Use method of flat foot correction screw and tool

Abstract

The invention discloses a use method of a flat foot correction screw and a tool, and particularly relates to the technical field of medical instruments, an arranged implant and an arranged surgical instrument are utilized, the use method comprises the steps that a first operation piece is connected with an end part section, so that a deformable section is kept in an initial state, and the first operation piece is connected with the end part section; the second operation piece is operated to rotate, the main body section is driven to rotate, the whole implant is implanted into a bone tunnel to a preset depth, main body implantation is achieved, the first operation piece is independently operated to rotate, the end section is driven to move axially, the deformable section is expanded in the radial direction to form anchoring, and expansion anchoring is achieved. According to the invention, the implant can be integrally implanted into a bone tunnel to a preset depth, and then the expansion action is independently controlled, so that the controllability of an operation and the positioning accuracy of the implant are remarkably improved, the technical problems of uncontrollable implantation operation, easiness in false triggering and the like in the prior art are solved, and the step-by-step accurate operation of'first implantation and second expansion 'is realized.

Description

Technical Field

[0001] This invention relates to the field of medical device technology, and more specifically, to a method of using a flatfoot correction screw and tool. Background Technology

[0002] Flatfoot is a common foot deformity characterized by collapsed arches, calcaneal eversion, and talus internal rotation, leading to pain, fatigue, and gait abnormalities. For cases unresponsive to conservative treatment, subtalar joint immobilization is a widely used minimally invasive procedure. The principle involves implanting an immobilizer within the tarsal sinus or tarsal canal formed by the junction of the talus and calcaneus to restrict excessive movement of the subtalar joint, thereby restoring arch height. In the prior art, such as the surgical tool for treating flat feet disclosed in CN113729895A, an integrated conical interface screw is used. After being positioned by a guide pin, a single screwdriver is used to screw the screw into the predetermined position. The anti-retraction performance is improved by the punching groove on the surface of the screw. Another example is the expansion type subtalar joint brake disclosed in CN223380633U, which adopts a structure in which the inner nail body and the outer nail body are separately fitted. During the operation, the outer nail body needs to be implanted first, and then the inner nail body is pressed into or screwed into the outer nail body, so that the expansion plate of the outer nail body expands to achieve fixation.

[0003] However, existing technologies and corresponding surgical methods still have the following shortcomings: On the one hand, existing implantation methods are all "one-time implantation" or "sequential assembly implantation," which cannot precisely control the different functional segments of the implant step by step and independently during the same implantation process. It is difficult for the surgeon to adjust the anchoring degree and support position in real time according to the bone tunnel morphology, and the correction effect is easily affected by the initial fixation not being firm or the support point deviation. On the other hand, the expansion action of existing expansion implants is usually coupled with the implantation action, and there is a lack of safety structure design to prevent the expansion segment from being accidentally triggered during the implantation process. If the expansion segment expands prematurely before reaching the predetermined depth, it may cause the screw to get stuck at the bone tunnel entrance, damage the bone tunnel wall, or even fracture, which seriously affects the safety of the surgery. In addition, existing methods lack an operation feedback mechanism. The implantation depth and the number of rotations depend entirely on the surgeon's experience, and the expansion piece is mostly irreversibly deformable. When adjustment or removal is required, destructive operations are often required, which increases the trauma and difficulty of revision surgery.

[0004] To address the aforementioned technical problems, this invention provides a method for using screws and tools for flatfoot correction. By precisely controlling the implantation process in stages and timing, a "first implantation, then expansion, and repositionable" workflow is achieved. This method not only prevents accidental triggering of the expansion segment during implantation but also adjusts the anchoring force in real time according to the bone tunnel morphology and enables reversible repositioning of the expansion piece when needed. This significantly improves the controllability, safety, and clinical efficacy of the surgery, while reducing the trauma and difficulty of revision surgery. Summary of the Invention

[0005] In order to overcome the above-mentioned defects of the prior art, embodiments of the present invention provide a method for using a flatfoot correction screw and tool to solve the problems mentioned in the background art.

