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Revista de Odontologia da UNESP

versão On-line ISSN 1807-2577

Rev. odontol. UNESP vol.45 no.1 Araraquara jan./fev. 2016  Epub 19-Jan-2016

http://dx.doi.org/10.1590/1807-2577.06715 

Original Articles

Modeling and validation of a 3D premolar for finite element analysis

Modelagem e validação 3D de um premolar para análise de elementos finitos

Letícia Brandão DURANDa  * 

Jackeline Coutinho GUIMARÃESb 

Sylvio MONTEIRO JUNIORc 

Luiz Narciso BARATIERIc 

aUFSM – Universidade Federal de Santa Maria, Santa Maria, RS, Brasil

bUFES – Universidade Federal do Espírito Santo, Vitoria, ES, Brasil

cUFSC – Universidade Federal de Santa Catarina, Florianópolis, SC, Brasil


Abstract

Introduction

The development and validation of mathematical models is an important step of the methodology of finite element studies.

Objective

This study aims to describe the development and validation of a three-dimensional numerical model of a maxillary premolar for finite element analysis.

Material and method

The 3D model was based on standardized photographs of sequential slices of an intact premolar and generated with the use of SolidWorks Software (Dassault, France). In order to validate the model, compression and numerical tests were performed. The load versus displacement graphs of both tests were visually compared, the percentage of error calculated and homogeneity of regression coefficients tested.

Result

An accurate 3D model was developed and validated since the graphs were visually similar, the percentage error was within acceptable limits, and the straight lines were considered parallel.

Conclusion

The modeling procedures and validation described allows the development of accurate 3D dental models with biomechanical behavior similar to natural teeth. The methods may be applied in development and validation of new models and computer-aided simulations using FEM.

Descriptors:  Computer simulation; validation studies; finite element analysis

Resumo

Introdução

O desenvolvimento e validação de modelos matemáticos é uma importante etapa da metodologia de estudos de elementos finitos.

Objetivo

Este estudo tem o objetivo descrever o desenvolvimento e validação de um modelo numérico tridimensional de um pré-molar superior para análise em elementos finitos.

Material e método

Fotografias padronizadas de cortes sequenciais de um pré-molar hígido serviram de referência para o desenvolvimento do modelo 3D, que foi construído por meio do programa SolidWorks (Dassault, França). A fim de validar o modelo testes de compressão e simulação numérica foram realizados. Os gráficos de carga versus deslocamento de ambos os ensaios foram comparados visualmente, a percentagem de erro calculada e homogeneidade dos coeficientes de regressão testada.

Resultado

Um modelo 3D preciso foi desenvolvido e validado, uma vez que os gráficos apresentavam-se visualmente semelhantes, o percentual de erro ficou dentro dos limites aceitáveis​​ e as retas foram consideradas paralelas.

Conclusão

Os procedimentos de modelagem e validação descritos permitem o desenvolvimento de modelos dentários 3D precisos com comportamento biomecânico semelhante aos dentes naturais. Os métodos podem ser aplicados no desenvolvimento e validação de novos modelos e estudos de simulações computacionais por meio do MEF.

Descritores:  Simulação por computador; estudos de validação; análise de elementos finitos

INTRODUCTION

The finite element method (FEM) was developed in the 1950s, initially for application in aerospace engineering. In Dentistry, the technique began to be studied in the 1970s1. The methodology has great versatility and analyzes the stresses produced in numerical models; it can be applied in research fields such as implantology2, orthodontics3, it can also simulate thermal4 mechanical cycling5, water sorption6 and polymerization shrinkage7 and can also be applied in cavity optimization8 and cusp bending9 studies.

One of the main advantages of finite element analysis (FEA) is its non-destructive and noninvasive nature3, it can also access stress distribution in inaccessible areas7. It costs less than laboratory studies and it overcomes the ethical issues surrounding the use and collection of extracted teeth for research10.

FEM offers a valid method for the analysis of complex situations in which the variables can be changed simulating various clinical conditions3. Improved computer and modeling techniques provide reliable and accurate approach in biomechanics11. Geometrically complex systems can be modeled and the accurate representation of each tissue is limited only by computational resources and modeling ability12.

The development of a numerical model is a complex task, particularly in multicomponent biological structures such as teeth and supporting tissues. Accurate models should predict the behavior of the structure that is represented13. In order to make predictions the model has to be validated14. The validity of the 3D model depends on the geometric modeling techniques applied during the construction15, correct geometry and assigned materials properties16. Furthermore, the accuracy of FE results is also dependent on element and node size, materials properties, boundary conditions and applied loads and validation against experimental data16.

