Additive manufacturing bionic bone trabecula full-porous interbody fusion cage

Abstract

The invention relates to the technical field of medical instruments, and discloses an additive manufacturing bionic bone trabecula full-porous interbody fusion cage which is applied to spinal fusion surgery and is of a bionic bone trabecula full-porous structure made of medical metal through a laser melting or electron beam melting additive manufacturing technology. The interbody fusion cage comprises a front end face, a rear end face, a first side surface, a second side surface, an upper fusion face and a lower fusion face, the upper fusion face and the lower fusion face make direct contact with a vertebral body end plate of a spine, anti-skid teeth are arranged on the surfaces of the upper fusion face and the lower fusion face, and a bone grafting window penetrating through the upper fusion face and the lower fusion face is formed in the center of the interbody fusion cage. The interbody fusion cage has the structure and mechanical property similar to those of cancellous bone and trabecular bone of a human body, can improve the bone combination area and bone ingrowth space, has excellent initial and long-term stability, and can effectively reduce stress shielding so as to improve the bone fusion capability.

Description

Technical Field

[0001] The present invention relates to the technical field of medical devices, and more particularly to an additively manufactured bionic trabecular fully porous intervertebral fusion device. Background Art

[0002] With the continuous development of medical technology, intervertebral fusion plays an increasingly important role in the treatment of spinal diseases. As the key implant device of intervertebral fusion, the structure and performance of intervertebral fusion device directly affect the surgical effect and the patient's recovery. Traditional intervertebral fusion device is a dense solid structure product made of titanium alloy and polyetheretherketone (PEEK) and other materials through mechanical processing. It does not have the ability of bone fusion itself and can only provide mechanical support. It relies on filling autologous bone or artificial bone in the bone graft window to achieve intervertebral bone fusion. Because the elastic modulus of the dense structure of these materials is too large and does not match the human skeleton, it causes stress shielding, resulting in a high incidence of fusion device sinking and dislocation; the friction coefficient of the dense structure is small, the initial implantation stability is low, and it is easy to cause the fusion device to dislocate; and bone tissue cannot grow into the dense structure, which makes the vertebral fusion time longer and the clinical treatment effect is poor.

[0003] In recent years, the preparation of porous intervertebral fusion devices through additive manufacturing technologies such as laser melting (SLM) and electron beam melting (EBM) has attracted widespread attention from academia and industry. The porous structure can provide space for bone ingrowth, increase the bone bonding area and bone fusion volume; its low elastic modulus is close to that of human bones, which reduces stress shielding and improves implant success rate and long-term stability.

[0004] Existing porous intervertebral fusion devices still have some shortcomings in terms of structural design and fusion effect. For example, due to the unsatisfactory porous structure design or the poor strength of the material itself, in order to ensure the mechanical properties, only a partially porous structure can be prepared, containing a dense solid frame, a small bone bonding area, less bone ingrowth space, and poor bone fusion performance. The unreasonable distribution of the porous structure may also lead to local stress concentration, affecting the mechanical reliability of the fusion device. Summary of the invention

[0005] In view of this, the present invention provides an additively manufactured bionic trabecular fully porous intervertebral fusion device. Compared with the existing dense solid frame, the intervertebral fusion device of the present invention has a structure and mechanical properties similar to those of human cancellous bone and trabecular bone, can increase the bone bonding area and bone ingrowth space, has excellent initial and long-term stability, and can effectively reduce stress shielding, thereby improving bone fusion ability.

[0006] To achieve the above-mentioned purpose, the present invention provides an additively manufactured bionic trabecular fully porous intervertebral fusion device, which is applied to spinal fusion surgery. The intervertebral fusion device is a bionic trabecular fully porous structure made of medical metal by laser melting or electron beam melting additive manufacturing technology.

[0007] The intervertebral fusion device comprises a front end face, a rear end face, a first side surface, a second side surface, an upper fusion surface and a lower fusion surface. The upper fusion surface and the lower fusion surface are in direct contact with the vertebral end plates of the spine, and the surfaces of the upper fusion surface and the lower fusion surface are both provided with anti-slip teeth. A bone grafting window is provided in the center of the intervertebral fusion device, which passes through the upper and lower fusion surfaces.

[0008] Preferably, the intervertebral fusion cage is a cervical fusion cage applied to the cervical vertebra in the spine, and the upper fusion surface and the lower fusion surface of the cervical fusion cage are arranged at an angle of 0° to 7°.

