# Stress Analysis of Osteoporotic Lumbar Vertebra Using Finite Element Model with Microscaled Beam-Shell Trabecular-Cortical Structure

Authors: Yoon Hyuk Kim; Mengying Wu; Kyungsoo Kim
Journal: Journal of Applied Mathematics
 (2013)

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## Abstract

Osteoporosis is a disease in which low bone mass and microarchitectural deterioration of bone tissue lead to enhanced bone fragility and susceptibility to fracture. Due to the complex anatomy of the vertebral body, the difficulties associated with obtaining bones for in vitro experiments, and the limitations on the control of the experimental parameters, finite element models have been developed to analyze the biomechanical properties of the vertebral body. We developed finite element models of the L2 vertebra, which consisted of the endplates, the trabecular lattice, and the cortical shell, for three age-related grades (young, middle, and old) of osteoporosis. The compressive strength and stiffness results revealed that we had developed a valid model that was consistent with the results of previous experimental and computational studies. The von-Mises stress, which was assumed to predict the risk of a burst fracture, was also determined for the three age groups. The results showed that the von-Mises stress was substantially higher under relatively high levels of compressive loading, which suggests that patients with osteoporosis should be cautious of fracture risk even during daily activities.


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## Body

## 1. Introduction

Osteoporosis is a disease in which low bone mass and microarchitectural deterioration of bone tissue lead to enhanced bone fragility and susceptibility to fracture [1]. Osteoporosis is one of the most common health problems affecting both men and women [2], and it is becoming increasingly prevalent in our aging society [3]. The degree of osteoporosis is categorized with the T-score, which is the number of standard deviations above or below that of an average young adult: normal, above −1.0; osteopenia, above −2.5 and below −1.0; osteoporosis, below −2.5; severe osteoporosis, the presence of one or more fragility facture [4, 5]. About 1.5 million fractures due to osteoporosis are reported annually in the United States, including over 700,000 vertebral fractures [6]. Spine fractures in particular result in a high mortality rate: survival is 72% in the first year and only 28% after five years [7].The human spine is composed of 24 spinal bones, called vertebrae, which are stacked on top of one another to create the spinal column. The spinal column is the body’s main upright support and the vertebral bone is the primary compressive load-bearing structure in the spine [8]. The vertebral bone is composed of a porous internal trabecular bone core surrounded by a thin shell of cortex. In osteoporosis, bone mineral density is reduced even in the outer layer, so the cortex is thinner than in normal bones. The structure of osteoporotic trabecular bone is similar to a lattice, while normal bone is plate like.Due to the complex anatomy of the vertebral body, the difficulties associated with obtaining bones for in vitro experiments, and the limitations on the control of the experimental parameters, finite element models have been developed to analyze the biomechanical properties of the vertebral body [9, 10]. Large-scale voxel-based models have been used to investigate the mechanics of bone, where the trabecular structure is modeled as a solid body with material properties obtained from previous experiments [11–13]. While the trabecular structure from three-dimensional microcomputed tomography (μCT) was directly implemented into a finite element using the cubic voxel meshes, an additional surface smoothing process was necessary [14]. Lattice models have been proposed to simulate osteoporotic and normal bone through variation in trabecular thickness, spacing, or random material removal [15–19]. Since these studies only addressed the trabecular structure within a small region, a more recent study combined the lattice beam element model of the trabecular core with a thin layer of shell elements for the cortical part to make a whole vertebra model, and analyzed compressive strength, compressive stiffness, and tissue-level strain [20]. In this paper, finite element models of normal and various grades of osteoporotic lumbar vertebrae that incorporate the microscaled trabecular structure of lattice models and the cortical area of shell elements were developed. The models were validated using the results of previous experimental and computational studies. The von-Mises stress was analyzed to predict the risk of the burst fracture in osteoporotic bones of various grades.


