sucked into the suction passage 13 from the suction port 131 in the second direction around the front side surface after being deflected, thereby forming a vortex-type fluid loop.

It is worth mentioning that in the process of the fluid exiting from the pouring opening 121 to impact the calculus, the higher the pouring pressure, the larger the pouring amount, the larger the impact force on the calculus, the more the crushed calculus can be impacted and trapped, the larger the impact force on the crushed calculus, the easier the crushed calculus can reach the suction channel 13, and the discharge of the calculus is facilitated. However, an increase in perfusion pressure will increase the risk of an increase in the internal pressure of the renal pelvis, and increasing the amount of perfusion by increasing the perfusion pressure conflicts with maintaining the internal pressure of the renal pelvis. The vibration anti-blocking ureteroscope 100 increases the perfusion volume by the rational arrangement of the perfusion channel 12 and the perfusion port 121, and maintains the intra-renal pelvis pressure by optimizing the perfusion volume and the discharge volume to reduce the risk of the intra-renal pelvis pressure rise.

Specifically, in a specific example of the present application, the inner diameter of the suction passage 13 is equal to or larger than one-half of the inner diameter of the tube structure main body 11. In one embodiment, the outer diameter of the tubular structure body 11 is 4.3 mm, the inner diameter of the suction channel 13 is 2.2 mm, and the equivalent diameter of the perfusion channel 12 is 1.2 mm or more. Here, the equivalent diameter of the perfusion channel 12 refers to an equivalent circular diameter of a cross section of the perfusion channel 12, and when the cross section of the perfusion channel 12 is a non-circular shape, a diameter of a circle having the same area as the cross section of the perfusion channel 12 is the equivalent diameter of the perfusion channel 12.

In a specific example of the present application, the perfusion channel 12 is arranged to: the perfusion channel 12 surrounds the suction channel 13. In one embodiment of the present application, the perfusion channel 12 is an annular channel and is circumferentially formed at the outer circumference of the suction channel 13.

In this particular example, the perfusion channel 12 is formed by a gap between at least two tubes of the vibrating anti-blocking ureteroscope 100. It is worth mentioning that the filling volume of the annular channel is relatively increased when the filling pressure is the same, compared to a circular channel formed by through holes in a single tube body, under the condition that the radial dimension occupied is the same, i.e. under the condition that the diameter of the circular channel is equal to the difference between the outer diameter and the inner diameter of the annular channel. Thus, relatively increased perfusion occurs at lower perfusion pressures. The fluid has fluidity and can smoothly pass through the gap between the tube bodies, thereby making full use of the internal space of the tube lens body 10.

Specifically, in one embodiment of the present application, the tubular structure body 11 includes an outer tube 70 and an inner tube 60 disposed inside the outer tube 70, the inner tube 60 and the outer tube 70 have a gap therebetween to form the perfusion channel 12, the inner tube 60 forms the suction channel 13, the inner diameter of the inner tube 60 is equal to the inner diameter of the suction channel 13, the inner diameter of the outer tube 70 is equal to the inner diameter of the tubular structure body 11, and the outer diameter of the outer tube 70 is equal to the outer diameter of the tubular structure body 11.

In other embodiments of the present application, the perfusion channel 12 and the suction channel 13 may also be formed in other ways. For example, the perfusion channel 12 is formed by a plurality of tubes surrounding the suction channel 13; for another example, the perfusion channel 12 and the suction channel 13 may be formed by a plurality of through holes provided in the scope body 10 itself. Further, the plurality of through holes may be obtained by perforating the solid tube or by a molding process, which is not limited in this application.

In other specific examples of the present application, the perfusion channels 12 may also be formed in other arrangements in the tube structure body 11, for example, two or more perfusion channels 12 are disposed on the same side of the tube mirror body 10, which is not limited by the present application.

In some embodiments of the present application, the ratio of the total opening area of the at least one pouring port 121 to the total opening area of the suction port 131 is equal to 1:1 to achieve flow balance and, in turn, maintain balance of the internal pressure of the renal pelvis. Here, the total opening area of the at least one pouring opening 121 refers to: the sum of the areas of the cross sections of all the pouring ports 121, and the total opening area of the suction ports 131 is the sum of the areas of the cross sections of all the suction ports 131. The balance of the internal pressure of the renal pelvis refers to: the internal pressure of the renal pelvis is maintained within a preset internal pressure range.

In a specific example of the present application, the number of the suction ports 131 is 1, and the number of the pouring ports 121 is 2. Correspondingly, the at least one pouring opening 121 comprises a first pouring opening 121 and a second pouring opening 121, and the sum of the area of the cross section of the first pouring opening 121 and the area of the cross section of the second pouring opening 121 is equal to the area of the cross section of the suction opening 131.

