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Research Papers

Lower Cervical Spine Motion Segment Computational Model Validation: Kinematic and Kinetic Response for Quasi-Static and Dynamic Loading

[+] Author and Article Information
Jeffrey B. Barker

Department of Mechatronics and
Mechanical Engineering,
University of Waterloo,
200 University Avenue West,
Waterloo, ON N2L 3G1, Canada
e-mail: jbarker@uwaterloo.ca

Duane S. Cronin

Department of Mechatronics and
Mechanical Engineering,
University of Waterloo,
200 University Avenue West,
Waterloo, ON N2L 3G1, Canada;
Department of Mechanical Engineering,
University of Waterloo,
200 University Avenue West,
Waterloo, ON N2L 3G1, Canada
e-mails: dscronin@uwaterloo.ca;
dscronin@mecheng1.uwaterloo.ca

Roger W. Nightingale

Division of Orthopaedic Surgery,
Department of Biomedical Engineering,
Duke University,
Box 90281,
Durham, NC 27708-0281
e-mail: rwn@duke.edu

1Corresponding author.

Manuscript received October 31, 2016; final manuscript received March 17, 2017; published online May 2, 2017. Assoc. Editor: Brian D. Stemper.

J Biomech Eng 139(6), 061009 (May 02, 2017) (11 pages) Paper No: BIO-16-1428; doi: 10.1115/1.4036464 History: Received October 31, 2016; Revised March 17, 2017

Advanced computational human body models (HBM) enabling enhanced safety require verification and validation at different levels or scales. Specifically, the motion segments, which are the building blocks of a detailed neck model, must be validated with representative experimental data to have confidence in segment and, ultimately, full neck model response. In this study, we introduce detailed finite element motion segment models and assess the models for quasi-static and dynamic loading scenarios. Finite element segment models at all levels in the lower human cervical spine were developed from scans of a 26-yr old male subject. Material properties were derived from the in vitro experimental data. The segment models were simulated in quasi-static loading in flexion, extension, lateral bending and axial rotation, and at dynamic rates in flexion and extension in comparison to previous experimental studies and new dynamic experimental data introduced in this study. Single-valued experimental data did not provide adequate information to assess the model biofidelity, while application of traditional corridor methods highlighted that data sets with higher variability could lead to an incorrect conclusion of improved model biofidelity. Data sets with continuous or multiple moment–rotation measurements enabled the use of cross-correlation for an objective assessment of the model and highlighted the importance of assessing all motion segments of the lower cervical spine to evaluate the model biofidelity. The presented new segment models of the lower cervical spine, assessed for range of motion and dynamic/traumatic loading scenarios, provide a foundation to construct a biofidelic model of the spine and neck, which can be used to understand and mitigate injury for improved human safety in the future.

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Figures

Grahic Jump Location
Fig. 1

Motion segment finite element model, with rigidized endplates for applying boundary conditions (C4–C5 segment shown)

Grahic Jump Location
Fig. 2

C4–C5 segment model range of motion comparison with Panjabi et al. [30] (1.0 N⋅m) and Moroney et al. [28] (1.8 N⋅m)

Grahic Jump Location
Fig. 3

C4–C5 model extension (left) and flexion (right) comparison with Wheeldon et al. [24], Nightingale et al. [26], and Camacho et al. [27]

Grahic Jump Location
Fig. 4

High rate C4–C5 model comparison with Nightingale et al. [26]

Grahic Jump Location
Fig. 5

Flexion loading just before (left) and just after (right) onset of failure due to ISL/CL rupture and C5 compressive bone fracture; moment = 17.5 N⋅m and angle = 20.4 deg

Grahic Jump Location
Fig. 6

Extension loading just before (left) and just after (right) onset of failure due to ALL rupture and disk avulsion; moment = 13.8 N⋅m and angle = 13.1 deg

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