Patent Description:
In current minimally invasive surgery and interventional procedures, an incision is made in the patient's body to allow for the insertion of instruments such as endoscopes or interventional catheters into the body, and the suturing of tissues and fixation of the suture end are completed in the patient's body.

As far as the fixation of the suture end is concerned, it is common to subject the end to multiple knotting and locking, i.e., knotting the suture end for multiple times for locking inside the patient's body with the relevant instruments, in order to avoid subsequent loosening. However, after the surgery, it is difficult to eliminate the loosening of the suture due to the movement of the tissues during the life activities and due to the material of the suture.

In order to solve these problems, some manufacturers have developed a locking device that locks the suture end by means of a locking pin. Specifically, the suture end is clamped through elastic deformation of the locking pin, and the deformed pin is attached to the surface of the human tissue to prevent the loosening of the suture.

When the suture is tightened by the existing locking device to ensure the effectiveness of the suturing, a structure arranged outside the human body that can be used to tighten the suture is required. In this way, the travel of the suture is relatively long, making it difficult to control the actual required suture tension after suturing because the suture is stretched over a relatively large distance.

<CIT> discloses a minimally invasive knot-tying device system which comprises a knot-tying device and a guide wire assembly. The knot-tying device comprises a handle, a trigger, a sleeving, a transmission rod, a cutting knife and a punching shear wedge. The trigger is connected with the handle through a spindle. The sleeving is fixedly arranged on the handle. The transmission rod is connected with the trigger, is arranged inside the sleeving and can move inside the sleeving in a reciprocating mode. The cutting knife is arranged at the front end of the transmission rod and is used for cutting suture lines. The punching shear wedge is arranged at the front end of the sleeving and can be opened and closed so as to be squeezed by the transmission rod to achieve closing so that squeezing action is generated. The guide wire assembly comprises a guide wire, a closing nail, a guide wire frame and a towing hook. The guide wire is used for guiding the suture line. The closing nail allows the guide wire and the suture line to penetrate through, can be arranged on the punching shear wedge and ligates the suture line by being squeezed by the punching shear wedge. The towing hook is used for towing the guide wire. The guide wire forms a guide wire circle, the closing nail is sleeved at the closing end of the guide wire circle, the closing end of the guide wire circle is connected with the towing hook, and the guide wire circle is arranged on the guide wire frame.

<CIT> discloses a locking device with locking feedback. The locking device comprises a locking assembly, a handle and a locking feedback piece, wherein the locking assembly is used for locking a target object; the locking assembly is connected with the handle, the handle comprises a movable part and a fixed part, and the movable part moves relative to the fixed part so as to drive the locking assembly to lock the target object; and the locking feedback piece is movably arranged in the fixed part and cooperates with the movable part of the handle to feed back whether the target object is locked or not. <CIT> further discloses a heart valve repair system. When the locking device with locking feedback is used for locking the target object, whether the target object is locked by the locking assembly or not can be judged through the locking feedback piece, the locking degree of the target object can be guaranteed, and therefore the locking effect is guaranteed, and the operation success rate is increased.

The present invention provides a minimally invasive surgical suture end locking device, which can effectively solve the problems discussed in the background section. Also, the present invention provides a minimally invasive surgical suture end locking operating gun with the same technical effects.

To this end, the present invention adopts technical solutions as described in the appended claims.

With the technical solutions of the present invention, the following technical effects can be achieved.

There is provided in the present invention a device that allows to tighten and lock the suture directly at the end proximal to the position where the suture is led out from the human tissue, which makes it easier to control the degree of tightness of the suture on the tissue as opposed to tightening the suture by pulling the suture out of the body through the entire locking device, alleviating the difficulty of control caused by the long travel of the suture and its elasticity.

In order to more clearly illustrate the embodiments of the present invention or the technical solutions in the prior art, the accompanying drawings to be used in the description of the embodiments or prior art will be briefly described below. It is obvious that the accompanying drawings in the following description are only some of the embodiments recorded in the present invention, and other accompanying drawings can be obtained according to these accompanying drawings without creative work for those of ordinary skill in the art.

