Critical evaluation of known bone material properties to realize anisotropic FE-simulation of the proximal femur

Wirtz, Dieter Christian; Schiffers, Norbert; Pandorf, Thomas; Radermacher, Klaus; Weichert, Dieter; Forst, Raimund

doi:10.1016/s0021-9290(00)00069-5

Cited by 428 publications

(297 citation statements)

References 35 publications

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“…This is unlike the cranial vault in which E 1 and E 2 are often similar and less in magnitude than E 3 (Peterson and Dechow, 2003). The cranial vault is unusual in this regard in that elastic properties superficially resemble the transverse isotropy of postcranial long bones (Katz and Meunier, 1987;Cowin and Hart, 1989;Weiner et al, 1999;Wirtz et al, 2000).…”

Section: Discussionmentioning

confidence: 94%

Material properties of the dentate maxilla

2006

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The aim of this study was to determine regional variability of material properties in the dentate maxilla. Cortical samples were removed from 15 sites of 15 adult dentate fresh-frozen maxillas. Cortical thickness, density, elastic properties, and the direction of greatest stiffness were obtained. Results showed that cortical bone in the alveolar region tended to be thicker, less dense, and less stiff. Cortical bone from the body of the maxilla was thinner, denser, and stiffer. Palatal cortical bone was intermediate in some features but overall was more similar to cortical bone from the alveolar region. The principal axes of stiffness varied regionally. The regions with the greatest consistency were the alveolar area and the frontomaxillary pillar, where the grain of the cortical bone was aligned vertically from the incisors to the medial external aspect of the orbit. Elastic properties in the human maxilla, especially the orientation of the principal axes of stiffness, were more variable than in the mandible. Incorporation of these properties into finite-element models should improve their accuracy and reliability. Anat Rec Part A, 288A:962-972, 2006. Key words: ultrasonic; cortical bone; biomechanics; function; finite-element modelingIn comparison to the mandible, understanding the biomechanics of the maxilla presents greater difficulties. The complexity of the maxilla results from the large number of sutures between the maxilla and bones contiguous with it and the sinuses that occupy almost the entire internal region of the body of the maxilla. The bone's unique gross morphology and shape allow for a variety of functions, including deglutition, respiration, and sensation (smell and sight), as well as serving as anchorage for a small portion of the masseter muscle. Due to this complexity, adaptation of the maxilla to function is not well understood.The maxilla is comprised of several distinct anatomical regions, including the palate, nasal floor, alveolus, and body. Crossing these regions are structures or pillars that are interpreted as supports for biting and mastication including the zygomaticomaxillary pillar, the temporozygomatic pillar, and frontomaxillary pillar (Sicher and DuBrul, 1970).Little is known experimentally about variability of the mechanical characteristics of the human dentate maxilla. In the monkey maxilla, patterns of bone strain suggest that significant loads are borne locally during mastication and biting and that bone sutures and adjacent cavities buffer occlusal forces (Saijo and Sugimuro, 1993). As occlusal forces are dispersed at different tooth positions, maxillary surfaces bend outward away from the sinuses. Presumably, mechanical stimuli caused by mastication and biting are important in the maintenance of cortical bone structure in the maxilla and result in variations of function depending on location relative to different elements of the dentition and muscle attachments.

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Section: Discussionmentioning

confidence: 94%

Material properties of the dentate maxilla

2006

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“…The evolution of the fracture is defined by the tensile and compressive plastic strains which define how the yielded material is spread after the ultimate strength is reached. Values for the density and elastic modulus for healthy, non-osteoporotic cortical and trabecular bone were taken from the literature [25,27,[30][31][32]. Young's modulus for osteoporotic bone was calculated by reducing the corresponding values of Young's modulus for healthy cortical and trabecular bone by 32% and 66% respectively.…”

Section: Methodsmentioning

confidence: 99%

Failure Analysis Following Osteochondroplasty for Hip Impingement in Osteoporotic and Non-Osteoporotic Bones

Jimenez-Cruz¹,

Mt²,

Cg³

et al. 2016

J Osteopor Phys Act

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Femoral osteochondroplasty is the most common treatment for femoroacetabular impingement (FAI). The risk of femoral neck fracture is increased following surgery and increases further when the bone is osteoporotic. The current requirement to undertake osteochondroplasty on patients with osteoporosis is forecast to increase, however, the effect of osteoporosis on the risk of postoperative fracture is currently unknown.We developed three three-dimensional (3D) finite element models using computerised tomography (CT) scan data for a hip with cam-type impingement and used them to investigate the association between osteoporosis and the increased possibility of femoral neck fracture after femoral osteochondroplasty.Femoral osteochondroplasty was performed "virtually" on the intact hip model to two different resection depths, a 'standard' (6mm) and a 'critical' resection (12mm) depth, corresponding to 18% and 36% of the overall femoral neck diameter, respectively. Cortical and trabecular bone were included in the intact and resection hip models, and material properties representing both non-osteoporotic and osteoporotic cases employed, overall, 18 scenarios were analysed. Loading corresponding to "descending stairs" and "stumbling" activities were applied in the models enabling fracture propensity to be estimated.Our model predicted that fracture propagation can occur in the bone of osteoporotic patients following osteochondroplasty during typical daily activities, such as descending stairs. 3The level of damage increases significantly when patients are subjected to high load conditions and activities, even in non-osteoporotic patients, indicating an increased likelihood of fracture occurring. In the "stumbling activity" simulation, osteoporotic trabecular bone damage volume approached 50% for the 6mm resection, rising to 70% at a resection depth of 12mm. The corresponding rise in osteoporotic cortical bone volume damage was from 6% to 10%.Our findings support the recommendation for protected weight-bearing in patients in the postoperative phase and suggest an extended period of protected weight-bearing in osteoporotic patients could be considered.

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“…An elastic modulus was subsequently assigned to each element based on 1) a previously published density-elasticity relationship (Figure 3-3a), or 2) density-elasticity relationships obtained through optimization (see Density-Elasticity Equations and Optimization). The Poisson's ratio for all elements was set to 0.3 in accordance with previous FE models of human bone (8,164,207,208). The boundary conditions of the FE models replicated the mechanical tests.…”

Section: Finite Element Modelingmentioning

confidence: 99%

Experimental validation of finite element predicted bone strain in the human metatarsal

Fung

Loundagin

Edwards

2017

Journal of Biomechanics

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The objective of this study was to verify and validate a finite element modeling routine for the human metatarsal, which is a common location for stress fractures. Experimental strain measurements on 33 human cadaveric metatarsals subject to cantilever bending were compared with strain predictions from finite element (FE) models generated from computed tomography images. For the material property assignment of the FE models, a published density-elasticity relationship was compared with density-elasticity equations developed using optimization techniques. The correlations between the measured and predicted and predicted strains were very high (r 2 ≥0.94) for all of the density-elasticity equations. However, the utilization of an optimized density-elasticity equation improved the accuracy of the finite element models, reducing the maximum error between measured and predicted strains by 10% to 20%. The finite element modeling routine could be used for investigating potential interventions to minimize metatarsal strains and the occurrence of metatarsal stress fractures.iii

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Critical evaluation of known bone material properties to realize anisotropic FE-simulation of the proximal femur

Cited by 428 publications

References 35 publications

Material properties of the dentate maxilla

Material properties of the dentate maxilla

Failure Analysis Following Osteochondroplasty for Hip Impingement in Osteoporotic and Non-Osteoporotic Bones

Experimental validation of finite element predicted bone strain in the human metatarsal

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