## 2. Materials and Methods

Trabecular bone was modeled as a lattice composed of many struts, including both vertical (longitudinal) and horizontal (transverse) struts. A single strut model was developed with two quadratic beam elements. By combining single strut models, we were able to develop a cylindrical core lattice model for different age groups: young (<50 years), middle (50 through 75 years), and old (>75 years) (Figure1(a)). The geometries, which were the horizontal and vertical thicknesses (dh and dv) and the horizontal and vertical lengths (lh and lv) of each strut, are provided for each age group in Table 1 based on [20, 21]. The elastic-perfectly plastic material properties of the struts were based on those of a previous study [20], in which Young’s modulus was 8.0 GPa, the Poisson ratio was 0.3, and the yield stress was 64 MPa. In order to mimic the irregular structure of the trabecular struts, the lattice models were perturbed by randomly moving vertex nodes with MATLAB (MathWorks Inc., MA, USA) (Figure 1(b)) [20, 22]. The distance that each vertex node was moved ranged between 0% and 30% of trabecular spacing (horizontal length lh and vertical length lv) according to a Gaussian distribution. The Gaussian distribution N(μ,σ) was given based on the assumption that the mean μ=0 and the random values are between -3σ and 3σ with the probability of 99.7%. Since the movement was constrained up to 30% of trabecular spacing, the standard deviation σ was supposed as σ=(1/3)×0.3×((lh+lv)/2)=(lh+lv)/20. The direction was also randomly generated to prevent the model from having a bias in one direction.Table 1
Geometries for trabecular lattice models for the young, middle, and old groups.
Thickness of a single strut (mm)
Length of a single strut (mm)
Horizontal (dh)
Vertical (dv)
Horizontal (lh)
Vertical (lv)
Young
0.150
0.208
0.674
0.633
Middle
0.116
0.187
0.861
1.100
Old
0.107
0.201
1.145
1.668Lattice models with a trabecular structure before and after perturbation for three age groups—young (<50 years); middle (50 through 75 years); and old (>75 years).
(a)
Before perturbation
(b)
After perturbationThe trabecular bone lattice models were validated by comparing the results for compressive strengthFc, which is the capacity of a material or structure to withstand axial forces, with those in the experimental study [21]. The geometry of the specimen (cylindrical shape, height of 10 mm, and radius of 3.5 mm), the boundary conditions, and the loading conditions were selected based on the experimental study [21]. The bottom nodes of the lattice model were fixed, and the total reaction force on all fixed bottom nodes in the axial direction was calculated until the top nodes were displaced by 2 mm downward in the axial direction, which was regarded as being compressed, using the ABAQUS/Standard (Dassault Systèmes, RI, USA). The maximum value of reaction force during the compression was considered as the compressive strength Fc.Computed tomography (CT) images of a 1 mm slice were obtained from L2 of a male subject with a height of 175 cm. Based on these CT images, two endplates and the cortical part of the vertebra were developed (Figure2). The elements of the S4 type and the C3D8 type composed the cortical shell and the solid endplates. The thickness of the endplates was 0.5 mm for all age groups, while the thickness of the cortical shell was 0.5 mm for the young and middle groups and 0.2 mm for the old group based on the results of a previous study [20]. The material properties of the endplates and the cortical shell were also based on the results of a previous study [20], in which Young’s modulus was 8.0 GPa, the Poisson ratio was 0.3, and the yield stress was 64 MPa. The trabecular lattice was tied with the cortical shell and endplates by fixing the ends of trabecular beam elements on the interfaces of the cortical shell and endplate for all translational and rotational degrees of freedom. In this case, the posterior element of the vertebra was not considered because the whole vertebral body has too many elements, and the posterior element plays only a minor role during compressive loading [23].Figure 2
Vertebral body models in the three age groups—young (<50 years); middle (50 through 75 years); and old (>75 years).The nodes on the bottom side of the bottom endplate were fixed, and the nodes of the top side of the upper endplate were controlled by a reference point. The reference point was displaced 6 mm downward in the axial direction. The compressive strengthFc which was the maximum total reaction force on the bottom endplate in the axial direction during the compression up to 6 mm was calculated using the ABAQUS/Standard (Dassault Systèmes, RI, USA). In addition, the compressive stiffness kc was estimated as kc=Fc/δc, where δc was the corresponding axial downward displacement of the reference point at the maximum compressive strength. The compressive strength Fc and stiffness kc were compared with those from previous experimental and computational studies [20, 24–27] for the validation of the model.The von-Mises stress in the trabecular lattice was then analyzed for the three age groups (young, middle, and old) under compressive loading. Since the intradiscal pressure in upright standing is around 0.5 MPa and the intradiscal pressure is 1.5 times the average pressure over the endplate, the pressure on the endplate was considered to be 0.3 MPa in upright standing [28–30]. Thus, the compressive loading on the entire upper endplate was assumed to be 0.15 MPa, 0.3 MPa, 0.45 MPa, 0.6 MPa, and 0.75 MPa. The ABAQUS/Explicit (Dassault Systèmes, RI, USA) was used for the analysis.