Reference signs: <NUM>. Hooking assembly; <NUM>. Annular structure; <NUM>. force application end; <NUM>. Support buckle; <NUM>. Clamping structure; <NUM>. Protruding portion; <NUM>. Convex structure; <NUM>. Guide surface; <NUM>. First clamping structure; 204a. Hole; <NUM>. Second clamping structure; <NUM>. Power rod; <NUM>. Pressing portion; <NUM>. Slope surface; <NUM>. Cutting portion; <NUM>. Connecting structure; <NUM>. First stop; <NUM>. Second stop; <NUM>. Connecting rod; <NUM>. Locking pin; <NUM>. Through area; <NUM>. Stop structure; <NUM>. Suture; <NUM>. End; <NUM>. End leading out from tissue; <NUM>. External conduit; <NUM>. Through hole; <NUM>. Guide seat; <NUM>. Guide groove; <NUM>. Plug; <NUM>. Operating assembly; <NUM>. Half shell; <NUM>. force application handle; <NUM>. Recess; <NUM>. Rod body; <NUM>. Stepped seat; <NUM>. Rotating structure; <NUM>. First end; <NUM>. Second end.

The technical solutions in the embodiments of the present invention will be described clearly and completely in conjunction with the accompanying drawings in the embodiments of the present invention. Obviously, the described embodiments are only a part of the embodiments of the present invention, rather than all the embodiments.

Unless otherwise defined, all technical and scientific terms used herein have the same meaning as commonly understood by those skilled in the art of the present invention. The terms used herein are for the purpose of describing specific embodiments only and are not intended to limit the invention. The term "and/or" as used herein includes any and all combinations of one or more of the related listed items.

<FIG> illustrate a minimally invasive surgical suture end locking device for clamping and securing the end of a suture <NUM> by means of a locking pin <NUM>, comprising: a hooking assembly <NUM>, a clamping structure <NUM>, a power rod <NUM>, a locking pin <NUM>, and an external conduit <NUM>, wherein the hooking assembly <NUM> comprises a closed flexible annular structure <NUM> and a force application end <NUM> leading out relative to the annular structure <NUM>, wherein the annular structure <NUM> is configured to lead out from a through area <NUM> of the locking pin <NUM> with a lead-out portion forming a closed area, and wherein the force application end <NUM> is configured to drive the suture <NUM> entering the closed area partially through the through area <NUM> by pulling the annular structure <NUM> under the action of an external force in the human body; wherein the clamping structure <NUM> is configured to press the locking pin <NUM> so that the locking pin <NUM> deforms and clamps the suture <NUM>, and wherein the power rod <NUM> is provided with a pressing portion <NUM> to press the clamping structure <NUM> by linear motion so that the clamping structure <NUM> moves and completes the pressing action; and wherein the clamping structure <NUM> and the power rod <NUM> are disposed in the external conduit <NUM>, wherein the locking pin <NUM> is configured to be inserted from an end of the external conduit <NUM> and the depth of insertion is limited by a stop structure <NUM> provided on an end of the locking pin, and wherein the external conduit <NUM> is provided with a through hole <NUM> through which a portion of the suture <NUM> passing through the through area <NUM> is led out by the pulling of the annular structure <NUM>, the through hole <NUM> being provided on the side corresponding to a contact position where the clamping structure <NUM> and the power rod <NUM> contact each other at a set distance from the contact position.

There is provided in the present invention a device that allows to tighten and lock the suture <NUM> directly at the end proximal to the position where the suture is led out from the human tissue, which makes it easier to control the degree of tightness of the suture <NUM> on the tissue as opposed to tightening the suture by pulling the suture out of the body through the entire locking device, alleviating the difficulty of control caused by the long travel of the suture <NUM> and its elasticity.

The connection of the annular structure <NUM> and the force application end <NUM> is preferably done in advance, so as to participate in the subsequent operation as a whole consumable. The connection of the locking pin <NUM> with respect to the external conduit <NUM> is preferably done after the connection with the hooking assembly <NUM> is completed. The connection of the hooking assembly <NUM> with the locking pin <NUM>, as shown in <FIG> and <FIG>, can be easily done by inserting the annular structure <NUM> into the through area <NUM> of the locking pin <NUM>. The force application end <NUM> can be inserted into the external conduit <NUM> and lead out through the through hole <NUM> before the locking pin <NUM> is inserted into the external conduit <NUM>, and then the locking pin <NUM> is inserted into the external conduit <NUM>, followed by fine adjustment of the position of the annular structure <NUM> and the force application end <NUM> relative to the locking pin <NUM>. The above connection process of the respective structures is a specific embodiment convenient for assembly and field use, and other connection processes that can obtain the final use state are also within the scope of protection of the present invention.