[0009] Preferably, the front end surface of the cervical fusion device is a smooth plane structure to reduce friction and interference during implantation.

[0010] Preferably, the rear end face on the cervical fusion device is an arc-shaped structure to reduce pressure and stimulation on the posterior tissue. The arc-shaped structure allows the rear end face to fit closely with the implant instrument, thereby increasing the area of ​​the knocking surface during the implantation process, ensuring that the cervical fusion device is evenly distributed with stress when being knocked or force is applied, and preventing structural damage or deformation during the implantation process. An instrument hole is provided on the rear end face that passes through the bone graft window for inserting and fixing the instrument.

[0011] Preferably, the first side surface and the second side surface on the cervical fusion cage are upright planes to enhance the overall strength of the cervical fusion cage and prevent deformation under lateral force. The first side surface and the second side surface form a certain angle to reduce resistance during the fusion cage implantation procedure.

[0012] Preferably, holes or openings are provided on both the first side surface and the second side surface to reduce the weight of the cervical fusion cage and provide channels for bone graft growth and fusion inside and outside the cervical fusion cage.

[0013] Preferably, the intervertebral fusion device is a lumbar fusion device applied to the lumbar vertebrae in the spine, and the front end surface of the lumbar fusion device adopts a double bullet head structure to reduce friction and interference with the intervertebral space and surrounding tissues.

[0014] Preferably, the upper fusion surface and the lower fusion surface of the lumbar fusion device are arcuate structures to increase the contact area with the end plates and evenly distribute the stress on the upper fusion surface and the lower fusion surface.

[0015] Preferably, the rear end surface of the lumbar fusion device is a planar structure, and symmetrical grooves are provided on the rear end surface.

[0016] Preferably, the first side surface and the second side surface of the lumbar fusion cage are respectively provided with side holes, and the side holes provide channels for bone graft growth and fusion inside and outside the lumbar fusion cage.

[0017] Through the above technical solutions, it can be known that compared with the prior art, the additively manufactured bionic trabecular fully porous intervertebral fusion device disclosed in the present invention, wherein the fully porous structure is precisely formed by additive manufacturing technology to ensure the uniform distribution and connectivity of the pores, and its three-dimensional through-hole bionic trabecular microporous structure quickly absorbs blood through the capillary effect, promotes bone fusion and vascularization, enables nutrients and metabolic waste to be effectively exchanged between the implant and the surrounding tissue, promotes the formation and maturation of new bone, and thus optimizes the speed and degree of bone ingrowth. The elastic modulus and other mechanical properties of the fusion device are close to those of human cancellous bone and trabecular bone, and have excellent biomechanical adaptability, no stress shielding risk, and avoid bone dissolution; its load-bearing capacity is outstanding, and immediate load-bearing can be achieved. The fusion device has a high friction coefficient with human bones, which enhances implant stability, and the high porosity can significantly promote bone and blood vessel ingrowth, further improving the fusion rate. In addition, the fusion device has high toughness, high plasticity and excellent fatigue resistance, good imaging effect, convenient postoperative evaluation, high long-term stability, strong anti-sinking ability, high anatomical morphology matching, and improved fusion rate and implant stability. This comprehensive design of the structure provides the fusion device with excellent biocompatibility and functional performance, meeting the clinical needs for rapid fusion and long-term stability. BRIEF DESCRIPTION OF THE DRAWINGS

[0018] In order to more clearly illustrate the embodiments of the present invention or the technical solutions in the prior art, the drawings required for use in the embodiments or the description of the prior art will be briefly introduced below. Obviously, the drawings described below are only embodiments of the present invention. For ordinary technicians in this field, other drawings can be obtained based on the provided drawings without paying creative work.

[0019] Figure 1 is a three-dimensional schematic diagram of a cervical fusion device in Embodiment 1 of the present invention;

[0020] Figure 2 The present invention Figure 1 Top view of the mid-cervical fusion cage;

[0021] Figure 3 The present invention Figure 2 Sectional view along AA;

[0022] Figure 4 The present invention Figure 1 Left view of the mid-cervical fusion cage;

[0023] Figure 5 The present invention Figure 1 Front view of the mid-cervical fusion cage;

[0024] Figure 6 is a three-dimensional schematic diagram of a lumbar fusion device in Embodiment 2 of the present invention;

[0025] Figure 7 The present invention Figure 6 Front view of mid-lumbar fusion cage;

