Integrated multi-hole mandibular implant prosthesis capable of being spliced

Abstract

The invention provides an integrated splicable porous mandibular implant prosthesis, which comprises a left prosthesis module, a right prosthesis module, a splicing connection part and a porous structure part, and is characterized in that the left prosthesis module and the right prosthesis module are detachably connected through the splicing connection part to form an integral structure; porous structure parts are arranged in the middle main body areas of the left prosthesis module and the right prosthesis module respectively, a plurality of double-end guide holes are evenly formed in the porous structure parts, and each double-end guide hole forms an independent hole opening in the front surface and the rear surface of the corresponding prosthesis module. The front hole opening and the rear hole opening are communicated with each other through communicating hole channels formed in the porous structure part; the splicing connecting part comprises an insertion tenon part arranged on the left prosthesis module and a mortise groove part arranged on the right prosthesis module; the splicing connecting part is provided with a limiting clamping structure; the left prosthesis module and the right prosthesis module are respectively provided with a plurality of fixing holes. During use, rapid assembly of the prosthesis modules is facilitated, and growth of bone tissue is facilitated.

Description

Technical Field

[0001] This application belongs to the technical field of medical devices, and more specifically, to the technical field of oral and maxillofacial surgical implant restoration devices, and particularly relates to an integrated spliceable porous mandibular implant prosthesis for repairing mandibular defects. Background Art

[0002] In the reconstruction treatment of mandibular defects, the implantation of artificial prostheses is widely used for structural replacement and function restoration. With the development of medical engineering and imaging technology, higher requirements have been put forward for the design of prostheses in clinical practice, especially emphasizing their adaptability to individual anatomical structures and the convenience of intraoperative operations. Therefore, a structural solution that can be customized according to the scope of the patient's lesion and adapted to the contour of the bone bed has gradually become the mainstream clinical choice.

[0003] Some existing reconstruction devices adopt the method of dividing the prosthesis into multiple regional components to improve the flexibility of surgical operations. This type of structure usually requires multiple components to be assembled during the operation. However, since the assembly process depends on the doctor to manually adjust the mating positions between the components in a limited space and lacks a clear docking control mechanism, it is often difficult to accurately control the connection positions of the components. Once there is a positioning deviation during the operation, it may cause the overall deviation of the structure, abnormal stress, and even affect the postoperative tissue fusion and the reconstruction effect of the occlusal function.

[0004] Therefore, there is still a key problem in the current structural design, that is, there is a lack of a clear and reliable docking control structure during the surgical connection of multiple components, making it difficult to ensure the accuracy of the overall position and the long-term stability of the structure. This situation is not uncommon in actual clinical practice, but it is often underestimated during the device design stage. In fact, it directly affects the intraoperative operation efficiency of the prosthesis and the postoperative biomechanical performance, and urgently needs to be solved from the structural design level. Summary of the Invention

[0005] The purpose of this application is to provide an integrated spliceable porous mandibular implant prosthesis, aiming to solve the problem of the lack of a reliable docking control structure during the intraoperative combination of multiple components of the mandibular implant prosthesis.

[0006] This application provides an integrated spliceable porous mandibular implant prosthesis, including a left prosthesis module, a right prosthesis module, a splicing connection part, and a porous structure part. The left prosthesis module and the right prosthesis module are detachably connected through the splicing connection part to form an overall structure; The middle main body regions of the left prosthesis module and the right prosthesis module are respectively provided with porous structure parts. A plurality of double-end guiding holes are uniformly arranged on the porous structure parts. Each double-end guiding hole forms independent orifices on the front surface and the rear surface of the prosthesis module respectively, and the front and rear orifices are interconnected through a communication channel arranged inside the porous structure part; The splicing connection part includes a tenon part arranged on the left prosthesis module and a mortise part arranged on the right prosthesis module. The tenon part is inserted into the mortise part to achieve mechanical plug-in fit. The splicing connection part is provided with a limit clamping structure for preventing loosening between the left prosthesis module and the right prosthesis module after plugging. A plurality of fixing holes are respectively arranged on the left prosthesis module and the right prosthesis module. The fixing holes are arranged in the edge solid structure area of the left and right prosthesis modules and are used to cooperate with fixing screws to fix the prosthesis to the patient's mandible.

[0007] As an optional mode of the present application, the double-end guiding holes of the porous structure part have a gradient hole structure, and the opening diameter of the double-end guiding holes on the front surface of the prosthesis module is smaller than the opening diameter on the rear surface of the prosthesis module.

[0008] As an optional mode of the present application, the opening diameter of the double-end guiding holes on the rear surface of the prosthesis module is 300-600 microns, and the opening diameter of the double-end guiding holes on the front surface of the prosthesis module is 50-150 microns.

[0009] As an optional mode of the present application, the communication channels are distributed in a dendritic structure in the porous structure part.

[0010] As an optional mode of the present application, the limit clamping structure includes a stop boss arranged at the tail end of the tenon part and a locking groove arranged on the inner wall of the mortise part. After the tenon part of the limit clamping structure is plugged into the mortise part, the stop boss is clamped and matched with the locking groove.

[0011] As an optional mode of the present application, the edges of the left prosthesis module and the right prosthesis module are provided with a solid structure area outside the porous structure part, and the fixing holes are opened on the solid structure area.

[0012] As an optional mode of the present application, the outer surfaces of the left prosthesis module and the right prosthesis module are provided with a roughened treatment layer for improving the bone cell adhesion performance.

[0013] As an optional mode of the present application, the left prosthesis module, the right prosthesis module and the fixing screws are all made of polyether ether ketone (PEEK) material.

[0014] As an optional mode of the present application, a transition structure area is arranged between the porous structure part and the solid structure area. The transition structure area is provided with a plurality of through holes. The through holes are perforations penetrating the thickness direction of the prosthesis. The aperture of the through holes is smaller than the aperture of the double-end guiding holes in the porous structure part, and the aperture of the through holes gradually decreases from the side close to the porous structure part to the side close to the solid structure area.

[0015] As an alternative embodiment of the present application, the splicing end faces where the tenon parts and mortise parts are located are mutually matching spatial arc surface structures. On the corresponding arc surfaces of the tenon parts and mortise parts, there are respectively arranged a guiding groove and a positioning rib that cooperate with each other. The guiding groove and the positioning rib are slidably matched with each other during the insertion process and can be used to guide the insertion direction.

