CN108635084B - Polyether-ether-ketone variable-modulus artificial bone substitute prepared by fused deposition 3D printing and preparation method thereof - Google Patents
Polyether-ether-ketone variable-modulus artificial bone substitute prepared by fused deposition 3D printing and preparation method thereof Download PDFInfo
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/02—Prostheses implantable into the body
- A61F2/28—Bones
-
- B—PERFORMING OPERATIONS; TRANSPORTING
- B33—ADDITIVE MANUFACTURING TECHNOLOGY
- B33Y—ADDITIVE MANUFACTURING, i.e. MANUFACTURING OF THREE-DIMENSIONAL [3-D] OBJECTS BY ADDITIVE DEPOSITION, ADDITIVE AGGLOMERATION OR ADDITIVE LAYERING, e.g. BY 3-D PRINTING, STEREOLITHOGRAPHY OR SELECTIVE LASER SINTERING
- B33Y10/00—Processes of additive manufacturing
-
- B—PERFORMING OPERATIONS; TRANSPORTING
- B33—ADDITIVE MANUFACTURING TECHNOLOGY
- B33Y—ADDITIVE MANUFACTURING, i.e. MANUFACTURING OF THREE-DIMENSIONAL [3-D] OBJECTS BY ADDITIVE DEPOSITION, ADDITIVE AGGLOMERATION OR ADDITIVE LAYERING, e.g. BY 3-D PRINTING, STEREOLITHOGRAPHY OR SELECTIVE LASER SINTERING
- B33Y80/00—Products made by additive manufacturing
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/02—Prostheses implantable into the body
- A61F2/28—Bones
- A61F2002/2835—Bone graft implants for filling a bony defect or an endoprosthesis cavity, e.g. by synthetic material or biological material
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/02—Prostheses implantable into the body
- A61F2/30—Joints
- A61F2/3094—Designing or manufacturing processes
- A61F2/30942—Designing or manufacturing processes for designing or making customized prostheses, e.g. using templates, CT or NMR scans, finite-element analysis or CAD-CAM techniques
- A61F2002/30943—Designing or manufacturing processes for designing or making customized prostheses, e.g. using templates, CT or NMR scans, finite-element analysis or CAD-CAM techniques using mathematical models
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/02—Prostheses implantable into the body
- A61F2/30—Joints
- A61F2/3094—Designing or manufacturing processes
- A61F2002/30985—Designing or manufacturing processes using three dimensional printing [3DP]
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- Health & Medical Sciences (AREA)
- Engineering & Computer Science (AREA)
- Chemical & Material Sciences (AREA)
- Manufacturing & Machinery (AREA)
- Materials Engineering (AREA)
- Transplantation (AREA)
- Cardiology (AREA)
- Oral & Maxillofacial Surgery (AREA)
- Orthopedic Medicine & Surgery (AREA)
- Biomedical Technology (AREA)
- Heart & Thoracic Surgery (AREA)
- Vascular Medicine (AREA)
- Life Sciences & Earth Sciences (AREA)
- Animal Behavior & Ethology (AREA)
- General Health & Medical Sciences (AREA)
- Public Health (AREA)
- Veterinary Medicine (AREA)
- Prostheses (AREA)
Abstract
The invention discloses a polyether-ether-ketone variable-modulus artificial bone substitute prepared by fused deposition 3D printing and a preparation method thereof, wherein the variable-modulus artificial bone substitute for bone grafting operation is prepared by taking a fused deposition molding technology as a processing method and taking polyether-ether-ketone and derivatives thereof as raw materials; according to the actual biomechanical environment and geometric characteristics of the prosthesis, the modulus gradient structure of the prosthesis is reasonably designed, so that the modulus of the prosthesis is more matched with that of the autologous bone, the stress is more effectively transferred to the bone tissue of a human body, and the stress shielding is reduced so as to improve the biocompatibility of the prosthesis implant; the variable modulus artificial bone substitute is integrally formed by adopting a fused deposition 3D printing technology, realizes natural transition and connection of parts with different moduli, has good biomechanical performance, can effectively avoid the stress shielding effect of a prosthesis, and better meets the mechanical environment and functional requirements of human bones.
