Materials Today: Proceedings xxx (xxxx) xxx Contents lists available at ScienceDirect Materials Today: Proceedings journal homepage: www.elsevier.com/locate/matpr Structural analysis of femur bone to predict the suitable alternative material K.C. Nithin Kumar a,⇑, Narendra Griya a, Amir Shaikh a, Vaishali Chaudhry a, Subhash Chavadaki b a b Graphic Era Deemed to be University, Dehradun, India School of Technology, GITAM (Deemed to be University), Bengaluru, India a r t i c l e i n f o Article history: Received 15 November 2019 Received in revised form 26 November 2019 Accepted 4 December 2019 Available online xxxx Keywords: Femur bone Biomechanical analysis Biomaterials FEA MSC Nastran a b s t r a c t This study is based on the biomechanical analysis of femur bone using Finite Element technique. Real life activities are taken as boundary conditions and the weight of a person is considered as load for walking, standing and jumping. For biomechanical analysis, three-dimensional CAD model of human femur bone is modelled from MRI/CT Scan data using ITK-Snap software. Pre-processing and post-processing operations are done using HYPERWORKS whereas the solver is NASTRAN 10.0. Analysis is done using three materials- natural bone material, AZ31 (magnesium alloy), CP Ti (Commercially Pure Titanium Alloy). Comparative study shows that CP-Ti material generates minimum stresses for jumping, standing and walking, which are 5.69, 5.34 and 5.71 MPa respectively. And also minimum displacements for jumping, standing and walking are 0.146, 0.0583 and 0.0623 mm respectively. It is found that AZ31 is the best suited material for Bone implants and as its weight is approximately same as natural bone. Ó 2019 Elsevier Ltd. All rights reserved. Selection and of the scientific committee of the 10th International Conference of Materials Processing and Characterization. 1. Introduction Biomechanics is a branch of engineering which applies principles of mechanical engineering to analyze the biological system. It is not easy to apply mechanical laws to biological objects, but nowadays, FEM has developed as an effective analysis tool to model and simulate biological objects. Artificial objects are simple and can be easily modelled but biological objects are difficult. Anisotropic and non-linear natures of biological objects create problems in meshing and analysis. For this, FEM is the excellent way for linear analysis and non-linear analysis of biological objects [1]. Femur is the strongest and longest bone in human anatomy. Femur is thigh bone which is extended from hip-joint to the knee. It can withstand 800–1100 kg of compressive load. It is the bone which provides support to body while performing daily activities like jumping, standing and walking. Femur shape is complex and it has different composition. Thickness of femur bone varies from 4 to 8 mm and length varies from 260 to 293 mm [2]. Various finite element techniques are employed to analyse the human femur bone behaviour under different loading conditions. ⇑ Corresponding author. CAD model of femur bone is created using CT and MRI scan data and then generating the finite element mesh and at last assigning the inhomogeneous property to the bone material Geometric 3D model is created by utilizing solid works, CATIA and Materialize MIMICS [3]. Also created CAD model of femur bone in partial with volume rendering by treating Computer Tomography (CT) images [4,5]. Author utilizes Pro/Engineer under restyle feature environment, which is a reverse engineering tool, to convert the polygon model of human femur bone into 3D CAD model [6]. From CT Scan data three-dimensional CAD model of bone was created using marching cubes algorithm in Visualization Toolkit (VTK) [7]. Inhomogeneous property is assigned to the bone material with the help of an empirical relationship in terms of modulus of elasticity and bone density. Both isotropic and orthotropic materials are considered for bone [8]. Author uses different bio-ceramic composites for the bone replacement operation of human. Bio-ceramic composite material combines with the human tissue and fluid in the body so that they can improve and replace anatomical elements of the human body. Some of the bio ceramic composite used are AISI 316L, CoCrMo, Ti6Al4V, UHMWPE, Alumina, Mg–Nd–Zn–based Magnesium alloy, CP Ti grade 2 (Commercially Pure Titanium Alloy) [9]. Hydroxyapatite bio ceramic material is also utilized for teeth and bone implants because of its excellent