Influence of sagittal balance on spinal lumbar loads: A numerical approach
Introduction
The development of bipedalism in humans determined a series of peculiar changes in the spinal anatomy and biomechanics in comparison to non-human primates, which could not be observed in other animals adopting the erect position such as birds, kangaroos and dinosaurs (Le Huec et al., 2011b). These changes include the verticalization of the pelvis (Berge, 1998) and the development of the spinal sagittal curvatures, i.e. lumbar lordosis and thoracic kyphosis, which are specific to humans but can be developed by non-human primates trained to walk bipedally (Preuschoft et al., 1988, Wagner et al., 2012). In its physiological conditions, the human spine exploits its curved shape in the sagittal plane to achieve equilibrium and stability with a minimal activation of the back musculature (Skoyles, 2006).
Despite the general effectiveness of the human spinal anatomy and biomechanics, pathological deformities (Roussouly and Pinheiro-Franco, 2011), both congenital and degenerative, may lead to loss of spine stability and sagittal imbalance. Classification systems based on radiographic assessment have been introduced and are currently used for the characterization of the sagittal balance of patients suffering from various spinal disorders (Roussouly et al., 2005, Wang et al., 2012). The correct use of these systems is critical in the planning of back surgeries, in which the restoration of a physiological balance was shown to be a strong determinant for the clinical outcome, especially in the presence of spondylolisthesis (Bourghli et al., 2011, Lamartina et al., 2012).
In recent times, a great amount of resources have been dedicated to epidemiological and clinical investigations of the relevance of spinal sagittal balance, supported by the increasingly widespread use of the EOS imaging system which allows for low-dose X-ray imaging of the spine in standing position (Dubousset et al., 2008). Nevertheless, data about the importance of sagittal balance in biomechanical terms are still lacking. To our knowledge, the effect of different patterns of sagittal imbalance on the loads acting in the spine was only marginally investigated (e.g. in Harrison et al., 2005, Keller et al., 2005, Kiefer et al., 1998), although it would be of critical importance in the management of spinal disorders. For example, the estimation of the amount of restoration to be achieved with surgical correction of the imbalance is still based on empirical formulas (reviewed in Lamartina et al., 2012), which have been proven to give acceptable results but could be optimized with a more scientific approach in which the post-operative spinal loads, stresses and muscle activation could be predicted. Methods which would allow for such an approach are currently already available, and include finite element analysis and numerical optimization, widely used for the investigation of other topics regarding spine biomechanics (Fagan et al., 2002).
This paper is therefore aimed at the development of optimization-based finite element models of the human spine in the standing position which can predict the loads acting in the lumbar spine and the activation of the spinal muscles. The models have been subsequently used to explore a wide range of sagittal balance conditions, covering both the inter-subject variability and pathological imbalance, in order to determine possible correlations between specific characteristics of the spinal shape and the resulting spinal biomechanics in terms of loads and muscle activation. Future uses of the models will include pre-operative planning of surgical imbalance correction.
Section snippets
Parametric spine model
The spine has been schematically simplified in two dimensions as three circular arcs representing the lumbar, thoracic and cervical segments (Fig. 1). Lumbar lordosis (LL), thoracic kyphosis (TK) and cervical lordosis (CL) have been defined as the angles subtended by the respective circular arcs. To describe the spatial orientation of the spine, other angular parameters have been introduced. Sacral slope (SS) was defined as the orientation of the S1 endplate with respect to the horizontal
Validation
The simulation of the physiological, well balanced spine in the standing position predicted average compressive stresses in the beams representing the lumbar intervertebral disks ranging from 0.38 to 0.5 MPa, which are in good agreement with in vivo intradiskal pressures measured in a healthy volunteer (Wilke et al., 1999).
The compressive loads in the lumbar intervertebral disks (Table 4) were in good agreement with those predicted by the literature model (El-Rich et al., 2004), both for the
Discussion
This paper presents an optimization-based method for the calculation of the spinal lumbar loads in dependence on the parameters describing the sagittal balance of the spine. The method was used for 1000 randomized spine models describing a wide range of clinical scenarios, including both inter-subject variability and pathological sagittal deformities.
Despite the methodological focus of the paper, it is worth analyzing the results of the calculations for the employed set of models. Coherently
Conclusions
The present modeling approach was found to be able to capture correlations between sagittal parameters describing the spinal shape and the loads acting in the lumbar spine due to body weight and muscle activity. The model, used here for a sensitivity analysis representing a wide range of clinical scenarios ranging from physiological inter-subject variability to pathological sagittal imbalance conditions, represents a good platform for future improvements aimed at patient-specific modeling to
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