Preferably, the first and second perfusion ports 121 and 121 are symmetrically arranged with respect to the suction port 131, the first and second perfusion ports 121 and 121 having the same size and shape configuration. It should be understood that the size, proportion, shape and number of the suction ports 131 and the perfusion ports 121 are not limited in this application, and the size, proportion, shape and number of the suction ports 131 and the perfusion ports 121 can be adjusted according to the practical application to realize controllable and ordered fluid loops.

It should be noted that the positions of the suction port 131 and the pouring port 121 are not limited to the present application, and in other specific examples, the suction port 131 and the pouring port 121 may be disposed at other positions. In another specific example of the present application, the suction port 131 and the infusion port 121 are provided on the outer peripheral surface 1102 and the front end surface, respectively.

In yet another specific example of the present application, the suction port 131 and the infusion port 121 are both provided to the front face 1101 of the tube structure body 11. Specifically, in this particular example, the at least one perfusion channel 12 includes a first perfusion channel having a first perfusion port at the front end portion 110 and a second perfusion channel having a second perfusion port at the front end portion 110, the first and second perfusion ports being on opposite sides of the suction port 131.

In the embodiment of the present application, the vibration blockage prevention type ureteroscope 100 further includes an image collecting device 300 and a light source 400 installed in the ureteroscope body 10 to capture images of the kidney and stones located in the kidney. The positions of the image capturing device 300 and the light source 400 are not limited in this application, and preferably, the suction port 131 of the suction channel 13 is located in the visible region of the image capturing device 300 to capture the situation near the suction port 131, so that the user can observe the guiding-out situation of the crushed stone. The light source 400 may be disposed near the image pickup device 300 to provide a sufficient amount of light to the image pickup device 300.

Accordingly, the operation portion 20 further includes a fourth operation terminal 25 (not shown) communicably connected to the image pickup device 300. Also, the image output device (e.g., a computer communicably connected to the image capturing device 300) may be communicably connected to the image capturing device 300 through the operating portion 20 to acquire images of the kidney and the stone located within the kidney, so as to facilitate medical staff to observe the condition of the stone within the renal pelvis.

It is worth mentioning that at least a part of the scope body 10 may be bent to bring the front end portion 110 to a target position and to enable the suction port 131 and the perfusion port 121 at the front end portion 110 to face stones at the target position. Accordingly, in this specific example, the tube lens main body 10 includes a bendable portion 1010 adjacent to the distal end portion 110 and a support portion 1020 coupled to the bendable portion 1010, so that the tube lens main body 10 can be bent while ensuring the stiffness of the tube lens main body 10. The connection relationship between the supporting portion 1020 and the bendable portion 1010 is not limited in the present application, for example, the supporting portion 1020 extends rearward from the bendable portion 1010; for another example, the support portion 1020 covers at least a portion of the bendable portion 1010; for another example, the bendable portion 1010 wraps around at least a portion of the support portion 1020.

In order to control the bending degree of the bendable portion 1010, the operating portion 20 further comprises a fifth operating end 26 operatively connected to the bendable portion 1010 and an operating mechanism 28 mounted on the fifth operating end 26, wherein the operating mechanism 28 is operatively connected to the bendable portion 1010 through the fifth operating end 26 to control the bending degree of the bendable portion 1010, so that the endoscope main body 10 can reach different target positions, and the bending degree of the bendable portion 1010 can be adjusted according to actual conditions. In one embodiment, the operating mechanism 28 includes a control wire connected to the bendable portion 1010 and a manipulator connected to the control wire, the manipulator being configured to drive the control wire to pull the bendable portion 1010 to bend the bendable portion 1010. The structure of the operating mechanism 28 and the manner of controlling the bending of the bendable portion 1010 are not limited in this application, i.e., the operating mechanism 28 may be designed in other structures and control the bending of the bendable portion 1010 in other manners.

In a specific example, the bendable portion 1010 includes an active bendable portion 1011 and a passive bendable portion 1012, the active bendable portion 1011 is bendable by the manipulation of the operation portion 20 and maintains a bent state, and the passive bendable portion 1012 is bent according to the bending of the active bendable portion 1011.

Accordingly, when at least a portion of the vibration rod corresponds to the bendable part 1010, at least a portion of the vibration rod corresponding to the bendable part 1010 may also be bent to accommodate the bending of the bendable part 1010.

