Biomechanics of Trabecular Bone

Keaveny, Tony M.; Morgan, Elise F.; Niebur, Glen L.; Yeh, Oscar C.

doi:10.1146/annurev.bioeng.3.1.307

Cited by 658 publications

(436 citation statements)

References 136 publications

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“…The higher shear force profiles in the fracture group may be explained by their larger endplate angles, thereby creating larger shear force vectors, specifically at the level of fracture. Keaveny et al [33] noted that from a strength perspective, trabecular bone properties are anisotropic. Trabecular bone has a lower strength in shear force compared to compression [21].…”

Section: Discussionmentioning

confidence: 99%

The effect of osteoporotic vertebral fracture on predicted spinal loads in vivo

et al. 2006

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The aetiology of osteoporotic vertebral fractures is multi-factorial, and cannot be explained solely by low bone mass. After sustaining an initial vertebral fracture, the risk of subsequent fracture increases greatly. Examination of physiologic loads imposed on vertebral bodies may help to explain a mechanism underlying this fracture cascade. This study tested the hypothesis that model-derived segmental vertebral loading is greater in individuals who have sustained an osteoporotic vertebral fracture compared to those with osteoporosis and no history of fracture. Flexion moments, and compression and shear loads were calculated from T2 to L5 in 12 participants with fractures (66.4 ± 6.4 years, 162.2 ± 5.1 cm, 69.1 ± 11.2 kg) and 19 without fractures (62.9 ± 7.9 years, 158.3 ± 4.4 cm, 59.3 ± 8.9 kg) while standing. Static analysis was used to solve gravitational loads while muscle-derived forces were calculated using a detailed trunk muscle model driven by optimization with a cost function set to minimise muscle fatigue. Least squares regression was used to derive polynomial functions to describe normalised load profiles. Regression co-efficients were compared between groups to examine differences in loading profiles. Loading at the fractured level, and at one level above and below, were also compared between groups. The fracture group had significantly greater normalised compression (p = 0.0008) and shear force (p < 0.0001) profiles and a trend for a greater flexion moment profile. At the level of fracture, a significantly greater flexion moment (p = 0.001) and shear force (p < 0.001) was observed in the fracture group. A greater flexion moment (p = 0.003) and compression force (p = 0.007) one level below the fracture, and a greater flexion moment (p = 0.002) and shear force (p = 0.002) one level above the fracture was observed in the fracture group. The differences observed in multi-level spinal loading between the groups may explain a mechanism for increased risk of subsequent vertebral fractures. Interventions aimed at restoring vertebral morphology or reduce thoracic curvature may assist in normalising spine load profiles.

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Section: Discussionmentioning

confidence: 99%

The effect of osteoporotic vertebral fracture on predicted spinal loads in vivo

et al. 2006

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“…Three trabecular structures were created; age < 50, age 50-75 and age > 75. A tissue modulus of 8GPa and a Poisson´s ratio of 0.3 were applied [7,8]. An elastic-perfectly plastic yield definition was included which had a yield strain of 0.85% and a yield stress of 68 MPa.…”

Section: A Modeling the Trabecular Corementioning

confidence: 99%

“…The mesh density gave shell elements 2mm in size. The material properties of the cortex were assumed to be the same as the trabecular bone [7,8]. The thickness of the shell elements was 0.5mm, which represents a normal cortical shell [11].…”

Section: B Modeling the Vertebramentioning

confidence: 99%

Relative Roles of Cortical and Trabecular Thinning in Reducing Osteoporotic Vertebral Body Stiffness: A Modeling Study

et al. 2009

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Abstract-While the effects of reduced bone density on osteoporotic vertebral strength are well known, the relative roles of cortical shell and trabecular architecture thinning in determining vertebral stiffness and strength are less clear. These are important parameters in investigating the changing biomechanics of the ageing spine, and in assessing the effect of stiffening procedures such as vertebroplasty on neighbouring spinal segments. This work presents the development of a microstructural computer model of the osteoporotic lumbar vertebral body, allowing detailed prediction of the effects of bone micro-architecture on vertebral stiffness and strength.Microstructural finite element models of an L3 human vertebral body were created. The cortex geometry was represented with shell elements and the trabecular network with a lattice of beam elements. Trabecular architecture was varied according to age. Each beam network model was validated against experimental data. Models were generated to represent vertebral bodies of age <50 years, age 50-75y and age >75y respectively. For all models, an initial cortical shell thickness of 0.5mm was used, followed by reductions in the age >75y models to 0.35mm and 0.2mm to represent cortical thinning in late stage osteoporosis. Loads were applied to simulate in vitro biomechanical testing, compressing the vertebra by 20% of its height.Predicted vertebral stiffness and strength reduced with progressive age changes in microarchitecture, demonstrating a 44% reduction in stiffness and a 43% reduction in strength, between the age <50 and age >75 models. Reducing cortical thickness in the age >75 models demonstrated a substantial reduction in stiffness and strength, resulting in a 48% reduction in stiffness and a 62% reduction in strength between the 0.5mm and 0.2mm cortical thickness models. Cortical thinning in late stage osteoporosis may therefore play an even greater role in reducing vertebral stiffness and strength than earlier reductions due to trabecular thinning.

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“…The bone is a bio composite material of a complex structural arrangement of components that determine the anisotropy of its mechanical properties [1][2][3][4]. Any skeletal bone (macro level) is composed of compact (cortical) and spongy (trabecular) bone tissue.…”

Section: Introductionmentioning

confidence: 99%

“…The microstructure of the spongy bone is formed by the directed location of trabeculae [3]. The direction of the location of the collagen-mineral fibers of the osteons and trabeculae of the bone tissue varies depending on the anatomical location of the bone fragments while being determined by the effected load [1,4,5].…”

Section: Introductionmentioning

confidence: 99%

Modeling and calculation of the stress-strain state of trabecular bone fragments

Lastovkina¹,

Kolmakova²

2016

AIP Conference Proceedings

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Abstract. The paper is devoted to modeling of the structure and calculation of the stress-strain state of trabecular bone tissue fragments under uniaxial compression. The influence of the number of trabeculae nodes used in models on the value of their average longitudinal strain is studied. The results of the research are needed to develop recommendations for creating mechanically compatible implants.

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Biomechanics of Trabecular Bone

Cited by 658 publications

References 136 publications

The effect of osteoporotic vertebral fracture on predicted spinal loads in vivo

The effect of osteoporotic vertebral fracture on predicted spinal loads in vivo

Relative Roles of Cortical and Trabecular Thinning in Reducing Osteoporotic Vertebral Body Stiffness: A Modeling Study

Modeling and calculation of the stress-strain state of trabecular bone fragments

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