[0006] To achieve the above objectives, the present invention provides the following technical solution: a method for using a flatfoot correction screw and tool, comprising the following steps:

[0007] An implant and a surgical instrument are provided. The implant includes: a main body segment located at the proximal end for providing main body support, an end segment located at the distal end for connecting to the surgical instrument, and a deformable segment connecting the main body segment and the end segment, the deformable segment being used to expand radially to form an anchor when axially driven; the surgical instrument includes: a first operating element and a second operating element coaxially arranged and rotatable relatively independently. S1: Pre-assembly: Connect the first operating member to the end segment to keep the deformable segment in its initial state; S2: Main body implantation: Operate the second operating member to rotate, drive the main body segment to rotate, and implant the entire implant into the bone tunnel to a predetermined depth; S3: Expansion anchoring, the first operating component is rotated independently, driving the end section to move axially, so that the deformable section expands radially to form an anchor.

[0008] Furthermore, in S1, the first operating member is initially engaged with the end segment but no axial driving force is applied, so that the rotation of the first operating member cannot be converted into an axial driving force on the end segment.

[0009] Furthermore, in S2, the distal end of the second operating member is provided with a force transmission structure, and the proximal end of the main body section is provided with a force receiving structure; the force transmission structure and the force receiving structure cooperate to transmit rotational driving force, and the cross-sectional shapes of the force transmission structure and the force receiving structure are both non-circular to prevent relative rotation.

[0010] Furthermore, in S2, when the second operating member is rotated during implantation, the first operating member rotates synchronously with the second operating member. However, since the first operating member only initially engages with the end segment, no axial driving force is applied to the end segment to prevent the deformable segment from being accidentally triggered during implantation.

[0011] Furthermore, in S3, the rotational motion is converted into axial movement of the end section by the cooperation of the first operating member with the end section screw drive, so that the expansion part of the deformable section expands radially; the degree of expansion of the expansion part is adjusted by controlling the number of rotations of the first operating member.

[0012] Furthermore, in S2 and S3, intermittent resistance changes or sound feedback are generated by the feedback structure set on the outer wall of the main body section to assist in determining the number of rotations or axial position.

[0013] A flatfoot correction implant for use in the above-described method, the implant being divided into a main body segment and an expansion segment from proximal to distal; The proximal end of the main body section is provided with a force-bearing structure for transmitting rotational driving force in conjunction with surgical instruments; The expansion section includes an end section and a deformable section. The end section is provided with a first connecting part that cooperates with the first operating member and a through first guiding channel. The deformable section is a thin-walled structure that can expand radially.

[0014] A surgical instrument for use in the above-described manner includes a first operating member and a second operating member that are coaxially arranged and can rotate relatively independently. The distal end of the first operating member is connected to the end section, and the interior of the first operating member is provided with a through second guide channel; The second operating component is movably sleeved outside the first operating component, and its distal end is provided with a force transmission structure that cooperates with the force-bearing structure of the main body section. Furthermore, the first operating member includes a guide portion and a second connecting portion. The guide portion slides through the deformable section, and the second connecting portion is inserted into a pre-set receiving groove inside the end section.

[0015] The technical effects and advantages of this invention are as follows: 1. Compared with existing technologies, the method of this invention, by setting independent pre-assembly, main body implantation, and expansion anchoring steps, allows the surgeon to first implant the entire implant into the bone tunnel to a predetermined depth, and then independently control the expansion action. This significantly improves the controllability of the surgery and the positioning accuracy of the implant, avoiding deviations in the corrective effect caused by chaotic operation sequence. Secondly, it prevents accidental triggering of the expansion segment from an operational perspective. In the pre-assembly stage, the first operating element only initially engages with the end segment without applying axial driving force; in the main body implantation stage, the first operating element rotates synchronously with the second operating element but does not drive the end segment. From an operational perspective, this ensures that the deformable segment remains in a contracted state during implantation, avoiding implantation failure or tissue damage caused by premature expansion. Furthermore, it utilizes an adjustable anchoring and operational feedback mechanism. By controlling the number of rotations of the first operating element, the degree of expansion can be precisely adjusted to adapt to the anchoring requirements of different bone tunnel morphologies; simultaneously, the intermittent resistance changes or sound feedback generated by the feedback structure assist the surgeon in judging the number of rotations or axial position, reducing reliance on the surgeon's experience. Therefore, it solves the technical problems of uncontrollable implantation operation and easy accidental triggering in the existing technology, and realizes the step-by-step precise operation of "implanting first and then expanding".