[0016] Compared with the prior art, the present application has the following beneficial effects: 1. The present application provides an integrated spliceable porous mandibular implant prosthesis. By dividing the mandibular implant prosthesis into a left prosthesis module and a right prosthesis module as a whole, it can be combined into a complete structure through the splicing connection part during the operation. The splicing connection part is located between the docking end faces of the two prosthesis modules and mainly includes a tenon part and a mortise part, and the two achieve spatial cooperation through structural fitting. Since the insertion structure is an entity structure with a matching relationship and no longer completely relies on the doctor's visual inspection or manual alignment during the operation to complete the module splicing, the operation difficulty can be reduced to a certain extent. This structure has a certain self-guiding function during the insertion process, which helps to improve the accuracy of module docking and reduce the connection skew or poor combination caused by factors such as deviation of the insertion direction.

[0017] 2. The present application also sets a limit clamping structure for the splicing connection part. The limit clamping structure is jointly composed of a stop boss arranged at the tail end of the tenon part and a locking groove on the inner wall of the mortise part. During the module insertion process, the tenon part is gradually pushed forward, and when the stop boss reaches the position of the locking groove, clamping and positioning are achieved. This structure realizes a mechanical locking method when the insertion is completed, which can not only reduce the displacement caused by the change of the operation angle during the operation at the connection, but also limit the insertion depth and direction through the structure itself, which helps to reduce the cooperation failure caused by incomplete insertion or over-insertion. The insertion and cooperation have a continuous process of guiding - transition - clamping, which is beneficial to standardize the operation path during the operation and reduce the influence of the doctor's lack of experience on the connection accuracy.

[0018] 3. The present application sets a plurality of fixing holes for screw fixation in the edge solid structure areas of the left prosthesis module and the right prosthesis module. These fixing holes are used to install the prosthesis on the patient's mandible and avoid applying direct loads on the splicing connection part, so that the splicing connection part can focus more on position control and insertion stability. This method can reduce the loosening risk of the splicing connection part caused by long-term use.

[0019] 4. In the middle main body regions of the two prosthesis modules (left prosthesis module and right prosthesis module) of the present application, porous structure parts are respectively arranged, and a plurality of double-ended guiding holes are evenly opened on each porous structure part. These left and right prosthesis modules penetrate through from front to back, and a three-dimensional channel network is formed inside through communication channels, thereby endowing the prosthesis with good bone integration potential. Since the porous structure parts are arranged in the middle regions of the prosthesis, the core parts of the mandibular defect can be aligned, forming a bone contact interface with a relatively large area. The double-ended guiding holes are respectively opened on the front surface and the back surface of the prosthesis, and the communication channels establish multi-dimensional penetration paths therebetween, which can guide the bone tissue to extend from the back to the front. At the same time, this pore structure can also promote the flow of body fluid in the pores after the operation, which helps to form a microenvironment suitable for the growth of bone cells, and further improves the integration uniformity and bonding depth between the prosthesis and the bone tissue. BRIEF DESCRIPTION OF THE DRAWINGS

[0020] In order to more clearly illustrate the technical solutions in the embodiments of the present application or the prior art, the following will briefly introduce the drawings required to be used in the description of the embodiments or the prior art. Obviously, the drawings in the following description are some embodiments of the present application. For those of ordinary skill in the art, without creative efforts, other drawings can also be obtained based on these drawings.

[0021] Figure 1 Structural schematic diagram of an integrated splicable porous mandibular implant prosthesis provided by an embodiment of the present application; Figure 2 Schematic diagram when the left prosthesis module and the right prosthesis module provided by an embodiment of the present application are spliced together; Figure 3 Structural schematic diagram of the right prosthesis module provided by an embodiment of the present application; Figure 4 Structural schematic diagram of the left prosthesis module provided by an embodiment of the present application; Figure 5 Structural schematic diagram of the left prosthesis module provided by another embodiment of the present application; Figure 6 Structural schematic diagram of the left prosthesis module provided by still another embodiment of the present application.

[0022] In the figure: 100, left prosthesis module; 200, right prosthesis module; 300, porous structure part; 310, double-ended guiding hole; 400, splicing connection part; 410, tenon part; 420, mortise groove part; 430, limit clamping structure; 431, stop boss; 432, locking groove; 500, solid structure area; 510, fixing hole; 600, roughened treatment layer; 700, transition structure area; 710, through hole; 800, fixing screw. DETAILED DESCRIPTION OF THE EMBODIMENTS

[0023] To make the objectives, technical solutions and advantages of the embodiments of this application clearer, the following describes the technical solutions in the embodiments of this application clearly and completely. Apparently, the described embodiments are some but not all of the embodiments of this application. All other embodiments obtained by those of ordinary skill in the art based on the embodiments in this application without creative efforts also belong to the scope of protection of this application.

[0024] To more clearly elaborate on the objectives, technical solutions and advantages of the embodiments of this application, the following will describe the technical solutions in the embodiments of this application in detail. It should be noted that the described embodiments are only some examples of this application and not all of the content. Any other implementation obtained by those skilled in the art based on the embodiments of this application without creative efforts also belongs to the scope of protection of this application.

[0025] In the description of this application, it should be understood that the orientation or positional relationships indicated by terms such as "center", "upper", "lower", "front", "rear", "left", "right", "vertical", "horizontal", "top", "bottom", "inner", "outer", etc. are based on the orientation or positional relationships shown in the drawings, and are only used for facilitating the description of this application and simplifying the explanation, rather than implying that the device or element must have a specific orientation, structure or operation mode. Therefore, it should not be regarded as a limitation to this application.

[0026] Terms such as "first", "second", etc. are only used to distinguish different technical features and do not represent the relative importance or specific quantity limitation of the feature. Therefore, the features described with "first", "second" can represent one or more of such features. In this application, unless otherwise specified, "a plurality" generally refers to two or more.

[0027] In the description of this application, it should be noted that unless clearly specified or particularly limited, the terms "installed", "connected", "coupled" should be interpreted in a broad sense. For example, it can refer to a fixed connection, a detachable connection or an integral connection. For those of ordinary skill in the art, the specific meanings of these terms in this application can be understood according to specific circumstances.

[0028] Please refer to Figures 1 - 6 , Figure 1 which is a schematic structural diagram of an integrated splittable porous mandibular implant prosthesis provided by an embodiment of this application; Figure 2 which is a schematic diagram when the left prosthesis module and the right prosthesis module are spliced together provided by an embodiment of this application; Figure 3 which is a schematic structural diagram of the right prosthesis module provided by an embodiment of this application; Figure 4 which is a schematic structural diagram of the left prosthesis module provided by an embodiment of this application; Figure 5Schematic diagram of the left prosthesis module provided by another embodiment of the present application; Figure 6 Schematic diagram of the left prosthesis module provided by still another embodiment of the present application. As Figures 1 - 6 shown, the integral spliceable porous mandibular implant prosthesis provided by the embodiments of the present application includes a left prosthesis module 100, a right prosthesis module 200, a splicing connection part 400, and a porous structure part 300. The left prosthesis module 100 and the right prosthesis module 200 are detachably connected through the splicing connection part 400 to form an integral structure.

