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Using Computational Simulation for Analysis and Development of Next-generation Orthopaedic Devices

Feerick, Emer M. PhD; McGarry, Patrick J. PhD

JAAOS - Journal of the American Academy of Orthopaedic Surgeons: July 2013 - Volume 21 - Issue 7 - p 440–442
doi: 10.5435/JAAOS-21-07-440
On the Horizon From the ORS

Topics from the frontiers of basic research presented by the Orthopaedic Research Society.

From the Department of Mechanical and Biomedical Engineering, College of Engineering and Informatics, National University of Ireland Galway, Galway, Ireland.

Dr. Feerick is a member of a speakers' bureau or has made paid presentations on behalf of Invibio Biomaterial Solutions. Dr. McGarry or an immediate family member has received research or institutional support and nonincome support (such as equipment or services), commercially derived honoraria, or other non-research-related funding (such as paid travel) from DePuy.

J Am Acad Orthop Surg 2013;21: 440-442

Copyright 2013 by the American Academy of Orthopaedic Surgeons.

Orthopaedic fracture fixation encompasses a broad range of fracture types. An orthopaedic surgeon may select from a wide array of commercially available devices for the surgical repair of a given fracture type. Complexity of fracture repair increases with the number of fracture fragments that result from the injury and with the level of displacement of these fragments. In the case of proximal humeral fractures, for example, several types of fixation devices have been developed and implemented clinically, ranging from locking plates to intramedullary nails.

Standard finite element analysis of fracture fixation devices models cortical bone as an isotropic elastic material, with material inhomogeneity based on Hounsfield units taken from CT scans.1 This simplified approach to the modeling of cortical bone allows for a preliminary assessment of device performance in terms of identification of stress concentrations in the device and in the bone. A recent study has extended this method to assess micromotion between fracture fragments.2 Additionally, the use of emerging device materials such as carbon fiber-reinforced polyetheretherketone has been investigated.2 Device failure commonly occurs because of pullout/pushout of orthopaedic screws from the surrounding cortical bone.3 Periprosthetic stress concentrations in the region of screw threads have been identified for locking plate and intramedullary nail simulations (Figure 1, A). Therefore, an improved understanding of the mechanism of bone damage leading to screw pullout is required to develop computational models that will guide the development of next-generation devices.

Figure 1 A,

Figure 1 A,

The alignment of the cortical bone microstructure relative to the screw axis is a critical factor in the force required for screw pullout. When osteons are aligned perpendicular to the screw axis (ie, transverse alignment), the experimentally measured screw pullout force is approximately two times higher than that recorded when osteons are aligned parallel to the screw axis (ie, longitudinal alignment).4 Furthermore, a novel experimental screw-pullout damage visualization technique has revealed an extensive zone of material damage and crack growth perpendicular to the screw axis for transverse osteon alignment (Figure 1, B, panel 2). In contrast, localized cracks parallel to the screw axis allow for pullout with minimal material damage for longitudinal osteon alignment (Figure 1, B, panel 1). The strong influence of osteon alignment on crack propagation in bone has also been observed in single mode and mixed-mode fracture mechanics tests.5,6

To provide reliable analysis and design of next-generation orthopaedic devices, the complex damage and fracture mechanics of bone must be incorporated into finite element models. Feerick and Mc-Garry4 have demonstrated that influence of osteon alignment on bone fracture during screw pullout can be accurately simulated using a composite damage model, which undergoes plastic yielding and damage initiation when a critical plastic strain is reached. Subsequent bone fracture is simulated using an element removal technique, and computed crack patterns correlate closely to experimental observations for both longitudinal and transverse screw pullout.

The explicit representation of the bone microstructure using the aforementioned composite-damage model provides accurate simulation of the experimental interaction of a single screw with the surrounding cortical bone (Figure 1, B, panels 3 and 4). However, such detailed microstructural modeling is too computationally demanding for the simulation of entire fracture fixation constructs under physiologic loading. To produce a bone fracture model that does not require explicit representation of the bone microstructure, an anisotropic damage criterion has been proposed in a study by Feerick et al,7 with the extended finite element method (XFEM) implemented to predict crack propagation. This model is shown to capture complex patterns of bone fracture under single mode and mixed-mode loading and correctly predicts crack trajectories during transverse and longitudinal screw pullout. Most importantly, given the computational efficiency of the XFEM method, this model can be used to design and analyze full orthopaedic devices, such as a locking plate for proximal humeral fixation (Figure 1, C). Additionally this computational tool offers the future potential to provide presurgical patient-specific guidance with regard to device selection and optimal screw spacing and screw orientation.

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1. Maldonado ZM, Seebeck J, Heller MO, et al: Straining of the intact and fractured proximal humerus under physiological-like loading. J Biomech 2003;36(12):1865-1873.
2. Feerick EM, Kennedy J, Mullett H, Fitzpatrick D, McGarry P: Investigation of metallic and carbon fibre PEEK fracture fixation devices for three-part proximal humeral fractures. Med Eng Phys 2013; 35(6):712-722.
3. Owsley KC, Gorczyca JT: Fracture displacement and screw cutout after open reduction and locked plate fixation of proximal humeral fractures [corrected]. J Bone Joint Surg Am 2008; 90(2):233-240.
4. Feerick EM, McGarry JP: Cortical bone failure mechanisms during screw pullout. J Biomech 2012;45(9):1666-1672.
5. Norman TL, Nivargikar SV, Burr DB: Resistance to crack growth in human cortical bone is greater in shear than in tension. J Biomech 1996;29(8):1023-1031.
6. Zimmermann EA, Launey ME, Barth HD, Ritchie RO: Mixed-mode fracture of human cortical bone. Biomaterials 2009;30(29):5877-5884.
7. Feerick EM, Liu XC, McGarry P: Anisotropic mode-dependent damage of cortical bone using the extended finite element method (XFEM). J Mech Behav Biomed Mater 2013;20:77-89.
© 2013 by American Academy of Orthopaedic Surgeons