CN210277413U - Spinal titanium mesh bone grafting fusion cage - Google Patents
Spinal titanium mesh bone grafting fusion cage Download PDFInfo
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- CN210277413U CN210277413U CN201822124590.5U CN201822124590U CN210277413U CN 210277413 U CN210277413 U CN 210277413U CN 201822124590 U CN201822124590 U CN 201822124590U CN 210277413 U CN210277413 U CN 210277413U
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- titanium
- titanium mesh
- bone grafting
- spinal
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- RTAQQCXQSZGOHL-UHFFFAOYSA-N Titanium Chemical compound [Ti] RTAQQCXQSZGOHL-UHFFFAOYSA-N 0.000 title claims abstract description 61
- 210000000988 bone and bone Anatomy 0.000 title claims abstract description 48
- 230000004927 fusion Effects 0.000 title claims description 31
- 229910052719 titanium Inorganic materials 0.000 abstract description 26
- 239000010936 titanium Substances 0.000 abstract description 26
- 230000006978 adaptation Effects 0.000 abstract description 3
- 238000010030 laminating Methods 0.000 abstract description 2
- 230000006837 decompression Effects 0.000 description 13
- 238000004519 manufacturing process Methods 0.000 description 9
- 238000010146 3D printing Methods 0.000 description 6
- 230000000694 effects Effects 0.000 description 6
- 238000002591 computed tomography Methods 0.000 description 5
- 238000000034 method Methods 0.000 description 4
- 238000002271 resection Methods 0.000 description 4
- 230000008468 bone growth Effects 0.000 description 3
- 239000000463 material Substances 0.000 description 3
- 230000009467 reduction Effects 0.000 description 3
- QNRATNLHPGXHMA-XZHTYLCXSA-N (r)-(6-ethoxyquinolin-4-yl)-[(2s,4s,5r)-5-ethyl-1-azabicyclo[2.2.2]octan-2-yl]methanol;hydrochloride Chemical compound Cl.C([C@H]([C@H](C1)CC)C2)CN1[C@@H]2[C@H](O)C1=CC=NC2=CC=C(OCC)C=C21 QNRATNLHPGXHMA-XZHTYLCXSA-N 0.000 description 2
- 208000010392 Bone Fractures Diseases 0.000 description 2
- 230000003044 adaptive effect Effects 0.000 description 2
- 230000000735 allogeneic effect Effects 0.000 description 2
- 230000009286 beneficial effect Effects 0.000 description 2
- 230000007547 defect Effects 0.000 description 2
- 238000011065 in-situ storage Methods 0.000 description 2
- 208000035473 Communicable disease Diseases 0.000 description 1
- 229910001200 Ferrotitanium Inorganic materials 0.000 description 1
- 206010023509 Kyphosis Diseases 0.000 description 1
- 206010028980 Neoplasm Diseases 0.000 description 1
- 208000031481 Pathologic Constriction Diseases 0.000 description 1
- 241000283984 Rodentia Species 0.000 description 1
- 229910001069 Ti alloy Inorganic materials 0.000 description 1
- 239000000654 additive Substances 0.000 description 1
- 230000000996 additive effect Effects 0.000 description 1
- 238000004458 analytical method Methods 0.000 description 1
- 230000004071 biological effect Effects 0.000 description 1
- 230000005540 biological transmission Effects 0.000 description 1
- 230000000740 bleeding effect Effects 0.000 description 1
- 238000002474 experimental method Methods 0.000 description 1
- 210000002082 fibula Anatomy 0.000 description 1
- 210000003692 ilium Anatomy 0.000 description 1
- 230000006872 improvement Effects 0.000 description 1
- 208000015181 infectious disease Diseases 0.000 description 1
- 208000014674 injury Diseases 0.000 description 1
- 238000007689 inspection Methods 0.000 description 1
- 230000007774 longterm Effects 0.000 description 1
- 230000005541 medical transmission Effects 0.000 description 1
- 238000012986 modification Methods 0.000 description 1
- 230000004048 modification Effects 0.000 description 1
- 230000000877 morphologic effect Effects 0.000 description 1
- 230000001537 neural effect Effects 0.000 description 1
- 230000011164 ossification Effects 0.000 description 1
- 230000002093 peripheral effect Effects 0.000 description 1
- 230000002980 postoperative effect Effects 0.000 description 1
- 238000007639 printing Methods 0.000 description 1
- 230000001737 promoting effect Effects 0.000 description 1
- 238000011084 recovery Methods 0.000 description 1
- 206010039073 rheumatoid arthritis Diseases 0.000 description 1
- 210000000614 rib Anatomy 0.000 description 1
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- 208000037804 stenosis Diseases 0.000 description 1
- 208000024891 symptom Diseases 0.000 description 1
- 230000008733 trauma Effects 0.000 description 1
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- 208000019392 vertebral column disease Diseases 0.000 description 1
- 230000000007 visual effect Effects 0.000 description 1
- 239000002699 waste material Substances 0.000 description 1
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Abstract
The utility model discloses a netted bone grafting of backbone titanium fuses ware, be in including netted cylinder of titanium and matched stack independent tip on the netted cylinder of titanium, the shape of its terminal surface is confirmed through the three-dimensional scanning of the terminal plate of treating the adaptation cervical vertebra, is set up to correspond the laminating into can with the terminal plate to print by 3D and form.
