Lumbar fusion device

Abstract

The utility model relates to the technical field of medical instruments, and provides a lumbar vertebra fusion device which comprises a magnesium-calcium alloy fusion cage and a magnesium fluoride coating, the magnesium fluoride coating wraps the surface of the magnesium-calcium alloy fusion cage, and the magnesium-calcium alloy fusion cage is used for being implanted into an intervertebral space. The lumbar fusion device provided by the utility model is used for overcoming the defects of high elastic modulus and insufficient biological activity of a fusion device in the prior art, and due to the arrangement of the magnesium-calcium alloy fusion device, the biocompatibility and the degradability of magnesium are reserved, and the mechanical property and the degradation behavior are optimized through the introduction of the calcium element. The magnesium fluoride coating is arranged, so that the degradation rate of the magnesium-calcium alloy can be slowed down, and the synostosis efficiency can be remarkably improved.

Description

TECHNICAL FIELD

[0001] The utility model relates to medical instrument technical field, especially a lumbar fusion device. BACKGROUND

[0002] In the field of orthopedic implant devices, fusion cages made of metal materials are generally used. However, the existing metal material intervertebral fusion cage has a significantly higher elastic modulus than human bone tissue, which easily causes stress shielding effect, leading to bone resorption and fusion cage subsidence problems. The prior art provides an artificial synthetic polyether ether ketone (PEEK) material to solve the above problems. Although the polyether ether ketone material can reduce the elastic modulus, it has insufficient surface bioactivity, making it difficult to achieve good bone-implant interface bonding and affecting the bone integration efficiency. SUMMARY

[0003] The utility model provides a lumbar fusion device to solve the defects of high elastic modulus and insufficient bioactivity of the fusion cage in the prior art. The magnesium-calcium alloy fusion cage not only retains the biocompatibility and degradability of magnesium, but also optimizes the mechanical properties and degradation behavior by introducing calcium elements. The magnesium fluoride coating can slow down the degradation rate of the magnesium-calcium alloy and significantly improve the efficiency of bone integration.

[0004] The lumbar fusion device provided by the utility model comprises a magnesium-calcium alloy fusion cage and a magnesium fluoride coating, the magnesium fluoride coating is wrapped on the surface of the magnesium-calcium alloy fusion cage, and the magnesium-calcium alloy fusion cage is used for implanting into the intervertebral space.

[0005] The lumbar fusion device provided by the utility model further comprises a bioactive layer, and the bioactive layer is wrapped on the surface of the magnesium fluoride coating.

[0006] The bioactive layer of the lumbar fusion device provided by the utility model comprises a polylactic acid coating.

[0007] The bioactive layer of the lumbar fusion device provided by the utility model comprises a calcium phosphate layer.

[0008] The lumbar fusion device provided by the utility model further comprises a fixing plate and a locking piece, the fixing plate is arranged at one end of the magnesium-calcium alloy fusion cage and can rotate relative to the magnesium-calcium alloy fusion cage, the locking piece is arranged in the fixing plate, and the locking piece is used for limiting the position of the fixing plate relative to the magnesium-calcium alloy fusion cage.

[0009] The end of the magnesium-calcium alloy fusion cage is provided with a first mounting portion and a second mounting portion.

[0010] The fixing plate is provided with a positioning part and a limiting part on one side of the magnesium-calcium alloy fixing device, the positioning part is rotationally matched with the first mounting part, the locking part is arranged in the positioning part, and the locking part is used for limiting the position of the positioning part relative to the first mounting part along the rotation radial direction;

[0011] The limiting part and the second mounting part correspond to each other, and the limiting part and the second mounting part are used for limiting the position of the fixing plate relative to the magnesium-calcium alloy fixing device along the rotation circumferential direction.

[0012] According to the lumbar fusion device provided by the utility model, the second mounting part comprises an arc-shaped rack, and the arc-shaped rack is arranged in the rotation circumferential direction;

[0013] The limiting part comprises at least one protrusion and / or notch matched with the arc-shaped rack.

