CN107607452A - A kind of method that porous prosthese porosity is determined by stress distribution - Google Patents
A kind of method that porous prosthese porosity is determined by stress distribution Download PDFInfo
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- CN107607452A CN107607452A CN201710710783.6A CN201710710783A CN107607452A CN 107607452 A CN107607452 A CN 107607452A CN 201710710783 A CN201710710783 A CN 201710710783A CN 107607452 A CN107607452 A CN 107607452A
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Abstract
The invention discloses a kind of method that porous prosthese porosity is determined by stress distribution.Include the extraction of CT data；Reverse modeling；Finite element dynamics are simulated；Position to be repaired is divided into by some stress areas according to stress distribution cloud atlas, and obtains zone leveling maximum stress value corresponding to each stress area, using the foundation of the designed porosity as loose structure；It is compressed experimental fit and draws the loose structure shape and the compressive yield stress formula of the Gibson Ashby porous metal materials under medical metal implant material；Using zone leveling maximum stress value to be oriented to, loose structure porosity value corresponding to the domain of different stressed zone under selected loose structure form and material is inversely calculated with Gibson Ashby formula.This method is applicable not only to mandibular prostheses difference defect, is also applied for the determination of the porosity parameter of other position metal prostheses loose structures.
Description
Technical field
The present invention relates to medical prosthesis field, more particularly to a kind of side that porous prosthese porosity is determined by stress distribution
Method.
Background technology
With the development of Scientific Medical technology, mandibular defect, missing are repaired this kind of complicated operation and also gradually improved.Mesh
Preceding mandible growth using it is more be to intercept people's autologous bone (such as fibula) under the fixation that prefabricated titanium plate and titanium are followed closely to be good for both ends
The method that health jaw bone parts are attached.Though such a method is not easy rejection and can realize good synosteosis, bone resource-constrained,
To taking bony site to cause damage, formalness is not easy to recover.
In recent years, scholars have found that some porous metal materials such as POROUS TITANIUM, porous nickel-titanium etc. are that the ideal of human body bone is replaced
Generation, loose structure can be effectively facilitated Bone Ingrowth and synosteosis, with the development of increases material manufacturing technology, emerged some on
The design of porous mandibular prostheses.
One of the characteristics of these designs are present is design philosophy and guidance method without system, it is impossible to is provided extensive
The property used for reference.In addition, existing design, often using homogeneous aperture, the loose structure of porosity distribution, stress is less to have part ownership
With loose structure intensive as stress major part, so as to result in the waste of these part materials.
The content of the invention
The shortcomings that it is an object of the invention to overcome above-mentioned prior art and deficiency, there is provided one kind is determined more by stress distribution
The method of hole prosthese porosity.
The present invention is achieved through the following technical solutions：
A kind of method that porous prosthese porosity is determined by stress distribution, comprises the following steps：
Step 1：CT data are extracted；Patient's limbs CT scan data is imported into mimics10.0 softwares, carries out the limbs
Position to be repaired (such as mandibular) model extraction；
Step 2：Reverse modeling；The tringle coal at position to be repaired is imported into geomagic studio softwares to carry out
Reverse modeling, obtain the position physical model to be repaired of IGS forms；
Step 3：Finite element dynamics are simulated；It is limited that the site model to be repaired of IGS forms is imported into the progress of ABAQUS softwares
First mechanical simulation is to obtain stress distribution cloud atlas；
Step 4：Position to be repaired is divided into by some stress areas according to stress distribution cloud atlas, and obtains each stressed zone
Zone leveling maximum stress value corresponding to domain, using the foundation of the designed porosity as loose structure；
Step 5：A kind of arbitrarily selected loose structure shape and medical metal implant material, are compressed experimental fit
Draw the loose structure shape and the compression yield of the Gibson-Ashby porous metal materials under medical metal implant material
Stress formula；
Step 6：Using zone leveling maximum stress value to be oriented to, inversely calculated with Gibson-Ashby formula selected
Loose structure porosity value corresponding to the domain of different stressed zone under loose structure form and material.
Reverse modeling described in above-mentioned steps two is specifically, by the position triangle to be repaired by the extraction of mimics10.0 softwares
Patch model imports geomagic studio softwares, smoothed denoising, editor's contour line, constructing curve piece, fitting surface piece behaviour
Make carry out reverse modeling, obtain the position physical model to be repaired of IGS forms.
Position to be repaired refers to mandible model described in above-mentioned steps three；The finite element dynamics simulation is by IGS forms
Mandible model import ABAQUS softwares and carry out finite element dynamics simulation, simulation mandible model is under central occlusion state
Stressing conditions, obtain stress distribution cloud atlas.
