Titanium-zinc mixed structure type degradable jawbone restoration

Abstract

A titanium-zinc mixed structure type degradable jaw bone restoration comprises a titanium alloy force bearing part and a zinc alloy planting part which are printed in a 3D mode, and the titanium alloy force bearing part and the zinc alloy planting part are connected through a connecting part located on the titanium alloy force bearing part and / or the zinc alloy planting part. The titanium alloy part serving as the base is mainly used for bearing force, it is guaranteed that the prosthesis cannot be broken in the using process, the zinc alloy of the upper half part is absorbed in the osteogenesis regulating and controlling process, then bony repair is completed, and planting can be conducted. And the height of the preferable zinc alloy planting part is enough for planting, and meanwhile, the titanium alloy at the lower half part does not influence final planting and can ensure the overall stability.

Description

Technical Field

[0001] The present invention belongs to the clinical field of oral and maxillofacial surgery, and particularly relates to a titanium-zinc hybrid degradable jaw repair body. Background Art

[0002] For the repair of segmental jaw defects, the existing technology mostly uses autologous bone transplantation or titanium alloy repair bodies in clinical practice. Autologous bone transplantation has become the preferred material for jaw defect repair at present because of its good biocompatibility and the possibility of subsequent implant denture repair. However, it requires surgical resection of autologous bone, which increases the surgical trauma. Titanium alloy materials are increasingly widely used in the field of organ defect repair due to their excellent biocompatibility and mechanical properties. Titanium-based biomaterials mainly composed of pure titanium or titanium alloy have become the preferred materials for fixing jaw defect repair at present and can partially replace autologous bone repair. However, from the perspective of clinical needs, the load-bearing part of titanium alloy is non-absorbable and cannot achieve complete osteogenesis replacement of autologous bone. Therefore, teeth cannot be directly implanted on the load-bearing part of titanium alloy.

[0003] Zinc alloy is a degradable metal with good biocompatibility. At present, many studies have applied it in vivo in the hope of replacing titanium alloy materials. However, its in vivo degradation rate is relatively slow and does not match the regeneration rate of the jaw. Although its in vivo degradation rate can be regulated through the design of the microstructure, there is still a gap from the actual clinical needs at present. In addition, the strength of zinc alloy is insufficient, it is difficult to withstand the complex chewing force of the jaw, and it is easy to deform and break, and it cannot repair large-segment defects of the jaw. Summary of the Invention

[0004] In order to solve the above problems of the existing technology, the present invention proposes a titanium-zinc hybrid degradable jaw repair body.

[0005] The specific solution of the present invention is as follows:

[0006] A titanium-zinc hybrid degradable jaw repair body, characterized in that it includes a 3D printed titanium alloy load-bearing part and a zinc alloy implant part, and the titanium alloy load-bearing part and the zinc alloy implant part are connected by a connecting part located on the titanium alloy load-bearing part and / or the zinc alloy implant part.

[0007] Preferably, in terms of mass fraction, Li in the zinc alloy is 0.4%-0.6%, Ni is 4.0%-6.0%, Ti is 3.5%-4.5%, P is 0.01%-0.1%, and Ca is 0.1%-1.0%.

[0008] Preferably, the height of the zinc alloy load-bearing part is 1-2 cm, the height of the titanium alloy implant part is 0.5-1 cm, and the height ratio of the zinc alloy implant part to the titanium alloy load-bearing part is 2:1-4:1.

[0009] Preferably, the connecting portion includes a protrusion extending from the bottom of the zinc alloy planting portion and a corresponding groove located at the titanium alloy forming portion.

[0010] Further preferably, the number of the connecting parts is 2-20, and the slots have a height of 0.1-0.5 cm and a diameter of 0.1-0.5 cm.

[0011] Preferably, the structure of the titanium alloy bearing part and the zinc alloy implant part is a porous structure, and the mesh structure is a diamond-shaped, regular hexahedron, regular dodecahedron and / or bionic structure.