Description
Technical Field
The invention belongs to the technical field of medical treatment, relates to an artificial prosthesis, and more particularly relates to a polyether-ether-ketone variable-modulus artificial bone substitute prepared by fused deposition 3D printing and a preparation method thereof.
Background
Artificial bone substitutes are widely used in human bone grafting surgery. In order to ensure sufficient strength of the bone substitute, the bone substitute currently used for bone grafting is mainly metal. However, the rigidity of the metal material is far higher than that of human skeleton, and obvious stress shielding effect can be generated after the metal material is implanted into human body, so that the bone atrophy is caused, and further the long-term loosening of the bone substitute is caused. Therefore, to avoid the problems associated with stress shielding, artificial bone substitutes implanted into the human body should have strength and material mechanical properties similar to those of the natural bone of the human body.
The metal porous structure can effectively reduce the modulus of the substituted bone, and the internal porous structure can promote the growth of surrounding bone tissues to form stable biological fixation, so that the problem of long-term loosening of the bone substitute can be effectively avoided. However, the modulus of the metal prosthesis is reduced by using the porous structure, so that the modulus of the metal prosthesis is only reduced to be close to that of cortical bone of a human body, and the modulus is still higher compared with that of most bones of the human body. While the modulus is reduced by utilizing the pores, the fatigue strength of the prosthesis is also remarkably reduced due to the increase of the porosity, which often leads to the failure of the metal porous prosthesis. In addition, residual powder inevitably exists in the inner part or on the surface of the porous structure prosthesis prepared by using the selective laser melting molding (SLM) technology, and the existence of the powder can cause the fatigue strength of the prosthesis to be obviously reduced, thereby seriously influencing the service life of the prosthesis and increasing the risk of the prosthesis revision. The metal material is inevitably released by corrosion after being placed in a human body for a long time, and excessive metal ions have certain influence on human tissues.
Due to different stress environments and functional forms of bones at different parts of a human body, the material properties such as Young modulus, bending modulus and the like of the bones are different, for example, the ribs of the human body need to expand and contract back and forth due to the respiratory motion of the human body, so that the ribs need to have certain rigidity to resist deformation, but the normal respiratory motion of the human body is hindered due to the overhigh rigidity. The pelvis is subjected to a large force in a sitting posture of a human body, and a large number of muscle attachment points exist on the pelvis to bear a large number of muscle forces, which requires the pelvis to have sufficient strength to bear stress. And the modulus of different parts of a single bone is also changed and non-uniform, for example, the modulus of cortical bone at the outer edge of a tibia of a human body is higher, the modulus of spongy bone in an inner cavity is lower, and stress is mainly born by the cortical bone. It can be seen that the modulus of human skeleton is non-uniform, and the artificial skeleton substitute has the same mechanical environment as the original human skeleton after being implanted into human body, and also has the same functional requirements as the original human skeleton, so as to be better matched with human tissue. Most of the existing artificial bone substitutes for bone transplantation are uniform in modulus, and ideal artificial bone substitutes are multi-modulus gradient substitutes truly simulating the modulus change characteristics of natural human bones.
Polyetheretherketone (PEEK) has a modulus close to that of human bones and has excellent biocompatibility and corrosion and fretting wear resistance, but it has not been proposed to prepare a modulus gradient bioprosthesis for bone grafting using PEEK as a raw material using Fused Deposition Modeling (FDM) technology.
Disclosure of Invention
Aiming at the requirements on the human bone substitute, the invention aims to provide the polyether-ether-ketone variable-modulus artificial bone substitute prepared by fused deposition 3D printing and the preparation method thereof, and solves the problems in the prior art.