biocompatibil- E-mail address: kcnkumar@ymail.com (K.C. Nithin Kumar). https://doi.org/10.1016/j.matpr.2019.12.031 2214-7853/Ó 2019 Elsevier Ltd. All rights reserved. Selection and of the scientific committee of the 10th International Conference of Materials Processing and Characterization. Please cite this article as: K. C. Nithin Kumar, N. Griya, A. Shaikh et al., Structural analysis of femur bone to predict the suitable alternative material, Materials Today: Proceedings, https://doi.org/10.1016/j.matpr.2019.12.031 2 K.C. Nithin Kumar et al. / Materials Today: Proceedings xxx (xxxx) xxx ity and bio activity [10]. Three-dimensional CAD model of human femur bone was imported to different FEM software where pre and post-processing is carried out, such as ANSYS, ABAQUS, HYPERWORKS [11,12]. FEA is applied to analyze stress distribution during normal walking, standing up, stair climbing and knee-bend boundary condition [13–15]. To analyze the stress and displacement 2500 N force is applied on the femur head and bottom of femur is kept fixed [16,17]. Analysis is done for walking condition with average speed of 3.9 km/h and standing up condition with height of chair 50 cm and arms kept at height of chest [10,18]. 2. Materials and method In any studies selections of materials and methods are most important. In this work the materials and method are chosen based on the previous work. Speciality of this study is that three dimensional models are prepared from CT-scan data using ITKSNAP open source software. This 3D model is imported in hyperworks for Preprocessing. 2.1. Materials There are different materials which are already in use for medical implants. Two of which, other than natural bone material, AZ31 and CP Ti are utilized here to show whose mechanical behaviour is closest to the bone material. 2.1.1. Material properties of femur bone Bone is porous in nature but for this analysis it is taken as isotropic material and its properties are taken from Amrita Francis et al. [2] which is given in Table 1 2.1.2. Material properties of AZ31 (magnesium alloy) Magnesium shows high strength and low weight ratio and because of which it has important application in automotive and aerospace industry. Magnesium is suitable for biodegradable medicinal implants, mainly to fix the fractured bones. Biodegradable implants slowly degrade in human body with time and are replaced by the evolving hard tissues. The material Properties of AZ31 are [22] shown in Table 2 2.1.3. Material properties of CP titanium CP Ti has four grades and grade 1, 2 and 3 of the first four grades is the one which is softer and much ductile in nature. It has the strongest formability, corrosion resistance and high impact toughness. Because of the above-mentioned qualities, Grade 1, 2 and 3 is the material which can be used for any application where formability is required and commonly available as titanium plates. This material is generally used in making medical implants and its mechanical properties are taken from Virginia Saenz et al. [19,20,23] shown in Table 3. 2.2. Boundary condition The boundary condition plays an importation role in the FE analysis. These boundary conditions are generally selected based on the working conditions of the femur bone to be analysed. In this study the following boundary conditions used are shown in Table 4 [21,24,10]. 3. Results and discussion The boundary conditions are applied for the natural bone, AZ31 and CP Ti. The results are discussed under following heads. 3.1. Natural bone The results are shown for the natural femur bone analysis for the real-life activities like jumping, standing and walking as boundary conditions. Von-Misses stresses and displacement are obtained for different boundary conditions. Fig. 1 and Fig. 2 show stress and displacement during jumping is 6.38 Mpa and 3.48 mm respectively and as compared to the literature it is the optimal solution [24,25]. Fig. 3 and Fig. 4 show stress and displacement during standing is 5.29 Mpa and 2.88 mm respectively and as compared to the literature it is the optimal solution [24,25]. Fig. 5 and Fig. 6 show stress and displacement during walking is 5.65 Mpa and 3.08 mm respectively and as compared to the literature it is the optimal solution [24,25]. 