[0026] Figure 8 The present invention Figure 6 Schematic diagram of the top of the mid-lumbar fusion cage;

[0027] Fig. 9 The present invention Figure 1 Cervical fusion cage and Figure 6 A close-up of the porous structure of the mid-lumbar fusion cage;

[0028] Fig.10 is a three-dimensional modeling diagram of the intervertebral fusion cage of the present invention, wherein a is a cervical fusion cage and b is a lumbar fusion cage;

[0029] Fig.11 is a schematic diagram of an actual product of the intervertebral fusion device of the present invention, wherein a is a cervical fusion device and b is a lumbar fusion device;

[0030] Fig.12 is a load-displacement curve of an embodiment of the intervertebral fusion device of the present invention;

[0031] Fig.13 The dynamic compression F-N curve of an embodiment of the intervertebral fusion device of the present invention;

[0032] Fig.14 is a bar graph showing the percentage increase in bone contact area between some embodiments of the intervertebral fusion device of the present invention and traditional dense products;

[0033] Fig.15 It is a histogram of pore volume that can be used for bone ingrowth in some embodiments of the intervertebral fusion device of the present invention;

[0034] Fig.16 This is an X-ray image of the animal experiment of the intervertebral fusion device embodiment of the present invention;

[0035] Fig.17 It is a bar graph of DSH (intervertebral disc height) measurement data at different implantation time points in an animal experiment of an intervertebral fusion device embodiment of the present invention;

[0036] Fig.18 These are the stained slice photos of different stages of implantation of the intervertebral fusion device embodiment of the present invention in animal experiments;

[0037] Fig.19 It is a bar graph of bone integration rate at different stages of implantation of an intervertebral fusion device embodiment of the present invention in an animal experiment.

[0038] Explanation of reference numerals: cervical fusion cage 10; front end face 12; rear end face 14; upper fusion surface 16; lower fusion surface 18; second side surface 20; first side surface 22; anti-slip teeth 24; bone grafting window 26; instrument hole 28; groove 44; side hole 48; lumbar fusion cage 50. DETAILED DESCRIPTION

[0039] The following will be combined with the drawings in the embodiments of the present invention to clearly and completely describe the technical solutions in the embodiments of the present invention. Obviously, the described embodiments are only part of the embodiments of the present invention, rather than all the embodiments. The following description of an exemplary embodiment is actually only illustrative and is by no means intended to limit the present invention and its application or use. Based on the embodiments of the present invention, all other embodiments obtained by ordinary technicians in this field without creative work are within the scope of protection of the present invention.

[0040] Please refer to the attached Figure 1-11 , is the additively manufactured bionic trabecular fully porous intervertebral fusion device disclosed in the present invention, see the attached Figure 12-15 The load-displacement curve, dynamic compression F-N curve and the percentage increase of bone contact area of ​​the intervertebral fusion device disclosed in the present invention compared with the traditional dense product are shown in the attached figure. Figure 16-19 The figures are related to the animal experiments of the intervertebral fusion device embodiment disclosed in the present invention.

[0041] The additively manufactured bionic trabecular fully porous intervertebral fusion device provided by the present invention is applied to spinal fusion surgery. The spine includes structures such as the cervical spine and the lumbar spine. The intervertebral fusion device is a bionic trabecular fully porous structure made of medical metal by laser melting or electron beam melting additive manufacturing technology. The fully porous structure is formed in one step by additive manufacturing technology to ensure the uniform distribution and connectivity of the pores and optimize the speed and degree of bone ingrowth. Figure 12-13 As shown, the bionic fully porous structure has high plasticity and mechanical reliability, excellent fatigue resistance, static compression stiffness greater than 10000N / mm, yield strength greater than 4000N, and compressive fatigue limit strength greater than 2000N under 5 million cycles of loading conditions, which can effectively reduce the risk of fracture failure of implants during long-term use.