In summary, the vibration anti-blocking ureteroscope 100 according to the embodiment of the present application is illustrated, wherein the vibration anti-blocking ureteroscope 100 is capable of changing the distribution of the crushed stones in the radial direction set by the vibration anti-blocking ureteroscope 100 to destroy the stacking of the crushed stones in the radial direction, thereby preventing the crushed stones from being blocked in the suction channel.

Exemplary vibration device

As shown in fig. 1 to 7C, a vibrating device 40 for a ureteroscope according to the present application is illustrated. The vibration device 40 can be used to guide the crushed stones in the vibration anti-blocking ureteroscope 100 to move back and forth in a direction forming a preset included angle with the radial direction set by the ureteroscope main body 10, so as to destroy the stacking of the crushed stones in the radial direction, and further avoid the crushed stones from being blocked. Specifically, the vibration device 40 includes a vibration rod 41 and a power source 42 coupled to the vibration rod 41, and the vibration rod 41 includes: a rod body 411 and a protrusion 412 protrudingly disposed at an outer circumferential side of the rod body 411, the power source 42 being configured to drive the vibration rod 41 to vibrate in a predetermined direction. The vibration device 40 further comprises a mounting carrier 43, the power source 42 is mounted on the mounting carrier 43, and the mounting carrier 43 is suitable for being mounted on the operation part 20 of the vibration anti-blocking ureteroscope 100. In a specific example of the present application, the vibration frequency of the vibration rod 41 is 0 hz to 40 hz.

Those skilled in the art will appreciate that the specific function and operation of the vibrating device has been described in detail in the above description of the ureteroscope 100 with reference to fig. 1 to 7C, and thus, a repetitive description thereof will be omitted.

Exemplary method of deriving a calculus

As shown in fig. 8, a method of using a ureteroscope to deliver stones according to the present application is illustrated, comprising: s110, smashing the calculus through laser emitted by the calculus smashing mechanism; s120, guiding the crushed stone to enter a suction channel; s130, guiding the crushed stones in the suction channel to be linearly arranged in the non-radial direction of the tube lens body through a vibration device, and gradually removing the stones out of the body through the suction channel under the impact of water flow.

The operation of the vibration anti-blocking ureteroscope 100 will be described below by taking the example of the application of the vibration anti-blocking ureteroscope 100 to the removal of stones in the renal pelvis.

In step S110, the laser beam emitted from the stone-hitting mechanism 200 hits and breaks the stones. In particular, preparation is required before the stone is struck. First, the tube scope body 10 may be inserted to an initial predetermined position of the kidney. Specifically, the scope body 10 may be advanced along the patient's ureter into the kidney and to an initial predetermined location. In this process, an image of the surrounding environment at which the tube lens body 10 passes can be collected and displayed by the image collecting device 300 provided to the tube lens body 10 and the image output device communicably connected to the image collecting device 300, and the tube lens body 10 is guided to the initial predetermined position in cooperation with the guide mechanism. Specifically, the guiding mechanism may enter the perfusion channel 12 through the operation portion 20 and guide the scope body 10 to the initial predetermined position, and the guiding mechanism may be removed after the scope body 10 reaches the initial predetermined position, or of course, the guiding mechanism may enter another channel through the operation portion 20 and guide the scope body 10 to the initial predetermined position.

The lithotomy mechanism 200 may be placed at the initial predetermined position of the kidney before or after the insertion of the tube scope body 10 to the initial predetermined position of the kidney. The stone striking mechanism 200 is provided in the stone striking passage 14 and extends from the distal end portion 110 of the tube lens body 10.

Then, the bendable portion 1010 is controlled to bend by the operating mechanism 28 of the operating portion 20 so that the leading end portion 110 can be directed toward the calculus at the target position within the renal pelvis. After the stone at the target position is moved toward the tip 110, the laser beam emitted from the stone striking mechanism 200 strikes the stone.

In controlling the bendable portion 1010 to be bent by the operating mechanism 28 of the operating portion 20, the bendable portion 1010 can be controlled to be bent at a desired degree of bending according to a target position. When vibration anti-blocking ureteroscope 100 is used for beating the calculus that is located pelvis on the kidney, bendable portion 1010 is controlled to be crooked with first crookedness, works as vibration anti-blocking ureteroscope 100 is used for beating the calculus that is located pelvis in the kidney when, bendable portion 1010 is controlled to be crooked with the second crookedness, works as vibration anti-blocking ureteroscope 100 is used for beating the calculus that is located pelvis under the kidney when, bendable portion 1010 is controlled to be crooked with the third crookedness, the third crookedness is greater than the second crookedness with first crookedness.