[0014] According to the lumbar fusion device provided by the utility model, the second mounting part is provided with two second mounting parts, the two second mounting parts are symmetrically arranged on the two sides of the first mounting part, and the number and position of the limiting part correspond to the number and position of the second mounting part.

[0015] According to the lumbar fusion device provided by the utility model, the first mounting part comprises an arc-shaped groove, and the arc-shaped groove is arranged in the rotation circumferential direction;

[0016] The positioning part comprises a first cantilever and a second cantilever, the first cantilever and the second cantilever are arranged at intervals and arranged in the arc-shaped groove, the locking part is arranged between the first cantilever and the second cantilever, and the locking part is used for adjusting the interval between the first cantilever and the second cantilever.

[0017] According to the lumbar fusion device provided by the utility model, the first mounting part further comprises an arc-shaped ring groove, the arc-shaped ring groove is arranged in the rotation circumferential direction and located on the inner side of the arc-shaped groove, and the arc-shaped groove and the arc-shaped ring groove are communicated;

[0018] The end of at least one of the first cantilever and the second cantilever is provided with a hook, and the hook is slidably arranged in the arc-shaped ring groove.

[0019] The magnesium-calcium alloy financial instrument is provided with magnesium-calcium alloy, and the magnesium-calcium alloy has the biocompatibility and the degradability of magnesium and the mechanical property and the degradation behavior of calcium.

[0020] Further, although the pure magnesium or the magnesium alloy with high calcium content has the degradation property, the degradation rate is too fast, which can cause the financial instrument to lose the supporting function too early, and the traditional calcium-phosphorus coating can delay the degradation, but the porous structure is easily penetrated by the body fluid, and the protection effect is unstable.

[0021] Compared with the financial instrument made of polyether ether ketone material in the prior art, the lumbar interbody fusion cage provided by the utility model has the advantages that the active degradation product of the magnesium-calcium alloy can directly participate in bone metabolism and promote the interface bone integration, and the magnesium fluoride coating can slow down the degradation rate of the magnesium-calcium alloy, so that the financial instrument can maintain sufficient mechanical support during the key period of bone fusion, and then gradually degrades synchronously with the new bone formation rate, thereby significantly improving the efficiency of bone integration. BRIEF DESCRIPTION OF DRAWINGS

[0022] In order to more clearly illustrate the technical solutions of the utility model or the prior art, the following will briefly introduce the drawings needed to be used in the embodiment or the prior art description.

[0023] Figure 1 is the axial side structure schematic view of the lumbar interbody fusion device provided by the utility model embodiment.

[0024] Figure 2 is the axial side schematic view of the magnesium-calcium financial instrument provided by the utility model embodiment.

[0025] Figure 3This is a schematic diagram of the axial structure of the fixing plate and locking component provided in this embodiment of the utility model.

[0026] Figure 4 This is a cross-sectional structural diagram of the magnesium-calcium alloy fusion device provided in this embodiment of the utility model.

[0027] Figure 5 This is a side view of the fixing plate and locking component provided in an embodiment of this utility model.

[0028] Figure label:

[0029] 100: Magnesium-calcium alloy fusion device; 110: First mounting part; 111: Arc-shaped groove; 112: Arc-shaped annular groove; 120: Second mounting part; 121: Arc-shaped rack;

[0030] 200: Fixing plate; 210: Positioning part; 211: First cantilever; 212: Second cantilever; 213: Hook; 220: Limiting part; 221: Protrusion; 222: Notch; 300: Locking part. Detailed Implementation

[0031] To make the objectives, technical solutions, and advantages of this utility model clearer, the technical solutions of this utility model will be clearly and completely described below with reference to the accompanying drawings. Obviously, the described embodiments are only some embodiments of this utility model, not all embodiments. Based on the embodiments of this utility model, all other embodiments obtained by those skilled in the art without creative effort are within the protection scope of this utility model.