[0042] The intervertebral fusion device includes a front face 12, a rear face 14, a first side surface 22, a second side surface 20, an upper fusion surface 16 and a lower fusion surface 18. The upper fusion surface 16 and the lower fusion surface 18 are in direct contact with the vertebral endplate of the spine, and the surfaces of the upper fusion surface 16 and the lower fusion surface 18 are both provided with anti-slip teeth 24. These anti-slip teeth 24 can effectively increase the friction between the implant and the vertebral endplate after implantation, prevent the implant from shifting or rotating after surgery, and thus improve the stability and fusion success rate of the intervertebral fusion device. A bone grafting window 26 that passes through the upper and lower fusion surfaces is provided in the center of the intervertebral fusion device for filling autologous bone or artificial bone material. The opening of the bone grafting window 26 is precisely designed to ensure that it is large enough to accommodate the required bone graft material while maintaining the structural strength of the implant. The through bone grafting window 26 maximizes the contact area between the bone graft material and the endplate, promotes the ingrowth and fusion of bone tissue, accelerates the healing process after surgery, and ensures the integration of the new bone and the implant, thereby improving the fusion effect. The precise position of the bone graft window 26 can be optimized according to specific circumstances to ensure the maximum contact area between the bone material and the upper and lower end plates, thereby improving the success rate of bone fusion.

[0043] Specifically, medical metals include but are not limited to tantalum, titanium, tantalum alloys and titanium alloys, which have excellent mechanical properties, corrosion resistance and biocompatibility, which are the key to successful long-term implantation. The porous metal structure is designed to simulate natural trabecular bone, promote bone integration and strengthen biological fixation. The anti-slip teeth 24 are arc-shaped and have a depth of 0.5 mm, which can reduce tissue damage caused during implantation, improve stress distribution, and reduce the risk of wear and debris generation during long-term use of the implant, thereby extending the service life of the implant.

[0044] Embodiment 1:

[0045] like Figure 1-5 As shown, the intervertebral fusion cage is specifically a cervical fusion cage 10 applied to the cervical spine in the spine, and its overall structural design fully considers the anatomical characteristics and biomechanical requirements of the cervical spine, aiming to provide excellent stability and fusion effect.

[0046] The front end face 12 is a planar structure, which is mainly used to provide a basic surface for implantation and positioning. The front end face 12 is designed to be smooth and without protrusions to reduce friction and interference during implantation, help the fusion device to smoothly enter the intervertebral space and reduce damage to the intervertebral disc tissue.

[0047] The upper fusion surface 16 and the lower fusion surface 18 are key areas that are in direct contact with the vertebral endplates. Their design directly affects the stability of the implant and the bone fusion effect. In order to adapt to the physiological structure of the vertebral endplates of different patients, the upper fusion surface 16 and the lower fusion surface 18 are set at an angle of 0° to 7°. This angle design is selected based on the normal physiological curvature of the cervical spine to ensure better fit and stability, thereby promoting the recovery of the natural physiological curvature of the spine.

[0048] The rear end face 14 is an arc-shaped structure, which is specially used to improve the compliance of the implant and the convenience of surgical operation. The rear end face 14 with an arc-shaped structure conforms to the anatomical curve of the cervical spine, which helps to reduce the pressure and stimulation of the implant on the posterior tissue, and at the same time improves the compliance and stability of the implant during surgery. More importantly, the arc-shaped structure design enables the rear end face 14 to fit tightly with the implant instrument, thereby increasing the area of ​​the knocking surface during the implantation process. This fit provides surgeons with greater operational stability during surgery, ensuring that the cervical fusion device 10 evenly distributes stress when it is knocked or force is applied, thereby preventing structural damage or deformation during the implantation process. An instrument hole 28 that passes through the bone graft window is provided on the rear end face 14 to facilitate the insertion and fixation of the instrument during surgery. The design of the instrument hole 28 is optimized to ensure the precise insertion of the tool without affecting the filling of the bone graft material and the progress of bone fusion.

[0049] The first side surface 22 and the second side surface 20 are planes at a certain angle, which provide overall structural support and lateral stability of the implant. The first side surface 22 and the second side surface 20 are designed as upright planes, which help to enhance the overall strength of the fusion device and prevent deformation under lateral force. The design of the angle between the first side surface 22 and the second side surface 20 can reduce the resistance during the fusion device surgical implantation. If necessary, the first side surface 22 and the second side surface 20 can also be designed with additional holes or openings to reduce the weight of the implant and provide additional bone ingrowth channels.

[0050] Embodiment 2:

[0051] like Figure 6-8 As shown, the intervertebral fusion cage is specifically a lumbar fusion cage 50 applied to the lumbar vertebra in the spine, and its overall structural design fully considers the anatomical characteristics and biomechanical requirements of the lumbar vertebra, aiming to provide excellent stability and fusion effect.