Loose structure shape described in above-mentioned steps five and the optional titanium alloy of medical metal implant material are simply octahedra.
Loose structure shape described in above-mentioned steps five and medical metal implant material, it is using SLM methods shaping hole
Four groups of selected loose structures that rate is 60%, 70%, 80%, 90%, and its aperture is met 300~1000 μm, it is carried out
Compression experiment is to be fitted the Gibson-Ashby porous metal material compressive yield stress formula drawn under the structure and material；
The compressive yield stress formula of Gibson-Ashby porous metal materials is
σc=A σs(1-f)2
Wherein, A is the strength factor of porous material, and σ s are the yield strength of matrix material, and f is the hole of loose structure
Rate；
The data obtained with compression experiment are carried out to the compressive yield stress formula of Gibson-Ashby porous metal materials
Curve matching, the structure and the compressive yield stress strength factor of the Gibson-Ashby porous metal materials under material can be obtained
A；
Loose structure porosity value f value can be expressed as follows
F=1- (σc/Aσs)1/2
Using the maximum mean stress value in different stressed zone domain to be oriented to, the pressure of Gibson-Ashby porous metal materials is utilized
Contracting yield stress formula backwards calculation draws loose structure porosity value f corresponding to the domain of different stressed zone.
Described in above-mentioned steps six based on the maximum mean stress value in some regions, according to the structure that draws of fitting and
Gibson-Ashby porous metal material compressive yield stress formula under material, are calculated more corresponding to the domain of different stressed zone
Pore structure porosity value.
The present invention is had the following advantages and effect relative to prior art：
The method proposed by the present invention that porous mandibular prostheses porosity is determined by stress distribution, be applicable not only to it is porous under
The establishment of the loose structure porosity parameter of jawbone prosthese, the porous prosthese porosity parameter at other positions of human body is also applied for,
It is the loose structure porosity choosing method of a system.
Meanwhile determining porous mandibular prostheses porosity by stress distribution so that the larger position of stress uses intensive hole,
Stress smaller part position uses sparse hole, more rationally efficiently realizes the utilization of metal material, avoids waste on the whole.
Brief description of the drawings
Fig. 1 is the method flow diagram that the present invention is determined porous prosthese porosity by stress distribution.
Embodiment
The present invention is more specifically described in detail with reference to specific embodiment.
Embodiment
A head CT scan data is taken, is conducted into mimics10.0 softwares, individually extracts the part of its mandibular
Data, obtain mandibular tringle coal.
The mandibular tringle coal extracted is imported into geomagic studio softwares, smoothed denoising, editor's wheel
The operation of the reverse modelings such as profile, constructing curve piece, fitting surface piece obtains the mandibular physical model of IGS forms.
The mandible model of IGS forms is imported into ABAQUS softwares and carries out finite element dynamics simulation.
Because the loose structure part of mandibular prostheses is primarily used to the replacement of cancellous bone, therefore in ABAQUS softwares
Modulus of elasticity of the modulus of elasticity 1370MPa of cancellous bone as the mandible model should be selected by setting during cast material attribute.
Again because the motion state of mandibular when human body is chewed often is central occlusion state, therefore main analog of the present invention is just
Biomethanics state during middle interlocking pattern, to masseter, temporalis, musculus pterygoideus medialis, the unit at lateral pterygoid muscle attachment enters row constraint, to not
The loading of the chewing simulating power of certain numerical value is carried out with tooth position, draws mandibular stress distribution cloud atlas.
According to stress distribution cloud atlas of the mandibular drawn under central occlusion state, mandibular is subjected to stress value area
Domain.
In view of mandibular some extreme stressing conditions that may be present, safety coefficient 2.8 can be multiplied by be on the safe side
The maximum mean stress value in different stressed zone domain is obtained, the foundation chosen as loose structure Pore genesis.
Selection for loose structure shape, however, it would be possible to appoint and take a kind of loose structure, by its aperture and hole
The adjustment of rate parameter obtains the maximum pore rate structure for being adapted to different stressed zone domain.
For the porous shape that this research uses to be simple octahedra, the material of selection is medical titanium alloy, designs and uses SLM
It is molded the simply octahedra loose structure of one group of titanium alloy that percent porosity is 60,70,80,90.
Experiment is compressed to one group of loose structure of shaping.The compression yield of Gibson-Ashby porous metal materials should
Power formula is
σc=A σs(1-f)2
Wherein A is the strength factor of porous material, and σ s are the yield strength of matrix material, and f is the porosity of loose structure.