[0029] The middle main body regions of the left prosthesis module 100 and the right prosthesis module 200 are respectively provided with a porous structure part 300. A plurality of double-ended guiding holes 310 are uniformly arranged on the porous structure part 300. Each double-ended guiding hole 310 forms independent orifices on the front surface and the rear surface of the prosthesis module respectively, and the front and rear orifices are communicated with each other through a communication channel arranged inside the porous structure part 300.

[0030] As Figures 1 - 3 shown, the splicing connection part 400 includes a tenon part 410 arranged on the left prosthesis module 100 and a mortise part 420 arranged on the right prosthesis module 200. The tenon part 410 is inserted into the mortise part 420 to achieve mechanical plug-in fit; the splicing connection part 400 is provided with a limit clamping structure 430 for preventing loosening between the left prosthesis module 100 and the right prosthesis module 200 after plugging.

[0031] A plurality of fixing holes 510 are respectively arranged on the left prosthesis module 100 and the right prosthesis module 200. The fixing holes 510 are arranged in the edge solid structure regions of the left and right prosthesis modules and are used to cooperate with fixing screws to fix the prosthesis to the patient's mandible.

[0032] In this embodiment, the mandibular implant prosthesis is integrally divided into a left prosthesis module 100 and a right prosthesis module 200, so that it can be combined into a complete structure through the splicing connection part 400 during the operation. The splicing connection part 400 is located between the butting end faces of the two prosthesis modules and mainly includes a tenon part 410 and a mortise part 420, and the two realize spatial fit through structural fitting. Since the plugging structure is an entity structure with a matching relationship and no longer completely depends on the doctor's visual inspection or manual alignment during the operation to complete the module splicing, the operation difficulty can be reduced to a certain extent. This structure has a certain self-guiding function during the plugging process, which helps to improve the docking accuracy of the module and reduce the connection skew or poor combination caused by factors such as plugging direction deviation.

[0033] Furthermore, in order to improve the stability of the connection process and reduce the risk of misalignment, a limit clamping structure 430 is provided for the splicing connection part 400 in this embodiment. The limit clamping structure 430 is jointly composed of a stop boss 431 provided at the tail end of the tenon part 410 and a locking groove 432 on the inner wall of the mortise part 420. Optionally, the stop boss 431 is provided on the front and rear surfaces at the tail end of the tenon part 410. During the module insertion process, the tenon part 410 is gradually advanced, and when the stop boss 431 reaches the position of the locking groove 432, clamping and positioning are achieved. This structure realizes a mechanical locking method when the insertion is completed, which can not only reduce the displacement caused by the change of the operation angle during the operation at the connection, but also limit the insertion depth and direction through the structure itself, helping to reduce the mating failure caused by incomplete insertion or over-insertion. The insertion and mating have a continuous process of guiding - transitioning - clamping, which is beneficial to standardize the operation path during the operation and reduce the impact of the doctor's lack of experience on the connection accuracy.

[0034] In addition, in order to maintain the morphological continuity and force balance of the overall prosthesis structure during the postoperative use process, a plurality of fixing holes 510 for screw fixation are provided in the edge solid structure area 500 of the left prosthesis module 100 and the right prosthesis module 200 in this embodiment. These fixing holes are used to install the prosthesis onto the patient's mandible and avoid applying direct loads on the splicing connection part 400, enabling the splicing connection part 400 to focus more on position control and insertion stability. This method can reduce the loosening risk of the splicing connection part 400 caused by long-term use.

[0035] As can be seen from the above, for the integrated spliceable porous mandibular implant prosthesis in the embodiment of the present application, through the coordinated cooperation of guiding connection, clamping limit, and edge fixation in the overall structure, problems such as inaccurate intraoperative positioning and insecure splicing existing in the traditional splicing structure are improved to a certain extent, which helps to enhance the reliability and stability of the prosthesis in clinical use.

[0036] Furthermore, in this embodiment, by dividing the prosthesis structure into a left prosthesis module 100 and a right prosthesis module 200 and providing a splicing connection part 400, the overall structure has the ability of modular assembly. Compared with the traditional one-piece large-volume prosthesis, the modular structure makes the large-volume prosthesis composed of relatively small spliceable module components, which helps to improve the flexibility during the intraoperative operation. Moreover, due to the relatively small volume of the modules, intraoperative positioning is also more convenient. With the mechanical insertion and mating completed by the splicing connection part 400, doctors can dynamically fine-tune the shape of the prosthesis after assembly according to the defect shape and range of the patient's mandible, further enhancing the anatomical adaptability. At the same time, the left prosthesis module 100 and the right prosthesis module 200 are designed to be detachable, which also facilitates the replacement or adjustment of some structures when needed after the operation, enhancing the flexibility of later repair and maintenance.

[0037] Meanwhile, in the middle main body regions of the two prosthesis modules (left prosthesis module 100 and right prosthesis module 200) of the present application embodiment, porous structure parts 300 are respectively arranged, and a plurality of double-ended guiding holes 310 are evenly opened on each porous structure part 300. These left prosthesis modules 100 and right prosthesis modules 200 penetrate through from front to back, and a three-dimensional channel network is formed inside through the communication channels, thereby endowing the prosthesis with good bone integration potential. Since the porous structure parts 300 are arranged in the middle region of the prosthesis, the core part of the mandibular bone defect can be aligned, forming a bone contact interface with a relatively large area. The double-ended guiding holes 310 are respectively opened on the front surface and the back surface of the prosthesis, and the communication channels establish a multi-dimensional penetration path therebetween, which can guide the bone tissue to extend from the back to the front. At the same time, this pore structure can also promote the flow of body fluid in the pores after surgery, help to form a microenvironment suitable for the growth of bone cells, and further improve the integration uniformity and binding depth between the prosthesis and the bone tissue.

[0038] In addition, a plurality of fixing holes 510 are arranged in the edge solid structure regions 500 of the left prosthesis module 100 and the right prosthesis module 200, which are used to cooperate with screws to stably install the prosthesis on the patient's bone bed. Through the above structural arrangement, on the one hand, the mechanical connection strength between the two prosthesis modules is enhanced, which helps to reduce the risk of loosening at the connection during or after surgery; on the other hand, the fixing holes 510 avoid the middle porous region (i.e., the region of the porous structure part 300), which not only does not affect the growth path of bone tissue, but also facilitates the selection of a suitable screw implantation path according to the actual bone quality conditions during surgery, so that the operation of fixing the prosthesis is more flexible and helps to improve the long-term stability of the fixation.