[0032] In the description of the embodiments of this application, it should be noted that, unless otherwise explicitly specified and limited, the terms "connected" and "linked" should be interpreted broadly. For example, they can refer to a fixed connection, a detachable connection, or an integral connection; they can refer to a mechanical connection or an electrical connection; they can refer to a direct connection or an indirect connection through an intermediate medium. Those skilled in the art can understand the specific meaning of the above terms in the embodiments of this application based on the specific circumstances.

[0033] In the embodiments of this application, unless otherwise expressly specified and limited, "above" or "below" the second feature can mean that the first feature is in direct contact with the second feature, or that the first feature is in indirect contact with the second feature through an intermediate medium. Furthermore, "above," "on top of," and "over" the second feature can mean that the first feature is directly above or diagonally above the second feature, or simply that the first feature is at a higher horizontal level than the second feature. "Below," "below," and "under" the second feature can mean that the first feature is directly below or diagonally below the second feature, or simply that the first feature is at a lower horizontal level than the second feature.

[0034] In the description of this specification, the references to terms such as "one embodiment," "some embodiments," "example," "specific example," or "some examples," etc., refer to specific features, structures, materials, or characteristics described in connection with that embodiment or example, which are included in at least one embodiment or example of the embodiments of this application. In this specification, the illustrative expressions of the above terms do not necessarily refer to the same embodiment or example. Furthermore, the specific features, structures, materials, or characteristics described may be combined in any suitable manner in one or more embodiments or examples. Moreover, without contradiction, those skilled in the art can combine and integrate the different embodiments or examples described in this specification, as well as the features of different embodiments or examples.

[0035] Figure 1 This is a schematic diagram of the axial structure of the lumbar fusion device provided in this embodiment of the utility model.

[0036] See Figure 1 This utility model provides a lumbar fusion device, which includes a magnesium-calcium alloy fusion unit 100 and a magnesium fluoride coating. The magnesium fluoride coating is wrapped around the surface of the magnesium-calcium alloy fusion unit 100. The magnesium fluoride coating can be surface fluorinated. The magnesium-calcium alloy fusion unit 100 is used for implantation into the intervertebral space.

[0037] Specifically, the manufacturing process of the magnesium-calcium alloy fusion device 100 is as follows: First, the magnesium-calcium alloy is smelted in an argon-protected environment, with the smelting temperature controlled at 700-800℃. It is understood that the inert protection of argon effectively prevents the magnesium-calcium alloy from oxidizing in the high-temperature molten state, avoiding the mixing of impurity elements (such as oxygen and nitrogen) into the alloy matrix, thereby ensuring the purity and uniformity of the material composition.

[0038] Subsequently, the molten alloy is molded at a casting temperature of 650-750℃. It is understandable that this temperature range can ensure the fluidity of the alloy to fill the mold details, while avoiding excessively high temperatures that could lead to grain coarsening and affect mechanical properties.

[0039] After forming, the alloy needs to undergo heat treatment under nitrogen protection, heating to 450-510℃ and holding for 1.5-3 hours. Understandably, this process, through recrystallization and grain boundary optimization, further enhances the alloy's toughness and fatigue resistance, making it more suitable for the long-term dynamic loads that the lumbar fusion device must withstand within the human body.

[0040] In this embodiment of the invention, the Ca content in the magnesium-calcium alloy is 0.5%-2%, with the remainder being Mg. It is understood that the addition of calcium can refine the grains and improve the alloy strength by forming the Mg2Ca phase; simultaneously, calcium can induce calcium phosphate deposition in the physiological environment, promoting bone integration. It should be noted that excessively high calcium content (e.g., >2%) will accelerate alloy degradation, while excessively low content (<0.5%) cannot effectively control the degradation rate.

