Strain rate dependent properties of younger human cervical spine ligaments

Mattucci, Stephen; Moulton, Jeffrey A.; Chandrashekar, Naveen; Cronin, Duane S.

doi:10.1016/j.jmbbm.2012.02.004

Cited by 118 publications

(44 citation statements)

References 69 publications

(182 reference statements)

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“…Optimized parameters were fitted separately for the six samples (sensitivity analysis described in Claeson et al, submitted), and then averaged to produce the following representative parameter set: C 1 =0.018±0.011 MPa , α =0.73±0.29, β =2.57±0.29, ξ =3.64±2.25 MPa , θ 1 =−22.39±8.63°, θ 2 =2.51±24.45°, b 1 =16.51±16.03.and b 2 =2.11±1.08. The FCL, as a viscoelastic tissue, exhibits rate-dependent loading as shown by Mattucci et al [26]. Because of the relative low rate and long duration of our previous testing, however, the data were fitted by a hyperelastic model ignoring the viscoelastic effects.…”

Section: Methodsmentioning

confidence: 99%

Computer simulation of lumbar flexion shows shear of the facet capsular ligament

Claeson

Barocas

2017

The Spine Journal

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BACKGROUND CONTEXT The lumbar facet capsular ligament (FCL) is a posterior spinal ligament with a complex structure and kinematic profile. The FCL has a curved geometry, multiple attachment sites, and preferentially aligned collagen fiber bundles on the posterior surface that are innervated with mechanoreceptive nerve endings. Spinal flexion induces three-dimensional (3D) deformations, requiring the FCL to maintain significant tensile and shear loads. Previous works aimed to study 3D facet joint kinematics during flexion, but to our knowledge none have reported localized FCL surface deformations likely created by this complex structure. PURPOSE The purpose of this study was to elucidate local deformations of both the posterior and anterior surfaces of the lumbar FCL to understand the distribution and magnitude of in-plane and through-plane deformations, including the prevalence of shear. STUDY DESIGN/SETTING The FCL anterior and posterior surface deformations were quantified through creation of a finite element model simulating facet joint flexion using a realistic geometry, physiological kinematics, and fitted constitutive material. METHODS Geometry was obtained from the micro-CT data of a healthy L3–L4 facet joint capsule (n=1); kinematics were extracted from sagittal plane fluoroscopic data of healthy volunteers (n=10) performing flexion; and average material properties were determined from planar biaxial extension tests of L4–L5 FCLs (n=6). All analyses were performed with the non-linear finite element solver, FEBio. A grid of equally spaced 3×3 nodes on the posterior surface identified regional differences within the strain fields and was used to create comparisons against previously published experimental data. This study was funded by the National Institutes of Health and the authors have no disclosures. RESULTS Inhomogeneous in-plane and through-plane shear deformations were prominent through the middle body of the FCL on both surfaces. Anterior surface deformations were more pronounced because of the small width of the joint space, whereas posterior surface deformations were more diffuse because the larger area increased deformability. We speculate these areas of large deformation may provide this proprioceptive system with an excellent measure of spinal motion. CONCLUSIONS We found that in-plane and through-plane shear deformations are widely present in finite element simulations of a lumbar FCL during flexion. Importantly, we conclude that future studies of the FCL must consider the effects of both shear and tensile deformations.

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Section: Methodsmentioning

confidence: 99%

Computer simulation of lumbar flexion shows shear of the facet capsular ligament

Claeson

Barocas

2017

The Spine Journal

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“…This increase is not linear; rather, it appears logarithmic suggesting that the effect diminishes at very high rates. Similarly, Mattucci et al [30] tested cervical spine ligaments at strain rates up to 250 s À1 and found a similar trend to that of McElhaney [29] in bone in the variation of material properties with strain rate. We conducted some preliminary experiments with the lateral collateral ligament of the porcine stifle joint up to 100 s À1 and found that there appears to be a strain-sensitivity limit at approximately 1 s À1 beyond which ligament properties are virtually unaffected by strain rate.…”

Section: Fibrous Tissue Levelmentioning

confidence: 61%

The High-Strain Rate Loading of Structural Biological Materials

Proud

Nguyen

et al. 2015

Metall Mater Trans A

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The human body can be subjected to violent acceleration as a result of explosion caused by military ordinance or accident. Blast waves cause injury and blunt trauma can be produced by violent impact of objects against the human body. The long-term clinical manifestations of blast injury can be significantly different in nature and extent to those suffering less aggressive insult. Similarly, the damage seen in lower limbs from those injured in explosion incidents is in general more severe than those falling from height. These phenomena increase the need for knowledge of the short-and long-term effect of transient mechanical loading to the biological structures of the human body. This paper gives an overview of some of the results of collaborative investigation into blast injury. The requirement for time-resolved data, appropriate mechanical modeling, materials characterization and biological effects is presented. The use of a range of loading platforms, universal testing machines, drop weights, Hopkinson bars, and bespoke traumatic injury simulators are given.

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“…The model was developed by a team of research university centres of excellence (COEs) around the world with the Full Body Model COE model integration centre located at Wake Forest University School of Medicine and the Virginia Tech -Wake Forest Center for Injury Biomechanics. The GHBMC neck model was developed at the Neck COE, the University of Waterloo, in Ontario, Canada (Fice et al 2011;DeWit and Cronin 2012;Fice and Cronin 2012;Mattucci et al 2012). It is composed of seven cervical vertebrae with detailed facet joints and accompanying intervertebral discs (IVDs), as well as nonlinear ratedependent ligaments, 3D passive muscles and 1D active muscles ( Figure 2).…”

Section: Brief Review Of Finite Element Neck Modelsmentioning

confidence: 99%

Cross-sectional neck response of a total human body FE model during simulated frontal and side automobile impacts

White

Moreno

Gayzik

et al. 2013

Computer Methods in Biomechanics and Biomedical Engineering

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Human body finite element (FE) models are beginning to play a more prevalent role in the advancement of automotive safety. A methodology has been developed to evaluate neck response at multiple levels in a human body FE model during simulated automotive impacts. Three different impact scenarios were simulated: a frontal impact of a belted driver with airbag deployment, a frontal impact of a belted passenger without airbag deployment and an unbelted side impact sled test. Cross sections were created at each vertebral level of the cervical spine to calculate the force and moment contributions of different anatomical components of the neck. Adjacent level axial force ratios varied between 0.74 and 1.11 and adjacent level bending moment ratios between 0.55 and 1.15. The present technique is ideal for comparing neck forces and moments to existing injury threshold values, calculating injury criteria and for better understanding the biomechanical mechanisms of neck injury and load sharing during sub-injurious and injurious loading.

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Strain rate dependent properties of younger human cervical spine ligaments

Cited by 118 publications

References 69 publications

Computer simulation of lumbar flexion shows shear of the facet capsular ligament

Computer simulation of lumbar flexion shows shear of the facet capsular ligament

The High-Strain Rate Loading of Structural Biological Materials

Cross-sectional neck response of a total human body FE model during simulated frontal and side automobile impacts

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