[0016] 2. Compared with existing technologies, this implant utilizes a segmented structural design. The main body provides structural support, the end section connects to the device, and the deformable section provides radial expansion and anchoring. Each functional segment has a clear division of labor and works in concert. The non-circular fit between the force-bearing and force-transmitting structures ensures stable transmission of driving force, while the feedback structure provides real-time operational prompts. The implant device employs a coaxially arranged and relatively independently rotatable first and second operating element, corresponding to the control of the end section and main body section respectively, resulting in a compact structure and easy operation. The segmented design of the guide and connecting parts of the first operating element ensures both smooth transmission and precise fit with the end section. Through the collaborative design of the implant and the implant device, a reliable structural guarantee is provided for precise step-by-step operation, prevention of accidental triggering, adjustable anchoring, and reversible repositioning, significantly improving the safety, controllability, and clinical efficacy of flat foot correction surgery. Attached Figure Description

[0017] Figure 1 This is a schematic diagram of the implant structure of the present invention.

[0018] Figure 2 This is a schematic diagram of the surgical instrument structure of the present invention.

[0019] Figure 3 This is a schematic diagram of the pre-assembled state of the implant and surgical instruments of the present invention.

[0020] Figure 4 This is a schematic diagram of the assembly of the guide wire, implant, and surgical instruments of the present invention.

[0021] Figure 5 This is a schematic diagram showing the state after the deformable section of the present invention has been expanded and anchored.

[0022] Figure 6 for Figure 5 A partial cross-sectional schematic diagram.

[0023] The attached figures are labeled as follows: 100. Implant; 110. Main body segment; 111. Load-bearing structure; 120. Expansion segment; 121. End segment; 1211. First connecting part; 1212. First guiding channel; 1213. Receiving groove; 122. Deformable segment; 1221. Expansion part; 200. Surgical instrument; 210. First operating element; 211. Guide part; 212. Second connecting part; 213. Second guide channel; 220. Second operating element; 221. Force transmission structure; 300. Guide wire. Detailed Implementation

[0024] To make the objectives, technical solutions, and advantages of this invention clearer, the invention will be further described in detail below with reference to the accompanying drawings and embodiments. It should be understood that the specific embodiments described herein are merely illustrative and not intended to limit the invention.

[0025] In the description of this invention, it should be understood that the term "proximal" refers to the end of the instrument that is closer to the operator (physician) in normal use, and the term "distal" refers to the end that is farther from the operator and enters the patient's body first. This orientation definition is only used to describe the relative positional relationship between the components and should not be construed as limiting the invention.

[0026] Example: like Figure 1 As shown, this embodiment provides an implant 100 for flat foot correction. The implant 100 is configured as a cone shape, and is divided into a main body segment 110 and an expansion segment 120 along its axial direction from the proximal end to the distal end.

[0027] The main body segment 110 is located at the proximal end of the implant 100 and is used to provide main support to maintain the arch height after implantation. A force-bearing structure 111 is provided on the end face of the main body segment 110 near the proximal end, which is used to cooperate with the surgical instrument 200 to transmit rotational driving force. In this embodiment, the force-bearing structure 111 is a concave limiting groove with a non-circular cross-sectional shape, such as a rectangle, a regular hexagon, or a regular octagonal star. A feedback structure is also provided on the outer wall of the main body segment 110. In this embodiment, the feedback structure is a circumferentially distributed spacer groove, making the external thread of the main body segment 110 a discontinuous thread, generating intermittent resistance changes or audible feedback during rotational engagement.

[0028] The expansion section 120 is located at the distal end of the implant 100 and includes an end section 121 and a deformable section 122. The end section 121 is located at the distal end of the expansion section 120 and is used to connect with the surgical instrument 200. A first connecting portion 1211 is provided at the center of the end section 121 near the main body section 110. In this embodiment, the first connecting portion 1211 is an internally threaded hole. A first guiding channel 1212 is provided axially at the distal end of the end section 121 for accommodating the guide wire 300. A receiving groove 1213 is also provided inside the end section 121, which is coaxial with and communicates with the first connecting portion 1211. The inner wall of the receiving groove 1213 is a smooth surface.

[0029] The deformable segment 122 connects the main body segment 110 and the end segment 121, and is used to expand radially to form an anchor when axially driven. The deformable segment 122 is a radially expandable thin-walled structure, including a proximal connecting ring, a plurality of evenly distributed expansion portions 1221, and a distal connecting ring. The proximal connecting ring is fixedly connected to the main body segment 110, the distal connecting ring is fixedly connected to the end segment 121, and the expansion portions 1221 are connected between the proximal connecting ring and the distal connecting ring. An axially extending gap is formed between adjacent expansion portions 1221, allowing the deformable segment 122 to expand radially outward when subjected to axial compression.