The invention provides a method for preparing a variable-modulus human bone substitute for bone grafting by using PEEK (polyetheretherketone) and derivative materials thereof and utilizing Fused Deposition Modeling (FDM)3D printing technology. The elastic modulus of PEEK material is about 3Gpa, which is very close to that of human bone compared to the elastic modulus of metal materials commonly used for prosthesis manufacture (about 200Gpa at most). The modulus of the prosthesis prepared by PEEK is more matched with that of autologous bone, and stress can be more effectively transferred to human bone tissues, so that stress shielding is reduced, the biocompatibility of the prosthesis implant is improved, and the problem of long-term loosening of the prosthesis is prevented; PEEK not only has good biocompatibility, but also has good corrosion resistance, and can hardly generate particles harmful to human tissues after being implanted into a human body, so that the toxicity to surrounding tissues is reduced; in the preparation process of the prosthesis, printing parameters (such as the temperature of a base plate and the temperature of a spray head to obtain different crystallinities of materials) can be controlled according to the bones at different parts and stress distribution of different sections of the bones, so that the multi-modulus gradient artificial bone substitute is printed.
The technical scheme adopted by the invention is as follows:
a polyetheretherketone variable-modulus artificial bone substitute prepared by fused deposition 3D printing is divided into a 1 st modulus layer, a 2 nd modulus layer, … and an n-th modulus layer in turn along the radial direction,
the Young modulus of each modulus layer is different, and the Young modulus of each modulus layer gradually increases from the 1 st modulus layer to the n-th modulus layer,
the 1 st modulus layer is positioned at the central position of the substituted bone and sequentially comprises a 2 nd modulus layer, … and an n th modulus layer outwards along the radial direction,
the nth modulus layer is the outermost layer of the substitute bone and is directly contacted with human tissues;
the artificial bone tissue substitute is prepared by 3D printing of polyether-ether-ketone PEEK and derivatives thereof serving as raw materials.
Furthermore, the 1 st modulus layer, the 2 nd modulus layer, … and the nth modulus layer are integrally formed through 3D printing.
Further, the artificial bone substitute comprises substitutes of human non-joint bones of ribs, pelvis, clavicle, intervertebral fusion device, skull, mandible, tibia and radius ulna.
Further, the preparation method of the polyetheretherketone variable modulus artificial bone tissue substitute prepared by fused deposition 3D printing comprises the following steps:
s1: reconstructing a three-dimensional model of the skeleton of the affected part;
s2: determining a three-dimensional model of a bone substitute based on a bone model of a diseased site;
s3: dividing a 1 st modulus layer, a 2 nd modulus layer, … and an n th modulus layer based on the three-dimensional model of the bone substitute;
s4: bone substitutes were prepared using fused deposition modeling FDM technology.
Further, in step S2, the three-dimensional model of the bone substitute may adopt the geometry of the healthy bone at the symmetrical position of the affected part.
Further, in step S3, the number of modulus layers is determined according to the size of the bone substitute; the cross-sectional profile of each modulus layer is referenced to the peripheral profile of the bone substitute; the thickness of each modulus layer may be the same or different.
Further, in step S4, when preparing different modulus layers, setting different values for the temperature of the showerhead of the FDM to realize the modulus change; and when the 1 st modulus layer is prepared, setting the temperature of the spray head to be lower, and then increasing the temperature of the spray head layer by layer to finally obtain the bone substitute with gradually increased modulus layer by layer.
The invention has the following effective effects:
1) the artificial bone substitute provided by the invention takes PEEK and derivatives thereof as raw materials, the modulus of the prepared prosthesis is more matched with that of autogenous bone, and stress can be more effectively transferred to human bone tissues, so that stress shielding is reduced, the biocompatibility of the prosthesis implant is improved, and the problem of long-term loosening of the prosthesis is prevented;
2) the invention can rapidly form the prosthesis which meets the requirements of the geometrical shape of the skeleton of the diseased part of the patient by using the FDM forming technology;
3) the invention can realize the preparation of the multi-modulus gradient prosthesis by using the FDM forming technology, effectively transfer stress to human skeleton, reduce stress shielding effect, stimulate the growth of surrounding bone tissues and avoid the long-term loosening of the prosthesis;
4) the material used by the invention mainly comprises PEEK, so that the stress shielding effect and toxicity risk possibly caused by the metal prosthesis are effectively reduced.
