Full length articleViscoelasticity of spinal cord and meningeal tissues
Graphical abstract
Introduction
Traumatic spinal cord injury (SCI) is typically initiated by high-velocity, dynamic events such as traffic accidents, falls, violence, or sport/recreation injuries [1], [2], [3], [4], [5], [6]. Due to the complex loading environments which occur during SCI, it is difficult to accurately model human injury and/or measure local tissue mechanical forces using in-vivo animal surrogates. In contrast, computational models provide an efficient, economical, and ethical method for investigating SCI mechanical etiology, prevention techniques, and clinical treatments. As tissue deformation and stress have been shown to correlate with injury severity and neurological impairment [6], [7], [8], [9], [10], [11], [12], finite element (FE) computational modeling allows researchers to conduct very controlled SCI simulations and predict the resultant internal tissue response (and associated injury severity) under various conditions [6], [7], [8], [13], [14]. However, it is important to highlight that the predictive value of an FE model is dependent on the implementation of accurate geometric and material models [9], [15], [16], [17], [18].
In the majority of FE models of the spine, the spinal cord itself is typically modeled as one homogenous material [7], [14], [15], [19], [20] or as a construct of gray and white matter regions [6], [8], [9], [10], [13], [16], [17], while explicit modeling of the innermost meningeal layers (the pia and arachnoid maters) is frequently neglected [6], [7], [8], [9], [10], [13], [14], [15], [19], [20]. The material models assigned to the various spinal cord components vary in complexity from linearly elastic [6], [7], [10], [13], [14], [15], [17], [18], [19], [21], [22], [23], [24], [25] to hyperelastic [10], [15], [16], [17], [19], [20] to viscoelastic [8], [9], [18], [21], [22], or some combination thereof. The material models utilized to represent the homogenous spinal cord are often developed using experimental data collected from spinal cord samples with at least the pia mater intact [9], [26], [27], [28], [29], [30]. However, as most published experimental procedures do not include detailed descriptions of dissection techniques beyond removal of the dura mater, it is difficult to determine if the arachnoid mater is also present (and contributing) to the reported results. These results are often reported as the mechanical properties of the gestalt “spinal cord”. For specificity in this work, the three-part construct of the neural and connective tissues will be referred to as the spinal-cord-pia-arachnoid construct (SCPC), with the spinal cord parenchyma referred to as the cord, and the construct of the innermost meninges as the pia-arachnoid complex (PAC).
As shown by the experimental results of Ozawa et al. [31] and Mazuchowski and Thibault [32], the presence of the PAC significantly effects the mechanical response of the SCPC. Specifically, comparisons of the response before and after PAC removal show a significant decrease in the compressive [31] and tensile stiffness [32], as well as shape recovery after compression [31]. However, to the authors’ knowledge, only one study has reported quantitative mechanical properties of isolated spinal PAC [16]. Unfortunately, little detail was provided with respect to the dissection of samples and only a strain-rate dependent linear elastic modulus was reported.
While some groups have included a distinct pia mater in their computational models [17], [18], [21], [22], [23], [24], [25], [33], the lack of appropriate mechanical properties in the literature constrains the predictive fidelity of explicitly modeling this tissue. For example, in a parametric FE study of the effect of material properties on the magnitude and distribution of stress and strain in the cord cross-section, Sparrey et al. concluded that “pia mater characteristics had limited (<4% change) effects on outcomes” [17]. However, the pia mater was modeled as a linearly elastic membrane with the tangent modulus varied from 600 kPa to 3 MPa [17]. While this range includes the modulus reported by Ozawa et al. [31], it does not include the higher stiffness values reported by Kimpara et al. for spinal pia mater [16] and by Jin et al. for cranial pia mater [34]. Indeed, a subsequent study by Sparrey which implemented the 40 MPa linear elastic modulus reported by Kimpara et al. concluded distinct modeling of the pia mater was necessary to match experimental measurements and tissue damage [33]. However, since the experimental results of Kimpara et al. and Jin et al. suggest the pia mater is a viscoelastic material, tangent moduli may not be adequate to describe its behavior under dynamic conditions. Jin et al. has published numerous studies of the viscoelastic response of cranial PAC under a variety of loading conditions [34], [35], [36], [37], [38], but due to differences in ultrastructure [39], [40], [41], [42], application of these properties to spinal PAC is questionable.
Therefore, the goal of this study was to compare the viscoelastic behavior of the isolated PAC, the isolated cord, and the SCPC to determine the mechanical contribution of each component. A novel numerical integration approach [43] was used to develop non-linear viscoelastic material models for each of the three tissues. Each material model was then validated through predictions of an independent (i.e., not included in the original model fits) data set. The results presented herein represent the first known published account to: (1) describe the nonlinear behavior of spinal PAC; (2) characterize the viscoelastic properties of the isolated cord; and (3) publish validated non-linear viscoelastic material models for the PAC and cord. These findings will allow researchers interested in modeling spinal cord injuries to make informed decisions about the balance of accuracy and complexity necessary for their specific modeling endeavors.
Section snippets
SCPC preparation
Eight cervical spines (C0–C7) were collected from skeletally mature (greater than 4 years old) ewes immediately following euthanasia for unrelated research studies. The spinal cord-meningeal complex, including the dura mater, was carefully removed from the spinal canal through gross dissection, use of an oscillating saw, and transection of nerve roots. As the dura mater is relatively loose at the cranial aspect (where it was previously connected to the cranial dura mater), surgical scissors
Results
In order to mitigate the effects of post-mortem neural tissue degradation [45], [46], [47], [48], [49], all experimental tests of the SCPC and cord conditions were completed within 5 h of animal sacrifice (SCPC: mean 2.8 h, max 3.5 h; cord: mean 4.5 h, max 5 h). Based on average cross-sectional area measurements, the cord parenchyma represented 94.5% of the total SCPC area (84.22 ± 14.05 mm2). The PAC’s mean circumference and thickness were measured to be 22.24 ± 2.71 mm and 0.20 ± 0.04 mm,
Discussion
It is well known that the predictive accuracy of FE computational models is dependent on how accurately the geometries and material properties implemented in the model reflect the native condition being simulated. Many models of the spinal cord do not include explicit geometries for the innermost meninges, and those which do include what is identified as pia mater often utilize linearly elastic material models to describe its behavior, despite experimental evidence that the tissue is
Conclusions
In conclusion, this work represents an important contribution to the knowledge of spinal and meningeal mechanics as it represents the first study to compare the SCPC, isolated cord, and PAC under the same testing conditions. The results show the spinal cord parenchyma has very little inherent stiffness and is reliant on the PAC for rigidity and recovery from loading, consistent with the limited previous works [31], [32]. Despite composing only 5.5% of the SCPC cross-section, the intact PAC
Acknowledgements
The authors would like to acknowledge Colorado State University’s Preclinical Surgical Research Laboratory, especially Kim Lebsock, for their assistance in collection of ovine cervical spines for this study, Nick Meis and Amy Holcomb for their help with data analysis, and Dr. Julia Sharp of Colorado State University’s F.A. Graybill Statistical Laboratory for her guidance on statistical modeling. The authors also wish to acknowledge the funding support of the Graduate Teaching Fellowship from
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