The data obtained with compression experiment are carried out to the compressive yield stress formula of Gibson-Ashby porous metal materials
Curve matching, the structure and the compressive yield stress intensity system of the Gibson-Ashby porous metal materials under material can be obtained
Number A.
Loose structure porosity value f value can be expressed as follows
F=1- (σc/Aσs)1/2
Using the maximum mean stress value in different stressed zone domain to be oriented to, the pressure of Gibson-Ashby porous metal materials is utilized
Contracting yield stress formula backwards calculation draws loose structure porosity value f corresponding to the domain of different stressed zone.
The present invention is applicable not only to mandibular difference defect, is also applied for human body other porous knots of position metal prostheses
The determination of the porosity parameter of structure.The present invention is by obtaining answering for mandibular to the mechanical simulation under mandibular central occlusion state
Power is distributed, and mandibular is divided into several stress gradient regions according to stress distribution feature, is put down with the maximum in each region
Equal stress value is foundation, the method being fitted using the Gibson-Ashby loose structures compression formula to classics, final meter
Calculation obtains the porosity that yield strength is adapted to each stress gradient region, is mandibular or even other position porous metals prostheses
Design provides scientific and reasonable mentality of designing.
As described above, the present invention can be better realized.
Embodiments of the present invention are simultaneously not restricted to the described embodiments, other any Spirit Essences without departing from the present invention
With made under principle change, modification, replacement, combine, simplification, should be equivalent substitute mode, be included in the present invention's
Within protection domain.
Claims (6)
- A kind of 1. method that porous prosthese porosity is determined by stress distribution, it is characterised in that：Comprise the following steps：Step 1：CT data are extracted；Certain limbs CT scan data of patient is imported into mimics10.0 softwares, carries out the limbs The extraction of site model to be repaired；Step 2：Reverse modeling；The tringle coal at position to be repaired is imported into geomagic studio softwares to carry out inversely Modeling, obtains the position physical model to be repaired of IGS forms；Step 3：Finite element dynamics are simulated；The site model to be repaired of IGS forms is imported into ABAQUS softwares and carries out limited elementary force Simulation is learned to obtain stress distribution cloud atlas；Step 4：Position to be repaired is divided into by some stress areas according to stress distribution cloud atlas, and obtains each stress area pair The zone leveling maximum stress value answered, using the foundation of the designed porosity as loose structure；Step 5：A kind of arbitrarily selected loose structure shape and medical metal implant material, are compressed experimental fit and draw The loose structure shape and the compressive yield stress of the Gibson-Ashby porous metal materials under medical metal implant material Formula；Step 6：Using zone leveling maximum stress value to be oriented to, inversely calculated with Gibson-Ashby formula selected porous Loose structure porosity value corresponding to the domain of different stressed zone under structural form and material.
- 2. the method for porous prosthese porosity is determined by stress distribution according to claim 1, it is characterised in that：Step 2 institute Stating reverse modeling is specifically, and the position tringle coal to be repaired by the extraction of mimics10.0 softwares is imported into geomagic Studio softwares, smoothed denoising, editor's contour line, constructing curve piece, the operation of fitting surface piece carry out reverse modeling, obtained The position physical model to be repaired of IGS forms.
- 3. the method for porous prosthese porosity is determined by stress distribution according to claim 1, it is characterised in that：Step 3 institute State position to be repaired and refer to mandible model；The finite element dynamics simulation is by the mandible model importing of IGS forms ABAQUS softwares carry out finite element dynamics simulation, stressing conditions of the simulation mandible model under central occlusion state, are answered Power cloud charts.
- 4. the method according to claim 1 that porous mandibular prostheses porosity is determined by stress distribution, it is characterised in that： Loose structure shape described in step 5 and the optional titanium alloy of medical metal implant material are simply octahedra.
- 5. the method according to claim 1 that porous mandibular prostheses porosity is determined by stress distribution, it is characterised in that： Loose structure shape described in step 5 and medical metal implant material, be use SLM methods be molded porosity for 60%, 70%th, four groups of 80%, 90% select loose structure, and make its aperture meet 300~1000 μm, it is compressed experiment with Fitting draws the Gibson-Ashby porous metal material compressive yield stress formula under the structure and material；The compressive yield stress formula of Gibson-Ashby porous metal materials isσc=A σs(1-f)2Wherein, A is the strength factor of porous material, and σ s are the yield strength of matrix material, and f is the porosity of loose structure；The data obtained with compression experiment carry out curve to the compressive yield stress formula of Gibson-Ashby porous metal materials Fitting, the structure and the compressive yield stress strength factor A of the Gibson-Ashby porous metal materials under material can be obtained；Loose structure porosity value f value can be expressed as followsF=1- (σc/Aσs)1/2Using the maximum mean stress value in different stressed zone domain to be oriented to, bent using the compression of Gibson-Ashby porous metal materials Take stress formula backwards calculation and draw loose structure porosity value f corresponding to the domain of different stressed zone.