[0041] It is understood that the magnesium-calcium alloy fusion device 100 in the lumbar fusion device provided in this embodiment of the invention retains the biocompatibility and biodegradability of magnesium, while optimizing mechanical properties and degradation behavior through the introduction of calcium. In a physiological environment, the magnesium-calcium alloy fusion device 100 can be gradually corroded by body fluids through controlled degradation. During this process, the released magnesium ions can promote osteoblast activity, while calcium can induce calcium phosphate deposition, directly enhancing the bonding strength of the bone-implant interface. Compared to traditional metal fusion devices (such as titanium alloys), the elastic modulus of magnesium-calcium alloy is closer to that of human cancellous bone, which can effectively reduce stress shielding effects and avoid the risk of postoperative intervertebral disc subsidence due to mechanical mismatch.

[0042] Furthermore, while pure magnesium or high-calcium magnesium alloys possess degradation characteristics, their rapid degradation rate can cause the fusion vessel to prematurely lose its supporting function. Traditional calcium-phosphorus coatings, although able to delay degradation, are susceptible to penetration by bodily fluids due to their porous structure, resulting in unstable protective effects. In this embodiment, a magnesium fluoride coating is applied to the surface of the magnesium-calcium alloy fusion vessel 100. This coating forms a dense and microporous protective layer on the magnesium-calcium alloy surface. Magnesium fluoride exhibits higher chemical stability than magnesium oxides or hydroxides, significantly delaying the corrosion of the substrate by Cl⁻ ions in bodily fluids. Secondly, the magnesium fluoride layer's microporous structure allows for slow penetration of bodily fluids and a controlled reaction with the substrate, enabling a gradual degradation reaction. This avoids the risk of "sudden failure" caused by the coating completely isolating the substrate from degradation.

[0043] Compared with polyetheretherketone (PEEK) fusion devices in the prior art, the lumbar fusion device provided in this embodiment allows the active degradation products of magnesium-calcium alloy to directly participate in bone metabolism and promote interfacial bone integration. Secondly, the magnesium fluoride coating can slow down the degradation rate of magnesium-calcium alloy to ensure that the fusion device maintains sufficient mechanical support during the critical period of bone fusion, and then gradually degrades in sync with the rate of new bone formation, which can significantly improve the efficiency of bone integration.

[0044] In an optional embodiment of this invention, a bioactive layer is further included, which is wrapped around the surface of the magnesium fluoride coating. It is understood that the bioactive layer covering the surface of the magnesium fluoride coating further optimizes the synergistic effect of bioactivity and degradation at the bone-implant interface. Specifically, the bioactive layer may be made of polylactic acid (PLA) or calcium phosphate, and is attached to the magnesium fluoride coating via electrospinning or chemical deposition.

[0045] The introduction of polylactic acid coating allows it to release lactic acid microenvironment during degradation, activating local osteoblast proliferation signaling pathways. At the same time, its degradation cycle is synchronized with the callus formation stage, which can avoid residual foreign bodies interfering with bone integration. The calcium phosphate layer can simulate the inorganic components of natural bone, directly enhance the interfacial chemical bonding strength, and promote the directional deposition of hydroxyapatite.

[0046] Compared to existing technologies such as magnesium fluoride or single calcium-phosphate coatings, this embodiment, based on the magnesium fluoride coating of the aforementioned embodiment, adds a bioactive layer to achieve layered "protection-degradation-bone growth promotion" functions: the magnesium fluoride coating acts as the bottom barrier, precisely regulating the degradation rate of the magnesium-calcium alloy; the bioactive layer acts as the outer medium, directly participating in the bone metabolism process. Specifically, the degradation product lactic acid of the polylactic acid coating can lower the local pH value, stimulating osteoblasts to secrete collagen matrix, while the calcium phosphate layer provides a mineralization template for new bone tissue. Compared to the magnesium-calcium alloy fusion device 100 without a bioactive layer, this embodiment, through the synergistic effect of the dual-layer functional coating, not only extends the mechanical support cycle but also transforms bone integration from passive contact to active induction, thus breaking the limitations of traditional biodegradable fusion devices that prioritize degradation control over bioactivity.

