CN115192272A - Irregular porous interbody fusion cage and processing method thereof - Google Patents

Abstract

The invention discloses a irregular porous interbody fusion cage which comprises a fusion cage body, wherein the fusion cage body comprises an upper surface and a lower surface, two opposite side surfaces between the upper surface and the lower surface are respectively a first side surface and a second side surface, the upper surface and the lower surface both form inclined slope surfaces, a first arc surface is formed between the lower ends of the two inclined slope surfaces, a second arc surface is formed between the higher ends of the two inclined slope surfaces, a plurality of through holes are formed in the upper surface, the lower surface, the first side surface, the second side surface, the first arc surface and the second arc surface of the fusion cage, any two or more through holes in the plurality of through holes are communicated to form a plurality of irregular channels, and the plurality of irregular channels are constructed on the basis of a Tage polygonal lattice. The invention realizes good elasticity of the fusion cage, achieves stable fusion effect, promotes the adhesion of bone cells on a plurality of surfaces of the structure and bone ingrowth, and solves the problems that the structure of the prior intervertebral fusion cage cannot achieve the preset fusion effect and has overhigh settleability.

Description

A kind of irregular porous interbody cage and its processing method

technical field

The invention relates to the technical field of medical equipment, in particular to a random porous intervertebral cage and a processing method thereof.

Background technique

Spinal fusion has become a routine technique in spine surgery and is widely used in the treatment of lumbar spine degeneration, cervical spine instability, intervertebral disc injury and spinal deformity. In general, spinal fusion surgery is an effective way to achieve spinal stabilization and nerve decompression. Spinal fusion is mainly the use of autologous bone, allogeneic bone or artificial prosthesis for implantation surgery, but the implantation of autologous bone is limited by some disadvantages of autologous bone, including additional surgical trauma, postoperative complications (such as infection, Due to the increased risk of hematoma and donor site pain) and limited supply, metal implants are increasingly favored in the medical field. Stable and good bone tissue growth effect.

Traditional machining methods cannot create porous structures of implants, which are prone to stress barriers. As an emerging cutting-edge technology, 3D printing technology does not require traditional tools, fixtures and multiple processing procedures. Using 3D design data, parts of any complex shape can be quickly and accurately manufactured on a single device, so as to achieve " Free to Manufacture", addressing the stress barrier problem.

In the past, threaded cages were used in the medical field to promote bone tissue fusion and compact growth. However, with the passage of time, the threaded cage has a high sedimentation rate, which has certain defects in the fusion effect. The structure of domestic self-designed cages is generally a regular lattice aperture structure in some areas and large-sized holes are opened, which is not conducive to the support of the cage and hinders the material exchange of cells, which affects the osteogenic ability. For example, the cage designed in the patent CN111529134A The structure only has through holes and windows on the upper and lower end surfaces and the inner and outer arc surfaces, while the porous structure is only in a certain area of the inner and outer arc surfaces, and the rest are all solid, which may cause stress concentration, resulting in the mechanical properties of the cage not matching the autogenous bone. It causes uneven force transmission and is not conducive to fusion and growth of the cage in multiple directions. At present, threadless cages are becoming more and more popular, but there are few studies on the structural design of personalized cages that match the mechanical properties of human bones and have irregular pores.

SUMMARY OF THE INVENTION

One object of the present invention is to propose a random porous interbody cage and a processing method thereof. The present invention utilizes the flexibility of the additive manufacturing printing process to print a spinal intervertebral body with a complex and random porous structure that matches the mechanics of human bones. The cage, through the organic combination of structure and material, avoids excessive rigidity of the structure, achieves good elasticity of the cage, achieves a stable fusion effect, promotes the adhesion of bone cells on multiple surfaces of the structure and bone ingrowth, and solves the problem of current intervertebral cages. The structure fails to achieve the predetermined fusion effect and the problem of excessive settlement.

A random porous interbody cage and a processing method thereof according to an embodiment of the present invention,

Specifically, a random porous intervertebral cage includes a cage body, the cage body includes an upper surface and a lower surface, and the opposite sides between the upper surface and the lower surface are a first arc surface and a lower surface, respectively. The second arc surface, the upper surface and the lower surface both form an inclined slope surface, a first arc surface is formed between the lower ends of the two inclined slope surfaces, and a first arc surface is formed between the higher ends of the two inclined slope surfaces The second arc surface, the upper surface, the lower surface, the first side surface, the second side surface, the first arc surface and the second arc surface of the cage are all provided with a number of through holes, and any number of the through holes The holes pass through to form a number of random channels, which are constructed based on the Tiger polygon lattice.