[0039] In some embodiments, the double-ended guiding holes 310 of the porous structure part 300 have a gradient pore structure, and the aperture of the opening of the double-ended guiding hole 310 on the front surface of the prosthesis module is smaller than the aperture of the opening on the back surface of the prosthesis module.

[0040] In this embodiment, the double-ended guiding holes 310 adopt a gradient pore structure, the aperture of the opening on the front surface is smaller, and the aperture of the opening on the back surface is relatively larger. This design of asymmetric apertures makes the channel have a certain directionality, thereby forming a directional three-dimensional penetration path. After the prosthesis module is implanted, usually its back surface (i.e., the large pore side) abuts against the defect surface of the patient's mandible. Based on this, designing a larger pore opening on the side close to the bone tissue can increase the contact area between bone cells and the pore entrance, providing a more sufficient access channel for cell growth inward. The small hole opening on the front surface plays a role of growth guidance to a certain extent, while inhibiting the excessive invasion of non-target fibrous tissues, and constructing a relatively clear bone growth path from the structure, which helps the tissue differentiation and space differentiation of the subsequent interface.

[0041] Meanwhile, based on the difference in pore diameters at the front and back, the gradient pore structure and the connecting pore channels provided inside the porous structure part 300 together constitute a continuous channel system, thereby establishing a transmission channel with a resistance gradient inside the prosthesis. In the initial stage of bone tissue repair, blood vessels, bone marrow-derived osteocytes, and related nutritional factors need to penetrate into the prosthesis structure from the bone contact surface through the pores. The large-pore section provides a low-resistance entrance, which is conducive to early cell migration and liquid penetration. As the pore diameter gradually narrows, the flow velocity in the pore channels slows down, which helps to maintain the relative stability of the local microenvironment and improve the cell adhesion efficiency and bone matrix deposition ability. At the same time, the small-pore end helps to reduce the risk of external contaminants or oral bacteria entering reversely along the channels. The overall structure presents a pore characteristic similar to that in natural bone tissue, namely "wide entrance and narrow exit", thus enhancing the bio-mimicry and physiological coordination of the prosthesis.

[0042] In addition, the differential setting of the pore diameters at the front and back also has a certain regulatory effect on the mechanical performance. In the large-pore area close to the bone tissue, due to its larger contact area with the newly formed bone, it can effectively disperse the local stress concentration generated by occlusal stress or muscle pulling force, thus helping to stabilize the stress distribution in this area. The small-pore area far from the bone tissue, on the premise of maintaining the structural integrity, avoids the edge weakening phenomenon caused by excessive opening. Through this gradient arrangement, the porous structure part 300 obtains more balanced support on the force-bearing path, which not only enhances the mechanical stability of the prosthesis during long-term use but also helps to reduce the risk of potential structural damage caused by micro-motion and fatigue, thereby extending the stable working cycle of the implant in the body.

[0043] In some embodiments, the opening pore diameter of the double-ended guiding hole 310 on the rear surface of the prosthesis module is 300 - 600 microns, and the pore diameter of the double-ended guiding hole 310 on the front surface of the prosthesis module is 50 - 150 microns.

[0044] In this embodiment, limiting the opening pore diameter of the double-ended guiding hole 310 on the rear surface of the prosthesis module between 300 and 600 microns helps to meet the physiological requirements of osteocyte adhesion and tissue ingrowth, and the size design is closer to the bioactive window of osteocytes. Relevant research shows that when the pore diameter is greater than 300 microns, it is conducive to the proliferation of bone tissue cells and the generation of new blood vessels. By setting this pore diameter range on the side of the porous structure part 300 close to the bone tissue, it can not only provide sufficient invasion paths for the bone tissue but also form a three-dimensional space suitable for cell expansion in terms of structure. At the same time, controlling the upper limit within 600 microns also maintains the integrity of the structure around the pore channels to a certain extent and reduces the risk of local mechanical property degradation caused by too large pore diameter. This design takes into account both the promotion of bone integration and the stability of the bearing strength.

[0045] Relatively, on the front surface of the prosthesis module, the aperture of the double-ended guiding hole 310 is set to be 50 to 150 micrometers, which helps to inhibit the entry of non-target tissues into the pore, while maintaining the structural density of the front surface. This surface usually faces the oral mucosa or soft tissue area. If the opening is too large, it may guide the growth of fibrous tissue into the pore, thus interfering with the formation of osseointegration. Appropriately reducing the aperture can form a selective filtration to a certain extent, enabling tissue fluid and signaling factors with smaller molecular weights to penetrate through the pore opening, while large particulate tissue structures are not easily invaded. In addition, the aperture within this range can also create a certain roughness on the surface, which is beneficial to enhancing the interfacial friction in this area, thereby enhancing the fitting effect of the prosthesis in the soft tissue direction and improving the stability accordingly.

[0046] In this embodiment, by adopting the double-ended guiding hole 310 with different aperture settings at the front and back, a gradient channel network with orientation, selectivity, and strength balance is formed in the structure of the double-ended guiding hole 310. The larger opening on the back surface provides spatial support for the migration of bone tissue and angiogenesis. The inside of the pore forms a slow-changing area for the flow of nutrients and cells. The smaller pore opening on the front surface controls the channel flow and strengthens the integrity of the surface layer. Generally speaking, the limitation of this aperture range makes the functional performance of the gradient structure more hierarchical, not only improving the spatial functional layout of the porous structure part 300, but also facilitating the differential forming of functional areas through precision processes such as 3D printing during manufacturing, enhancing the prosthesis performance from two dimensions of structural design and process implementation.

[0047] In some embodiments, the communication pores are distributed in a dendritic structure within the porous structure part 300.

[0048] In this embodiment, the communication pores are distributed in a dendritic structure within the porous structure part 300. This design helps to improve the spatial connectivity between the double-ended guiding holes 310, thereby enhancing the permeability of the overall pore network. Compared with the common linear channel structure, the dendritic path has the characteristics of multi-directional extension and multi-point intersection in space, and can differentiate multiple sub-channels leading to different regions from a single entrance. Through this internal staggered arrangement, each double-ended guiding hole 310 not only has basic longitudinal permeability, but also can form an interconnection with multiple surrounding guiding holes in the transverse direction. This three-dimensional network helps to enrich the cell migration path and provides more possibilities for the in-depth diffusion of body fluids and nutrient factors in the pores, thereby improving the tissue adaptation environment inside the porous structure part 300.