Description
Technical Field
The utility model relates to the field of medical equipment, especially, relate to a netted bone grafting of backbone titanium fuses ware.
Background
The vertebral column vertebral body secondary total resection decompression bone grafting fusion (ACCF) is widely applied to the operation treatment of various vertebral column diseases in clinic, including spinal canal stenosis, trauma, infectious diseases, tumor, rheumatoid arthritis and the like, and has the advantages of large operation visual field, convenient operation, thorough decompression, exact curative effect and the like. The key aspect of the ACCF operation is complete decompression and symptom improvement, and the other aspect is good bone grafting fusion, which can reconstruct the physiological curvature and the intervertebral height of the spine, maintain the stability of the spine and ensure the long-term curative effect of the operation. There are three main bone grafting methods used clinically at present: 1. autogenous bone (ilium, rib or fibula); 2. allogeneic bone; 3. adopting titanium net to plant bone in situ. Although autologous bone is an ideal bone grafting material, has good bone growth activity and a high fusion rate, it increases the operation time and the amount of bleeding during the operation, and may cause infection, pain, and complications such as fracture in the bone supplying region. Although allogeneic bone grafting can avoid complications of a bone supplying area, the allograft bone grafting has poor biological activity and low fusion rate, a bone grafting block is easy to collapse, and certain rejection reaction and risk of disease transmission exist. The in-situ bone grafting method adopting the titanium mesh has convenient operation, can avoid complications in a bone supplying area, has higher bone grafting fusion rate and is widely applied by spinal surgeons. In the operation, the crushed bone blocks after the vertebral body is completely cut off are filled into the titanium net and implanted into the decompression groove, so that the physiological curvature and the intervertebral height of the spine can be effectively reconstructed, the stability of the cervical vertebra is maintained, and the crushed bone after local decompression is fully utilized to achieve the purpose of autogenous bone grafting and bone fusion. However, before the titanium mesh is used, two ends of the common titanium mesh need to be trimmed according to the length of the pressure reduction groove, actual contact between the constructed titanium mesh and the end plate is point contact, and stress transmission is concentrated. The proportion of subsidence after operation is quite high, and the subsidence of titanium net can lead to the original physiological curvature of backbone and the loss of intervertebral height, causes the postoperative patient to appear local pain, and neural function recovery stops or aggravates once more, even appears the kyphosis deformity, fuses serious complication such as fixed failure, needs the operation once more.
The invention discloses a Chinese patent application CN 201040010Y, which is a complete contact spinal titanium reticular bone grafting fusion device, and consists of a titanium reticular column and a complete contact upper end surface and a complete contact lower end surface which are uniquely designed at two ends; the upper end surface is in an annular dome shape, the upper end surface is arched and raised on the crown surface, the outer wall of the part close to the end surface is thickened and is similar to an annular gasket, on one hand, the titanium net is in surface contact with the end plate, and on the other hand, the strength of the titanium net on the contact surface is also increased. The lower end surface is also annular and inclines backwards on the sagittal plane to be matched with the upper end plate of the lower vertebral body. The invention solves the problem of the subsidence of the titanium mesh after the operation of the vertebral column vertebral body sub-total resection decompression bone grafting fusion to a certain extent, but because of the individual anatomical difference of patients, the contact surface of the titanium mesh produced according to the fixed specification model and the vertebral column vertebral body is still difficult to be completely attached to an end plate, the problem of stress concentration is still not completely solved, and the risk of the subsidence of the titanium mesh still exists.
SUMMERY OF THE UTILITY MODEL
In view of the above-mentioned defects in the prior art, the technical problem to be solved by the present invention is how to reduce the incidence of the post-operation titanium mesh subsidence.
In view of the above-mentioned defect of prior art, the utility model provides a netted bone grafting of backbone titanium fuses ware, including the netted cylinder of titanium and the independent tip of matched stack on the netted cylinder of titanium, the shape of the terminal surface of tip is set up to correspond the laminating with the endplate of treating the adaptation cervical vertebra. The shape of the end face of the end plate is determined by three-dimensional scanning of the end plate and is printed in 3D.
Preferably, the end part and the titanium net-shaped column body are assembled through a latch structure.