There are different ways to perform validation. Direct validation requires comparison of computer simulation with in vitro mechanical tests performed at either the same or a closely collaborating institution. In indirect validation, comparison is performed with laboratory tests or clinical studies published in the literature. The disadvantage of indirect validation is that the variables and test conditions cannot be controlled17.

The validation can be done by the comparative analysis of the fracture patterns and stress patterns observed on the experimental and numerical models10,18. Furthermore, validation can also be performed by the comparison of strain-gauge studies14 and cusp deflection in computer simulation19,20.

The association between numerical simulation and traditional mechanical tests may be the best way to study materials and techniques used in Dentistry. When the results of mechanical tests are similar to those of the simulation, the validation of the model can be confirmed10. The aim of this study was to present and describe the modeling and the direct validation of a three-dimensional numerical model of an intact maxillary premolar. The hypothesis considered was that the 3D premolar numerical model and the real dental structure would have similar mechanical behavior under the same loading conditions.

MATERIAL AND METHOD

Compression Test

For the compression test, 10 intact maxillary premolars were selected and embedded in cylinders with epoxy resin. A vertical load was applied until fracture, at speed of 1 mm/min by means of a 6-mm-diameter sphere placed on the occlusal surface of the specimen. Data were collected, mean values were obtained and a load versus displacement graphs was generated.

Computational Simulation

Numerical modeling

The three-dimensional model was based on a maxillary second premolar donated by the Department of Morphological Sciences, after approval by the Ethical Committee in Human Research of the Institution. The tooth was embedded in epoxy resin blocks and sliced into 1-mm thick sequential cross sections perpendicular to the long axis on a precision cutting machine.

The slices were photographed in a standardized manner and each photograph was transferred to SolidWorks Software (Waltham, Massachusetts, USA) The external contour of all slices, as well as the internal dentin and pulp contour, were outlined and subsequently assembled. The design of the cusps and occlusal anatomy were refined with the available software tools, generating individual three-dimensional solid models of the external anatomy of the premolar, pulp and coronary portion of the dentin. The superposition of the solid components and exclusion of common structures enabled the generation of the pulpal cavity and the internal and external contour of the enamel. The cementum was not modeled because of its small dimensions and difficulty in visualizing and delimiting boundaries. The components previously constructed were positioned, aligned, brought together, and assembled in an assembly workbench to generate a 3D model of a maxillary premolar composed of enamel, dentin, pulp cavity and pulp.

A cylinder measuring 20 mm height and 18 mm in internal diameter was built with the same program. Procedures of superposition and subtraction of the cylinder and the premolar model were applied to create a representative model of the epoxy cylinder, similar to the one obtained during the preparation of specimens for compressive testing. These files were brought together and assembled, generating the representative numerical model of the test specimens used in the compressive test. A 6-mm-diameter sphere, identical to the sphere used in mechanical testing, was constructed in the SolidWorks software. This sphere was placed on the occlusal surface of the numerical model to define the locations where the load would be applied.

Finite elements modeling

The mesh was composed of tetrahedral parabolic elements and the total number of node points and elements obtained were 222,915 and 145,659, respectively (Figure 1). The level of refinement of the mesh was defined by convergence studies in the ANSYS Workbench program (Swanson Analysis Inc., Houston, PA, USA).

Figure 1 Discretization of model and boundary and loading conditions applied. 

Definition of mechanical properties

All constituents of the models were considered isotropic, elastic, and continuous. The elastic modulus and Poisson ratio of structures modeled were researched in the literature and are described in Table 1.

Table 1 Mechanical properties of the constituents of the numerical model 

Tissue/Material E ν
Enamel 72.7 GPa 0.33
Dentin 18.6 GPa 0.31
Epoxy resin 270 GPa 0.35

Definition of boundary and loading conditions

The model was constrained on the surrounding surfaces and at the base of the epoxy resin cylinder, assuming to be fixed in all directions. During computational simulation, a load of 1000 N was applied on the occlusal surface. This load was distributed linearly into 10 stages to obtain the intermediate points of displacement, which allowed the construction of a load versus displacement graph of the numerical model. The value of 1000 N was chosen based on the mean data of fracture strength obtained in a previous compressive test.