[0049] In addition, the dendritic structure can also form a region similar to a flow buffer inside the channels, thereby achieving a more uniform diffusion state of tissue fluid, which helps to balance the distribution of osteocytes in the porous region. Due to the existence of multiple turning points and intersection nodes in the dendritic through-holes, the velocity of the liquid is naturally slowed down during the flow process, avoiding local infiltration deficiency caused by high-speed unidirectional flow. This slow diffusion mode is beneficial to stabilizing the microenvironment in the pores, increasing the attachment probability of cells in different channel segments, and promoting the formation of a local microcirculation system. With the help of this branched structure, osteocytes can expand over a larger range, facilitating the formation of a more continuous bone tissue filling, and contributing to increasing the integration depth between the prosthesis and the bone interface.

[0050] From the perspective of structural mechanics, the dendritic distribution of the connected channels can, to a certain extent, relieve the phenomenon of local stress concentration, thereby reducing the risk of microcracks occurring in the porous structure part 300 under long-term load. After the prosthesis is implanted, it needs to bear multi-directional complex stresses such as chewing force and muscle traction force. If the channels are in a regular straight shape, potential weak areas are likely to form at the junction positions or stress concentration points. The dendritic structure has good force dispersion ability, and its staggered paths can transfer the external load to multiple branch channels, thus realizing the redistribution of the load in space. This structural layout is closer to the arrangement mode of natural trabecular bone. It not only performs better in terms of structural stability but also can reduce the impact of fatigue accumulation on the prosthesis during long-term use, contributing to extending its service life in the body.

[0051] In some embodiments, as Figure 1 , Figure 3 and Figure 4 shown, the limit snap-fit structure 430 includes a stop boss 431 provided at the tail end of the tenon part 410 and a locking groove 432 provided on the inner wall of the mortise part 420. After the tenon part 410 of the limit snap-fit structure 430 is inserted into the mortise part 420, the stop boss 431 is engaged with the locking groove 432.

[0052] In this embodiment, a stop boss 431 is provided at the tail end of the tenon part 410, and a locking groove 432 is formed on the inner wall of the mortise part 420. The two form a matching mechanical snap-fit structure in terms of structure, which is used to enhance the connection stability between the left prosthesis module 100 and the right prosthesis module 200. After the insertion is completed, the stop boss 431 just fits into the locking groove 432 to achieve a blocking effect, which helps to reduce the possibility of sliding or dislocation between the left prosthesis module 100 and the right prosthesis module 200. This structural connection method with a limit is different from the traditional insertion mode that relies on friction for positioning. It has a more definite stop control during use and is more suitable for withstanding repeated stress loads during long-term use, improving the overall connection reliability and stable retention ability of the prosthesis.

[0053] At the same time, this position-limiting snap-in structure can achieve "insertion and positioning" when used, and has high convenience in intraoperative operation. During the operation, the tenon portion 410 and the mortise portion 420 only need to be inserted in accordance with the design direction to complete the position guidance and mechanical snap-in, without the assistance of external tools such as screws and clamps. This structure is particularly suitable for mandibular areas with limited space. It can reduce the number of times the doctor repeatedly adjusts the position of the prosthesis module during the operation, shorten the assembly time, and is conducive to controlling the expansion of the wound, reducing tissue interference caused by misinsertion or repeated insertion and removal, and improving the efficiency and accuracy of actual surgical operations.

[0054] In addition, the clamping structure also provides a certain degree of anti-rotation ability and pull-out resistance at the connection part. The stop boss 431 forms a surface-to-surface fit in the locking groove 432. In addition to the axial limit function, it can also limit the relative rotation of the two prosthesis modules in the circumferential direction. When used in the mandibular area, the prosthesis often needs to withstand the multi-directional shear force and torsional load generated by the occlusion. This structure helps to reduce the structural micro-shift caused by rotational looseness.

[0055] In some embodiments, Figure 1 As shown, the edges of the left prosthesis module 100 and the right prosthesis module 200 are provided with a solid structure area 500 located outside the porous structure part 300 , and fixing holes 510 are opened on the solid structure area 500 .

[0056] In the above embodiment, the fixing holes 510 are arranged on the solid structure area 500 surrounding the porous structure part 300, which can reduce the interference with the continuity of the porous area structure while maintaining the connection strength, thereby achieving a more coordinated balance between mechanical properties and bio-fusion ability. The porous structure part 300 is mainly used to support the growth of bone tissue and cell adhesion. Its internal pore structure is relatively fragile and is not suitable for directly bearing the local stress concentration caused by screw fixation. Transferring the fixing point to the solid structure area 500 with a denser structure and higher strength makes the force path more reasonable, helps to reduce the pressure on the pore network, reduces the possibility of structural deformation, and is conducive to maintaining the functional integrity of the double-ended guide holes 310 and the connecting pores.

[0057] At the same time, in this embodiment, the solid structure area 500 is arranged in the edge area of ​​the left prosthesis module 100 and the right prosthesis module 200. Its position close to the outer contour of the prosthesis is convenient for intraoperative identification and tool contact, and also convenient for doctors to quickly complete the positioning operation of the joint bone surface. During the operation, the doctor can use the good visibility and operation margin of the edge area to more accurately select the fixed angle and path, and reduce the risk of screws mistakenly entering the middle pore area. This design layout not only optimizes the operation process, but also can reduce intraoperative bleeding and tissue interference to a certain extent, which has a positive effect on improving the safety and efficiency of clinical operations.

[0058] In addition, this embodiment adopts a spatial partition design with a porous structure part 300 in the middle and a solid structure area 500 at the edge, which helps to form a clear functional division in the structural composition of the prosthesis. The middle region focuses on providing a suitable growth environment for bone tissue and has good biocompatibility; while the peripheral solid structure area 500 undertakes the main mechanical connection and force sharing functions, forming a support framework. This structural layout is not only more efficient in space utilization but also improves the pertinence of function realization. By reasonably dividing and integrating the mechanical and biological properties, this embodiment can enhance the comprehensive performance of the prosthesis during intraoperative installation, postoperative stability, and long-term service.

[0059] In some embodiments, as Figure 6 shown, the outer surfaces of the left prosthesis module 100 and the right prosthesis module 200 are provided with a roughened treatment layer 600 for improving the bone cell adhesion performance. Figure 6 Only the left prosthesis module 100 provided with the roughened treatment layer 600 is shown as an example. Similarly, the outer surface of the right prosthesis module 200 is also provided with the roughened treatment layer 600.

[0060] The outer surfaces of the left prosthesis module 100 and the right prosthesis module 200 are provided with the roughened treatment layer 600, which helps to improve the micro-roughness of the prosthesis surface, thereby enhancing the bone cells' recognition ability and adhesion tendency to the surface in the initial stage of implantation. Compared with a smooth surface, the rough surface can form an irregular concave-convex morphology in the nano-to-micron scale range, increasing the density of anchor points during cell attachment. The bone cell membrane is more likely to spread between these micro-protrusions, thereby activating a series of biological reactions such as cytoskeleton remodeling and adhesion-related signaling pathways. The enhancement of such early adhesion behavior is of positive significance for accelerating the cell response in the pre-osteogenesis stage and can provide a good starting point for the subsequent integration of bone tissue.