[0052] The front end face 12 adopts a double bullet head structure design. This streamlined structure can effectively reduce the implantation resistance, making it easier to position the lumbar fusion cage 50 during surgery, thereby reducing the complexity of the surgery and the operation time. The double bullet head shape not only simplifies the implantation process, but also reduces the risk of tissue damage by reducing friction and interference with the intervertebral space and surrounding tissues, and improves the compliance of the fusion cage.

[0053] The upper fusion surface 16 and the lower fusion surface 18 are designed as curved surfaces, and the diameter of the curved surface is fixed at 150 mm. This design can accurately adapt to the lumbar end plate, improve the stability of the initial implant, and reduce the risk of displacement and settlement of the implant after surgery. The curved surface structure helps to increase the contact area between the implant and the end plate, improve the stress distribution, make the stress distribution more uniform, and thus reduce the risk of collapse of the end plate after compression.

[0054] The rear end face 14 is designed to be flat and has symmetrical grooves 44 for holding the implant instrument. The groove 44 design provides a stable gripping point, allowing the surgeon to more accurately manipulate and position the implant during surgery, ensuring the stability and accuracy of the implantation process. The presence of the symmetrical grooves 44 also improves the ease of operation of the implant and reduces errors during surgery.

[0055] The first side surface 22 and the second side surface 20 are both provided with side holes 48. The design of the side holes 48 is conducive to the growth and fusion of bone grafts inside and outside the fusion device. The side holes 48 not only reduce the weight of the implant, but also provide additional channels for the growth of bone tissue, thereby promoting the integration of the implant with the surrounding bone tissue. The side holes 48 increase the air permeability of the implant, facilitate the vascularization process, and further accelerate the healing process.

[0056] like Fig. 9 As shown, the porous structure of the intervertebral fusion device of the present invention adopts a fully porous design. Compared with the traditional fusion device with a dense solid part, the present invention greatly increases the volume of bone ingrowth and significantly improves the bone fusion effect. Figure 14-15 As shown, after measurement, compared with the traditional dense fusion device products, the fully porous structure of the present invention increases the surface area by about 1.5 to 3.5 times and the area by about 400 to 1500 mm 3 Pore ​​volume available for bone ingrowth. This design provides a larger bone integration area and more space for bone cells to attach and grow, thereby accelerating the bone fusion process. The pore structure units are irregular polygons and are randomly arranged in all directions, showing mechanical isotropy. This design can better adapt to the complex biomechanical environment of the spine, provide uniform stress distribution and good biomechanical stability. The porous structure averages 240 to 800 microns, the average pore diameter is 200 to 500 microns, and the porosity is 50% to 90%, which is consistent with the structural characteristics of human cancellous bone. This porous structure not only helps to reduce the overall elastic modulus of the implant, making it closer to the mechanical properties of natural bone, but also provides sufficient space and channels to facilitate the ingrowth of bone cells and the generation of blood vessels, further promoting the integration and fusion of bone tissue and implants.

[0057] In order to verify the bone fusion performance of the additively manufactured bionic trabecular fully porous intervertebral fusion device of the present invention, animal experiments were conducted, and the bone fusion effect at different time points (3 months, 6 months and 12 months) was evaluated by combining medical imaging technology, DSH measurement data and tissue section staining results. X-ray, CT and other imaging examinations were performed at 3 months, 6 months and 12 months after surgery, and the formation of trabeculae and changes in bone density were quantitatively analyzed to preliminarily determine the new bone formation. Figure 16-19 As shown, the imaging results show that the porous intervertebral fusion device of the present invention shows good bone fusion effect within 3 months, 6 months and 12 months after implantation, the trabecular structure gradually increases, and the bone bonding interface is clear, indicating that effective bone bonding is formed between the new bone and the scaffold material; the DSH (distal disc height) test results show that there is no significant difference in the disc height immediately after implantation, 3 months after implantation and 6 months after implantation, indicating that the implant has not undergone significant displacement and has excellent stability; the HE staining method is used to perform section analysis on the bone fusion area after 3 months, 6 months and 12 months, and the results show that the implant material can be seen in the bone defect area, osteoblasts can be seen at the edge of the bone defect, new bone is formed at the boundary of the bone defect, and new bone is formed between the implant material and the pores. 6 months after surgery, D-level intervertebral fusion is achieved, that is, the bone tissue bridges the entire fusion area, at least at the density achieved during the operation (or greater than); 12 months after surgery, the bone bonding rate exceeds 85%.