The product connected as above may be considered as ready for delivery. The product may be placed in a clean and airtight package and can be used directly after unpacking. To prevent the hooking assembly <NUM> from falling off during transportation and during the process of entering the human body, as shown in <FIG>, a support buckle <NUM> may be provided to support the annular structure <NUM> leading out from the locking pin <NUM>. Of course, the support here preferably makes the annular structure <NUM> obtain a certain elastic expansion so as to ensure a tight fit with the support buckle <NUM>, or other structures such as a slot may be provided on the support buckle <NUM> to receive the annular structure <NUM>. The support buckle <NUM> can be removed before use.

In order to reduce the difficulty of connection and installation of the above structures, as shown in <FIG>, the through hole <NUM> is a straight hole extending along the direction of linear movement of the power rod <NUM>, thus making easier the process of determining the position of the hooking assembly <NUM> relative to the outer conduit <NUM>. Especially for the process of the force application end <NUM> passing through the through hole <NUM>, a larger space is obtained.

As a preferred structural form of the force application end <NUM> to facilitate in vivo operation, based on the above objectives and as a preferred embodiment, as shown in <FIG> and <FIG>, the force application end <NUM> adopts a hook structure, which makes it easier to apply force to it with existing instruments and is easy to machine.

In order to reduce the operation steps and shorten the operation time, the structural form of the power rod <NUM> is optimized, specifically, an end of the power rod <NUM> is provided with a cutting portion <NUM>. The cutting portion <NUM> approaches one sidewall of the through hole <NUM> along with the pressing movement of the power rod <NUM> until it reaches a close enough distance with respect to the one sidewall of the through hole <NUM> and continues to approach, the cutting portion <NUM> thus cutting the suture <NUM> passing through the through hole <NUM> by cooperating with the edge of the sidewall.

The cutting portion <NUM> can be directly shaped during the processing of the power rod <NUM>, and the pressing portion <NUM> can be obtained in the same way, so that the power rod <NUM> as a whole can ensure better stability in the process of power supply and cutting, and is more robust and durable, making the installation of the product less difficult.

As shown in <FIG>, the cutting action of the cutting portion <NUM> is carried out in parallel with the power rod <NUM> pressing the clamping structure <NUM>, which can completely omit an independent step of cutting the suture <NUM>. Before pressing and cutting, it is necessary to ensure that the suture <NUM> is stretched properly. As the cutting portion <NUM> approaches one sidewall of the through hole <NUM>, the cutting portion <NUM> and the sidewall of the through hole <NUM> form a near double-edged structure. For the suture <NUM> passing between the two edges, when the pressing pressure between the edges reaches a certain value and the suture <NUM> acquires a certain tension, the purpose of cutting is more easily achieved.

In order to improve the cutting effects, the shape of the cutting portion <NUM> can be optimized to control the sharpness of the cutting edge provided by it. The power rod <NUM> is installed inside the external conduit <NUM> and will not cause any impact on the patient. There is more room for improvement compared to the improvement of the sidewall of the through hole <NUM>. Referring to <FIG>, the shape of the cutting portion, which is located at the end of the power rod <NUM>, can be controlled by the subsequent machining process.

In practical application, one side of the external conduit <NUM> extends into the human body and the other side is located outside the human body, so the length is relatively large and it is difficult to directly install the clamping structure <NUM> at its end. To solve this problem, as shown in <FIG> , the external conduit <NUM> further includes a guide seat <NUM> installed at the end thereof, the guide seat <NUM> is configured to limit the insertion depth of the locking pin <NUM> and guide the movement of the clamping structure <NUM>. When the guide seat <NUM> is separated from the external conduit <NUM>, the clamping structure <NUM> can be installed, and after the installation is completed, it can be directly installed as a whole. The guide function here can achieve the relative fixation of the clamping structure <NUM> in a narrow space, and accurately limit the direction of its movement.

During the operation, in addition to meeting the installation needs of the locking pin <NUM>, a possibly smaller external dimensions of the external conduit <NUM> is more preferable for the patient. For this purpose, it is more desirable that the clamping structure <NUM> imparts a greater degree of compression on the locking pin <NUM> through a smaller range of motion, and for this purpose, the movement of the clamping structure <NUM> is perpendicular to the direction of insertion of the locking pin <NUM> into the guide seat <NUM>.

