Dynamic sagittal flexibility coefficients of the human cervical spine

Ivancic, Paul C.; Ito, Shigeki; Panjabi, Manohar M.

doi:10.1016/j.aap.2006.10.015

Cited by 11 publications

(5 citation statements)

References 22 publications

(37 reference statements)

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“…This is particularly true for soft tissues, which exhibit nonlinearity, non-homogeneity, anisotropy, viscoelasticity (ArItan et al, 2008) and tension/compression asymmetry (Takaza et al, 2013). Skeletal muscle tissue accounts for almost half of human body weight (Wang et al, 1997), so the constitutive properties of passive muscle tissue are crucial for many musculoskeletal models in diverse applications from impact biomechanics (Muggenthaler et al, 2008, Ivancic et al, 2007 to rehabilitation engineering (Linder-Ganz et al, 2008, Linder-Ganz et al, 2007, surgical simulation (Lim andDe, 2007, Audette et al, 2004) and soft tissue drug transport (Wu and Edelman, 2008).…”

Section: Introductionmentioning

confidence: 99%

A structural model of passive skeletal muscle shows two reinforcement processes in resisting deformation

Gindre

Takaza

Moerman

et al. 2013

Journal of the Mechanical Behavior of Biomedical Materials

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Passive skeletal muscle derives its structural response from the combination of the titin filaments in the muscle fibres, the collagen fibres in the connective tissue and incompressibility due to the high fluid content. Experiments have shown that skeletal muscle tissue presents a highly asymmetrical three-dimensional behaviour when passively loaded in tension or compression, but structural models predicting this are not available. The objective of this paper is to develop a mathematical model to study the internal mechanisms which resist externally applied deformation in skeletal muscle bulk. One cylindrical muscle fibre surrounded by connective tissue was considered. The collagenous fibres of the endomysium and perimysium were grouped and modelled as tension-only oriented wavy helices wrapped around the muscle fibre. The titin filaments are represented as non-linear tensiononly springs. The model calculates the force developed by the titin molecules and the collagen network when the muscle fibre undergoes an isochoric along-fibre stretch. The model was evaluated using a range of literature based input parameters and compared to the experimental fibre-direction stress-stretch data available. Results show the fibre direction non-linearity and tension/compression asymmetry are partially captured by this structural model. The titin filament load dominates at low tensile stretches, but for higher stretches the collagen network was responsible for most of the stiffness. The oblique and initially wavy collagen fibres account for the non-linear tensile response since, as the collagen fibres are being recruited, they straighten and re-orient. The main contribution of the model is that it shows that the overall compression/tension response is strongly influenced by a pressure term induced by the radial component of collagen fibre stretch acting on the incompressible muscle fibre. Thus for along-fibre tension or compression the model predicts that the collagen network contributes to overall muscle stiffness through two different mechanisms: 1) a longitudinal force directly opposing tension and 2) a pressure force on the muscle fibres resulting in an indirect longitudinal load. Although the model presented considers only a single muscle fibre and evaluation is limited to along-fibre loading, this is the first model to propose these two internal mechanisms for resisting externally applied deformation of skeletal muscle tissue.2

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Section: Introductionmentioning

confidence: 99%

A structural model of passive skeletal muscle shows two reinforcement processes in resisting deformation

Gindre

Takaza

Moerman

et al. 2013

Journal of the Mechanical Behavior of Biomedical Materials

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“…The MASI inherited body segment inertial properties mostly from the ‘2354’ model [23], whilst the cervical spine and head segments inertial properties were derived from in vitro data [43]. …”

Section: Methodsmentioning

confidence: 99%

Cervical Spine Injuries: A Whole-Body Musculoskeletal Model for the Analysis of Spinal Loading