[0058] The above description of the disclosed embodiments enables one skilled in the art to implement or use the present invention. Various modifications to these embodiments will be apparent to one skilled in the art, and the general principles defined herein may be implemented in other embodiments without departing from the spirit or scope of the present invention. Therefore, the present invention will not be limited to the embodiments shown herein, but rather to the widest scope consistent with the principles and novel features disclosed herein.

Claims

1. An additively manufactured bionic trabecular fully porous intervertebral fusion cage, used in spinal fusion surgery, characterized in that: The intervertebral fusion cage is a bionic bone trabecular fully porous structure made of medical metal by laser melting or electron beam melting additive manufacturing technology. The intervertebral fusion device comprises a front end face (12), a rear end face (14), a first side surface (22), a second side surface (20), an upper fusion surface (16) and a lower fusion surface (18); the upper fusion surface (16) and the lower fusion surface (18) are in direct contact with the vertebral end plates of the spine, and the surfaces of the upper fusion surface (16) and the lower fusion surface (18) are both provided with anti-slip teeth (24); a bone grafting window (26) penetrating the upper and lower fusion surfaces is provided in the center of the intervertebral fusion device.

2. The additively manufactured bionic trabecular fully porous intervertebral fusion cage according to claim 1, characterized in that: The intervertebral fusion device is specifically a cervical fusion device (10) applied to the cervical vertebra in the spine, and the upper fusion surface (16) and the lower fusion surface (18) of the cervical fusion device (10) are arranged at an angle of 0° to 7°.

3. The additively manufactured bionic trabecular fully porous intervertebral fusion cage according to claim 2, characterized in that: The front end surface (12) on the cervical fusion device (10) is a smooth plane structure to reduce friction and interference during the implantation process.

4. The additively manufactured bionic trabecular fully porous intervertebral fusion cage according to claim 2, characterized in that: The rear end face (14) on the cervical fusion device (10) is an arc-shaped structure to reduce pressure and stimulation on the posterior tissue. The arc-shaped structure allows the rear end face (14) to fit tightly with the implantation instrument, thereby increasing the area of ​​the knocking surface during the implantation process, ensuring that the cervical fusion device (10) is evenly distributed with stress when being knocked or force is applied, and preventing structural damage or deformation during the implantation process. The rear end face (14) is provided with an instrument hole (28) that passes through the bone graft window (26) for inserting and fixing the instrument.

5. The additively manufactured bionic trabecular fully porous intervertebral fusion cage according to claim 2, characterized in that: The first side surface (22) and the second side surface (20) on the cervical fusion cage (10) are upright planes to enhance the overall strength of the cervical fusion cage (10) and prevent deformation under lateral force. The first side surface (22) and the second side surface (20) form a certain angle to reduce resistance during the fusion cage implantation procedure.

6. The additively manufactured bionic trabecular fully porous intervertebral fusion cage according to claim 5, characterized in that: Holes or openings are provided on the first side surface (22) and the second side surface (20) to reduce the weight of the cervical fusion cage (10) and provide channels for bone graft growth and fusion inside and outside the cervical fusion cage (10).

7. The additively manufactured bionic trabecular fully porous intervertebral fusion cage according to claim 1, characterized in that: The intervertebral fusion device is specifically a lumbar fusion device (50) applied to the lumbar vertebrae in the spine. The front end surface (12) of the lumbar fusion device (50) adopts a double bullet head structure to reduce friction and interference with the intervertebral space and surrounding tissues.

8. The additively manufactured bionic trabecular fully porous intervertebral fusion cage according to claim 7, characterized in that: The upper fusion surface (16) and the lower fusion surface (18) of the lumbar fusion device (50) are arcuate structures to increase the contact area with the end plate and evenly distribute the stress on the upper fusion surface (16) and the lower fusion surface (18).

9. The additively manufactured bionic trabecular fully porous intervertebral fusion cage according to claim 7, characterized in that: The rear end surface (14) of the lumbar fusion device (50) is a planar structure, and symmetrical grooves (44) are provided on the rear end surface (14).

10. The additively manufactured bionic trabecular fully porous intervertebral fusion cage according to claim 7, characterized in that: The first side surface (22) and the second side surface (20) of the lumbar fusion cage (50) are respectively provided with side holes (48), and the side holes (48) provide channels for bone graft growth and fusion inside and outside the lumbar fusion cage (50).

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