Furthermore, as shown in <FIG>, the guide seat <NUM> is provided with a guide groove <NUM>, and the clamping structure <NUM> is provided with a protruding portion <NUM> that moves along the guide groove <NUM>. This is a most convenient implementation and the guidance is stable. In the present invention, the number of clamping structures <NUM> is selected comprehensively considering the installation space in the external conduit <NUM>, the shape of the power rod <NUM>, etc. <FIG> shows two clamping structures <NUM>. Correspondingly, it is sufficient to provide two pressing portions <NUM> at the end of the power rod <NUM>.

Alternatively, as another embodiment of the clamping structure <NUM>, the clamping structure <NUM> is configured in the form of a V-shaped clamp, as shown in <FIG>. Here, the V-shaped clamp specifically includes a first clamping structure <NUM> and a second clamping structure <NUM> arranged at a preset angle. When the first clamping structure <NUM> is fixedly arranged, the second clamping structure <NUM> can move close to the first clamping structure <NUM> through its own elastic deformation under the pressing of the power rod <NUM>, or through an elastic change in angle relative to the first clamping structure <NUM>, or through both of the above. When the pressing force is removed, the elastic reset can be realized.

When the clamping structure <NUM> of this structural form is adopted, the purpose of pressing and deforming the locking pin can be achieved simply by placing the locking pin <NUM> between the two clamping structures at the desired clamping position. In this structural form, extending the length of the first clamping structure <NUM> and the second clamping structure <NUM> as much as possible can make the above-mentioned elastic change easier. For this purpose, a recessed area for partial accommodation of the clamping structure <NUM> may be provided at the end of the power rod <NUM> to accommodate the extension of length.

As a more optimized form of the clamping structure <NUM> in this structural form, the clamping structure <NUM> may be integrally formed with a plug <NUM> used to block the end of the external conduit <NUM>, thereby further reducing the difficulty of installation. Specifically, the plug <NUM> may be connected to the first clamping structure <NUM>. To impart larger strength to the first clamping structure <NUM>, it may be provided with a stepped structure, so that the locking pin <NUM> can be further positioned through the stepped surface while the strength is improved. Other shape forms that meet the space requirements are also within the scope of protection of the present invention. Since the clamping structure <NUM> of this structural form occupies a large area in the external conduit <NUM>, it may significantly affect the leading out of the suture from the through hole <NUM>. In order to solve this problem, the first clamping structure <NUM> may be provided with a hole 204a corresponding to the through hole <NUM>, thus avoiding the occurrence of interference. In practice, even if the suture <NUM> is clamped and fixed by the locking pin <NUM>, there is still a risk that it may fall off during the subsequent continuous movement of the human tissue. To minimize such risk, the clamping structure <NUM> may be provided with at least one raised structure <NUM> facing the locking pin <NUM> and partially pressing the locking pin <NUM>. Compared with flatting the locking pin <NUM> as a whole, the pressing of the locking pin <NUM> by the raised structure <NUM> can form a more concentrated pressing position for the suture <NUM>, such as the position indicated by the arrow in <FIG>, that is, the position where the suture <NUM> obtains centralized pressing. <FIG> shows the position of the force on the locking pin <NUM> that ensures stable fixation of the suture <NUM> by a concentrated pressing. Of course, in addition to the centralized pressing position, other positions of the locking pin <NUM> can be deformed by means of flattening, so as to obtain a slightly smaller pressing force compared to the centralized pressing position. <FIG> shows the position of the force on the locking pin <NUM> when the clamping structure <NUM> is provided with more than one, specifically two raised structures <NUM>, which function in the same way as <FIG> and, of course, provide better fixation of the suture <NUM>, but will appropriately increase the machining difficulty of the clamping structure <NUM>. <FIG> shows the position of the force on the locking pin <NUM> when two clamping structures <NUM> are provided and each clamping structure <NUM> is provided with one raised structure <NUM> to press the locking pin <NUM>. <FIG> shows the position of the force on the locking pin <NUM> when two clamping structures <NUM> are provided and each clamping structure <NUM> is provided with more than one, specifically two raised structures <NUM>. In such configuration, it is preferred that the raised structures <NUM> on the two clamping structures <NUM> are staggered, as shown in the figure, so that the pressed locking pin <NUM> obtains a final shape that is approximately wavy, which provides better fixation of the suture <NUM>. The above solutions can be selected according to actual needs. In the implementation, in addition to the raised structure <NUM>, a corresponding recessed area can be provided. The area pressed and deformed due to the raised structure <NUM> can be deformed into the recessed area, as shown in <FIG>, which shows how the recessed area can be provided. Specifically, the recessed area may be a part of the clamping structure <NUM>, or a part of the external conduit <NUM>.