[0047] Continue reading Figure 1 In an optional embodiment of the present invention, the lumbar fusion device further includes a fixing plate 200 and a locking member 300. The fixing plate 200 is disposed at one end of the magnesium-calcium alloy fusion device 100 and can rotate relative to the magnesium-calcium alloy fusion device 100. The locking member 300 passes through the fixing plate 200 and is used to limit the position of the fixing plate 200 relative to the magnesium-calcium alloy.

[0048] When using it, first insert the magnesium-calcium alloy fusion piece 100 into the cone gap, then adjust the position of the fixing plate 200 relative to the magnesium-calcium alloy fusion piece 100. After the position is adjusted, lock the position of the fixing plate 200 relative to the magnesium-calcium alloy fusion piece 100 using the locking piece 300.

[0049] It is understood that, in this embodiment of the invention, the rotatable connection design between the fixation plate 200 and the magnesium-calcium alloy fusion device 100, through the dynamic adjustment and locking function of the locking element 300, significantly improves the flexibility of intraoperative operation and postoperative stability. During use, the fixation plate 200 can rotate freely around the interbody fusion device, allowing the surgeon to precisely adjust the fixation plate 200 to the oblique safe channel according to the patient's anatomical structure (such as the course of the lumbar plexus and psoas major muscle), avoiding nerve or muscle damage caused by forced implantation of traditional fixed-angle fusion devices. Compared to rigidly connected fusion devices in the prior art, the adjustable design of this embodiment allows for real-time adjustment of the fixation plate 200 angle during surgery, eliminating the need for complex positioning tools or repeated trial and error, effectively shortening surgical time and reducing operational risks.

[0050] Figure 2 This is an isometric view of the magnesium-calcium alloy fusion device provided in this embodiment of the present invention; Figure 3 This is a schematic diagram of the axial structure of the fixing plate and locking component provided in this embodiment of the utility model.

[0051] See Figures 1 to 3 In an optional embodiment of this utility model, the end of the magnesium-calcium alloy fusion device 100 is provided with a first mounting part 110 and a second mounting part 120. The fixing plate 200 is provided with a positioning part 210 and a limiting part 220 on the side facing the magnesium-calcium alloy fusion device 100. The positioning part 210 is rotatably engaged with the first mounting part 110. The locking member 300 passes through the positioning part 210 and is used to limit the position of the positioning part 210 relative to the first mounting part 110 along the rotational radial direction. That is to say, in this embodiment, the position of the positioning part 210 relative to the first mounting part 110 along the rotational radial direction (the radius of the circle drawn by the positioning part 210 with respect to the rotational center) is adjustable. It should be noted that the position along the rotational radial direction mentioned here refers to the distance of the positioning part 210 relative to the rotational center.

[0052] The second mounting portion 120 is a constraint structure at the end of the fusion unit, and its position corresponds to the limiting portion 220 of the fixing plate 200, used to limit the displacement of the fixing plate 200 along the rotational circumferential direction. Specifically, the second mounting portion 120 can be a limiting block or guide groove provided at the end of the fusion unit, and the limiting portion 220 is a snap-fit ​​structure on the fixing plate 200 that matches the limiting block / guide groove. When the fixing plate 200 rotates to the target angle, the limiting portion 220 engages with the second mounting portion 120, preventing the fixing plate 200 from further displacing along the rotational circumferential direction, ensuring the stability of the angle adjustment.

[0053] The locking member 300 passes through the positioning part 210. By tightening the locking member 300 (such as a screw), friction is generated between the contact surface of the positioning part 210 and the first mounting part 110, thereby locking the angle of the fixing plate 200. During this process, the engagement between the second mounting part 120 and the limiting part 220 further restricts the circumferential displacement of the fixing plate 200, forming a double locking mechanism.