Drawings
Figure 1 is a schematic diagram of a multi-modulus gradient graded artificial rib substitute.
Figure 2 is a schematic cross-sectional view of a multi-modulus gradient graded artificial pelvic bone substitute.
Fig. 3 is a schematic cross-sectional view of a multi-modulus gradient artificial tibia.
In the figure, 1-reserved human rib, 2-1 st modulus layer, 3-2 nd modulus layer, 4-3 rd modulus layer, 5-4 th modulus region, 6-FDM formed multi-modulus gradient artificial rib, 7-FDM formed multi-modulus gradient artificial pelvis, and 8-FDM formed multi-modulus gradient artificial tibia.
Detailed Description
The present invention will be described in detail below with reference to the accompanying drawings and specific embodiments. It should be understood that the specific examples described herein are intended to be illustrative only and are not intended to be limiting.
To obtain a multi-modulus artificial rib replacement as shown in fig. 1, three-dimensional data of the affected part of the rib of the patient is first acquired, for example, by CT scanning. And constructing a skeleton model of the rib disease part and the periphery by using related software (such as MIMICS17.0) according to the CT scanning result, wherein the obtained partial skeleton model of the patient comprises the rib and the peripheral skeleton and bone tumor parts of the patient. Then, the bone tumor is removed from the established three-dimensional model of the patient rib according to the guidance of the expert doctor, and if necessary, certain bone removal is carried out. If the partial replacement needs to consider the design of the matching surface of the artificial bone substitute and the human bone, the reserved human rib 1 is matched with the artificial bone, and a three-dimensional model of the rib part needing to be printed is cut out. In addition, stress analysis is performed by using finite element analysis software (such as ABAQUS6.14) to establish a skeletal muscle model of the patient's rib. According to the stress analysis result, a multi-modulus region of the FDM-shaped multi-modulus gradient artificial rib 6 is defined, the high-stress region of the rib is set as a high-modulus printing region, namely a 4 th modulus region 5, and the low-stress region is set as a 1 st modulus layer 2, a 2 nd modulus layer 3 and a 3 rd modulus layer 4 in sequence from low to high. The built model is then exported to the STL file. Reading the STL file to set printing parameters (e.g., control printing temperature, hot bed temperature) so that the material has different crystallinity in different regions, e.g., the material has higher crystallinity in the 3 rd modulus layer 4, thereby obtaining high modulus properties; the material is made to have a lower crystallinity in the 1 st modulus layer 2 to achieve low modulus properties. Finally, the mechanical property of the formed skeleton is integrally evaluated, and after the qualified performance is determined, the bone transplantation operation of the patient is carried out by a specialist doctor.
A section of the pelvis is artificially replaced by a multi-modulus as shown in fig. 2, where different modulus distributions are represented by different grey scale regions. The modulus distribution of the pelvis can be known according to the anatomical structure of the pelvis, the stress distribution condition of the pelvis can be known through finite element analysis, the peripheral region of the pelvis can be known to be a muscle attachment region according to the structure of the musculus ossis around the pelvis of a human body, most of muscle force needs to be borne, and the pelvis is born with great pressure in daily sitting and standing postures. The distribution of the modulus of the multi-modulus artificial replacement pelvis bone, which is obtained from known results and analysis, should be gradually reduced from outside to inside.
In actual cases, in order to obtain a multi-modulus artificial replacement pelvis as shown in fig. 2, three-dimensional data of the affected part of the pelvis of a patient needs to be acquired, for example, by means of CT scanning and the like. And constructing a skeleton model of the pelvis diseased part and the periphery by using related software (such as MIMICS17.0) according to the CT scanning result. Then, the established three-dimensional model of the pelvis of the patient is subjected to bone resection according to the guidance of the specialist doctor. Defining a multi-modulus region for a multi-modulus gradient-gradient artificial pelvis 7 formed by FDM, setting a certain thickness region at the periphery of the pelvis as a high-modulus printing region (a 4 th modulus layer 5), setting a low-stress region as a low-modulus printing region (a 1 st modulus layer 2), and transiting the 4 th modulus layer 5 and the 1 st modulus layer 2 by a 2 nd modulus layer 3 and a 3 rd modulus layer 4 to ensure that the strength of the artificial bone substitute printed by 3D has a gradient characteristic. The built model is then exported to the STL file. Reading the STL file to set printing parameters (e.g., control printing temperature, hot bed temperature) so that the material has different crystallinity in different regions, e.g., the material has higher crystallinity in the 4 th modulus layer 5, thereby obtaining high modulus properties; the material is made to have a lower crystallinity in the 1 st modulus layer 2 to achieve low modulus properties. Finally, the mechanical property of the formed skeleton is integrally evaluated, and after the qualified performance is determined, the bone transplantation operation of the patient is carried out by a specialist doctor.