[0012] More preferably, the pore size of the titanium alloy bearing part is 100-400 μm, the wire diameter is 0.3-0.5 mm, the pore size of the zinc alloy planting part is 400-800 μm, the wire diameter is 0.1-0.3 mm,

[0013] Preferably, it further comprises an alloy jaw connecting piece, wherein the alloy jaw connecting piece comprises an alloy side and a jaw side, and each side has a screw hole.

[0014] Further preferably, the alloy side has four screw holes, and the jawbone side has one screw hole.

[0015] Preferably, at least four alloy jaw connecting plates are included, which are respectively located on both sides of the titanium alloy load-bearing part and the zinc alloy implant part.

[0016] The beneficial effects of the present invention are as follows:

[0017] The present invention provides a 3D printed restoration of a titanium and zinc composite. First, the load-bearing part of the titanium alloy is 3D printed, and then the zinc alloy powder is replaced. On the basis of the titanium alloy, the zinc alloy part is printed, and the two are formed into a whole through the connecting part. The titanium alloy part as the base is mainly used to bear the load to ensure that the restoration will not break during use. The zinc alloy in the upper part is absorbed at the same time during the process of regulating osteogenesis, and then the bone repair is completed and can be implanted. The height of the preferred zinc alloy implant part of the present invention is sufficient for implantation, and the titanium alloy in the lower part will not affect the final implantation and can ensure the overall stability.

[0018] The purpose of restoration structure design is to regulate the degradation rate of zinc alloy so that its degradation rate is consistent with the rate of jaw regeneration.

[0019] The pore size design can be filled with composite osteogenic active materials to promote osteogenic repair.

[0020] Due to the presence of the supporting part, the selection of the alloy components can focus on improving non-mechanical properties such as adjusting degradation uniformity and reducing local corrosion.

[0021] The zinc alloy planting part preferably has a relatively larger pore diameter and a smaller wire diameter, which is beneficial for absorption. The titanium alloy bearing part has a slightly larger wire diameter to better bear the weight. BRIEF DESCRIPTION OF THE DRAWINGS

[0022] Figure 1 is an overall schematic diagram of an embodiment of the present invention;

[0023] Figure 2 is a partial schematic diagram of the connecting part in a separated state;

[0024] Figure 3 is a schematic cross-sectional view of the connecting part.

[0025] The reference numerals in the drawings are listed as follows:

[0026] 1 - titanium alloy bearing part, 2 - zinc alloy planting part, 3 - protrusion, 4 - card slot, 5 - alloy jawbone connecting piece, 6 - screw hole. DETAILED DESCRIPTION OF THE INVENTION

[0027] The present invention will be further described below with reference to the drawings and embodiments.

[0028] Embodiment 1

[0029] As Figures 1-3 shown, a titanium-zinc hybrid degradable jawbone repair body in this embodiment includes a titanium alloy bearing part 1, a zinc alloy planting part 2, and a connecting part located between the titanium alloy bearing part 1 and the zinc alloy planting part 2. The connecting part includes a protrusion 3 extending from the bottom of the zinc alloy planting part 2 and a corresponding card slot 4 located in the titanium alloy bearing part. First, the titanium alloy bearing part 1 is 3D printed, and then the zinc alloy powder is replaced. On the basis of the titanium alloy bearing part 1, the zinc alloy planting part 2 is printed, and the two form an integral body through the connecting part.

[0030] In terms of mass fraction, Li in the zinc alloy is 0.4%, Ni is 6.0%, Ti is 4.5%, P is 0.05%, and Ca is 0.2%. The titanium alloy can be the titanium alloy commonly used in current medical treatment.

[0031] The zinc alloy bearing part 1 has a height of 1 cm, and the titanium alloy planting part 2 has a height of 0.5 cm.

[0032] The number of the connecting parts is 12, Figure 2 、 3 and a part is schematically shown. The height of the card slot is 0.2 cm and the diameter is 0.1 cm. <9000076>The structures of the titanium alloy load-bearing part 1 and the zinc alloy implant part 2 are porous structures, and the mesh structures are mainly various polyhedrons in the shape of a rhombus. The pore diameter of the titanium alloy load-bearing part 1 is about 150 μm, and the wire diameter is about 0.4 mm. The pore diameter of the zinc alloy implant part is about 700 μm, and the wire diameter is about 0.15 mm.