[0054] It is understood that, through the coordinated design of the first mounting part 110, the second mounting part 120, the positioning part 210, and the limiting part 220, this utility model embodiment achieves the dual technical effects of flexible intraoperative angle adjustment and stable postoperative locking. Specifically, the rotational cooperation structure (such as a rotating shaft or hinge) of the first mounting part 110 and the positioning part 210 allows the fixation plate 200 to rotate freely around the axis of the magnesium-calcium alloy fusion device 100. During the operation, the fixation plate 200 can be adjusted to the optimal angle according to the patient's anatomical conditions (such as the course of the lumbar plexus nerves or the morphology of the intervertebral foramen), avoiding nerve or muscle damage caused by the limited implantation path of traditional fixed-angle fusion devices.

[0055] Compared to existing technologies that rely on a single screw for locking, this embodiment uses the mechanical engagement of the second mounting part 120 and the limiting part 220 (such as the engagement of the limiting block and the slot) to form a double locking mechanism after the locking member 300 is tightened: the friction force generated by the locking member 300 fixes the angle, while the engagement of the limiting part 220 and the second mounting part 120 further restricts circumferential displacement. This can effectively reduce the risk of angle reversion caused by vibration or activity after surgery.

[0056] Furthermore, the mechanical engagement design between the second mounting part 120 and the limiting part 220 ensures that even if the locking member 300 becomes slightly loose, the angle remains fixed due to the physical blocking effect of the limiting structure. Compared to the shortcomings of traditional solutions where loose screws lead to angle loss of control, the redundant locking mechanism of this embodiment significantly improves the reliability of the implant.

[0057] Continue reading Figure 2 and Figure 3 In an optional embodiment of the present invention, the second mounting part 120 includes an arc-shaped rack 121 extending along the rotational circumference. The arc-shaped rack 121 is disposed at the end of the magnesium-calcium alloy fusion device 100. The limiting part 220 includes at least one protrusion 221 or recess 222 that matches the arc-shaped rack 121. The protrusion 221 or recess 222 of the limiting part 220 is disposed on the side of the fixing plate 200 facing the magnesium-calcium alloy fusion device 100 and matches the tooth groove size of the arc-shaped rack 121 to ensure that staged positioning feedback is provided during engagement.

[0058] In use, after loosening the locking member 300, the fixing plate 200 rotates around the magnesium-calcium alloy fusion device 100, and the protrusion 221 or recess 222 of the limiting part 220 slides along the arc-shaped rack 121 tooth by tooth. Optionally, each tooth slide corresponds to a certain range of angle change of the fixing plate 200 (e.g., 2°-3°). When the fixing plate 200 rotates to the target angle, the protrusion 221 or recess 222 is fully engaged with the corresponding tooth groove of the arc-shaped rack 121 to form a mechanical engagement. At this time, tightening the locking member 300 completes the final fixation.

[0059] Understandably, as the fixation plate 200 rotates around the axis of the fusion device, the protrusion 221 or the notch 222 slides along the rack tooth by tooth. The surgeon can quickly confirm the adjustment progress through touch or intraoperative imaging. The fixed angle increment corresponding to each tooth makes the adjustment process more repeatable. The meshing design can transform continuous angle adjustment into discrete quantitative operations, which not only improves positioning accuracy but also simplifies the intraoperative procedure.

[0060] Continue reading Figure 2 and Figure 3 In an optional embodiment of this utility model, two second mounting portions 120 are provided, and the two second mounting portions 120 are symmetrically arranged on both sides of the first mounting portion 110. The number and position of the limiting portions 220 correspond to the position and number of the second mounting portions 120.

[0061] It is understood that in this embodiment of the present invention, the two second mounting portions 120 are symmetrically distributed on both sides of the first mounting portion 110, and the number and position of the limiting portions 220 correspond one-to-one with those of the second mounting portions 120. This arrangement, through a bilateral cooperative constraint mechanism, significantly improves the balance of intraoperative angle adjustment and postoperative torsional stability. Based on the aforementioned embodiment of the arc-shaped rack 121, the limiting portion 220 of the fixing plate 200 can match the two second mounting portions 120 on both sides, and can also form a bilateral synchronous meshing mechanical constraint.