On the basis of the above solution, the diameter of the plurality of through holes ranges from 0.5 mm to 1 mm.

On the basis of the above solution, a plurality of tooth-shaped anti-skid protrusions are provided on the upper surface and the lower surface.

On the basis of the above solution, a first side surface is formed between the lower ends of the two inclined slope surfaces, and a second side surface is formed between the higher ends of the two inclined slope surfaces.

On the basis of the above solution, the angle range of the included angle formed between the extension lines of the lower ends of the two inclined slope surfaces is 6°-10°, and the included angle between the two inclined slope surfaces and the horizontal plane The angle range is 3°-5°.

On the basis of the above solution, the cage body is a cashew nut-like structure, the inner arc surface of the first arc surface and the inner arc surface of the second arc surface are arranged in the same direction, and the first side surface and the second side surface are arranged in the same direction. All are arcs.

On the basis of the above solution, the cage body is a rugby-like structure, the inner arc surface of the first arc surface and the inner arc surface of the second arc surface are oppositely arranged, and the first side surface and the second side surface are both Arc.

On the basis of the above solution, the length of the cage body is 20-30mm, the width is 10mm, and the height is 8-12mm.

On the basis of the above solution, the upper surface and the lower surface of the cage body are made of tantalum alloy material, and the cage body except the upper surface and the lower surface is made of titanium alloy material.

A method for processing an irregular porous intervertebral cage, applicable to any one of the irregular porous cages, comprising the following steps:

S1: According to the image data of the CT scan, use the 3D image generation software to reverse engineer the spine of the patient, import the STL format into the editing processing software to materialize it, and obtain the intervertebral space data;

S2: Using the intervertebral space data obtained in step S1, using computer-aided design software, based on the Voronoi Thiessen polygonal structure, changing the diameter of the aperture to 0.5mm-1mm and the range of density parameters to 0.5mm-0.75mm to design an aperture suitable for bone growth structure;

S3: Import the aperture structure file of step S2 into ANSYS in IGS format, use ANSYS finite element simulation for analysis, set cortical bone, cancellous bone and cartilage, cortical bone elastic modulus is 12GPa, cancellous bone elastic modulus is 100MPa, The material parameters of cartilage elastic modulus of 50MPa and Poisson's ratio of 0.3 simulate the elastic modulus of the cage, adjust the size of the structure aperture, and adjust the structure size;

S4: Using SLM technology, import the random porous fusion device data into the slice processing software in STL format, and the slice thickness is 0.02mm. In the process of starting the processing, a thin layer of tantalum alloy is firstly spread on the substrate of the forming cylinder Powder, high-power laser beam performs selective laser melting on the current layer. After the molten metal powder is cooled and solidified, the processing platform is lowered by one layer thickness, and a titanium alloy layer with a thickness of 2mm is printed out with a roller on the processed layer. After the tantalum alloy powder is laid, the laser beam starts to scan a new layer, so that the layers are superimposed, and when the processing thickness is 8mm, the titanium alloy powder is replaced again for printing, until the whole part is formed;

Among them, the process parameters when printing titanium alloy powder: the laser power is 230-250W, the scanning speed is 800-1000mm/s, and the scanning distance is 0.1-0.12mm; the process parameters when printing tantalum alloy powder: the laser power is 300W-340W, The scanning speed is 1200mm/s, the scanning distance is 0.07mm, and the shape of the fusion cage is printed by using two alloy materials using SLM technology, and the length and size of the cage are in the range of 25-30mm, and the width of the cage is in the range of 10-15mm;

S5: grinding and polishing the parts obtained in step S4 to obtain the desired random porous fusion device.

The beneficial effects of the present invention are:

(1) The present invention is an irregular porous structure without threads, which breaks the structure of traditional cages. No threads can prevent high subsidence, and it is no longer removed after surgery, which is convenient for surgical operations; the bionic human bones with irregular porous structures can not only increase the The contact area of bone tissue promotes the ingrowth of bone tissue, accelerates the fusion efficiency, and at the same time ensures that in the case of high pore size, the combination of structure and material can meet the mechanical properties of human bone tissue and improve the fusion effect of the cage;

(2) The processing method of the random porous intervertebral cage of the present invention uses the rapid prototyping technology. Due to the unique structure of the random porous intervertebral cage, the printing of different materials at different positions can be realized, and the advantages of the high friction coefficient of the tantalum material are used. The friction between the upper and lower surfaces of the cage in contact with the spine is enhanced to improve the stability of implantation. Titanium alloy is used for the rest of the cage to maintain a large aperture ratio and still meet the mechanical performance requirements. Different specifications are printed according to the CT intervertebral space data of different patients. Fusion device to achieve personalized customization.