As a preferred embodiment, see <FIG>, the pressing portion <NUM> includes a slope <NUM> for pressing the clamping structure <NUM>, wherein the end of the slope <NUM> forms a sharp structure that can be inserted into a gap between the clamping structure <NUM> and the inner wall of the external conduit <NUM>, and wherein the slope <NUM> is inclined relative to the direction in which the guide seat <NUM> guides the clamping structure <NUM>. The slope <NUM> is provided to translate the linear motion of the power rod <NUM> into the linear motion of the clamping structure <NUM>, achieving the change of direction.

As shown in <FIG>, the clamping structure <NUM> may be provided with a guide surface <NUM> corresponding to the slope <NUM> in order to accommodate mutual pressing with the pressing portion <NUM>, or, as shown in <FIG>, the clamping structure <NUM> may be directly provided as a shaft body structure or a structure having a partially curved surface, so as to produce mutual pressing with the slope <NUM> through the curved surface.

As a locking method of the above-described minimally invasive surgical suture end locking device, specific reference can be made to the following steps so as to achieve optimal effects. As shown in <FIG>, there is provided a minimally invasive surgical suture end locking method using the minimally invasive surgical suture end locking device as described above, comprising the following steps of:.

The control of the end of the suture <NUM> may be implemented in the following two ways.

As shown in <FIG>, the first way of controlling the end of suture <NUM> includes pulling the end of suture <NUM> on the side of the locking pin <NUM> proximate to the sutured tissue such that during the pulling of the force application end <NUM>, the suture <NUM> deviating from the end overlaps and penetrates through the through area <NUM> of the locking pin <NUM>.

In this case, the end <NUM> of the suture <NUM> and the end <NUM> of the suture <NUM> leading out from the tissue are located on one side of the locking pin <NUM>, wherein the end <NUM> is controlled by an instrument and the end <NUM> leading out from the tissue is restricted by the tissue. In this process, the suture <NUM> is pulled by the force application end <NUM>, causing the suture <NUM> to form a portion in which the suture is overlapped and doubled and which is finally pressed and fixed in the through area <NUM> of the locking pin <NUM>. In this way, the number of sutures <NUM> inside the locking pin <NUM> is increased, making the pressing more stable, and the end <NUM> is fixed by the instrument throughout the process, effectively avoiding the problem of loosening of the suture <NUM>. However, in this way, the size of the through area <NUM> of the locking pin <NUM> may be relatively large.

As shown in <FIG>, the second way of controlling the end of suture <NUM> includes pulling the force application end <NUM> to drive the end <NUM> of suture <NUM> through the through area <NUM> of the locking pin <NUM> by the annular structure <NUM>, and pulling the end of suture <NUM> on the side of the locking pin <NUM> away from the sutured tissue.

Here, the end <NUM> refers to the most marginal part of the end having a certain length range of the suture <NUM>. The end <NUM> of the suture <NUM> passes completely through the through area <NUM>, and after this process is completed, the suture <NUM> can be pulled on the other side of the locking pin <NUM>. The size of the locking pin <NUM> can be reduced because the number of sutures <NUM> passing through the locking pin <NUM> in this process is small. During the process of the end <NUM> passing through the through area <NUM>, the suture <NUM> may be loosened to a certain extent, but it can be pulled again later by pulling the end.

The above two ways are within the protection scope of the present invention and can be selected according to actual needs.

The minimally invasive surgical suture end locking device according to the present invention can work when installed onto an operating gun, as detailed in the following embodiments.

As shown in <FIG>, there is provided a minimally invasive surgical suture end locking operating gun, comprising the minimally invasive surgical suture end locking device described above and an operating assembly disposed outside the human body for operation.

The operating assembly <NUM> comprises two half-shells <NUM> assembled in a docking manner to form a cavity, and a force application handle <NUM> partially disposed within the cavity and rotatably connected to the half-shells <NUM>, wherein one end of the force application handle <NUM> located within the cavity is slidably connected to the power rod <NUM>, wherein the outer cross-section of the external conduit <NUM> is a cylinder having an axis fixed relative to the half-shells <NUM>, and wherein the force application handle <NUM> presses the power rod <NUM> during rotation.