[0062] Continue reading Figure 2 and Figure 3In an optional embodiment of this utility model, the first mounting part 110 includes an arc-shaped groove 111, which is arranged along the circumferential direction of rotation; the positioning part 210 includes a first cantilever 211 and a second cantilever 212 spaced apart, both of which pass through the arc-shaped groove 111, and the spacing is changed by adjusting the locking member 300 to lock the angle of the fixing plate 200. Specifically, the arc-shaped groove 111 is located at the end of the magnesium-calcium alloy fusion unit 100, and its groove width is slightly larger than the thickness of the cantilever; the first cantilever 211 and the second cantilever 212 are symmetrically arranged on the side of the fixing plate 200 facing the fusion unit, and the distance between them is adjusted by tightening or loosening the locking member 300 (such as an expansion screw). When the locking member 300 is tightened, the distance between the two cantilever arms is reduced and presses the inner wall of the arc-shaped groove 111, generating friction to fix the angle; when loosened, the distance between the cantilever arms is restored, allowing the fixing plate 200 to rotate freely around the fusion unit.

[0063] Understandably, with this configuration, the sidewall of the arc-shaped groove 111 can not only work in conjunction with the first cantilever 211 and the second cantilever 212 to fix the position of the fixing plate 200, but also guide the rotation process of the first cantilever 211 and the second cantilever 212, ensuring that the fixing plate 200 moves relative to the magnesium-calcium alloy fusion device 100 along a predetermined rotation trajectory, thus ensuring the accuracy of the final rotation angle, rotation direction, and relative position.

[0064] Figure 4 This is a cross-sectional structural schematic diagram of the magnesium-calcium alloy fusion device provided in this embodiment of the utility model; Figure 5 This is a side view of the fixing plate and locking component provided in an embodiment of this utility model.

[0065] See Figure 4 and Figure 5 In an optional embodiment of the present invention, the first mounting part 110 further includes an arc-shaped annular groove 112. The arc-shaped annular groove 112 is arranged along the rotational circumference and is located inside the arc-shaped groove 111. The arc-shaped annular groove 112 is connected to the arc-shaped groove 111. From another perspective, the arc-shaped groove 111 is a slot opened on the side wall of the arc-shaped annular groove 112.

[0066] After passing through the arc-shaped groove 111, the first cantilever 211 and the second cantilever 212 are located in the arc-shaped annular groove 112. At least one of the first cantilever 211 and the second cantilever 212 is provided with a hook 213 at its end. The hook 213 is slidably disposed in the arc-shaped annular groove 112 and abuts against the side wall of the arc-shaped annular groove 112 to form a limiting structure. When the locking member 300 is not locked, the fixing plate 200 and the magnesium-calcium alloy fusion device 100 can form a floating connection based on the limiting structure of the hook 213 and the arc-shaped annular groove 112, that is, the two are not completely separated, and the depth of the first cantilever 211 and the second cantilever 212 extending into the arc-shaped annular groove 112 can vary. At the same time, the first cantilever 211 and the second cantilever 212 can slide in an arc along the arc-shaped annular groove 112 and the arc-shaped groove 111, that is, the fixing plate 200 rotates relative to the magnesium-calcium alloy fusion device 100.

[0067] It is understood that in this embodiment, by setting the arc-shaped annular groove 112 and the hook 213, the fixation plate 200 and the magnesium-calcium alloy fusion device 100 can be kept in a floating connection, which facilitates transportation and storage. During use, this floating connection can also eliminate the need for the assembly steps of the fixation plate 200 and the magnesium-calcium alloy fusion device 100, reduce the difficulty of operation, and facilitate the doctor's operation during the operation.

[0068] It should be noted that the technical solutions in the various embodiments of this utility model can be combined with each other, but the basis for such combination is that they can be implemented by those skilled in the art. When the combination of technical solutions is contradictory or cannot be implemented, it should be considered that such combination of technical solutions does not exist, that is, it is not within the protection scope of this utility model.