[0034] It also includes four alloy jaw connecting pieces 5, which are respectively located on both sides of the titanium alloy load-bearing part 1 and the zinc alloy implant part 2. The alloy jaw connecting piece 5 includes an alloy side and a jaw side. The alloy side has four screw holes 6, and the jaw side has one screw hole 6.

[0035] Example 2

[0036] The overall structure of this example is the same as that of Example 1. In terms of mass fraction, Li in the zinc alloy is 0.6%, Ni is 4.0%, Ti is 3.5%, P is 0.08%, and Ca is 0.2%.

[0037] The height of the zinc alloy load-bearing part 1 is 2 cm, and the height of the titanium alloy implant part 2 is 0.5 cm.

[0038] The number of the connecting parts is 8. Figure 2 、 3 The part shown schematically in. The height of the card slot is 0.4 cm, and the diameter is 0.3 cm.

[0039] The structures of the titanium alloy load-bearing part 1 and the zinc alloy implant part 2 are porous structures. The pore diameter of the titanium alloy load-bearing part 1 is about 350 μm, and the wire diameter is about 0.4 mm. The pore diameter of the zinc alloy implant part is about 500 μm, and the wire diameter is about 0.15 mm.

[0040] Through clinical trials, the above examples have completed tooth implantation on the zinc alloy implant part, achieved complete osteogenic replacement of the large segmental defect of the jawbone with autologous bone, and there is no deformation or fracture during normal use, meeting the clinical requirements.

[0041] It should be noted that the above specific embodiments can enable those skilled in the art to understand the present invention more comprehensively, but do not limit the present invention in any way. Therefore, although this specification has described the present invention in detail with reference to the drawings and embodiments, those skilled in the art should understand that the present invention can still be modified or equivalently replaced. In short, all technical solutions and their improvements that do not depart from the spirit and scope of the present invention should be covered by the protection scope of the patent of the present invention.

Claims

1. A titanium-zinc mixed structure degradable jawbone repair body, characterized in that It includes a 3D-printed titanium alloy load-bearing part and a zinc alloy implant part, and the titanium alloy load-bearing part and the zinc alloy implant part are connected through a connecting part located on the titanium alloy load-bearing part and / or the zinc alloy implant part.

2. The prosthesis according to claim 1, wherein In the zinc alloy by mass fraction, Li is 0.4%-0.6%, Ni is 4.0%-6.0%, Ti is 3.5%-4.5%, P is 0.01%-0.1%, and Ca is 0.1%-1.0%.

3. The prosthesis according to claim 1, wherein The height of the zinc alloy load-bearing part is 1-2 cm, the height of the titanium alloy implant part is 0.5-1 cm, and the height ratio of the zinc alloy implant part to the titanium alloy load-bearing part is 2:1-4:

1.

4. The prosthesis according to claim 1, wherein The connecting part includes a protrusion extending from the bottom of the zinc alloy implant part and a corresponding card slot located on the titanium alloy load-bearing part.

5. The prosthesis according to claim 4, wherein the number of the connecting parts is 2-20, the height of the card slot is 0.1-0.5 cm, and the diameter is 0.1-0.5 cm.

6. The prosthesis according to claim 1, wherein The structures of the titanium alloy load-bearing part and the zinc alloy implant part are porous structures, and the mesh structures are diamond-shaped, regular hexahedron, regular dodecahedron and / or bionic structures.

7. The prosthesis according to claim 6, wherein The pore diameter of the titanium alloy load-bearing part is 100-400 μm, and the wire diameter is 0.3-0.5 mm. The pore diameter of the zinc alloy implant part is 400-800 μm, and the wire diameter is 0.1-0.3 mm.

8. The prosthesis according to claim 1, characterized in that It further includes an alloy jaw connecting piece, which includes an alloy side and a jaw side, and each side has screw holes respectively.

9. The prosthesis according to claim 8, wherein The alloy side has four screw holes, and the jaw side has one screw hole.

10. The prosthesis according to claim 8, characterized in that There are at least four of the alloy jaw connecting pieces, which are respectively located on both sides of the titanium alloy load-bearing part and the zinc alloy implant part.

Images