[0061] Moreover, under the action of the roughened treatment layer 600, a multi-scale texture structure is formed on the prosthesis surface, which can improve the deposition efficiency of the extracellular matrix, thereby improving the interface quality between the newly formed bone tissue and the prosthesis. The rough texture can guide cell migration and directional proliferation in the microenvironment, helping osteoblasts to form stable attachment areas on the surface and expand along the microstructural paths. At the same time, such micro-configurations can enhance the adsorption and deposition ability of calcium phosphate components, promoting the bone mineralization process.

[0062] In addition, the roughened layer 600 also brings certain advantages in terms of mechanical properties, which can enhance the mechanical interlocking effect at the contact interface between the prosthesis and the bone tissue, thereby improving the initial stability and suppressing the tendency of micromotion. The mandibular region will bear complex tensile forces, shear forces and cyclic loads caused by chewing after surgery. If the contact interface is too smooth, displacement accumulation is likely to occur during repeated loading. The surface microstructure forms an "interlocking effect" between the bone bed and the prosthesis, increasing the interface friction, thereby restricting micromotion and reducing the probability of early prosthesis loosening. This structural support is of positive significance for maintaining the coherence of the bone integration process, helping to improve the long-term stability after implantation and making the use safer.

[0063] In some embodiments, the left prosthesis module 100, the right prosthesis module 200 and the fixing screw 800 are all made of polyetheretherketone (PEEK) material.

[0064] The left prosthesis module 100, the right prosthesis module 200 and the fixing screw are all made of polyetheretherketone (PEEK) material, which generally improves the biocompatibility of the prosthesis and helps to reduce the probability of postoperative rejection. As a stable medical polymer material, PEEK shows good biocompatibility in the long-term implantation environment. It does not release harmful ions after implantation and will not have adverse chemical reactions with human tissues, and can maintain a relatively stable physiological state at the tissue interface. By uniformly using this material in the left and right prosthesis modules and the fixing screw, the interface mismatch between different materials can be avoided, and the potential risks of microstimulation or tissue hyperplasia can be reduced, thus helping to improve the tissue tolerance during long-term use.

[0065] At the same time, PEEK material has both high mechanical strength and low elastic modulus. While maintaining the structural stability, its mechanical properties are closer to natural bone tissue. Metal prostheses often cause insufficient load on the surrounding bone tissue due to their too high modulus, which in turn leads to problems such as bone resorption or osteoporosis. The elastic modulus of PEEK is similar to that of cortical bone, which can achieve more balanced load transfer and enhance the bone tissue's ability to reconstruct under physiological stress. Applying this material to the left prosthesis module 100 and the right prosthesis module 200 and maintaining material consistency in the fixing screw can reduce the stiffness difference between different components, improve the overall force distribution of the prosthesis, and thus reduce local stress concentration.

[0066] During the postoperative management process, PEEK materials also have imaging advantages, which can effectively reduce the interference of metal artifacts on postoperative evaluation. Different from metal materials such as titanium alloy, PEEK appears as a low-density or semi-transparent structure in imaging examinations such as CT and MRI, and is not prone to generating occlusion or halo artifacts, facilitating doctors to observe the status of tissues around the prosthesis. By clearly presenting the bone integration situation, peripheral soft tissue changes, or the presence of local infections in the implanted area, it can provide more intuitive and accurate imaging evidence for postoperative follow-up, improving the scientific nature of clinical evaluation and the convenience of operation.

[0067] When forming the roughened treatment layer 600 on the outer surfaces of the left prosthesis module 100 and the right prosthesis module 200, it can be achieved according to the forming stage of 3D printing or CNC precision machining, combined with surface microstructure construction processes such as laser micro-etching or sandblasting. The specific method is as follows: After the initial forming of the prosthesis surface, first perform degreasing, cleaning, and drying treatments on its outer surface, and then form regular or irregular concave and convex microstructures on the surface through laser scanning, or use the sandblasting method to impact the PEEK surface at high speed with tiny ceramic particles to form a uniform micron-level rough surface. If the laser microstructure process is adopted, it is recommended to use a fiber laser with a power of 10W - 20W and a wavelength of 1064nm, and control the scanning speed at 150 - 300mm per second to form a microstructure texture with a depth of 10 - 30μm and a spacing of 20 - 100μm. This roughened layer treatment process is integrally formed with the prosthesis body material, without the need for additional coatings or bonding, and the process is stable and highly controllable.

[0068] In order to meet the functional requirements of bone integration and tissue attachment in clinical practice, the roughened treatment layer 600 should have a specific range of surface parameters. Observed through a scanning electron microscope (SEM), the roughened surface should present a three-dimensional structure with micron-level pits and protrusions arranged alternately, and the surface roughness Ra value should be controlled between 2μm and 8μm, with an optimal value of about 4μm, which can effectively improve the adhesion rate and expansion activity of osteoblasts. At the same time, this layer should not have sharp edges or protrusions to avoid the risk of mechanical damage when contacting the surrounding soft tissues after surgery. The above parameter range and process methods can guide those skilled in the art to select appropriate methods to construct the roughened treatment layer 600 that meets the requirements under different production conditions.

[0069] In some embodiments, as Figure 5 shown, a transition structure area 700 is provided between the porous structure part 300 and the solid structure area 500. The transition structure area 700 is provided with a plurality of through holes 710. The through holes 710 are perforations penetrating the thickness direction of the prosthesis. The aperture of the through holes 710 is smaller than the aperture of the double-ended guiding holes 310 in the porous structure part 300, and the aperture of the through holes 710 gradually decreases from the side close to the porous structure part 300 to the side close to the solid structure area 500.