In step S120, the crushed stones are guided into the suction channel 13. Specifically, during the process of hitting the calculus with the laser emitted from the calculus hitting mechanism 200, or after the calculus is hit by the calculus hitting mechanism 200, the fluid may be ejected from the infusion port 121 of the vibration anti-blocking ureteroscope 100 in a first direction to a target position to impact the hit calculus. Specifically, a fluid may be injected into the perfusion channel 12 through the injection device connected to the operating portion 20, and the fluid may be caused to exit and reach the inside of the renal pelvis to impact the crushed stones.

During the impact of the crushed stones, the crushed stones and fluid may be attracted such that the fluid is diverted to back-entrain the crushed stones from the suction port 131 in a second direction to the suction channel 13 to form a fluid loop. Thus, the crushed stones are guided to the suction port 131 by the fluid loop and enter the suction passage 13 from the suction port 131, as shown in fig. 7A. Specifically, the crushed stones and the fluid may be sucked by the suction device connected to the operating portion 20, so that the fluid and the crushed stones are discharged through the suction passage 13 to maintain the intra-renal pelvis pressure. In the process of attracting the crushed stones into the attraction channel 13 of the scope body 10, the attraction force of the fluid and the crushed stones can be adjusted by adjusting the air pressure in the attraction channel 13.

In the claimed embodiment, the perfusion port 121 is oriented in a first orientation, the suction port 131 is oriented in a second orientation, and fluid can be injected from the perfusion port 121 into a target location in the renal pelvis in a first direction directed in the first orientation along the perfusion channel 12 and sucked from the suction port 131 into the suction channel 13 of the vibration anti-blocking ureteroscope 100 in a second direction directed in the second orientation after being deflected to form a fluid loop.

The radial dimension of the vibration anti-blocking ureteroscope 100 is limited, and the radial space of the suction channel 13 is also limited due to the constraint of the radial dimension of the vibration anti-blocking ureteroscope 100. When a large number of crushed stones enter the suction channel 13 at the same time in the course of guiding the crushed stones to the suction port 131, the large number of crushed stones move in the same direction, and the crushed stones located in the suction channel 13 are stacked in the radial direction set by the scope body 10, easily block the suction channel 13, and are difficult to move backward. Thus, not only the crushed stones blocked in the blocked section of the suction channel 13 are difficult to be discharged, but also the crushed stones located in front of the blocked section of the suction channel 13 are blocked in the suction channel 13 or outside the suction channel 13 due to the blocking of at least one section of the suction channel 13, and more crushed stones are deposited in the suction channel 13 to form a stone street, which is difficult to be discharged, resulting in low stone discharge efficiency and long operation time.

The vibration device 40 may be configured to drive the crushed stones in the suction channel 13 to reciprocate in the non-radial direction of the tube lens body 10, and to destroy the stack of the crushed stones in the radial direction set by the tube lens body 10, so as to change the gap between the crushed stones in the non-radial direction, so as to guide the stones in the suction channel 13 to be linearly arranged in the non-radial direction, and prevent the crushed stones from being blocked in the channel and being led out through the suction channel 13.

Accordingly, in step S130, the crushed stones in the suction channel are guided by the vibration device 40 to be linearly aligned in the non-radial direction of the tube lens body. Specifically, the vibration device 40 includes a vibration rod 41 disposed in the suction channel 13, and the vibration rod 41 is driven to vibrate in a direction forming a preset included angle with the radial direction set by the tube lens main body 10 in an operating state. The vibration rod 41 includes a rod body 411 and at least one protrusion 412 protrudingly disposed on an outer circumferential side of the rod body 411. As shown in fig. 7B and 7C, when the vibration rod 41 is driven to move in the operating state, the vibration rod 41 vibrates in the suction passage 13 in a direction at a preset angle with respect to the radial direction set by the tube lens body 10, that is, the vibration rod 41 vibrates in the suction passage 13 in a non-radial direction. When the crushed stones hit the protrusion 412, the crushed stones are hit off the protrusion 412, then fall back to the protrusion 412, then bounce off by the protrusion 412, then fall back to the protrusion 412 again, and so on. In this way, the stack of the crushed stones in the radial direction is broken and the gap of the crushed stones in the non-radial direction changes, being linearly aligned in the non-radial direction. The oscillating rod 41 prevents the crushed stones from being blocked in the suction channel 13 as much as possible, so that the crushed stones can be more quickly discharged through the suction channel 13, and the stone discharge efficiency is improved.