Description of drawings

The accompanying drawings are used to provide a further understanding of the present invention, and constitute a part of the specification, and are used to explain the present invention together with the embodiments of the present invention, and do not constitute a limitation to the present invention. In the attached image:

Fig. 1 is the structural representation of a kind of irregular porous intervertebral cage (like cashew nut type) proposed by the present invention;

Fig. 2 is the structural representation of a kind of irregular porous intervertebral cage (rugby-like type) proposed by the present invention;

Fig. 3 is the left side view of Fig. 2;

Fig. 4 is the right side view of Fig. 2;

Fig. 5 is the partial sectional view of Fig. 1;

Fig. 6 is the partial sectional view of Fig. 2;

Fig. 7 is the model diagram of Fig. 1;

Fig. 8 is the model diagram of Fig. 2;

9 is a schematic diagram of a SLM technology preparation method of a method for processing a random porous interbody cage of the present invention;

Detailed ways

The present invention will now be described in further detail with reference to the accompanying drawings.

Example 1

As shown in Figures 1-8, specifically, a random porous interbody cage includes a cage body, the cage body includes an upper surface 1 and a lower surface 2, and the upper surface 1 and the lower surface 2 are between the upper surface 1 and the lower surface 2. The opposite sides between the two sides are the first side 7 and the second side 8 respectively, the upper surface 1 and the lower surface 2 both form an inclined slope, and a first arc surface is formed between the lower ends of the two inclined slopes 3. A second arc surface 4 is formed between the higher ends of the two said inclined slopes, and the upper surface 1, lower surface 2, first side surface 7, second side surface 8, first arc surface 3 and The second arc surface 4 is provided with a plurality of through holes 5 , any two or more of the through holes 5 in the plurality of through holes 5 pass through to form a plurality of random channels, and the plurality of random channels are constructed based on the Tiger polygon lattice.

This structure of the cage body is based on the Thiessen polygonal lattice, which is formed by the combination of multiple spatial Thiessen structures. The irregular hollow porous structure and no threads can not only achieve a good compressive elastic modulus, but also benefit the bone tissue. It grows in, promotes bone cell fusion, facilitates implantation, and realizes personalized customization. At the same time, the upper and lower surfaces 2 are set to be inclined at a certain angle, which is conducive to the curvature of the spine of patients after surgery. SLM printing technology is used to print different materials at different positions of the cage. At the same time, the interior and exterior are all porous hollow structures without threads, which have good biocompatibility and can induce bone ingrowth, which is beneficial to improve the rate of spinal fusion and bone regeneration, and achieve a more stable fusion effect.

Preferably, the diameter of the plurality of through holes 5 ranges from 0.5 mm to 1 mm.

Among them, the porous structure with a pore diameter of 0.5-0.75mm and a density of 0.6mm-0.75mm is suitable for people with a bone density T value between -1 and 1; the porous structure with a pore diameter of 0.75-1mm and a density of 0.5mm-0.6mm The structure is suitable for people with a bone mineral density T value of less than -1.

As shown in Figures 3-4, the upper surface 1 and the lower surface 2 are provided with a plurality of tooth-shaped anti-skid protrusions 6 to increase the unevenness and prevent the cage from slipping off after implantation.

As shown in Figures 3-4, a first arc surface 3 is formed between the lower ends of the two inclined slope surfaces, and a second arc surface 4 is formed between the higher ends of the two inclined slope surfaces.

The angle range of the included angle A between the extension lines of the lower ends (that is, the front convexity) of the two sloped slopes is 6°-10°, and the included angle C between the two sloped slopes and the horizontal plane The angle range is 3°-5°.

Preferably, the angle A formed between the extension lines of the lower ends (that is, the front convexity) of the two inclined slopes is 6°, and the angle formed between the two inclined slopes and the horizontal plane is 6°. The angle of C is 3°. In order to avoid the bending behavior of the spine after the cage is implanted, the upper surface 1 and the lower surface 2 are set to a certain inclination angle, which is helpful to restore the physiological curvature of the lumbar spine.

