Individual-specific multi-scale finite element simulation of cortical bone of human proximal femur
Graphical abstract
Introduction
The structure of bone changes across macro- and micro-structural scales, affording bone seemingly contradictory characteristics of rigidity, strength, toughness, flexibility, lightness and porosity. Macro-level finite element (FE) models of the human femur, based usually on scanning by one or the other of magnetic resonance imaging (MRI) or quantitative computed tomography (QCT), have addressed the trabecular and cortical components, supplemented in the case of trabeculae by microQCT [1], [2], [3], [4], [5], [6], [7], [8]. Because cortical bone forms 80% of the adult skeleton and makes a corresponding contribution to bone strength [9], [10], [11], we focused the multi-scale modeling on the cortex of the human femur. The computation of material properties from the grey scale values, calibrated during imaging preparation, in terms of bone mineral density (BMD), yields isotropic material properties of the macro-structural model. However, morphometric studies of bone indicate heterogeneity of orientation of Haversian system [12], [13]. At the micro-level, although the anisotropy due to the orientation of collagen and of apatite has been included in micro-FE models adjacent to osteocyte lacunae and elsewhere in the lamellae, we here address this anisotropy for the first time in individual-specific and experimentally verified multi-scale models of bone [14], [15], [16], [17], [18], [19]. Such osteon groups, and in particular single osteons, show specificity of distribution of collagen orientation to regions of tension or compression due to physiological mechanical stimulation as optimized to support function, with variations in the presence of bone disease [20], [21], [22], [23], [24], [25].
Although the processes by which genetic, environmental and clinical factors affect bone structure at various levels of the multi-scale remain inadequately understood, the well-grounded understanding that in aggregate they do affect the structure of bone at various levels of the multi-scale motivates the preparation of individual-specific, multi-scale FE models. Indeed, current patient-specific FE models prepared from a patient’s CT scan, that address only the macro-level, can predict hip fractures only as well as, or just slightly better than epidemiological data based on clinical history or bone density, none of which are satisfactory [4], [5], [26], [27], [28], [29], [30], [31], [32]. One source of the limited value of the macro-level FE models is their reliance on material properties obtained from local values of BMD. Because such values are isotropic, the material properties used are isotropic. However, cortical bone tissue shows direction-dependent properties, some of which are independent of BMD, and that previously have been found to affect the mechanical response to loading. This motivates inclusion of the anisotropy of the micro-structure in order to improve fracture prediction [33], [34]. As a partial step towards addressing anisotropy, non patient-specific macro-FE models of the cortical components of long bones, have employed either orthotropic or transversely isotropic material properties at the macro-level so as to account for the preferential orientation of the Haversian system, hypothesized to provide reinforcements to the structure along orientation of greater strain or stress (see e.g. [8], [12], [13], [35]). However, the orientation of collagen within the Haversian system, which follows the experimentally observed distributions adjacent to the osteocyte lacunae and elsewhere in the lamellae, has not previously been modeled in conjunction with the osteon-specific degree of calcification within a hierarchical macro-micro simulation of long bone. We undertake such modeling here.
The macro- and micro-structures of the human femur have not yet been biomechanically linked with attention to the main micro-structural variables, nor has their interaction yet been well explored. Micro-level structural analysis of bone specimens isolated from the human femur has established that the orientation of collagen and of carbonated hydroxyapatite needles (here called apatite), as well as the local degree of calcification, are fundamental micro-structural variables [9]. Specifically, such variables form patterns at the macro-structural level and at the micro-structural level, differently so around osteocyte lacunae locally and elsewhere in the tissue. Such patterns affect the strain and stress distributions at the micro-level [17]. In particular, strains are significantly amplified at the osteocyte lacunae, augmenting the strain perceived by the osteocytes, important for bone remodeling signaling [36], [37], [38], [39]. Micro-cracks in bone (1) occur when strain exceeds the elastic limit; (2) locally parallel collagen orientation; (3) show density and length that differ between regions mechanically stimulated under tensile vs. compressive loading; (4) accumulate faster with higher strains; (5) trigger resorption of tissue; and (6) lead to impaired mechanical properties that can cause suffering of the individual or even death of the elderly [39], [40], [41], [42], [43], [44], [45], [46], [47], [48], [49], [50], [51], [52]. At the micro-level, although the anisotropy due to the orientation of collagen and of apatite has been included in micro-FE models, it has not heretofore been addressed in patient-specific, multi-scale models of bone [17], [36]. Further, we model specifically the osteon groups that we observe in the bone tissue of the individual at the region of interest.
The objective of this research was to develop individual-specific multi-scale models, experimentally validated at each structural level, that take into account collagen-apatite anisotropy and presence of osteocyte lacunae. The application of such models will serve to investigate the micro-structural strains in response to physiological loading in terms of age, sex, and ethnicity (e.g. [35], [53], [54]), as well as clinical factors including presence of disease and pharmacological treatment that affect the bone tissue (e.g. [55], [56]). We here present the modeling method and three examples of its application that point to new findings in agreement with previous experimental and modeling results. The method can simulate types of physiological loading different from the ones presented. It can also incorporate alternative mechanical properties obtained from different experiments.
Section snippets
Multi-scale computational methods and modeling strategies
Finite element (FE) analysis is performed three times, at macro-, meso- and micro-structural levels, with each analysis at a greater level of refinement, using Abaqus software (Simulia Inc.) (Fig. 1, Table 1).
Results/discussion
We present three examples of multi-scale models for the proximal diaphysis of two femurs. We describe the results of the FE analysis of three multi-scale FE analyses in three ROI’s, one in femur 1’s medial (1M) sector and two in femur 2’s posterior-medial (2PM) and anterior-lateral (2AL) sectors. The first femur showed approximately one third the bone density of the second femur at the examined ROI’s. The second example focuses on two regions of interest of same bone density and different
Applying these methods to predict integrative physics and physiology in biological systems
The simulation methods presented provide distributions of deformations, strains and stresses at the ROI of the individual’s femur modeled. Our simulation allows for comparison between different loading conditions, different ROIs, or different material properties, including by way of example, osteon models with specific collagen orientations and/or degrees of calcification. These models allow prediction of distribution of strain and stress in the bone of an individual from the individual’s QCT
Conflicts of interest
Dr. Ascenzi is the inventor under granted and pending published patent applications related to her bone micro-structural research, the rights to which are licensed to Micro-Generated Algorithms, LLC, a California limited liability company in which she holds an interest.
Roles of authors
Each author has materially participated in the research and manuscript preparation. Drs. Ascenzi and Keyak conceived and designed the multi-scale model. Dr. Ascenzi developed the meso- and micro-structural models, and wrote the manuscript. Dr. Keyak developed the macro-structural model and the transition from macro- to meso-level models. Under Dr. Nackenhorst’s supervision, Dr. Lutz designed and implemented the overall modeling approach of the smooth-surface macro-structural model, and Dr.
Acknowledgments
This research was supported in part by the National Science Foundation through TeraGrid and XSEDE resources provided by NCSA and SDSC under grant TG-BCS100001. We specifically acknowledge the assistance of Mahidas Tatenani (Trestles, SDSC), Seid Koric (Ember, NCSA) and Tajendra Singh (Hoffman2 cluster, Academic Technology Services, UCLA) with supercomputing; and of Allison K. Roe with manuscript preparation.
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