Preferably, the end face of the end portion is of a porous structure.
The utility model also provides a manufacturing method of the spinal titanium mesh bone grafting fusion cage, which comprises the following steps:
(1) three-dimensional scanning is carried out on an end plate of the cervical vertebra to be adapted to obtain shape data of the end plate;
(2) according to the shape data of the end plate, the end part is manufactured through 3D printing, so that the end face of the end part can be correspondingly attached to the end plate;
(3) the titanium mesh cylinder is manufactured so that the end portions can be assembled on the titanium mesh cylinder.
Preferably, the end part and the titanium net-shaped column body are assembled through a latch structure.
Preferably, the end face of the end portion is of a porous structure.
Compared with the prior art, the utility model discloses specific beneficial effect as follows has:
1. compared with the anatomical adaptation type titanium net produced by the common manufacturing process, the utility model discloses can solve the problem that the matching degree brought by the individual difference between different patients is not accurate enough, realize that the netted bone grafting of backbone titanium fuses ware and the complete match of supporting the end plate and closely laminate, the titanium net that brings is sunk in the most at utmost to the reduction stress concentration
2. Compare with ordinary 3D printing titanium net, the utility model discloses a matched stack formula design makes 3D printing technique advance to use the manufacturing of upper and lower extreme structure, and titanium net column major structure still adopts the tradition to subtract material manufacturing process. On one hand, the problem that the length design of the titanium mesh is difficult to complete through preoperative planning is solved by manufacturing columnar main body structures with different sizes, and different sizes can be tried temporarily to be finally determined; on the other hand, the problem that the whole printing design needs to prepare prostheses with a plurality of lengths is avoided, only one prosthesis is finally selected, and other prostheses cannot be used for other patients due to the specificity of the upper end face and the lower end face, so that huge cost waste is caused. The specific upper and lower end structures in the assembled prosthesis do not need to be changed, and the rest columnar main body can be selected to be matched with the upper and lower end structures of other patients, so that the manufacturing cost is greatly saved
3. The porous design of the surfaces of the upper end and the lower end of the titanium mesh bone grafting fusion device is beneficial to the expansion of bone tissues, improves the bone grafting fusion rate and increases the firmness of the prosthesis. The conception, the specific structure and the technical effects of the present invention will be further described with reference to the accompanying drawings, so as to fully understand the objects, the features and the effects of the present invention.
Drawings
FIG. 1 is a schematic view of a titanium mesh spinal fusion cage according to an embodiment of the present invention;
fig. 2 is a schematic view of the spinal titanium mesh bone grafting fusion cage according to an embodiment of the present invention.
Detailed Description
The following describes embodiments of the present invention in detail with reference to the accompanying drawings.
An embodiment according to the invention is shown in fig. 1 and 2. The titanium net bone grafting fusion cage for the vertebral column is of a combined and assembled structure integrally and comprises a titanium net column body 1, an upper end part 2 and a lower end part 3. The titanium reticular column body 1 is hollow, the cross section is in an arc-shaped ellipse shape with two side edges at the front and the back, the peripheral wall is a rhombic or triangular reticular hollow structure 11, and two ends are connected with the upper end part and the lower end part. The upper end portion 2 and the lower end portion 3 are obtained by additive manufacturing techniques 3D printing. The upper end part 2 is approximately annular and is upwards arched in a dome shape on a sagittal plane, the upper end surface 12 is designed and molded through data acquired by three-dimensional CT scanning of the adaptive cervical vertebra, the upper layer is a porous structure suitable for bone growth, the other end is regularly spliced with a titanium reticular column, and four latch structures 21 are extended out of the inner wall to clamp the joint part. The lower end part 3 is also annular and is in an inclined plane shape inclined towards the back upper side on the sagittal plane, the lower end surface 32 is also designed and molded through data acquired by three-dimensional CT scanning of the adaptive cervical vertebra and is completely attached to the upper end plate of the lower vertebral body, the upper layer is in a porous structure suitable for bone growth, the other end of the upper layer is also orderly spliced with the reticular cylinder, and the inner wall of the upper layer extends out of four latch structures 31 to clamp the joint part. The titanium mesh column 1 may be a kit comprising a plurality of dimensional specifications.
According to the corresponding data of the vertebral body, the upper and lower end plates and the surgical pressure reduction groove, the common specification of the spinal titanium mesh bone grafting fusion cage is as follows: the height of the titanium reticular cylinder 1 is 20-50 mm, the maximum transverse diameter is 10-30 mm, the maximum front and back diameter is 10-30 mm, the thickness is 1-2 mm, and the side length of the rhombic or triangular hollow 1.1 is 4-6 mm. The size and shape of the upper end portion 2 and the lower end portion 3 are designed and 3D printed from pre-operative CT three-dimensional scan data of each patient. The thickness of the porous layer on the surface is 2mm, the thickness of the latch is 2mm, and the height is 2-3 mm.