[0069] Finally, it should be noted that the above embodiments are only used to illustrate the technical solutions of this utility model, and not to limit it. Although this utility model has been described in detail with reference to the foregoing embodiments, those skilled in the art should understand that modifications can still be made to the technical solutions described in the foregoing embodiments, or equivalent substitutions can be made to some of the technical features. Such modifications or substitutions do not cause the essence of the corresponding technical solutions to deviate from the spirit and scope of the technical solutions of the embodiments of this utility model.

Claims

1. A lumbar fusion device, characterized in that, The device includes a magnesium-calcium alloy fusion device (100) and a magnesium fluoride coating, the magnesium fluoride coating being wrapped around the surface of the magnesium-calcium alloy fusion device (100), the magnesium-calcium alloy fusion device (100) being used for implantation into the intervertebral space.

2. The lumbar fusion device according to claim 1, characterized in that, It also includes a bioactive layer, which is wrapped around the surface of the magnesium fluoride coating.

3. The lumbar fusion device according to claim 2, characterized in that, The bioactive layer includes a polylactic acid coating.

4. The lumbar fusion device according to claim 2, characterized in that, The bioactive layer includes a calcium phosphate layer.

5. The lumbar fusion device according to any one of claims 1 to 4, characterized in that, It also includes a fixing plate (200) and a locking member (300). The fixing plate (200) is located at one end of the magnesium-calcium alloy fusion unit (100) and can rotate relative to the magnesium-calcium alloy fusion unit (100). The locking member (300) passes through the fixing plate (200) and is used to limit the position of the fixing plate (200) relative to the magnesium-calcium alloy fusion unit (100).

6. The lumbar fusion device according to claim 5, characterized in that, The magnesium-calcium alloy fusion device (100) is provided with a first mounting part (110) and a second mounting part (120) at its end. The fixing plate (200) is provided with a positioning part (210) and a limiting part (220) on the side facing the magnesium-calcium alloy fusion device (100). The positioning part (210) is rotatably engaged with the first mounting part (110). The locking member (300) passes through the positioning part (210) and is used to limit the position of the positioning part (210) relative to the first mounting part (110) in the rotational radial direction. The limiting part (220) and the second mounting part (120) correspond to each other and are used to limit the position of the fixing plate (200) relative to the magnesium-calcium alloy fusion device (100) in the circumferential direction of rotation.

7. The lumbar fusion device according to claim 6, characterized in that, The second mounting part (120) includes an arc-shaped rack (121) that extends along the rotational circumference; The limiting portion (220) includes at least one protrusion (221) and / or recess (222) that matches the arc-shaped rack (121).

8. The lumbar fusion device according to claim 6, characterized in that, There are two second mounting parts (120), which are symmetrically arranged on both sides of the first mounting part (110). The number and position of the limiting parts (220) correspond to the number and position of the second mounting parts (120).

9. The lumbar fusion device according to claim 6, characterized in that, The first mounting part (110) includes an arc-shaped groove (111) which is arranged along the rotational circumference; The positioning part (210) includes a first cantilever (211) and a second cantilever (212), the first cantilever (211) and the second cantilever (212) are spaced apart and pass through the arc-shaped groove (111), the locking member (300) passes between the first cantilever (211) and the second cantilever (212), and the locking member (300) is used to adjust the distance between the first cantilever (211) and the second cantilever (212).

10. The lumbar fusion device according to claim 9, characterized in that, The first mounting part (110) further includes an arc-shaped annular groove (112), which is arranged along the rotational circumference and located inside the arc-shaped groove (111), and the arc-shaped groove (111) communicates with the arc-shaped annular groove (112); At least one of the first cantilever (211) and the second cantilever (212) is provided with a hook (213) at its end, and the hook (213) is slidably disposed in the arc-shaped annular groove (112).

Images