Cazzola¹,

Holsgrove²,

Preatoni³

et al. 2017

PLoS ONE

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Cervical spine trauma from sport or traffic collisions can have devastating consequences for individuals and a high societal cost. The precise mechanisms of such injuries are still unknown as investigation is hampered by the difficulty in experimentally replicating the conditions under which these injuries occur. We harness the benefits of computer simulation to report on the creation and validation of i) a generic musculoskeletal model (MASI) for the analyses of cervical spine loading in healthy subjects, and ii) a population-specific version of the model (Rugby Model), for investigating cervical spine injury mechanisms during rugby activities. The musculoskeletal models were created in OpenSim, and validated against in vivo data of a healthy subject and a rugby player performing neck and upper limb movements. The novel aspects of the Rugby Model comprise i) population-specific inertial properties and muscle parameters representing rugby forward players, and ii) a custom scapula-clavicular joint that allows the application of multiple external loads. We confirm the utility of the developed generic and population-specific models via verification steps and validation of kinematics, joint moments and neuromuscular activations during rugby scrummaging and neck functional movements, which achieve results comparable with in vivo and in vitro data. The Rugby Model was validated and used for the first time to provide insight into anatomical loading and cervical spine injury mechanisms related to rugby, whilst the MASI introduces a new computational tool to allow investigation of spinal injuries arising from other sporting activities, transport, and ergonomic applications. The models used in this study are freely available at simtk.org and allow to integrate in silico analyses with experimental approaches in injury prevention.

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“…( 1 ( ), 2 ( )) = 1 ( 1 ( ) − 3) + 2 ( 2 ( ) − 3) 1 For incompressible materials, = det( ) = 1 and therefore 2 ( ) = 1 ( −1 ), allowing the Mooney-Rivlin form to be rewritten in terms of principal stretches as:…”

Section: Introductionmentioning

confidence: 99%

“…Realistic constitutive modelling for biological soft tissue is relevant to research areas such as impact biomechanics [1][2][3] , rehabilitation engineering [4][5][6][7] , tissue engineering 8 , gait analysis 9 , surgical simulation [10][11][12] , and modelling of soft tissue drug transport 13,14 . Many biological materials present with significantly different behaviour for tensile or compressive loading (e.g.…”

Section: Introductionmentioning

confidence: 99%

Control of tension–compression asymmetry in Ogden hyperelasticity with application to soft tissue modelling

Moerman

Simms

Nagel

2016

Journal of the Mechanical Behavior of Biomedical Materials

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This paper discusses tension-compression asymmetry properties of Ogden hyperelastic formulations. It is shown that if all negative or all positive Ogden coefficients are used, tension-compression asymmetry occurs the degree of which cannot be separately controlled from the degree of non-linearity. A simple hybrid form is therefore proposed providing separate control over the tension-compression asymmetry. It is demonstrated how this form relates to a newly introduced generalised strain tensor class which encompasses both the tension-compression asymmetric Seth-Hill strain class and the tension-compression symmetric Bažant strain class. If the control parameter is set to q=0.5 a tension-compression symmetric form involving Bažant strains is obtained with the property Ψ(λ1,λ2,λ3)=Ψ(1λ1,1λ2,1λ3). The symmetric form may be desirable for the definition of ground matrix contributions in soft tissue modelling allowing all deviation from the symmetry to stem solely from fibrous reinforcement. Such an application is also presented demonstrating the use of the proposed formulation in the modelling of the non-linear elastic and transversely isotropic behaviour of skeletal muscle tissue in compression (the model implementation and fitting procedure have been made freely available). The presented hyperelastic formulations may aid researchers in independently controlling the degree of tension-compression asymmetry from the degree of non-linearity, and in the case of anisotropic materials may assist in determining the role played by, either the ground matrix, or the fibrous reinforcing structures, in generating asymmetry.

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Dynamic sagittal flexibility coefficients of the human cervical spine

Cited by 11 publications

References 22 publications

A structural model of passive skeletal muscle shows two reinforcement processes in resisting deformation

A structural model of passive skeletal muscle shows two reinforcement processes in resisting deformation

Cervical Spine Injuries: A Whole-Body Musculoskeletal Model for the Analysis of Spinal Loading

Control of tension–compression asymmetry in Ogden hyperelasticity with application to soft tissue modelling

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