[0070] In the above embodiments, by providing a transition structure region 700 between the porous structure portion 300 and the solid structure region 500 and forming a through-hole 710 penetrating the thickness direction in this region, it helps to achieve a smooth transition in structural function from a high-porosity region to a dense region, reducing the stress concentration phenomenon caused by sudden stiffness changes at different structural interfaces. The porosity characteristics of the porous structure portion 300 are relatively obvious, while the solid structure region 500 is a continuous non-porous region. If directly spliced, it is easy to cause problems of mechanical discontinuity at the interface between the two. In this embodiment, by introducing the transition structure region 700 and distributing a number of through-holes 710 therein, the overall porosity shows a gradient change in space, making the structural transition natural and coordinated, and thus helping to enhance the mechanical stability and fatigue tolerance performance of the prosthesis in a long-term loaded environment. The distribution of the through-holes 710 in the transition structure region 700 in this embodiment adopts an arrangement with gradually decreasing pore diameters, with the size being larger at one end close to the porous structure portion 300 and gradually narrowing towards the solid structure region 500. This structure forms a directional migration path for cells and nutrients in space, providing a basis for the hierarchical extension of biological functions. The end close to the porous structure portion has a larger pore diameter, which can create convenient conditions for the entry of osteoblasts and new blood vessels; as the pore diameter gradually decreases, cells gradually penetrate along the through-holes 710 towards the solid region, realizing continuous support from the bone-bonding region to the structure-fixing region. This transitional channel design not only provides structural support for the cell attachment and migration process, but also can extend the residence time of cells in the channel, enhance the local osteogenic activity, and help to form a more balanced and stable fusion interface between the prosthesis and the mandible. Moreover, the through-holes 710 provided in the transition structure region 700 penetrate the entire thickness direction of the prosthesis, and combined with their arrangement of decreasing pore diameters from large to small, they can form a structural unit with a "filter layer" characteristic in function. This channel can form a certain restriction on the penetration of surrounding non-target tissues or foreign bodies while maintaining internal penetration unobstructed. Especially on the side close to the solid structure region, the smaller pore diameter section effectively blocks fibrous tissues, impurities or other adverse factors that may affect biological integration, reducing the risk of the porous region being disturbed or contaminated. This structural characteristic not only helps to optimize the microenvironment inside the porous structure portion 300, but also can improve the physiological stability of the prosthesis-tissue interface after implantation, enhancing the biological adaptation performance of the structure during long-term use.

[0071] In addition, the continuity of the geometric configuration of the through-holes 710 and the gradient transition of the hole diameters can strengthen the interfacial connection effect between the porous structure part 300 and the solid structure area 500. Different from the completely separated pore and solid boundaries, this transition region constructs a "physiological buffer zone" inside the prosthesis, which plays a connecting and coordinating role in the processes of tissue growth and mechanical conduction. During the process of cells passing through the large-pore section and entering the narrowing area, their behavior patterns and arrangement manners gradually change, thereby improving the interfacial adaptability and reducing the stress concentration caused by structural mutations. Generally speaking, this gradually changing through-hole design shows significant advantages in both tissue biology and structural mechanics aspects, providing important support for the long-term stable fusion of the prosthesis.

[0072] In some embodiments, the splicing end faces where the tenon part 410 and the mortise part 420 are located are mutually matching spatial arc surface structures. Guiding grooves and positioning ribs are respectively arranged on the corresponding arc surfaces of the tenon part 410 and the mortise part 420. The guiding grooves and the positioning ribs are in sliding fit with each other during the plugging process and can be used to guide the plugging direction.

[0073] In the above embodiments, the splicing end faces where the tenon part 410 and the mortise part 420 are located are designed as mutually matching spatial arc surface structures, which helps to achieve a more fitting cooperation mode between the left prosthesis module 100 and the right prosthesis module 200, and guides the docking direction during the plugging process, improving the overall registration accuracy of the prosthesis. Compared with the traditional planar plugging structure, the three-dimensional curved surface geometric shape of the spatial arc surface has certain self-positioning properties. During the assembly process, a curvature contact between surfaces is formed between the two arc surfaces, which can actively guide the modules to fit and achieve plugging connection.

[0074] Meanwhile, in this embodiment, guiding grooves and positioning ribs are further arranged on the spatial arc surface structure. The two form a sliding fit relationship during the plugging action, making the assembly process between the modules smoother and more reliable. The positioning ribs can slide into the guiding grooves along the path, and complete the module docking through a way similar to "track guiding", thereby being able to reduce the plugging error caused by limited intraoperative vision or narrow operating space, which can simplify the intraoperative assembly operation and has a certain promoting effect on improving the surgical efficiency.

[0075] The usage method of the integrated splicable porous mandibular implant prosthesis provided by the embodiment of the present application during the operation is as follows: Before the operation is officially carried out, the doctor needs to complete the preoperative evaluation based on the patient's three-dimensional mandibular imaging data, and use the modeling software to complete the customized modeling of the left prosthesis module 100 and the right prosthesis module 200. The overall prosthesis is made of polyetheretherketone (PEEK) material, which has excellent biocompatibility and moderate elastic modulus, and can better match the mechanical properties of bone tissue. The middle area of ​​the left prosthesis module 100 and the right prosthesis module 200 is provided with a porous structure part 300, which is evenly distributed inside a plurality of double-ended guide holes 310, and a through passage is formed through the connecting channel. The gradient hole structure design of each double-ended guide hole 310 is conducive to the directional growth of bone cells and the internal and external circulation of tissue fluid. During the operation stage, the doctor first debride the defect area to expose the residual edge of the mandible, and trim the bone bed according to the specific situation to provide a stable bone support surface for the fitting placement of the prosthesis.

[0076] Subsequently, the doctor places the left prosthesis module 100 and the right prosthesis module 200 into the mandibular defect area according to the direction of preoperative planning, so that the porous structure part 300 is positioned toward the bone tissue contact surface, and the hole is as close to the mandibular surface as possible to facilitate tissue introduction. The two modules are mechanically connected through the tenon part 410 and the mortise part 420. The plug-in action is guided by the spatial arc surface structure provided on the splicing end face. As the tenon part 410 is gradually inserted to the terminal position, the stop boss 431 at its tail end and the lock groove 432 on the inner wall of the mortise part 420 form a bite fit to achieve limited clamping, thereby structurally limiting the relative movement between the modules in the axial and rotational directions, making the overall connection more stable.

[0077] After completing the splicing connection of the left and right modules, the doctor uses several fixing holes 510 arranged on the solid structure area 500 for screw fixation. The screws are implanted into the mandibular bone area through the fixing holes 510 to further enhance the overall stability between the prosthesis and the mandible. The fixing holes 510 are located in the dense structure area at the edge of the prosthesis, avoiding the porous area in the middle, reducing the risk of damage to the channel structure, and improving the mechanical reliability of screw fixation. After all the screws are fixed, the doctor needs to check whether the prosthesis contour fits the mandibular morphology, whether the splicing position is stable, and complete the soft tissue suture after confirming that there is no looseness or dislocation. In the postoperative stage, bone cells and microvessels can gradually extend and grow along the double-ended guide holes 310 in the porous structure part 300 and the internal dendritic connecting channels, promote the biological integration process between the prosthesis and bone tissue, and help rebuild the function and morphology of the mandible.