During manufacturing, the titanium mesh column 1 is generally produced by a common material reducing manufacturing process, and can be manufactured by 3D printing, but the cost is high. When the upper end part 2 and the lower end part 3 are manufactured, three-dimensional scanning such as CT (computed tomography) needs to be carried out on the upper end plate and the lower end plate of the cervical vertebra to be adapted to obtain shape data of the upper end plate and the lower end plate, and then the upper end part and the lower end part are manufactured through 3D printing according to the shape data of the upper end plate and the lower end plate, so that the upper end surface and the lower end surface of the upper end part and. Titanium mesh cylinders are typically made of titanium alloys.
Taking cervical vertebra operation as an example, when in use, firstly, the anterior cervical vertebra sub-total resection decompression operation is carried out according to the conventional operation steps, after the complete decompression and the trimming of a decompression groove are finished, a small opening is bitten on the lower edge of the vertebra right in front of the upper vertebra by using a gun-shaped rongeur, a Casper spreader is properly spread, the length and the transverse diameter of the decompression groove are measured, a titanium mesh column body 1 with a proper model is selected and spliced with an upper end part 2 and a lower end part 3 to form a titanium mesh bone grafting fusion device whole, the length of the titanium mesh bone grafting fusion device is just matched with the decompression groove, broken bone blocks are filled, the titanium mesh bone grafting fusion device is planted into the decompression groove by using a vascular forceps or a holder, and the spreader is loosened, so that the latch mark in front of the titanium mesh bone grafting fusion device is embedded into the bone on the lower edge of. Conventionally installing a anterior cervical titanium steel plate to fix the operation segment, and carrying out perspective inspection on whether the position of the titanium mesh bone grafting fusion cage is ideal.
The utility model can not only effectively recover the physiological curvature and the intervertebral height of the cervical vertebra, but also the appearance of the utility model is more in line with the morphological characteristics of the cervical vertebra centrum end plate, the contact surface of the end plate is enlarged, and the problem that the existing titanium mesh bone grafting fusion cage is easy to sink after operation is solved; the porous surface of the bone fusion cage can play a role in promoting fusion and bone formation by controlling the porosity, and further improves the fusion rate and the surgical curative effect. The utility model has simple operation and safe use, and is suitable for the secondary total resection and decompression of vertebral bodies for bone grafting fusion.
The foregoing has described in detail preferred embodiments of the present invention. It should be understood that numerous modifications and variations can be devised by those skilled in the art in light of the teachings of the present invention without undue experimentation. Therefore, the technical solutions that can be obtained by a person skilled in the art through logic analysis, reasoning or limited experiments based on the prior art according to the concepts of the present invention should be within the scope of protection defined by the claims.
Claims (4)
1. The titanium mesh bone grafting fusion cage is characterized by comprising a titanium mesh column and an independent end part assembled on the titanium mesh column, wherein the shape of the end face of the end part is set to be correspondingly attached to an end plate of cervical vertebra to be adapted, and the shape of the end face is determined by three-dimensional scanning of the end plate; the end part comprises an upper end part and a lower end part, the upper end surface of the upper end part is respectively attached to the lower surface of the upper vertebral end plate, and the lower end surface of the lower end part is attached to the upper surface of the lower vertebral end plate.
2. The spinal titanium mesh bone graft fusion device of claim 1, wherein said end surface is 3D printed.
3. The spinal titanium mesh bone graft fusion device according to claim 1, wherein said end portion and said titanium mesh column are assembled by a latch structure.
4. The spinal titanium mesh bone graft fusion device of claim 1, wherein said end surface is of a porous structure.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN201822124590.5U CN210277413U (en) | 2018-12-18 | 2018-12-18 | Spinal titanium mesh bone grafting fusion cage |
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| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN201822124590.5U CN210277413U (en) | 2018-12-18 | 2018-12-18 | Spinal titanium mesh bone grafting fusion cage |
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| CN210277413U true CN210277413U (en) | 2020-04-10 |
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| CN201822124590.5U Active CN210277413U (en) | 2018-12-18 | 2018-12-18 | Spinal titanium mesh bone grafting fusion cage |
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Cited By (1)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN111329628A (en) * | 2018-12-18 | 2020-06-26 | 上海交通大学医学院附属第九人民医院 | A kind of spine titanium mesh bone graft cage and manufacturing method thereof |
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2018
- 2018-12-18 CN CN201822124590.5U patent/CN210277413U/en active Active
Cited By (1)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN111329628A (en) * | 2018-12-18 | 2020-06-26 | 上海交通大学医学院附属第九人民医院 | A kind of spine titanium mesh bone graft cage and manufacturing method thereof |
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