As shown in Figures 4 and 6, the cage body is a cashew-like structure, the inner arc surface of the first arc surface 3 and the inner arc surface of the second arc surface 4 are arranged in the same direction, and the first side surface 7 and the second side surface 8 are arc surfaces.

As shown in FIGS. 5 and 7 , the cage body is a football-like structure, the inner arc surface of the first arc surface 3 and the inner arc surface of the second arc surface 4 are arranged opposite to each other, and the first side surface 7 and the second arc surface are opposite to each other. Both side surfaces 8 are arc surfaces.

In actual use, the two shapes need to be selected according to the intervertebral space obtained by CT scanning. The sides of the cages of the two structures are designed as arc surfaces, which can adapt to the internal structure of the human vertebral body.

On the basis of the above solution, the length L of the cage body is 20-30 mm, the width B is 10-15 mm, and the height is 8-12 mm.

Example 2

An irregular porous intervertebral spacer cage, the upper surface 1 and the lower surface 2 of the cage body are made of tantalum alloy material, and the cage body is made of titanium alloy material except the upper surface 1 and the lower surface 2, and the two are made of titanium alloy. The different mechanical properties and structures of these materials are matched to achieve elastic modulus and mechanical properties that are compatible with human bone tissue.

Specifically, the upper surface 1 and the lower surface 2 (2 mm each) are made of tantalum alloy material, and the high friction coefficient of tantalum alloy is used to achieve stable implantation and prevent slipping after implantation. The middle part (6mm) is made of titanium alloy material, accounting for 60% of the total volume, and the mechanical properties of the cage are still ensured when the aperture ratio is 80%.

Tantalum alloy, titanium alloy and tantalum alloy material are used in different positions of the upper, middle and lower parts of the cage structure. The high friction coefficient of tantalum alloy improves the surface friction of the cage. Good fix.

Among them, the ratio of titanium-tantalum alloy is 1:13:1.

Example 3

As shown in Figure 9, a method for processing an irregular porous intervertebral cage, which is applicable to the irregular porous intervertebral cage described in Embodiment 1 or 2, includes the following steps:

S1: According to the image data of CT scan, use 3D image generation software (such as Mimics software) to reverse engineer the spine of the patient, import the STL format into editing and processing software (such as Geomagic software) to materialize it, and obtain intervertebral space data;

S2: Use computer-aided design software (such as Materialise 3-matic software) to change the intervertebral space data obtained in step S1, based on the Voronoi Thiessen polygonal structure, to change the aperture range to 0.5mm-1mm and the density parameter range to 0.5mm-0.75mm , design a pore structure suitable for bone growth;

S3: Import the aperture structure file of step S2 into ANSYS in IGS format, use ANSYS finite element simulation for analysis, set cortical bone, cancellous bone and cartilage, cortical bone elastic modulus is 12GPa, cancellous bone elastic modulus is 100MPa, The material parameters of cartilage elastic modulus of 50MPa and Poisson's ratio of 0.3 simulate the elastic modulus of the cage, adjust the size of the structure aperture, and adjust the structure size;

S4: Using SLM technology, import the random porous fusion device data into the slice processing software in STL format, and the slice thickness is 0.02mm. In the process of starting the processing, a thin layer of tantalum alloy is firstly spread on the substrate of the forming cylinder Powder, high-power laser beam performs selective laser melting on the current layer. After the molten metal powder is cooled and solidified, the processing platform is lowered by one layer thickness, and a titanium alloy layer with a thickness of 2mm is printed out with a roller on the processed layer. After the tantalum alloy powder is laid, the laser beam starts to scan a new layer, so that the layers are superimposed, and when the processing thickness is 8mm, the titanium alloy powder is replaced again for printing, until the whole part is formed;

Among them, the process parameters when printing titanium alloy powder: the laser power is 230-250W, the scanning speed is 800-1000mm/s, and the scanning distance is 0.1-0.12mm; the process parameters when printing tantalum alloy powder: the laser power is 300W-340W, The scanning speed is 1200mm/s, the scanning distance is 0.07mm, and the shape of the fusion cage is printed by using two alloy materials using SLM technology, and the length L of the cage is 25-30mm, and the width B size is 10-15mm;

S5: grinding and polishing the parts obtained in step S4 to obtain the desired random porous fusion device.

