Development and Validation of a Three-Dimensional Finite Element Model of the Pelvic Bone

Dalstra, Michel; Huiskes, R.; Erning, L.J.T.O. van

doi:10.1115/1.2794181

Cited by 257 publications

(200 citation statements)

References 18 publications

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“…sionai finite element model (Dalstra et al, 1994). By Consisting mainly of low-density trabecular bone incorporating new information about hip joint and , which by itself is not strong muscle loads, it was our intention to prescribe external enough by far to withstand such high loads, it is totally loading as realistically as possible.…”

Section: Introductionmentioning

confidence: 99%

Load transfer across the pelvic bone

Dalstra

Huiskes

1995

Journal of Biomechanics

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309

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Earlier experimental and finite element studies notwithstanding, the load transfer and stress distribution in the pelvic bone and the acetabulum in normal conditions are not well understood. This hampers the development of orthopaedic reconstruction methods. The present study deals with more precise finite element analyses of the pelvic bone, which are used to investigate its basic load transfer and stress distributions under physiological loading conditions. The analyses show that the major part of the load is transferred through the cortical shell. Although the magnitude of the hip joint force varies considerably, its direction during normal walking remains pointed into the anterior/superior quadrant of the acetabulum. Combined with the fact that the principal areas of support for the pelvic bone are the sacro-iliac joint and the pubic symphysis, this caused the primary areas of load transfer to be found in the superior acetabular rim, the incisura ischiadaca region and, to a lesser extent, the pubic bone. Due to the 'sandwich' behavior of the pelvic bone, stresses in the cortical shell are about 50 times higher than in the underlying trabecular bone (15 to 20 MPa vs 0.3-0.4 MPa at one-legged stance). Highest intraarticular pressures are found to occur during one-legged stance and measured about 9 MPa. During the swing phase, these pressures decrease less than linearly with the magnitude of the hip joint force. Muscle forces have a stabilizing effect on the pelvic load transfer. Analysis without muscle forces show that at some locations stresses are actually higher than when muscle forces are included.

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Section: Introductionmentioning

confidence: 99%

Load transfer across the pelvic bone

Dalstra

Huiskes

1995

Journal of Biomechanics

Self Cite

309

240

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“…The incisor's solid model was generated using literature data 21) for dentin and enamel in terms of internal volumes and morphologies, while the external shape of the maxillary central incisor was obtained by laser-based 3D digitizing (Cyberware Inc., Monterey, CA, USA) of a plaster cast (Thanaka manufacturer, Tokyo, Japan). Scanned profiles were assembled into a 3D wire frame structure using a 3D CAD tool (AutoCAD 12, Autodesk Inc., San Rafael, CA, USA) and exported into a 3D parametric solid modeler (ProEngineering 16.0, Parametric Technologies, Needham, MA, USA).…”

Section: Generation Of Finite Element Modelsmentioning

confidence: 99%

“…The Finite Element Analysis (FEA) tool allows researchers to achieve detailed evaluations of the mechanical behaviors of biologic and/or restorative systems, even in nonhomogeneous bodies 11,[20][21][22] . If correctly validated, the FEA could be useful in optimizing restorative design criteria and material choice and in predicting potential fracture under given circumstances 11) .…”

Section: Introductionmentioning

confidence: 99%

Non-linear Viscoelastic Finite Element Analysis of the Effect of the Length of Glass Fiber Posts on the Biomechanical Behaviour of Directly Restored Incisors and Surrounding Alveolar Bone

et al. 2008

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The study aimed at estimating the effect of insertion length of posts with composite restorations on stress and strain distributions in central incisors and surrounding bone. The typical, average geometries were generated in a FEA environment. Dentin was considered as an elastic orthotropic material, and periodontal ligament was coupled with nonlinear viscoelastic mechanical properties. The model was then validated with experimental data on displacement of incisors from published literature. Three post lengths were investigated in this study: root insertion of 5, 7, and 9 mm. For control, a sound incisor model was generated. Then, a tearing load of 50 N was applied to both sound tooth and simulation models. Post restorations did not seem to affect the strain distribution in bone when compared to the control. All simulated post restorations affected incisor biomechanics and reduced the root ' s deforming capability, while the composite crowns underwent a higher degree of deformation than the sound crown. No differences could be noticed in incisor stress and strain. As for the influence of post length, it was not shown to affect the biomechanics of restored teeth.

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“…To compensate for the lack of structural detail, this approach enhances the accuracy of the prediction by using apparent, nonlinear material properties (Keyak 2001;Schileo et al 2008) and elastic moduli computed from local bone mineral density values (Dalstra et al 1995;Keyak et al 1998;Kopperdahl & Keaveny 1998;Kopperdahl et al 2002;Taddei et al 2004). Typically, these models attempt to map local values of Young's moduli according to the local value of bone mineral density.…”

Section: Organ-level Fe Modelsmentioning

confidence: 99%

Multiscale modelling and nonlinear finite element analysis as clinical tools for the assessment of fracture risk

Christen

Webster

Müller

2010

Phil. Trans. R. Soc. A.

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The risk of osteoporotic fractures is currently estimated based on an assessment of bone mass as measured by dual-energy X-ray absorptiometry. However, patient-specific finite element (FE) simulations that include information from multiple scales have the potential to allow more accurate prognosis. In the past, FE models of bone were limited either in resolution or to the linearization of the mechanical behaviour. Now, nonlinear, high-resolution simulations including the bone microstructure have been made possible by recent advances in simulation methods, computer infrastructure and imaging, allowing the implementation of multiscale modelling schemes. For example, the mechanical loads generated in the musculoskeletal system define the boundary conditions for organ-level, continuum-based FE models, whose nonlinear material properties are derived from microstructural information. Similarly microstructure models include tissuelevel information such as the dynamic behaviour of collagen by modifying the model's constitutive law. This multiscale approach to modelling the mechanics of bone allows a more accurate characterization of bone fracture behaviour. Furthermore, such models could also include the effects of ageing, osteoporosis and drug treatment. Here we present the current state of the art for multiscale modelling and assess its potential to better predict an individual's risk of fracture in a clinical setting.

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Development and Validation of a Three-Dimensional Finite Element Model of the Pelvic Bone

Cited by 257 publications

References 18 publications

Load transfer across the pelvic bone

Load transfer across the pelvic bone

Non-linear Viscoelastic Finite Element Analysis of the Effect of the Length of Glass Fiber Posts on the Biomechanical Behaviour of Directly Restored Incisors and Surrounding Alveolar Bone

Multiscale modelling and nonlinear finite element analysis as clinical tools for the assessment of fracture risk

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