An FE investigation simulating intra-operative corrective forces applied to correct scoliosis deformity

BackgroundAdolescent idiopathic scoliosis (AIS) is a deformity of the spine, which may require surgical correction by attaching a rod to the patient’s spine using screws implanted in the vertebral bodies. Surgeons achieve an intra-operative reduction in the deformity by applying compressive forces across the intervertebral disc spaces while they secure the rod to the vertebra. We were interested to understand how the deformity correction is influenced by increasing magnitudes of surgical corrective forces and what tissue level stresses are predicted at the vertebral endplates due to the surgical correction.MethodsPatient-specific finite element models of the osseoligamentous spine and ribcage of eight AIS patients who underwent single rod anterior scoliosis surgery were created using pre-operative computed tomography (CT) scans. The surgically altered spine, including titanium rod and vertebral screws, was simulated. The models were analysed using data for intra-operatively measured compressive forces – three load profiles representing the mean and upper and lower standard deviation of this data were analysed. Data for the clinically observed deformity correction (Cobb angle) were compared with the model-predicted correction and the model results investigated to better understand the influence of increased compressive forces on the biomechanics of the instrumented joints.ResultsThe predicted corrected Cobb angle for seven of the eight FE models were within the 5° clinical Cobb measurement variability for at least one of the force profiles. The largest portion of overall correction was predicted at or near the apical intervertebral disc for all load profiles. Model predictions for four of the eight patients showed endplate-to-endplate contact was occurring on adjacent endplates of one or more intervertebral disc spaces in the instrumented curve following the surgical loading steps.ConclusionThis study demonstrated there is a direct relationship between intra-operative joint compressive forces and the degree of deformity correction achieved. The majority of the deformity correction will occur at or in adjacent spinal levels to the apex of the deformity. This study highlighted the importance of the intervertebral disc space anatomy in governing the coronal plane deformity correction and the limit of this correction will be when bone-to-bone contact of the opposing vertebral endplates occurs.

[1]  D. Maiman,et al.  Finite element modeling of the cervical spine: role of intervertebral disc under axial and eccentric loads. , 1999, Medical engineering & physics.

[2]  L. Lenke Anterior Endoscopic Discectomy and Fusion for Adolescent Idiopathic Scoliosis , 2003, Spine.

[3]  J. P. Little,et al.  Effects of surgical joint destabilization on load sharing between ligamentous structures in the thoracic spine: a finite element investigation. , 2011, Clinical biomechanics.

[4]  Jean Dansereau,et al.  Biomechanical simulations of scoliotic spine correction due to prone position and anaesthesia prior to surgical instrumentation. , 2005, Clinical biomechanics.

[5]  T. Hedman,et al.  1. Stability provided by the sternum and rib cage in the thoracic spine , 2004 .

[6]  T Belytschko,et al.  A model for studies of mechanical interactions between the human spine and rib cage. , 1974, Journal of biomechanics.

[7]  Paul B. Hoeber,et al.  Scoliosis , 1926, The Indian Medical Gazette.

[8]  K. Kaneda,et al.  An In Vitro Human Cadaveric Study Investigating the Biomechanical Properties of the Thoracic Spine , 2002, Spine.

[9]  M. Kamimura,et al.  Preoperative CT examination for accurate and safe anterior spinal instrumentation surgery with endoscopic approach. , 2002, Journal of spinal disorders & techniques.

[10]  K. Scheffler,et al.  Intraoperative determination of the load–displacement behavior of scoliotic spinal motion segments: preliminary clinical results , 2012, European Spine Journal.

[11]  I A Stokes,et al.  Three-dimensional osseo-ligamentous model of the thorax representing initiation of scoliosis by asymmetric growth. , 1990, Journal of biomechanics.

[12]  F. Pernus,et al.  A review of methods for quantitative evaluation of spinal curvature , 2009, European Spine Journal.

[13]  A Shirazi-Adl,et al.  Mechanical Response of a Lumbar Motion Segment in Axial Torque Alone and Combined with Compression , 1986, Spine.

[14]  J. Little,et al.  The measurement of applied forces during anterior single rod correction of adolescent idiopathic scoliosis , 2009 .

[15]  J. P. Little,et al.  Patient‐specific computational biomechanics for simulating adolescent scoliosis surgery: Predicted vs clinical correction for a preliminary series of six patients , 2010 .

[16]  H Labelle,et al.  Biomechanical Modeling of Posterior Instrumentation of the Scoliotic Spine , 2003, Computer methods in biomechanics and biomedical engineering.

[17]  J. Paige Little,et al.  Parametric equations to represent the profile of the human intervertebral disc in the transverse plane , 2007, Medical & Biological Engineering & Computing.

[18]  Jürgen Harms,et al.  Anterior Single-Rod Instrumentation of the Thoracic and Lumbar Spine: Saving Levels , 2003, Spine.

[19]  M Guillot,et al.  Biomechanical properties of spinal ligaments and a histological study of the supraspinal ligament in traction. , 1985, Journal of biomechanics.

[20]  W C Hutton,et al.  Do Bending, Twisting, and Diurnal Fluid Changes in the Disc Affect the Propensity to Prolapse? A Viscoelastic Finite Element Model , 1996, Spine.

[21]  J. Little,et al.  The Effect of Soft Tissue Properties on Spinal Flexibility in Scoliosis: Biomechanical Simulation of Fulcrum Bending , 2009, Spine.

[22]  J. P. Little,et al.  Finite Element Modelling Of Anular Lesions in the Lumbar Intervertebral Disc , 2004 .

[23]  King H. Yang,et al.  Development of a Three-Dimensional Finite Element Chest Model for the 5(th) Percentile Female. , 2005, Stapp car crash journal.

[24]  J. Paige Little,et al.  Towards determining soft tissue properties for modelling spine surgery: current progress and challenges , 2011, Medical & Biological Engineering & Computing.

[25]  A N Natali,et al.  A hyperelastic and almost incompressible material model as an approach to intervertebral disc analysis. , 1991, Journal of biomedical engineering.

[26]  T. Hedman,et al.  Stability Provided by the Sternum and Rib Cage In the Thoracic Spine , 2005, Spine.

[27]  M. Hawes,et al.  A century of spine surgery: What can patients expect? , 2008, Disability and rehabilitation.

[28]  Hutton Wc,et al.  Do bending, twisting, and diurnal fluid changes in the disc affect the propensity to prolapse? A viscoelastic finite element model , 1996 .

[29]  A. Nachemson,et al.  Lumbar intradiscal pressure. Experimental studies on post-mortem material. , 1960, Acta orthopaedica Scandinavica. Supplementum.

[30]  Antonius Rohlmann,et al.  Effect of different surgical strategies on screw forces after correction of scoliosis with a VDS implant , 2006, European Spine Journal.

[31]  W. Skalli,et al.  Characterization of the mechanical behaviour parameters of the costo-vertebral joint , 1998, European Spine Journal.

[32]  Masami Iwamoto,et al.  Development of a Three-Dimensional Finite Element Chest Model for the 5(th) Percentile Female. , 2005, Stapp car crash journal.

[33]  R Dumas,et al.  Finite element simulation of spinal deformities correction by in situ contouring technique , 2005, Computer methods in biomechanics and biomedical engineering.