Processing and post-processing

The processing stage was also performed in the ANSYS Workbench program (Swanson Analysis Inc., Houston, PA, USA). The results were visualized by color diagram for displacement obtained during simulation.

Validation

The validation of the numerical model was performed by: a) Visual analysis of the similarity between the load versus displacement graphs of the experimental test and numerical simulation; b) Calculation of the percentage error of the regression coefficients (slopes) of the numerical and experimental equations; and c) Regression slope homogeneity test (test of parallelism) of experimental and numerical trend lines. Regression trend lines were traced to determine the equation of the straight lines in both tests (numerical and experimental). Through the equations, it was possible to obtain the regression coefficients (slopes) of the lines and latter calculate the percentage of error and test the homogeneity of regression slops (test of parallelism).

RESULT

The mean values of load and displacement from compressive strength test and numerical simulation are shown in Table 2. Superposition of load/displacement data can be visualized in Figure 2. A similar behavior between numerical and experimental tests can be identified in the visual analysis.

Table 2 Mean load and displacement values of compressive strength test and load and displacement values of numerical simulation 

Experimental Numerical
Displacement (mm) Load (N) Displacement (mm) Load (N)
0.000 12.3 0.0000 0.0
0.025 56.0 0.0145 59.2
0.050 123.3 0.0290 118.4
0.075 209.1 0.0435 177.6
0.100 308.3 0.0580 236.8
0.125 415.9 0.0725 296.0
0.150 527.0 0.0870 355.2
0.175 636.3 0.1015 414.4
0.200 738.9 0.1160 473.6
0.225 829.8 0.1305 532.8
0.250 903.8 0.1450 592.0
0.275 955.9 0.1595 651.2
0.300 981.2 0.1740 710.4
0.1885 769.6
0.2030 828.8
0.2175 888.0

Figure 2 Load versus displacement graph of numerical simulation and experimental test. 

Figure 3 shows the trend lines that determined the equation of the straight lines. The slopes of numerical and experimental equations were: a-num = 4082.8; and a-exp = 4279.3.

Figure 3 Regression trend lines of load versus displacement graph of numerical analysis and experimental test. 

The percentage error of the regression coefficients (slopes) was 4.6%. According to Lin et al.20, a percentage error of 10% is acceptable to validate numerical models. Therefore, the percentage error obtained in the present study is acceptable.

The result of the homogeneity of regression slopes (test of parallelism) show that the straight lines of experimental and numerical tests are considered parallel, which means that the numerical model and the real structure have similar behavior when subjected to the same loading conditions (Table 2).

DISCUSSION

The reliability of studies applying finite element method is related to the quality of the numerical model, the boundary and loading conditions, and properties applied during the simulation16. The validation process is an important step of the methodology and the purpose is to demonstrate that the mathematical model has the same mechanical behavior as the real physical structure17. This process indicates that the results are reliable and accurate14. Although convergence studies indicates the reliability of the model, validation assures the accuracy of the results16. Once the model is constructed and validated, new analyses can be performed by alteration of properties and loading conditions.

Only few studies address validation of numerical models in dental literature. Recently, researchers from other fields have been attending to the need to validate models12,21. There is no standard methodology that describes the validation process. Some authors use compressive strength results for validation22, while others use strain-gauges14 and data from fatigue tests10,14,18. The studies that performed validation do not describe the methodology in detail, making it difficult to reproduce most of the procedures adopted.

The present study used three parameters to validate the maxillary premolar model: a) superposition and visual comparison of load versus displacement graphs of compressive strength tests and computer simulation; b) calculation of the percentage error of the regression coefficients of the straight lines; and c) application of the homogeneity test of regression coefficients that determines the existence of parallelism between straight lines. Besides validation against experimental data carried out by the authors, further validation can be performed by experimental data available in the literature16.

The visual comparison of the graphs was performed in the studies of Ausiello et al.22-24, The calculation of percentage error was conducted by Chang et al.25 and Lin et al.20. The validation through parallelism analysis between the straight lines is less frequent. It is believed that this type of analysis is more objective because a statistical test is applied. Once parallelism is proven, the mathematical model is considered similar to the real physical structure regarding displacement when subjected to the same loading conditions.

Validation is a challenging step of FEM studies. However, the models cannot be completely validated since it is not possible to measure all the parameters that the model can predict. A limitation that should be highlighted is the fact that the validation was performed on a 3D model of a premolar embedded in epoxy resin, bone structures and periodontal ligament were not simulated. Hence validation must not be regarded as absolute proof, but an indication of the behavior of the model17.