## 3. Results and Discussion

In order to mimic a realistic trabecular structure, we developed a model in which perturbation of the vertex nodes occurred within 30% of the trabecular spacing according to a Gaussian distributionN(μ,σ), where the mean μ was 0 mm in all age groups and the standard deviation σ was 0.065 mm in the young group, 0.098 mm in the middle group, and 0.141 mm in the old group. We used a perturbation factor of 30% because Silva and Gibson showed that cross-sectional images of a model with 30% perturbation were comparable to those of specimens [21]. The mechanical anisotropy was also included in the model due to the discrepancy in horizontal and vertical geometries of trabecular lattice models. Therefore, we developed a model with an anisotropic irregular trabecular structure, and this model can be regarded as clinically relevant.The compressive strengthFc of the trabecular bone lattice model was 1.74 MPa for the middle group, while it was 1.35 ± 0.64 MPa in [22]. For the whole-body model, the compressive strength Fc was 7.35 kN for the young group, 3.80 kN for the middle group, and 1.36 kN for the old group. In a previous computational study with the same age classes, the compressive strength was 5.74 kN for the young group, 4.06 kN for the middle group, and 1.25 kN for the old group [20]. In experimental studies using normal vertebrae, the compressive strengths have ranged from 0.9 to 15.9 kN (0.9 to 5.0 kN in [24], 1.5 to 4.5 kN in [25], 2.0 to 8.0 kN in [26], and 2.0 to 15.9 kN in [27]). In addition, the compressive stiffness kc was 5.6 kN/mm for the young group, 15.8 kN/mm for the middle group, and 29.4 kN/mm for the old group, respectively. In a previous computational study, the compressive stiffness was 8.0 kN/mm for the young group, 18.7 kN/mm for the middle group, and 29.4 kN/mm for the old group [20]. These results indicate that the presented model could be considered as being validated for the compression.The highest von-Mises stresses occurred in the middle of the trabecular region (Figure3). The maximum stress was strongly related to age: maximum values were about 50% higher for the middle group than the young group and about 120% higher for the old group than the young age group (Figures 4 and 5). In addition, the maximum stress was greater than 50% of the yield stress (64 MPa) when compressive loading exceeded 0.45 MPa for middle group and 0.3 MPa for the old group; in contrast, the maximum stress did not reach 50% of the yield stress even under 0.75 MPa for the young group. The 0.45 MPa of compressive loading on the endplate equates to about 0.7 MPa of intradiscal pressure, which is similar to that produced during daily activities, such as standing while bent forward (1.10 MPa), standing up from a chair (1.10 MPa), and lifting or holding a weight of 20 kg (1.10–2.30 MPa) [30]. These results suggest that osteoporosis can affect the stress acting on the vertebra even during routine daily activities.Figure 3
Cross-sectional view in the middle sagittal plane of the von-Mises stress distribution for the three age groups under 0.15 MPa, 0.3 MPa, 0.45 MPa, 0.6 MPa, and 0.75 MPa of compressive loading.Figure 4
Maximum stress for the three age groups under 0.15 MPa, 0.3 MPa, 0.45 MPa, 0.6 MPa, and 0.75 MPa of compressive loading.Figure 5
Ratios of the maximum stress for the middle and old groups relative to the young group under 0.15 MPa, 0.3 MPa, 0.45 MPa, 0.6 MPa, and 0.75 MPa of compressive loading.The vertebra model that incorporates a realistic trabecular structure is advantageous because it permits the simulation of in vivo specimens for the study of osteoporosis. The microscale trabecular structure represented by tiny struts would provide the mechanism that the strut deformation or buckling leads to the fracture in a whole vertebra. In addition, various grades of osteoporosis can be incorporated into the model by changing the spacing between the struts.This study has some limitations. The validity of models was indirectly confirmed by comparing the compressive strength and compressive stiffness of the developed models to those in the previous experimental and computational studies. The full validation of the model through experiments with the same specimen from which the model was generated can enhanced the confidence of this study. In addition, the generic lattice model was randomly perturbed, and the thicknesses of the endplates and the cortical shell were assumed to be uniform for all age groups. Patient-specific information on the microstructure and geometry of the bone using data from CT scans would improve the accuracy and relevance of the stress analysis. Finally, the quantitative relationship between the von-Mises stress and the fracture risk was not investigated. Mechanical tests that measure the stress and failure strength of bone, as well as clinical observations that accurately identify the region of the fracture site, would improve the prediction of vertebral fracture in osteoporotic patients.


## 4. Conclusions

Osteoporosis is a major contributor to the increased risk of fracture with age due to low bone mass and structural change. We developed finite element models of the L2 vertebra, which consisted of the endplates, the trabecular lattice, and the cortical shell, for three age-related grades of osteoporosis. The compressive strength and stiffness results revealed that we had developed a valid model that was consistent with the results of previous experimental and computational studies. The von-Mises stress, which was assumed to predict the risk of a burst fracture, was also determined for the three age groups. The results showed that the von-Mises stress was substantially higher under relatively high levels of compressive loading, which suggests that patients with osteoporosis should be cautious of fracture risk even during daily activities.



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*Source: 285165-2013-05-15.xml*