- 6. the method according to claim 1 that porous mandibular prostheses porosity is determined by stress distribution, it is characterised in that： Described in step 6 based on the maximum mean stress value in some regions, under the structure and material drawn according to fitting Gibson-Ashby porous metal material compressive yield stress formula, are calculated loose structure hole corresponding to the domain of different stressed zone Gap rate value.
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Cited By (10)
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| CN109249022A (en) * | 2018-09-21 | 2019-01-22 | 华中科技大学 | A kind of double graded metal porous materials and preparation method thereof |
| CN110680567A (en) * | 2019-11-07 | 2020-01-14 | 江苏科技大学 | Method and system for manufacturing porous tibial implant |
| CN111728742A (en) * | 2020-06-30 | 2020-10-02 | 蒋青 | Porous meniscus substitute modeling and preparation method thereof |
| CN112199790A (en) * | 2020-09-29 | 2021-01-08 | 华侨大学 | Sole with regular polyhedron porous heel area filling structure and design method thereof |
| CN112711885A (en) * | 2020-12-30 | 2021-04-27 | 湖南普林特医疗器械有限公司 | Reverse optimization method for porous structure material design |
| CN112966398A (en) * | 2021-04-13 | 2021-06-15 | 宁波大学 | Voronoi porous gradient structure generation method based on stress distribution |
| CN114632951A (en) * | 2022-03-21 | 2022-06-17 | 河北科技大学 | Structure-component composite regulation and control method for compressive strength of selective laser melting titanium alloy |
| CN116663086A (en) * | 2023-07-28 | 2023-08-29 | 南昌东森牙科器材有限公司 | Method for reversely constructing implant based on biomechanical analysis grid cell mapping |
| CN117257529A (en) * | 2023-11-21 | 2023-12-22 | 北京力达康科技有限公司 | Tantalum coating hip joint prosthesis system |
| CN112199790B (en) * | 2020-09-29 | 2024-06-07 | 华侨大学 | Regular polyhedron porous heel area filling structure sole and design method thereof |
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Cited By (14)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN109249022A (en) * | 2018-09-21 | 2019-01-22 | 华中科技大学 | A kind of double graded metal porous materials and preparation method thereof |
| CN110680567A (en) * | 2019-11-07 | 2020-01-14 | 江苏科技大学 | Method and system for manufacturing porous tibial implant |
| CN111728742A (en) * | 2020-06-30 | 2020-10-02 | 蒋青 | Porous meniscus substitute modeling and preparation method thereof |
| CN111728742B (en) * | 2020-06-30 | 2023-03-10 | 蒋青 | Porous meniscus substitute modeling and preparation method thereof |
| CN112199790B (en) * | 2020-09-29 | 2024-06-07 | 华侨大学 | Regular polyhedron porous heel area filling structure sole and design method thereof |
| CN112199790A (en) * | 2020-09-29 | 2021-01-08 | 华侨大学 | Sole with regular polyhedron porous heel area filling structure and design method thereof |
| CN112711885A (en) * | 2020-12-30 | 2021-04-27 | 湖南普林特医疗器械有限公司 | Reverse optimization method for porous structure material design |
| CN112711885B (en) * | 2020-12-30 | 2022-12-13 | 湖南华翔医疗科技有限公司 | Reverse optimization method for porous structure material design |
| CN112966398A (en) * | 2021-04-13 | 2021-06-15 | 宁波大学 | Voronoi porous gradient structure generation method based on stress distribution |
| CN114632951A (en) * | 2022-03-21 | 2022-06-17 | 河北科技大学 | Structure-component composite regulation and control method for compressive strength of selective laser melting titanium alloy |
| CN116663086B (en) * | 2023-07-28 | 2024-05-28 | 南昌东森牙科器材有限公司 | Method for reversely constructing implant based on biomechanical analysis grid cell mapping |
| CN116663086A (en) * | 2023-07-28 | 2023-08-29 | 南昌东森牙科器材有限公司 | Method for reversely constructing implant based on biomechanical analysis grid cell mapping |
| CN117257529A (en) * | 2023-11-21 | 2023-12-22 | 北京力达康科技有限公司 | Tantalum coating hip joint prosthesis system |
| CN117257529B (en) * | 2023-11-21 | 2024-02-09 | 北京力达康科技有限公司 | Tantalum coating hip joint prosthesis system |
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