The two half-shells <NUM> are docked by the existing fixing method, and the docking here may be done in a detachable manner, so as to facilitate the observation of the internal structure, etc. For the rotational connection between the force application handle <NUM> and the half-shells <NUM>, it can be implemented by arranging a shaft body on the force application handle <NUM> and a hole for insertion of the shaft body on the half-shells <NUM>, so that the force application handle <NUM> can be naturally fixed during the docking and assembling process of the two half-shells <NUM>. The force application handle <NUM> may be an integral structure or an assembled structure, which can be selected according to the actual production needs.

During operation, the power rod <NUM> is pressed by controlling the counterclockwise rotation of the force application handle <NUM> as shown in <FIG> and <FIG>. When the force application handle <NUM> moves in the opposite direction, the pressure is naturally released, whereby the removal of the locking pin <NUM> from the external conduit <NUM> can be realized. In order to reduce the force on the locking pin <NUM> during the above removal process, as shown in <FIG> and <FIG>, the end of the power rod <NUM> is provided with a connecting structure <NUM> slidably connected with the force application handle <NUM>.

The connection structure <NUM> comprises a first stop <NUM> and a second stop <NUM> provided side by side along the length of the power rod, the first stop <NUM> and the second stop <NUM> being connected to each other by a connecting rod <NUM> that may be arranged to be parallel with the power rod <NUM>. The force application handle <NUM> is provided with a recess <NUM> at an end thereof to accommodate the connecting rod <NUM>, the end of the force application handle <NUM> being affixed to the first stop <NUM> and second stop <NUM>, respectively, wherein the first stop <NUM> is relatively close to the minimally invasive surgical suture end locking device.

In this way, reverse rotation is achieved by the force application handle <NUM> pressing the connecting structure <NUM>, so that the power rod <NUM> can be driven to reset when the power rod <NUM> is released from pressing the clamping structure <NUM>. Therefore, the clamping structure <NUM> in contact with the locking pin <NUM> is no longer subjected to the pressing force, which facilitates the removal of the locking pin <NUM> relative to the external conduit <NUM>.

As a preferred embodiment, as shown in <FIG>, the first stop <NUM> is in contact with the force application handle <NUM> through a spherical surface, and the force application handle <NUM> is correspondingly provided with a curved surface that is curved in the same direction to fit the spherical surface. The fitting between the spherical surface and the curved surface makes sliding smoother and reduce the friction surface damage caused by hard friction during the sliding process of the force application handle <NUM> relative to the first stop <NUM>. The spherical surface may be one of a spherical or ellipsoidal surface, but is preferably a regular surface, so as to facilitate the machining. The curved surface on the force application handle <NUM> may be arranged to follow the curved form of the spherical surface, and may be formed synchronously with the force application handle <NUM> or obtained by subsequent machining.

As a preferred embodiment, the force application handle <NUM> is in contact with the second stop <NUM> through the curved surface. However, there is no additional machining requirement for the second stop <NUM>, because the pressing force between the force application handle <NUM> and the second stop <NUM> is small during the return stroke of the force application handle <NUM>. Therefore, the purpose of smooth sliding between the two can be completely satisfied by the curved surface of the force application handle <NUM>, thereby reducing the machining difficulty of the second stop <NUM>. The stop <NUM> is formed as a circular piece, and a blocking structure is provided inside the cavity to limit the limit position of the return stroke. The combined structure composed of the first stop <NUM>, the second stop <NUM> and the connecting rod <NUM> can be integrally formed, and after being independently machined, connected to the main body of the power rod <NUM> to obtain the complete structure of the power rod <NUM>. This way is relatively simple and the shape is easier to control.

As a preferred embodiment, the minimally invasive surgical suture end locking operation gun further comprising a rotating structure <NUM> having a first end <NUM> jacketed on the external conduit <NUM> and located outside the cavity and fixedly connected to the external conduit <NUM>, and a second end <NUM> jacketed on the power rod <NUM> and located inside the cavity and driving the power rod <NUM> to rotate.