[0078] During the actual operation, in order to successfully complete the implantation of the one-piece, splicable, porous mandibular implant prosthesis and improve the stability of the postoperative structure, the following aspects should be noted.

[0079] First, before installing the prosthesis, the mandibular defect area should be thoroughly cleaned to remove the covering soft tissue and expose the complete bone bed, so that the porous structure parts 300 of the left prosthesis module 100 and the right prosthesis module 200 can be fully attached to the bone tissue surface. This direct contact relationship helps to provide a biological channel for bone cells to enter the pores and promote early bone integration. Incomplete debridement or residual soft tissue may hinder the tissue growth path and affect the pore permeability.

[0080] When performing the splicing operation between the left prosthesis module 100 and the right prosthesis module 200, the plugging action should be slowly advanced along the direction defined by the spatial arc surface structure of the splicing end face. The guiding cooperation between the tenon part 410 and the mortise part 420 should be kept smooth to avoid affecting the meshing accuracy between the stop boss 431 and the locking groove 432 due to the deviation of the plugging angle. It is recommended to use microsurgical instruments for fine alignment during the plugging process. During the entire plugging process, excessive force or repeated plugging and unplugging should be avoided to prevent deformation or fatigue wear of the connection structure, which may affect the subsequent locking tightness and the mechanical stability of the splicing part.

[0081] In the screw fixation stage, a pre-drilling operation should be carried out at the position of the fixing hole 510 according to the pre-operative designed drilling direction. The fixing hole 510 is set in the solid structure area 500. Medium-length screws should be preferably selected, which can not only be embedded in the bone mass to achieve stable implantation but also avoid penetrating the bone plate to cause unnecessary damage. It is recommended to install the screws sequentially from near the splicing connection part 400 to both ends of the prosthesis to achieve uniform force distribution and reduce local stress concentration. To improve the connection reliability, the repeated disassembly and assembly of the module should be minimized during the operation to reduce the mechanical fatigue of the limit clamping structure 430. In the postoperative stage, it is recommended to provide soft diet management for the patient in the initial recovery period to reduce the chewing load, slow down the compression degree of the porous structure part 300, and provide a relatively stable physiological environment for the growth of bone cells through the double-end guiding holes 310 and the connecting channels. By reasonably implementing the above intraoperative and postoperative precautions, it helps to improve the biological adaptability and implantation stability of the prosthesis and enhance the practical value of this embodiment in the clinical application of mandibular reconstruction.

[0082] Finally, it should be noted that the above embodiments are only used to illustrate the technical solutions of the present application, rather than to limit it; although the present application has been described in detail with reference to the foregoing embodiments, those of ordinary skill in the art should understand that they can still modify the technical solutions described in the foregoing embodiments, or perform equivalent replacements on some or all of the technical features; and these modifications or replacements do not make the essence of the corresponding technical solutions deviate from the scope of the technical solutions of the embodiments of the present application.

Claims

1. An integrated spliceable porous mandibular implant prosthesis, characterized in that, It includes a left prosthesis module, a right prosthesis module, a splicing connection part and a porous structure part. The left prosthesis module and the right prosthesis module are detachably connected through the splicing connection part to form an integral structure; In the middle main body regions of the left prosthesis module and the right prosthesis module, porous structure parts are respectively arranged. A plurality of double-ended guiding holes are uniformly arranged on the porous structure parts. Each double-ended guiding hole forms independent orifices on the front surface and the rear surface of the prosthesis module respectively, and the front and rear orifices are interconnected through a communication channel arranged inside the porous structure part; The splicing connection part includes a tenon part arranged on the left prosthesis module and a mortise part arranged on the right prosthesis module. The tenon part is inserted into the mortise part to achieve mechanical plug-in fit; The splicing connection part is provided with a limit clamping structure for preventing loosening between the left prosthesis module and the right prosthesis module after plugging; A plurality of fixing holes are respectively arranged on the left prosthesis module and the right prosthesis module. The fixing holes are arranged in the edge solid structure regions of the left and right prosthesis modules and are used to cooperate with fixing screws to fix the prosthesis to the patient's mandible.

2. The one-piece spliceable porous mandibular implant prosthesis according to claim 1, characterized in that, The double-ended guiding holes of the porous structure part have a gradient hole structure, and the opening diameter of the double-ended guiding hole on the front surface of the prosthesis module is smaller than the opening diameter on the rear surface of the prosthesis module.

3. The integrated spliceable porous mandibular implant prosthesis according to claim 2, wherein The opening diameter of the double-ended guiding hole on the rear surface of the prosthesis module is 300-600 microns, and the aperture of the double-ended guiding hole on the front surface of the prosthesis module is 50-150 microns.

4. The one-piece spliceable porous mandibular implant prosthesis according to any one of claims 1-3, characterized in that, The communication channels are distributed in a dendritic structure inside the porous structure part.

5. The one-piece spliceable porous mandibular implant prosthesis according to claim 4, characterized in that, The limit clamping structure includes a stop boss arranged at the tail end of the tenon part and a locking groove arranged on the inner wall of the mortise part. After the tenon part of the limit clamping structure is plugged into the mortise part, the stop boss is clamped and matched with the locking groove.

6. The one-piece spliceable porous mandibular implant prosthesis according to claim 1, wherein The edges of the left prosthesis module and the right prosthesis module are provided with solid structure areas outside the porous structure part, and the fixing holes are opened on the solid structure areas.

7. The integrated spliceable porous mandibular implant prosthesis according to claim 4, characterized in that, The outer surfaces of the left prosthesis module and the right prosthesis module are provided with a roughened treatment layer for improving the bone cell attachment performance.

8. The one-piece spliceable porous mandibular implant prosthesis according to claim 1, characterized in that, The left prosthesis module, the right prosthesis module and the fixing screws are all made of polyether ether ketone (PEEK) material.

9. The one-piece spliceable porous mandibular implant prosthesis according to claim 6, characterized in that, A transition structure area is arranged between the porous structure part and the solid structure area. The transition structure area is provided with a plurality of through holes. The through holes are perforations penetrating the thickness direction of the prosthesis. The aperture of the through holes is smaller than the aperture of the double-ended guiding holes in the porous structure part, and the aperture of the through holes gradually decreases from the side close to the porous structure part to the side close to the solid structure area.

10. The one-piece spliceable porous mandibular implant prosthesis according to claim 5, characterized in that, The splicing end surfaces where the tenon part and the mortise part are located are mutually matching space arc surface structures. Guiding grooves and positioning ribs are respectively arranged on the corresponding arc surfaces of the tenon part and the mortise part. The guiding grooves and the positioning ribs slide and cooperate with each other during the plugging process and can be used to guide the plugging direction.

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