Accordingly, step S130 includes: a vibrating rod 41 that drives the vibrating device 40 to vibrate in a non-radial direction of the tube mirror main body 10; impacting the crushed stones with the protrusions 412 of the vibration device 40; and driving the crushed stones to reciprocate in the non-radial direction of the tube lens main body.

In summary, a method for removing a stone using a ureteroscope according to an embodiment of the present application is described, by which a crushed stone can be prevented from being clogged in the suction channel 13 of the ureteroscope 100 as much as possible, thereby improving stone removal efficiency.

It will be appreciated by persons skilled in the art that the embodiments of the invention described above and shown in the drawings are given by way of example only and are not limiting of the invention. The objects of the present invention have been fully and effectively accomplished. The functional and structural principles of the present invention have been shown and described in the examples, and any variations or modifications of the embodiments of the present invention may be made without departing from the principles.

Claims (14)

1. The utility model provides a vibration prevents stifled formula ureteroscope which characterized in that includes:

an operation section;

a tube lens body having a front end and a rear end, comprising: a tube structure body, at least one perfusion channel extending within the tube structure body from the rear end to the front end, a suction channel extending within the tube structure body from the front end to the rear end, the suction channel having a suction port at the front end, the operating portion being coupled to the rear end of the tube scope body; and

set up in the vibrating device of tube mirror main part, vibrating device including set up in attract the vibrating arm in the passageway, the vibrating arm is driven under operating condition with the tube mirror main part sets up radially become the direction vibration of predetermineeing the contained angle, in order to drive attract the interior garrulous calculus of being hit of passageway to be in be reciprocating motion in the non-radial direction of tube mirror main part, through such mode guide is in attract the interior calculus of passageway to be in linear arrangement on the non-radial direction passes through under the impact of rivers attract the passageway to remove gradually externally.

2. The vibrating anti-clogging ureteroscope according to claim 1, wherein the vibrating rod comprises a rod body and at least one protrusion protrudingly provided at a peripheral side of the rod body.

3. The vibrating anti-clogging ureteroscope according to claim 2, wherein the front end of the protrusion is adjacent to the suction port.

4. The vibrating block-resistant ureteroscope according to claim 3, wherein the vibrating rod extends forward to the suction port in the axial direction set by the scope body.

5. The vibrating block-resistant ureteroscope according to claim 4, wherein the tube structure body has a front end surface, and the suction port is formed in the front end surface.

6. The vibrating anti-clogging ureteroscope according to claim 5, wherein the tube structure body further has an outer peripheral surface, and the front end surface extends obliquely forward from a first side of the outer peripheral surface to a second side opposite to the first side along an axial direction set by the tube structure body.

7. The vibrating anti-blocking ureteroscope according to claim 3, wherein the vibrating rod is located within the suction channel.

8. The vibrating anti-blocking ureteroscope according to claim 3, wherein the vibrating rod has a vibration frequency of 20 to 40 Hz.

9. The vibrating anti-blocking ureteroscope according to claim 1, wherein the vibrating rod is driven to vibrate to drive the crushed stones in the suction channel to reciprocate in the axial direction set by the ureteroscope body.

10. The vibrating anti-blocking ureteroscope according to claim 2, wherein the vibrating device further comprises a power source coupled to the vibrating rod, the power source configured to drive the vibrating rod to vibrate in a preset direction.

11. The vibrating anti-blocking ureteroscope according to claim 1, wherein the scope body further comprises a stone striking channel for allowing passage of a stone striking mechanism, the stone striking channel extending from the front end to the rear end within the tubular structure body.

12. A method of using a ureteroscope to deliver a stone, comprising:

the laser emitted by the stone-hitting mechanism hits and breaks stones;

guiding the crushed stone into a suction channel; and

the broken stones in the suction channel are guided by the vibration device to be linearly arranged in the non-radial direction of the tube lens main body, and are gradually removed from the body through the suction channel under the impact of water flow.

13. The method of using a ureteroscope to deliver stones according to claim 12, wherein guiding the struggled stones in the suction channel by a vibrating device in a linear arrangement in a non-radial direction of the scope body comprises:

a vibrating rod that drives the vibrating device to vibrate in a non-radial direction of the tube mirror main body;

impacting the crushed stone by a projection of the vibration device; and

the crushed calculi are driven to do reciprocating motion in the non-radial direction of the tube lens main body.

14. A vibrating device for a ureteroscope, comprising:

a vibration rod including a rod body and a protrusion portion protrudingly provided at an outer circumferential side surface of the rod body; and

a power source coupled to the vibration rod and configured to drive the vibration rod to vibrate in a preset direction.

Images