As shown in Figure 1, the structure of the cage of this embodiment is a random porous structure based on Thiessen polygons. In order to meet the needs of human movement and the fusion effect of the spine, two structural shapes are designed as "kidney" and "rugby". It can induce the ingrowth of bone tissue in multiple directions, and achieve the effect of fast ingrowth and good fusion. At the same time, no thread structure is designed, which is not only convenient for implantation, but also avoids high subsidence after implantation. 1 and 2 , the length L and height H of the two cage structures in this embodiment are both 25 mm and 10 mm, and the width B is 10 mm and 15 mm, respectively. The side surfaces of the cages of the two structures are designed as arc curved surfaces to adapt to the internal structure of the human vertebral body. The upper surface 1 and the lower surface 2 are provided with a plurality of tooth-shaped convex surfaces to increase friction. In addition to increasing friction in structure, The upper surface 1 and the lower surface 2 (2mm each) are made of tantalum alloy material, and the high friction coefficient of tantalum alloy is used to achieve stable implantation and prevent slipping after implantation. The middle part (6mm) is shown in Figure 3 and Figure 4, all of which are made of titanium alloy, accounting for 60% of the total volume, and the mechanical properties of the cage are still ensured when the porosity is 80%. As shown in Figure 2, in order to avoid the bending behavior of the spine after the cage is implanted, the upper surface 1 and the lower surface 2 are set to a certain inclination angle, the lordosis angle formed by the two surfaces is 6°, and the upper and lower surfaces are inclined. The angle between the slope and the horizontal is 3°, which helps to restore the physiological curvature of the lumbar spine.

A specific embodiment of the method for processing an irregular porous intervertebral cage according to the present invention is shown in Figures 1-9, and the steps are as follows:

(1) The doctor performs a CT scan on the patient's spine to obtain the patient's CT image data, uses the Mimics software to reverse engineer the patient's spine, and imports the STL format into Geomagic to materialize it to obtain the intervertebral space data.

(2) Design the approximate shape of the cage according to the intervertebral space data, use the Materialise 3-matic software, based on the Voronoi Thiessen polygon structure, change the aperture (0.5mm-1mm) and density parameters (0.5mm-0.75mm), and design it suitable for bone growth. porous structure.

(3) Import the file into ANSYS in IGS format, use finite element simulation for analysis, set cortical bone (elastic modulus 12GPa), cancellous bone (elastic modulus 100MPa) and cartilage (elastic modulus 50MPa) and Poisson's ratio 0.3 The material parameters simulate the elastic modulus of the cage, adjust the pore size of the structure, and realize the hollow porous structure with different pore sizes to adapt to people with different bone densities.

(4) For different groups of people, according to the irregular porous structure, the length and size range is 25-30mm; Processing software, slice thickness is 0.02mm. In the process of starting the processing, a thin layer of tantalum alloy powder with a thickness of 0.03mm is firstly laid on the substrate of the forming cylinder. The high-power laser beam performs selective laser melting on the current layer. After the molten metal powder is cooled and solidified, the processing The platform is lowered by one layer height, and a titanium alloy layer with a thickness of 2mm is printed. After the tantalum alloy powder is spread on the processed layer with a roller, the laser beam starts to scan a new layer, so that the layers are superimposed, and the processing thickness is 8mm Then switch to titanium alloy powder again and print until the whole part is formed. Among them, the process parameters when printing titanium alloy powder: the laser power is 230W, the scanning speed is 1000mm/s, and the scanning distance is 0.12mm; the process parameters when printing tantalum alloy powder: the laser power is 300W, the scanning speed is 1200mm/s, the scanning The pitch is 0.07mm.

(5) grinding and polishing the parts obtained in step (4) to obtain the required parts.

In some embodiments, the random porous cage is 25mm in length, 10mm in width, 10mm in height, 6° in lordosis, 0.75mm in aperture, and 0.5mm in density.

In some embodiments, the random porous cage has a length of 25 mm, a width of 10 mm, a height of 10 mm, a lordosis angle of 6°, a hole diameter of 0.5 mm, and a density of 1 mm.

In some embodiments, the random porous cage has a length of 30 mm, a width of 15 mm, a height of 10 mm, a lordosis angle of 6°, a hole diameter of 1 mm, and a density of 0.5 mm.

