Mathematical Modelling of Crack Fractography after Implant Failure of Titanium 4.5 LCP Used for Flexible Bridging Osteosynthesis in a Miniature Pig

Biomechanics of fracture fixation and testing of mechanical properties of bone/implant construct from the viewpoint of checking the strength and resistance ability to acting forces are of current interest. Computer modelling known as mathematical modelling is regarded as an alternative to mechanical testing of properties on a testing machine. As a result, we get a 3D model of a real object (i.e., implant for fracture fixation in our case), which can be exposed to deformation processes in the environment of the mathematical software in order to characterize forces acting on the implant and subsequently analyze the forces causing the implant failure (broken plate). The goal of this study was to employ mathematical-statistical modelling for determination of forces that caused failure (broken implant) of a five-hole titanium 4.5 mm Locking Compression Plate. This plate has been used for flexible bridging osteosynthesis of segmental femoral diaphyseal defect in a miniature pig to investigate bone healing after transplantation of mesenchymal stem cells in combination with biocompatible scaffolds. Mathematical modelling has been performed with COMSOL Multiphysics software. Numerical study that describes deformation processes taking place in implant failure demonstrates the possibilities of deformation of five-hole titanium 4.5 mm LCP in the case of exceeding the elastic limits of a material. Knowledge of the forces acting on implants used for fracture fixation acquired from mathematical modelling might be used in clinical practice in order to prevent undesirable implant failure. Plate, bone defect, fracture, deformation, crack driving face, stress field Segmental bone defects in the form of comminuted fracture constitute a frequent problem in veterinary medicine (Hulse et al. 1997). In clinical practice, various methods of fixation are used (Hulse et al. 1997). Every method has advantages and disadvantages and it is not simple to choose a suitable method of fixation for a given type of fracture to secure the optimal process of bone recovery. In cases of comminuted fractures with loss of continuity of bone column, an anatomic reduction is not possible; an osteosynthesis using the bridging plate is frequently used (Koch 2005; Nečas et al. 2007). Likewise, after bone tumour excision, it is necessary to perform bridging osteosynthesis. Similar situation (segmental ostectomy) has been induced in experimental study dealing with segmental bone healing (Nečas et al. 2010a,b). The function of the bridging plate is to prevent undesirable dislocation of bone fragments as a result of action of shearing and bending forces within the fracture line (Koch 2005). Satisfying this point is crucial from the viewpoint of possible implant failure due to incapability to sufficiently withstand all the acting forces that have been not accurately described in animals yet. In the bridging fracture fixation, the implant failure and bone nonunion can be a problem. Therefore, there are attempts to support healing of the bone by transplantation of mesenchymal stem cells in combination with biomaterial scaffolds (Crha 2009), similarly to the healing of physeal and articular cartilage lesions (Jančář et al. 2007; Koláčná et al. 2007; Krupa et al. 2007; Plánka et al. 2007; Varga et al. 2007; Míčková et al. 2008; Planka et al. 2008; Jančář et al. 2009; Plánka et al. 2009a,b; Nečas et al. 2010c). ACTA VET. BRNO 2010, 79: 621-626; doi:10.2754/avb201079040621 Address for correspondence: Prof. MVDr. Alois Nečas, Ph.D., MBA Department of Surgery and Orthopaedics Small Animal Clinic, Faculty of Veterinary Medicine University of Veterinary and Pharmaceutical Sciences Brno Palackeho 1-3, 612 42 Brno, Czech Republic Phone: +420 541 562 344 Fax: +420 541 562 344 E-mail: [email protected] http://www.vfu.cz/acta-vet/actavet.htm The testing of mechanical properties of some types of fracture fixations and verification and comparison of their strength and resistance ability to various types of acting forces are currently of significant scientific interest as evidenced by some studies (Hulse et al. 1997; Zahn et al. 2008; Filipowicz et al. 2009, Urbanová et al. 2010). However, in these studies, it is not clearly defined which acting force causes eventual implant failure. The above-mentioned studies focus on ex vivo testing of strength of various bone-implant constructs especially upon bending, compression (static of cyclic) and application of twisting forces. All these studies required to produce testing samples and to use a testing machine. In addition, a construction of new experimental device (Tyler et al. 2008) was often needed to simulate a predetermined load of bone/implant construct. As an alternative to mechanical testing, we chose computer modelling (known as mathematical modelling) which allows to create an accurate 3D model of bone/ implant structure that can be exposed to deformation tests in the environment of mathematical software without the need of using test samples. The issue of deformation of elastic bodies (Brenner and Scott 1994; Ciarlet 2000; Slaughter 2002) can be found in various applications (Ciarlet 2005). There is a set of standard numerical methods and ways how to solve these deformation-oriented problems. In this study, we report on a mathematical modelling-aided simulation of failure of bone/ plate construct, representing bridging plate osteosynthesis, and determination of the most probable type of possible implant failure. Based on the knowledge of forces acquired from mathematical modelling, we assume that acting on an implant used for a given type of fixation will enable preventing undesirable failure of particular osteosynthesis in vivo. In addition, we propose that this relatively cheap simulation method might replace expensive and time-consuming mechanical ex vivo tests of bone/implant construct performed in a laboratory. Materials and Methods For the mathematical modelling of crack fractography of an implant, a five-hole titanium 4.5 mm LCP (Synthes®, Switzerland) (Plate X, Fig. 1) was chosen. The implant had been used for a flexible bridging osteosynthesis of segmental diaphyseal defect of left femur in 10-month-old miniature pig, within the scope of broader research project (NPV II 2B06130). The implant was used in an in vivo study of bone healing after transplantation of mesenchymal stem cells in combination with biocompatible scaffolds (Nečas et al 2009; Nečas et al 2010a; Nečas et al. 2010b). In the experimental animal, we observed implant failure in the form of broken plate; the animal was lege artis euthanized. Femur was excised, the failed implant was removed and passed on for mathematical modelling performed at the Regional Centre of Advanced Technologies and Materials and Department of Mathematical Analysis and Applications of Mathematics at the Palacký University in Olomouc. The mathematical modelling was carried out by means of COMSOL Multiphysics software (a standard package of programs for numerical solution of partial differential equations in 3D). A simplified geometrical model of this five-hole titanium LCP was created, with the model of two screws attached to it in the most proximal and in the most distal plate holes. The other three holes were left empty (see Fig. 2). Compared to real geometry, this model is simplified substantially, in order to capture only the essential features of the plate. The following parameters were used to simulate the material: Young’s modulus E = 105 × 109 [Pa], Poisson’s ratio ν = 0.33 [1] and density ρ = 4940 [kg/m3]. These parameters then enter the system of second-order partial differential equations in the form where σ denotes tensor field of stress [N/m2] and F represents the vector field of density of volume forces [N/m3], which in our case vanishes. The symbol Ω stands for the three-dimensional set representing the plate. System (1), is accompanied by the so-called boundary conditions capturing the load by external forces with a known distribution, i.e., for each part of the implant surface (the boundary of Ω), stress or strain is specified. The boundary conditions have the form 622