Technical noteSelecting boundary conditions in physiological strain analysis of the femur: Balanced loads, inertia relief method and follower load
Introduction
Kinematic models and inverse-dynamics methods have been widely introduced into biomechanical research to map external loading to internal forces and moments [1], [2], [3], [4], [5], [6], [7]. These methods usually employ rigid body assumptions and approximation of kinematics to estimate in vivo loads. Analyzing tissue straining by means of finite element (FE) technologies facilitates extending local load information towards local strain. Such approaches have proven to be powerful to predict implant loading in various clinical situations after joint replacement [8], [9], [10], fracture fixations [11], [12] or even simulating bone remodeling following total joint replacements [13] or fracture fixations [14], [15].
Mandatory to these mechanical analyses is a proper understanding of mechanical boundary conditions (BCs) represented by the set of muscle and joint contact forces and fixation in space to achieve load equilibrium. Force balancing (FB), inertia relief (IR), and follower load (FL) are different options beside the widely used conventional fixation of nodes in space (displacement constraints) to achieve balanced loading.
Force balancing: Musculoskeletal models based on reasonable assumptions (e.g. muscle force optimization criterion) and measurements during gait analysis can be used to evaluate joint and muscle loads at specific points assumed a priori. These loads are in equilibrium with estimated inertial, measured external and estimated gravity forces. When additional information, for instance from measurements, is used to refine or alter the model, these forces may need to be re-balanced to achieve physiologic loading: when forces are distributed (i.e. on joint surface), added (e.g. iatrogenic pull during an operation or rehabilitation, or active implants), dropped (e.g. cut muscles or alternative muscle activation) or if there is high deformation or deflection, re-balancing of loads (adapting load estimates) within an FE model becomes essential. An example is the medio-lateral load distribution within the knee joint. Distribution of loads is difficult to measure in vivo while total reaction force and moment can be assessed reliably [16], [17]. We suggest distributing the total central load using two singular medial and lateral compartment loads to assess physiologic straining of bones while neglecting the exact joint surface pressure distribution [18], [19]. This re-distribution may cause non-physiological deflection through an additional moment. The loads have to be re-balanced or widely used constraints for the femur [20] can prevent non-physiological deflection but may result in high reaction forces which do not reflect in vivo loads. Reaction forces depend on the selection of the fixed nodes and constraints [20] and thus reflect a somewhat arbitrary concept, and differ among models and studies [21], [24].
Inertia relief: Standard FE BCs constrain at least six degrees of freedom (DOF). Using the IR method [25], [26] enables FE analysis without setting arbitrary constraints, putting the FE model in a dynamic equilibrium simulating static loading conditions without reaction forces [25]. When loads are reasonably well known, one node of relative acceleration in space can be set with optional additional displacement constraints. With IR, only the stress influencing elastic deformation is calculated and forces in excess of force equilibrium are converted to accelerations (Fig. 1), which may serve as a control variable for validation.
Follower load: FL has been introduced in spine biomechanics [27] as force which follows surface orientation by rotating with the body. Although follower load may not be a physiological loading configuration itself for all activities, FL has been shown to lead to more realistic results of an in vitro experiment of spine loading [27] and in different computer models [28], [29].
BCs defined by Speirs et al. [20] can be used as a simple standard for FE models of the whole femur [53]. The purpose of the present study is to compare the BCs inertia relief method (IR), force balancing (FB) and follower load (FL) in respect to their relevance on bone strains in intact and fractured femoral bones using a patient-specific FE model. Our hypothesis is that adopting a combination of IR, FB and FL leads to a set of BCs with results that are physiologically realistic and comparable to results when using the definitions of Speirs et al. [20] (BCS) as described in the methods section. We aim at concluding with recommendations for the use of these BCs in biomechanical investigations of bone straining in FE analyses.
Section snippets
Patient data
A data set including gait, quantitative computed tomography (qCT) and ground reaction force data of one representative patient [13], [30] forms the basis of this analysis.
Geometry
Patient-specific FE models were created from the qCT data set using Amira v.5.3 (Visage Imaging, San Diego, USA) for segmentation, Geomagic Studio 10 (Geomagic, Morrisville, USA) for creation of NURBS (Non Uniform Rational B-Splines) and Abaqus/CAE v.6.9 (Dassault Systèmes, Vélizy-Villacoublay, France) to create a solid body
Displacements
In global coordinates, using BCS the epiphyses are held in place and the shaft is deflected while for IR the bone bends around the center of mass and the most distant nodes are deflected most. However excluding FL, relative displacements of node N2 (hip joint load application) to N1 or the femoral shaft to node N1 (knee center) are similar with maximum deviations of 0.7 mm for intact bone and 3.8 mm for stabilized bone. Using BCS, the FL reduces the relative displacement up to 3 % at the
Discussion
Balanced musculoskeletal loading is essential to investigate the mechanical status within a bone and at its boundaries. Specifically, if deformations of the bones are taken into considerations, the explicit set of BCs and their balance is essential to strain results. There is an inconsistency in defining BCs for FE models of the femur across study groups [21], [22], [23], [24].
Standard methods use reasonable loads in combination with reasonable displacement constraints. However, BCs influence
Conflict of interest
No author has any financial and personal relationships with other people or organizations that could inappropriately influence their work.
Acknowledgments
We would like to thank Daniel Andermatt and Depuy Synthes for the support and providing the geometry of the locking plate. This study was supported by Synthes, Zuchwil, Switzerland.
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