Fig. 3 is a schematic diagram of the modulus distribution of the multi-modulus artificial replacement tibia, wherein different grayscale regions are used to represent different modulus distributions. According to the existing analysis result, the outer edge of the tibia is subjected to larger stress, and the stress value is gradually reduced inwards. According to known research results, the modulus distribution design of the artificial replacement tibia should be a gradient of modulus from the outer high modulus region to the inner low modulus region.
In actual cases, in order to obtain a multi-modulus artificial replacement tibia as shown in fig. 3, three-dimensional data of a diseased part of the tibia of a patient needs to be acquired, for example, by means of CT scanning and the like. And constructing a skeleton model of the tibia diseased part and the periphery by using related software (such as MIMICS17.0) according to the CT scanning result, and considering the design of the matching surface of the artificial bone substitute and the human skeleton if partial replacement. Then, a finite element analysis software (such as ABAQUS6.14) is used for establishing a skeletal muscle model of the tibia of the patient, and stress analysis is carried out. According to the stress analysis result, a multi-modulus region is defined for the FDM-molded multi-modulus gradient artificial tibia 8, a certain thickness region on the periphery of the tibia is set as a high-modulus printing region (a 4 th modulus layer 5), a low-stress region is set as a low-modulus printing region (a 1 st modulus layer 2), the 4 th modulus layer 5 and the 1 st modulus layer 2 are transited through a 2 nd modulus layer 3 and a 3 rd modulus layer 4, and the strength of the 3D-printed artificial bone substitute has a gradient characteristic. The built model is then exported to the STL file. Reading the STL file to set printing parameters (e.g., control printing temperature, hot bed temperature) so that the material has different crystallinity in different regions, e.g., the material has higher crystallinity in the 4 th modulus layer 5, thereby obtaining high modulus properties; the material is made to have a lower crystallinity in the 1 st modulus layer 2 to achieve low modulus properties. Finally, the mechanical property of the formed skeleton is integrally evaluated, and after the qualified performance is determined, the bone transplantation operation of the patient is carried out by a specialist doctor.
It is to be understood that in the above examples, the gradient of the modulus of the multi-modulus gradient prosthesis is not limited to 3 or 4 gradient gradients, and that the present invention also encompasses more than 4 multi-modulus gradient artificial bone substitutes.
The above description is only a preferred embodiment of the present invention, and is not intended to limit the scope of the present invention: it is intended that the following claims be interpreted as including all such alterations, modifications, and equivalents as fall within the true spirit and scope of the invention.