The random porous intervertebral cage of the present invention and the preparation method thereof adopts the porous structure of bionic bone, and the whole has no threads, and is an integrated model of the irregular porous structure, which can make the contact surface between the cage and the vertebrae tighter, and accelerate the fusion of bone tissue from The cage can grow and migrate on multiple surfaces, speed up the fusion effect, avoid high subsidence caused by the existence of threads, and do not need to fill the cage with bone material during the operation, which simplifies the operation of the operation.

The above description is only a preferred embodiment of the present invention, but the protection scope of the present invention is not limited to this. The equivalent replacement or change of the inventive concept thereof shall be included within the protection scope of the present invention.

Claims (9)

1. a random porous intervertebral cage, comprising a cage body, the cage body comprises an upper surface and a lower surface, and the opposite sides between the upper surface and the lower surface are respectively the first side and the second On the side, both the upper surface and the lower surface form an inclined slope, a first arc is formed between the lower ends of the two inclined slopes, and a second arc is formed between the higher ends of the two inclined slopes It is characterized in that the upper surface, the lower surface, the first side, the second side, the first arc surface and the second arc surface of the cage are provided with several through holes, and any two of the several through holes are provided with a plurality of through holes. A plurality of through holes are connected to form a plurality of random channels, and the plurality of random channels are constructed based on a Tiger polygon lattice. 2 . The random porous interbody cage according to claim 1 , wherein the diameters of the plurality of through holes range from 0.5 mm to 1 mm. 3 . 3 . The random porous interbody cage according to claim 1 , wherein a plurality of tooth-shaped anti-skid protrusions are provided on the upper surface and the lower surface. 4 . 4. The random porous interbody cage according to claim 1, wherein the angle of the included angle formed between the extension lines of the lower ends of the two inclined slope surfaces is 6°-10° °, the angle range of the included angle between the two inclined slope surfaces and the horizontal plane is 3°-5°. 5. A kind of irregular porous intervertebral cage according to claim 1, characterized in that, the cage body is a cashew-like structure, the inner arc of the first arc surface and the inner arc of the second arc The inner arc surfaces are arranged in the same direction, and the first side surface and the second side surface are both arc surfaces. 6. The random porous intervertebral cage according to claim 1, wherein the cage body is a rugby-like structure, the inner arc of the first arc surface and the inner arc of the second arc surface The arc surfaces are oppositely arranged, and the first side surface and the second side surface are both arc surfaces. 7 . The random porous interbody cage according to claim 1 , wherein the cage body has a length of 20-30 mm, a width of 10-15 mm, and a height of 8-12 mm. 8 . 8. The random porous intervertebral cage according to claim 1, wherein the upper surface and the lower surface of the cage body are made of tantalum alloy material, and the cage body is made of tantalum alloy except for the upper surface and the lower surface. Made of titanium alloy. 9. A method for processing an irregular porous intervertebral cage, applicable to a kind of irregular porous intervertebral cage according to any one of claims 1-8, characterized in that, comprising the following steps: S1: According to the image data of the CT scan, use the 3D image generation software to reverse engineer the spine of the patient, import the STL format into the editing processing software to materialize it, and obtain the intervertebral space data; S2: Using the intervertebral space data obtained in step S1, using computer-aided design software, based on the Voronoi Thiessen polygonal structure, changing the diameter of the aperture to 0.5mm-1mm and the range of density parameters to 0.5mm-0.75mm to design an aperture suitable for bone growth structure; S3: Import the aperture structure file of step S2 into ANSYS in IGS format, use ANSYS finite element simulation for analysis, set cortical bone, cancellous bone and cartilage, cortical bone elastic modulus is 12GPa, cancellous bone elastic modulus is 100MPa, The material parameters of cartilage elastic modulus of 50MPa and Poisson's ratio of 0.3 simulate the elastic modulus of the cage, adjust the size of the structure aperture, and adjust the structure size; S4: Using SLM technology, import the data of the random porous fusion device into the slicing processing software in STL format. In the process of starting the processing, a thin layer of tantalum alloy powder is firstly spread on the substrate of the forming cylinder, and the high-power laser beam The current layer is selectively laser melted. After the molten metal powder is cooled and solidified, the titanium alloy layer is printed and the tantalum alloy powder is laid on the processed sheet. The laser beam starts to scan a new layer, and the layers are superimposed. Switch to titanium alloy powder again for printing until the entire part is formed; S5: grinding and polishing the parts obtained in step S4 to obtain the desired random porous fusion device.

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