CONCLUSION

The modeling procedures and validation described in this study support the development of accurate 3D dental models with a biomechanical behavior similar to natural teeth. The methods may be applied on construction and validation of new models and FEM computer-aided simulations.

REFERENCES

1 Farah JW, Craig RG. Distribution of stresses in porcelain-fused-to-metal and porcelain jacket crowns. J Dent Res. 1975 Mar-Apr;54(2):255-61. PMid:1054335. [ Links ]

2 Bulaqi HA, Mashhadi MM, Safari H, Samandari MM, Geramipanah F. Effect of increased crown height on stress distribution in short dental implant components and their surrounding bone: a finite element analysis. J Prosthet Dent. 2015 Jun;113(6):548-57. http://dx.doi.org/10.1016/j.prosdent.2014.11.007. PMid:25794917. [ Links ]

3 Chaudhry A, Sidhu MS, Chaudhary G, Grover S, Chaudhry N, Kaushik A. Evaluation of stress changes in the mandible with a fixed functional appliance: a finite element study. Am J Orthod Dentofacial Orthop. 2015 Feb;147(2):226-34. http://dx.doi.org/10.1016/j.ajodo.2014.09.020. PMid:25636557. [ Links ]

4 Güngör MA, Küçük M, Dündar M, Karaoğlu C, Artunç C. Effect of temperature and stress distribution on all-ceramic restorations by using a three-dimensional finite element analysis. J Oral Rehabil. 2004 Feb;31(2):172-8. http://dx.doi.org/10.1111/j.1365-2842.2004.01005.x. PMid:15009603. [ Links ]

5 Li Y, Carrera C, Chen R, Li J, Chen Y, Lenton P, et al. Fatigue failure of dentin–composite disks subjected to cyclic diametral compression. Dent Mater. 2015 Jul;31(7):778-88. http://dx.doi.org/10.1016/j.dental.2015.03.014. PMid:25958269. [ Links ]

6 Huang M, Thompson VP, Rekow ED, Soboyejo WO. Modeling of water absorption induced cracks in resin-based composite supported ceramic layer structures. J Biomed Mater Res B Appl Biomater. 2008 Jan;84(1):124-30. http://dx.doi.org/10.1002/jbm.b.30852. PMid:17497681. [ Links ]

7 Pishevar L, Ghavam M, Pishevar A. Stress analysis of two methods of ceramic inlay preparation by finite element. Indian J Dent Res. 2014 May-Jun;25(3):364-9. http://dx.doi.org/10.4103/0970-9290.138339. PMid:25098996. [ Links ]

8 Durand LB, Guimarães JC, Monteiro S Jr, Baratieri LN. Effect of ceramic thickness and composite bases on stress distribution of inlays - a finite element analysis. Braz Dent J. 2015 Mar-Apr;26(2):146-51. http://dx.doi.org/10.1590/0103-6440201300258. PMid:25831105. [ Links ]

9 Guimarães JC, Soella GG, Durand LB, Horn F, Baratieri LN, Monteiro S Jr, et al. Stress amplifications in dental non-carious cervical lesions. J Biomech. 2014 Jan;47(2):410-6. http://dx.doi.org/10.1016/j.jbiomech.2013.11.012. PMid:24315624. [ Links ]

10 Magne P. Virtual prototyping of adhesively restored, endodontically treated molars. J Prosthet Dent. 2010 Jun;103(6):343-51. http://dx.doi.org/10.1016/S0022-3913(10)60074-1. PMid:20493323. [ Links ]

11 Borcic J, Anic I, Smojver I, Catic A, Miletic I, Ribaric SP. 3D finite element model and cervical lesion formation in normal occlusion and in malocclusion. J Oral Rehabil. 2005 Jul;32(7):504-10. http://dx.doi.org/10.1111/j.1365-2842.2005.01455.x. PMid:15975130. [ Links ]

12 Dumont ER, Grosse IR, Slater GJ. Requirements for comparing the performance of finite element models of biological structures. J Theor Biol. 2009 Jan;256(1):96-103. http://dx.doi.org/10.1016/j.jtbi.2008.08.017. PMid:18834892. [ Links ]