Claims (4)
1. A preparation method of a polyetheretherketone variable-modulus artificial bone substitute prepared by fused deposition 3D printing comprises the steps of sequentially dividing the artificial bone substitute into a 1 st modulus layer, a 2 nd modulus layer, … and an n-th modulus layer along the radial direction,
the Young modulus of each modulus layer is different, and the Young modulus of each modulus layer gradually increases from the 1 st modulus layer to the n-th modulus layer,
the 1 st modulus layer is positioned at the central position of the substituted bone and sequentially comprises a 2 nd modulus layer, … and an n th modulus layer outwards along the radial direction,
the nth modulus layer is the outermost layer of the substitute bone and is directly contacted with human tissues;
the artificial bone substitute is prepared by 3D printing of polyether-ether-ketone PEEK and derivatives thereof serving as raw materials;
the preparation method of the polyether-ether-ketone variable-modulus artificial bone substitute prepared by fused deposition 3D printing is characterized by comprising the following steps of:
s1: reconstructing a three-dimensional model of the skeleton of the affected part;
s2: determining a three-dimensional model of a bone substitute based on the three-dimensional model of the bone of the affected site;
s3: dividing a 1 st modulus layer, a 2 nd modulus layer, … and an n th modulus layer based on the three-dimensional model of the bone substitute;
s4: preparing a bone substitute by Fused Deposition Modeling (FDM) technology;
in S3, the number of modulus layers is determined according to the size of the bone substitute; the cross-sectional profile of each modulus layer is referenced to the peripheral profile of the bone substitute; the thickness of each modulus layer is the same or different;
in S4, when preparing different modulus layers, setting different values for the temperature of the showerhead of the fused deposition modeling FDM to realize the modulus change; the temperature of the spray head is gradually increased from the 1 st modulus layer to the n modulus layer to realize the gradual increase of the modulus layer by layer.
2. The method for preparing the polyetheretherketone variable modulus artificial bone substitute according to claim 1, wherein in S2, the three-dimensional model of the bone substitute adopts the geometry of the healthy bone at the symmetrical position of the affected part.
3. The method for preparing the polyetheretherketone variable modulus artificial bone substitute according to claim 1, wherein the 1 st modulus layer, the 2 nd modulus layer, … and the n-th modulus layer are integrally formed by fused deposition 3D printing.
4. The method for preparing the polyetheretherketone variable-modulus artificial bone substitute according to claim 1, wherein the artificial bone substitute is a substitute for human ribs, pelvis, clavicle, intervertebral cage, skull, mandible, tibia, radius, ulna or other bones of human non-joint parts.
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| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN201810486134.7A CN108635084B (en) | 2018-05-21 | 2018-05-21 | Polyether-ether-ketone variable-modulus artificial bone substitute prepared by fused deposition 3D printing and preparation method thereof |
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| CN201810486134.7A CN108635084B (en) | 2018-05-21 | 2018-05-21 | Polyether-ether-ketone variable-modulus artificial bone substitute prepared by fused deposition 3D printing and preparation method thereof |
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| CN108635084A CN108635084A (en) | 2018-10-12 |
| CN108635084B true CN108635084B (en) | 2021-05-07 |
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| CN110193926A (en) * | 2019-05-08 | 2019-09-03 | 西安交通大学 | A kind of design and manufacturing method of the bionical multi-level joint prosthesis of polyether-ether-ketone |
| CN110393610B (en) * | 2019-05-15 | 2021-08-10 | 上海大学 | Three-layer composite bone implant prosthesis and preparation method thereof |
| CN110141401A (en) * | 2019-06-21 | 2019-08-20 | 云南增材佳唯科技有限公司 | A kind of clavicle implantation material based on 3D printing technique preparation |
| CN112402063A (en) * | 2019-08-23 | 2021-02-26 | 北京智塑健康科技有限公司 | Model construction method, system and device of bone structure prosthesis and readable storage medium thereof |
| CN112402065A (en) * | 2019-08-23 | 2021-02-26 | 北京智塑健康科技有限公司 | Manufacturing method, system and device of fusion device and storage medium thereof |
| CN114053485B (en) * | 2020-07-31 | 2023-02-10 | 华中科技大学 | Single cell structure for biological stent and application thereof |
| CN112060581B (en) * | 2020-08-31 | 2021-11-23 | 四川大学 | Dental implant with bionic gradient modulus local functionalization and preparation method thereof |
| CN112220588B (en) * | 2020-10-15 | 2021-06-29 | 北京理工大学 | Method and system for generating controllable gradient bone tissue engineering scaffold |
| CN112691233A (en) * | 2020-12-28 | 2021-04-23 | 南昌大学 | 3D printing interbody fusion cage and preparation method thereof |
| CN114429045A (en) * | 2022-01-26 | 2022-05-03 | 华侨大学 | Optimization design method for variable-gradient dental crown structure of molar prosthesis |
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