Rib fractures under anterior–posterior dynamic loads: Experimental and finite-element study

Li, Zuoping; Kindig, Matthew W.; Kerrigan, Jason; Untaroiu, Costin D.; Subit, Damien; Crandall, Jeff R.; Kent, Richard W.

doi:10.1016/j.jbiomech.2009.08.040

Cited by 122 publications

(87 citation statements)

References 25 publications

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“…25 The remaining material properties were taken from literature. [26][27][28] The material parameters that consider the strain rate effects are not simply measured and determined, some of them are empirically determined through special experimental and optimisation process. 19 The drill bit was assumed to be a rigid body, since its stiffness is much higher than the bone.…”

Section: Materials Propertiesmentioning

confidence: 99%

Thermo-mechanical stresses distribution on bone drilling: Numerical and experimental procedures

Fernandes

Fonseca

Jorge

2017

Proceedings of the Institution of Mechanical Engineers, Part L:

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In bone drilling, the temperature and the level of stresses at the bone tissue are function of the drilling parameters. If certain thresholds are exceeded, irreversible damages may occur on the bone tissue. One of the main challenges in the drilling process is to control the associated parameters and even more important, to avoid the surrounding tissue damage. In this study, a dynamic numerical model is developed to determine the thermo-mechanical stresses generated during the bone drilling, using the finite element method. The numerical model incorporates the geometric and dynamic characteristics involved in the drilling processes, as well the developed temperature inside the material. The numerical analysis has been validated by experimental tests using polyurethane foam materials with similar mechanical properties to the human bone. Results suggest that a drill bit with lower drill speed and higher feed rate can reduce the strains and stresses in bone during the drilling process. The proposed numerical model reflected adequately the experimental results and could be useful in determination of optimal drilling conditions that minimise the bone injuries.

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Section: Materials Propertiesmentioning

confidence: 99%

Thermo-mechanical stresses distribution on bone drilling: Numerical and experimental procedures

Fernandes

Fonseca

Jorge

2017

Proceedings of the Institution of Mechanical Engineers, Part L:

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“…These image data were used to create the CAD geometries for the model through image segmentation and conditioning. The CAD geometries were meshed and validated by university consortium members on a region-by-region basis, including the Head, 33 Neck, 7,10 Thorax, 29,30 Abdomen, 3 Pelvis, and Lower Extremities. 45,57 No modifications were made to the material properties or meshes of the validated regional models during the integration process.…”

Section: Methodsmentioning

confidence: 99%

“…These regional models were meshed and validated by various investigators. 3,7,10,29,30,33,45,57 The aim of this study is to describe the validation of the aforementioned model, known as the Global Human Body Models Consortium (GHBMC) 50th percentile male seated occupant model (M50), in lateral sled and drop tests. Computational models require validation for confidence in simulation results, and these boundary conditions are representative of impacts sustained during side impact MVCs.…”

Section: Introductionmentioning

confidence: 99%

Lateral Impact Validation of a Geometrically Accurate Full Body Finite Element Model for Blunt Injury Prediction

et al. 2012

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This study presents four validation cases of a mid-sized male (M50) full human body finite element model-two lateral sled tests at 6.7 m/s, one sled test at 8.9 m/s, and a lateral drop test. Model results were compared to transient force curves, peak force, chest compression, and number of fractures from the studies. For one of the 6.7 m/s impacts (flat wall impact), the peak thoracic, abdominal and pelvic loads were 8.7, 3.1 and 14.9 kN for the model and 5.2 ± 1.1 kN, 3.1 ± 1.1 kN, and 6.3 ± 2.3 kN for the tests. For the same test setup in the 8.9 m/s case, they were 12.6, 6, and 21.9 kN for the model and 9.1 ± 1.5 kN, 4.9 ± 1.1 kN, and 17.4 ± 6.8 kN for the experiments. The combined torso load and the pelvis load simulated in a second rigid wall impact at 6.7 m/s were 11.4 and 15.6 kN, respectively, compared to 8.5 ± 0.2 kN and 8.3 ± 1.8 kN experimentally. The peak thorax load in the drop test was 6.7 kN for the model, within the range in the cadavers, 5.8-7.4 kN. When analyzing rib fractures, the model predicted Abbreviated Injury Scale scores within the reported range in three of four cases. Objective comparison methods were used to quantitatively compare the model results to the literature studies. The results show a good match in the thorax and abdomen regions while the pelvis results over predicted the reaction loads from the literature studies. These results are an important milestone in the development and validation of this globally developed average male FEA model in lateral impact.

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“…The development of this HBM was based on a multimodality medical image and external anthropometry data set of a volunteer representing a 50th percentile male in terms of height (174.9 cm) and weight (78.6 ± 0.77 kg), described by Gayzik et al (Gayzik et al 2011;Gayzik et al 2012). The model has since undergone numerous validation simulations at both the regional (e.g., DeWit et al 2012;Li et al 2010;Shin et al 2012;Soni et al 2015) and full body levels (e.g., Hayes et al 2014;Toyota 2010;Yang et al 2006). Additional information on the development of the model can be found in the GHBMC M50 user's manual (GHBMC 2011).…”

Section: Introductionmentioning

confidence: 99%

Modular use of human body models of varying levels of complexity: Validation of head kinematics

Decker

Koya

Davis

et al. 2017

Traffic Injury Prevention

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Objective: The significant computational resources required to execute detailed human body finiteelement models has motivated the development of faster running, simplified models (e.g., GHBMC M50-OS). Previous studies have demonstrated the ability to modularly incorporate the validated GHBMC M50-O brain model into the simplified model (GHBMC M50-OS+B), which allows for localized analysis of the brain in a fraction of the computation time required for the detailed model. The objective of this study is to validate the head and neck kinematics of the GHBMC M50-O and M50-OS (detailed and simplified versions of the same model) against human volunteer test data in frontal and lateral loading. Furthermore, the effect of modular insertion of the detailed brain model into the M50-OS is quantified. Methods: Data from the Navy Biodynamics Laboratory (NBDL) human volunteer studies, including a 15g frontal, 8g frontal, and 7g lateral impact, were reconstructed and simulated using LS-DYNA. A five-point restraint system was used for all simulations, and initial positions of the models were matched with volunteer data using settling and positioning techniques. Both the frontal and lateral simulations were run with the M50-O, M50-OS, and M50-OS+B with active musculature for a total of nine runs. Conclusion:The greatest departure from the detailed occupant models were noted in lateral flexion, potentially indicating the need for further study. Precise modeling of the belt system however was limited by available data. A sensitivity study of these parameters in the frontal condition showed that belt slack and muscle activation have a modest effect on the ISO score. The reduction in computation time of the M50-OS+B reduces the burden of high computational requirements when handling detailed HBMs. Future work will focus on harmonizing the lateral head response of the models and studying localized injury criteria within the brain from the M50-O and M50-OS+B.

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Rib fractures under anterior–posterior dynamic loads: Experimental and finite-element study

Cited by 122 publications

References 25 publications

Thermo-mechanical stresses distribution on bone drilling: Numerical and experimental procedures

Thermo-mechanical stresses distribution on bone drilling: Numerical and experimental procedures

Lateral Impact Validation of a Geometrically Accurate Full Body Finite Element Model for Blunt Injury Prediction

Modular use of human body models of varying levels of complexity: Validation of head kinematics

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