13 Genovese K, Lamberti L, Pappalettere C. Finite element analysis of a new customized composite post system for endodontically treated teeth. J Biomech. 2005 Dec;38(12):2375-89. http://dx.doi.org/10.1016/j.jbiomech.2004.10.009. PMid:16214485. [ Links ]

14 Dordoni E, Petrini L, Wu W, Migliavacca F, Dubini G, Pennati G. Computational modeling to predict fatigue behavior of NiTi stents: what do we need? J Funct Biomater. 2015 May;6(2):299-317. http://dx.doi.org/10.3390/jfb6020299. PMid:26011245. [ Links ]

15 Chang K-H, Magdum S, Khera SC, Goel VK. An advanced approach for computer modeling and prototyping of the human tooth. Ann Biomed Eng. 2003 May;31(5):621-31. http://dx.doi.org/10.1114/1.1568117. PMid:12757205. [ Links ]

16 Kiapour A, Kiapour AM, Kaul V, Quatman CE, Wordeman SC, Hewett TE, et al. Finite element model of the knee for investigation of injury mechanisms: development and validation. J Biomech Eng. 2014 Jan;136(1):011002. http://dx.doi.org/10.1115/1.4025692. PMid:24763546. [ Links ]

17 Jones AC, Wilcox RK. Finite element analysis of the spine: towards a framework of verification, validation and sensitivity analysis. Med Eng Phys. 2008 Dec;30(10):1287-304. http://dx.doi.org/10.1016/j.medengphy.2008.09.006. PMid:18986824. [ Links ]

18 Ausiello P, Franciosa P, Martorelli M, Watts DC. Numerical fatigue 3D-FE modeling of indirect composite-restored posterior teeth. Dent Mater. 2011 May;27(5):423-30. http://dx.doi.org/10.1016/j.dental.2010.12.001. PMid:21227484. [ Links ]

19 Tajima K, Chen K-K, Takahashi N, Noda N, Nagamatsu Y, Kakigawa H. Three-dimensional finite element modeling from CT images of tooth and its validation. Dent Mater J. 2009 Mar;28(2):219-26. http://dx.doi.org/10.4012/dmj.28.219. PMid:19496403. [ Links ]

20 Lin C-L, Chang Y-H, Liu P-R. Multi-factorial analysis of a cusp-replacing adhesive premolar restoration: a finite element study. J Dent. 2008 Mar;36(3):194-203. http://dx.doi.org/10.1016/j.jdent.2007.11.016. PMid:18221831. [ Links ]

21 Czyż M, Scigała K, Jarmundowicz W, Będziński R. Numerical model of the human cervical spinal cord--the development and validation. Acta Bioeng Biomech. 2011 Dec;13(4):51-8. PMid:22339282. [ Links ]

22 Ausiello P, Apicella A, Davidson CL, Rengo S. 3D-finite element analyses of cusp movements in a human upper premolar, restored with adhesive resin-based composites. J Biomech. 2001 Oct;34(10):1269-77. http://dx.doi.org/10.1016/S0021-9290(01)00098-7. PMid:11522306. [ Links ]

23 Ausiello P, Apicella A, Davidson CL. Effect of adhesive layer properties on stress distribution in composite restorations--a 3D finite element analysis. Dent Mater. 2002 Jun;18(4):295-303. http://dx.doi.org/10.1016/S0109-5641(01)00042-2. PMid:11992906. [ Links ]

24 Ausiello P, Rengo S, Davidson CL, Watts DC. Stress distributions in adhesively cemented ceramic and resin-composite Class II inlay restorations: a 3D-FEA study. Dent Mater. 2004 Nov;20(9):862-72. http://dx.doi.org/10.1016/j.dental.2004.05.001. PMid:15451242. [ Links ]

25 Chang Y-H, Lin W-H, Kuo W-C, Chang C-Y, Lin C-L. Mechanical interactions of cuspal-coverage designs and cement thickness in a cusp-replacing ceramic premolar restoration: a finite element study. Med Biol Eng Comput. 2009 Apr;47(4):367-74. http://dx.doi.org/10.1007/s11517-008-0379-y. PMid:18679734. [ Links ]

Received: April 01, 2015; Accepted: July 30, 2015

CONFLICTS OF INTERESTS The authors declare no conflicts of interest.

*Correspondig author: Letícia Brandão Durand, UFSM – Universidade Federal de Santa Maria, Rua Tiradentes 76/304, 97050 730 Santa Maria - RS, Brasil, e-mail:leticia_durand@yahoo.com

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