[0030] like Figure 2 As shown, this embodiment also provides a surgical instrument 200 for use with the implant 100 described above. The surgical instrument 200 includes a first operating member 210 and a second operating member 220 arranged coaxially.

[0031] The first operating member 210 is used to drive the end section 121 to move axially. The distal end of the first operating member 210 is provided with a second connecting portion 212 that mates with the first connecting portion 1211 of the end section 121. In this embodiment, the second connecting portion 212 is externally threaded. The interior of the first operating member 210 has a through second guide channel 213 along the axial direction for accommodating the guide wire 300. The first operating member 210 includes a guide portion 211 and a second connecting portion 212. The guide portion 211 is located on the proximal side and is used to slide through the deformable section 122. The second connecting portion 212 is located on the distal side and is used to insert into the receiving groove 1213 of the end section 121 and mate with the first connecting portion 1211.

[0032] The second operating member 220 is used to drive the main body segment 110 to rotate. The second operating member 220 is movably sleeved outside the first operating member 210, and both ends of the first operating member 210 extend through the second operating member 220. The second operating member 220 and the first operating member 210 are rotatably connected, and the two can rotate relatively independently. The distal end of the second operating member 220 is provided with a force transmission structure 221, which is used to cooperate with the force-receiving structure 111 of the main body segment 110 to transmit the rotational driving force. In this embodiment, the force transmission structure 221 is an outwardly protruding limiting block, and its cross-sectional shape matches that of the force-receiving structure 111, both being non-circular to prevent relative rotation.

[0033] The proximal ends of the first operating element 210 and the second operating element 220 are respectively provided with operating handles, which are convenient for the operator to operate them separately.

[0034] like Figure 1-6 As shown: The detailed description of the method of using this invention is as follows: Preparations before the steps, such as Figure 3As shown, the implant 100 and surgical instrument 200 are prepared. The implant 100 includes a main body segment 110, a deformable segment 122, and an end segment 121; the surgical instrument 200 includes a first operating element 210 and a second operating element 220.

[0035] S1: Pre-assembly: Connect the first operating member 210 to the end section 121. Specifically, insert the guide portion 211 of the first operating member 210 into the deformable section 122, so that its second connecting portion 212 initially engages with the first connecting portion 1211 of the end section 121. In this embodiment, the fine threaded rod engages with the internal threaded hole, but the first operating member 210 does not apply axial driving force to the end section 121. At this time, the deformable section 122 remains in its initial contracted state. Then, the guide wire 300 is sequentially passed through the second guide channel 213 of the first operating member 210 and the first guide channel 1212 of the end section 121 to guide the implant 100 to the implantation site.

[0036] S2: Main implantation: such as Figure 4 As shown, the second operating member 220 is rotated. The second operating member 220, through its distal force-transmitting structure 221, engages with the proximal force-receiving structure 111 of the main body segment 110, transmitting rotational driving force to the main body segment 110. Since both the force-transmitting structure 221 and the force-receiving structure 111 have non-circular cross-sections, they fit tightly together to prevent relative rotation and ensure effective transmission of driving force. When the second operating member 220 rotates, the first operating member 210 rotates synchronously with it, i.e., there is no relative movement. However, since the first operating member 210 and the end segment 121 only initially engage and are not fully locked, the rotation of the first operating member 210 cannot be converted into an axial driving force on the end segment 121. Therefore, the deformable segment 122 remains in a contracted state and will not be accidentally triggered during implantation. Subsequently, through the continuous rotation of the second operating member 220, the implant 100 is screwed into the bone tunnel to the predetermined depth. During this process, the feedback structures on the outer wall of the main body 110, such as the spacer groove, will generate intermittent changes in resistance and sound feedback to help the surgeon determine the number of rotations and axial position.

[0037] S3: Expansion anchoring: such as Figure 5 As shown, when the implant 100 reaches the predetermined depth, the first operating member 210 is rotated independently. Through the helical transmission between the first operating member 210 and the end section 121, the rotational motion is converted into axial movement of the end section 121 towards the proximal end. When the end section 121 moves towards the proximal end, axial compression is applied to the expansion portion 1221 through the distal connecting ring, causing the expansion portion 1221 to expand radially outward and fit tightly against the bone tunnel wall to form an anchor.