During the locking operation through the operating gun, due to the limited space inside the human body, in order to avoid the human tissue structure, the opening direction of the through hole <NUM> of the external conduit <NUM>, that is, the leading out direction of the force application end <NUM>, has many possibilities. In order to accommodate such possibilities and facilitate the control of the opening direction of the through hole <NUM>, as shown in <FIG>, a rotating structure <NUM> is provided. Through the control of the first end <NUM>, the operator rotates the external conduit <NUM>. Of course, during the rotation, the external conduit <NUM> only rotates around a fixed rotation axis, without moving in the axial direction and the radial direction. During the rotation, the second end <NUM> moves synchronously with the first end <NUM>, thereby driving the power rod <NUM> to rotate synchronously, but the rotation here does not affect the movement of the power rod <NUM> along the length direction. During the rotation, the rotation is made smoother through cooperation with the above optimized structure in which the first stop <NUM> contacts with the force application handle <NUM> through the spherical surface.

A snap slot is provided between the first end <NUM> and the second end <NUM> to accommodate a partial edge of the half-shells <NUM>, thereby acting as a limiter, making the installation of the entire rotating structure <NUM> easier. The second end <NUM> is affixed to the power rod <NUM> through a prismatic through hole to realize transmission of rotational power. A local part of the power rod <NUM> cooperating with the prismatic through hole is a corresponding prismatic structure that be integrally formed with the structure including the first stop <NUM>, the second stop <NUM> and the connecting rod <NUM> in the above preferred embodiment and both structures, as a whole, are fixedly connected with the end of the main body of the power rod <NUM> to facilitate machining.

As a preferred embodiment, the operating gun further comprises a sensing structure, as shown in <FIG>, wherein the sensing structure comprises a rod body <NUM> leading out from the force application handle <NUM>, and a stepped seat <NUM> disposed on the inner wall of the cavity and having a plurality of stepped structures, wherein the rod body <NUM> is arranged against the stepped seat, so that it sequentially reaches different stepped structures on the stepped seat <NUM> during rotation of the force application handle <NUM>, creating a jamming feeling which is transmitted to the operator through the force application handle <NUM>. With this structural form, the operator can perceive the operation process through the frequency and number of occurrences of the jamming feeling during the operation, thereby making the control more precise.

Claim 1:
A minimally invasive surgical suture end locking device for clamping and securing the end of a suture (<NUM>) by means of a locking pin (<NUM>), comprising: a hooking assembly (<NUM>), a clamping structure (<NUM>), a power rod (<NUM>), a locking pin (<NUM>), and an external conduit (<NUM>);
wherein the hooking assembly (<NUM>) comprises a closed flexible annular structure (<NUM>) and a force application end (<NUM>) leading out relative to the annular structure (<NUM>), wherein the annular structure (<NUM>) is configured to lead out from a through area (<NUM>) of the locking pin (<NUM>) with a lead-out portion forming a closed area, and wherein the force application end (<NUM>) is configured to drive the suture (<NUM>) entering the closed area partially through the through area (<NUM>) by pulling the annular structure (<NUM>) under the action of an external force in the human body;
wherein the clamping structure (<NUM>) is configured to press the locking pin (<NUM>) so that the locking pin (<NUM>) deforms and clamps the suture (<NUM>), and wherein the power rod (<NUM>) is provided with a pressing portion (<NUM>) to press the clamping structure (<NUM>) by linear motion so that the clamping structure (<NUM>) moves and completes the pressing action; and
wherein the clamping structure (<NUM>) and the power rod (<NUM>) are disposed in the external conduit (<NUM>), wherein the locking pin (<NUM>) is configured to be inserted from an end of the external conduit (<NUM>) and the depth of insertion is limited by a stop structure (<NUM>) provided on the locking pin (<NUM>), and wherein the external conduit (<NUM>) is provided with a through hole (<NUM>) through which a portion of the suture (<NUM>) passing through the through area (<NUM>) is led out by the pulling of the annular structure (<NUM>), the through hole (<NUM>) being provided on the side corresponding to a contact position where the clamping structure (<NUM>) and the power rod (<NUM>) contact each other at a set distance from the contact position,
wherein the external conduit (<NUM>) comprises a guide seat (<NUM>) mounted at an end thereof,
wherein the guide seat (<NUM>) is configured to limit the insertion depth of the locking pin (<NUM>) and guide the movement of the clamping structure (<NUM>), and
characterized in that the guide seat (<NUM>) is provided with a guide groove (<NUM>), and the clamping structure (<NUM>) is provided with a protruding portion (<NUM>) moving along the guide groove (<NUM>).