[0038] The operator can precisely adjust the axial displacement of the end section 121 by controlling the number of rotations of the first operating element 210, thereby controlling the radial expansion degree of the expansion section 1221 to adapt to the anchoring needs of different patients' bone tunnel morphologies.

[0039] After expansion and anchoring are completed, the surgeon can use the second manipulator 220 to fine-tune the angle or depth of the main body segment 110 as needed to complete the final implantation. Reversing the first manipulator 210 allows the surgical instrument 200 to be removed.

[0040] It should be noted that, in this document, relational terms such as "first" and "second" are used only to distinguish one entity or operation from another, and do not necessarily require or imply any such actual relationship or order between these entities or operations. Furthermore, the terms "comprising," "including," or any other variations thereof are intended to cover non-exclusive inclusion, such that a process, method, article, or apparatus that comprises a list of elements includes not only those elements but also other elements not expressly listed, or elements inherent to such process, method, article, or apparatus.

[0041] Although embodiments of the invention have been shown and described, it will be understood by those skilled in the art that various changes, modifications, substitutions and alterations can be made to these embodiments without departing from the principles and spirit of the invention, the scope of which is defined by the appended claims and their equivalents.

Claims

1. A method of using a flatfoot correction screw and tool, characterized in that, Includes the following steps: An implant and a surgical instrument are provided. The implant includes: a main body segment located at the proximal end for providing main body support, an end segment located at the distal end for connecting to the surgical instrument, and a deformable segment connecting the main body segment and the end segment, the deformable segment being used to expand radially to form an anchor when axially driven; the surgical instrument includes: a first operating element and a second operating element coaxially arranged and rotatable relatively independently. S1: Pre-assembly: Connect the first operating member to the end segment to keep the deformable segment in its initial state; S2: Main body implantation: Operate the second operating member to rotate, drive the main body segment to rotate, and implant the entire implant into the bone tunnel to a predetermined depth; S3: Expansion anchoring, the first operating component is rotated independently, driving the end section to move axially, so that the deformable section expands radially to form an anchor.

2. The method of use according to claim 1, characterized in that: In step S1, the first operating member is initially engaged with the end segment but no axial driving force is applied, so that the rotation of the first operating member cannot be converted into an axial driving force on the end segment.

3. The method of use according to claim 1, characterized in that: In S2, a force transmission structure is provided at the distal end of the second operating member, and a force receiving structure is provided at the proximal end of the main body section; the force transmission structure and the force receiving structure cooperate to transmit rotational driving force, and the cross-sectional shapes of the force transmission structure and the force receiving structure are both non-circular to prevent relative rotation.

4. The method of use according to claim 1, characterized in that: In S2, when the second operating member is rotated during implantation, the first operating member rotates synchronously with the second operating member. However, since the first operating member only initially engages with the end segment, no axial driving force is applied to the end segment to prevent the deformable segment from being accidentally triggered during implantation.

5. The method of use according to claim 1, characterized in that: In step S3, the rotational motion is converted into axial movement of the end section by the cooperation of the first operating member with the end section helical transmission, so that the expansion part of the deformable section expands radially; the degree of expansion of the expansion part is adjusted by controlling the number of rotations of the first operating member.

6. The method of use according to claim 1, characterized in that: In S2 and S3, intermittent resistance changes or sound feedback are generated by the feedback structure set on the outer wall of the main body section to help determine the number of rotations or axial position.

7. A flatfoot correction implant for use in any one of claims 1 to 6, characterized in that, The implant is divided into a main segment and an expansion segment from proximal to distal; The proximal end of the main body section is provided with a force-bearing structure for transmitting rotational driving force in conjunction with surgical instruments; The expansion section includes an end section and a deformable section. The end section is provided with a first connecting part that cooperates with the first operating member and a through first guiding channel. The deformable section is a thin-walled structure that can expand radially.

8. A surgical instrument for use in any one of claims 1 to 6, characterized in that, It includes a first operating element and a second operating element that are coaxially arranged and can rotate relatively independently; The distal end of the first operating member is connected to the end section, and the interior of the first operating member is provided with a through second guide channel; The second operating component is movably sleeved on the outside of the first operating component, and a force transmission structure is provided at the far end to cooperate with the force-bearing structure of the main body section.

9. The surgical instrument according to claim 8, characterized in that: The first operating component includes a guide portion and a second connecting portion. The guide portion slides through the deformable section, and the second connecting portion is inserted into a pre-set receiving groove inside the end section.

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