3.2. AZ31 biomaterial The results shown below (Figs. 7–12) show that when AZ31 Magnesium alloy is used for standing, normal walking and jumping as boundary conditions. Von-Misses stress and displacement obtained are low as compared to that of natural bone. Table 1 Material properties of Femur Bone. Properties of Femur Bone Modulus of Elasticity E (GPa) Poisson’s Ratio (c) Ultimate Tensile Strength (MPa) Ultimate Yield Strength (MPa) Density (q) (g/cm3) 3–20 0.33 135 130–193 1.8–2.1 Modulus of Elasticity E (GPa) Poisson’s Ratio (c) Properties of AZ31 Ultimate Tensile Strength (MPa) Ultimate Yield Strength (MPa) Density (q) (g/cm3) 45 0.35 260 160 1.81 Modulus of Elasticity E (GPa) Poisson’s Ratio (c) Ultimate Tensile Strength (MPa) Ultimate Yield Strength (MPa) Density (q) (g/cm3) 110–117 0.37 397.2 758–1117 4.4 Table 2 Material properties of AZ31. Table 3 Material properties of CP Titanium. Properties of CP Titanium Please cite this article as: K. C. Nithin Kumar, N. Griya, A. Shaikh et al., Structural analysis of femur bone to predict the suitable alternative material, Materials Today: Proceedings, https://doi.org/10.1016/j.matpr.2019.12.031 K.C. Nithin Kumar et al. / Materials Today: Proceedings xxx (xxxx) xxx 3 Table 4 Boundary conditions. Conditions Load (N) Loading End Fixed end Jumping Standing Walking 850 705 750 Knee joint Knee joint Knee joint Femur Head Femur Head Femur Head Fig. 5. Stress during walking for bone. Fig. 1. Stress during jumping for bone. Fig. 6. Displacement during walking for bone. Fig. 2. Displacement during jumping for bone. Fig. 7. Stress during jumping for AZ31. Fig. 3. Stress during standing for bone. Fig. 8. Displacement during walking for AZ31. Fig. 4. Displacement during standing for bone. Fig. 7 and Fig. 8 show stress and displacement during jumping is 6.42 Mpa and 0.165 mm respectively and as compared to the literature it is the optimal solution [24–27]. Fig. 9 and Fig. 10 show stress and displacement during standing is 5.32 Mpa and 0.137 mm respectively and as compared to the literature it is the optimal solution [24–27]. Fig. 9. Stress during standing for AZ31. Please cite this article as: K. C. Nithin Kumar, N. Griya, A. Shaikh et al., Structural analysis of femur bone to predict the suitable alternative material, Materials Today: Proceedings, https://doi.org/10.1016/j.matpr.2019.12.031 4 K.C. Nithin Kumar et al. / Materials Today: Proceedings xxx (xxxx) xxx Fig. 10. Displacement during standing for AZ31. Fig. 11. Stress during walking for AZ31. Fig. 14. Displacement during jumping for CP Ti. Fig. 15. Stress during standing for CP Ti. Fig. 16. Displacement during standing for CP Ti. Fig. 12. Displacement during walking for AZ31. Fig. 11 and Fig. 12 show stress and displacement during walking is 5.69 Mpa and 0.146 mm respectively and as compared to the literature it is the optimal solution [24–27]. 3.3. CP Ti biomaterial The results shown below shows that when Commercially Pure Titanium (CP Ti) used for standing, normal walking and jumping like real life activities, Von-Misses stress and displacement obtained are comparatively low as compared to natural bone. Fig. 13 and Fig. 14 show stress and displacement during jumping is 5.69 Mpa and 0.146 mm respectively and as compared to the literature it is the optimal solution [24–27]. Fig. 13. Stress during jumping for CP Ti. Fig. 15 and Fig. 16 show stress and displacement during standing is 5.34 Mpa and 0.058 mm respectively and as compared to the literature it is the optimal solution [24–27]. Fig. 17 and Fig. 18 show stress and displacement during walking is 5.71 Mpa and 0.0623 mm respectively and as compared to the literature it is the optimal solution [24–27]. The results are shown in Table 5. The Von-Misses stresses and displacement are obtained for different boundary conditions for the natural bone AZ31 and CP Ti. The stress is optimal for AZ31 as compared to CP Ti. The stresses are minimal at the femur head where it is fixed for the given materials and at the loading end (the Knee joint) minimal displacement can be observed. Fig. 17. Stress during walking for CP Ti. Please cite this article as: K. C. Nithin Kumar, N. Griya, A. Shaikh et al., Structural analysis of femur bone to predict the suitable alternative material, Materials Today: Proceedings, https://doi.org/10.1016/j.matpr.2019.12.031 K.C. Nithin Kumar et al. / Materials Today: Proceedings xxx (xxxx) xxx Fig. 18. Displacement during walking for CP Ti. Table 5 Comparison of stress and displacement for different materials. Parameters Boundary conditions Natural Bone AZ31 CP Ti Maximum stress (MPa) Jumping Standing Walking Jumping Standing Walking 6.38 5.29 5.65 3.48 2.88 3.08 6.42 5.32 5.69 0.165 0.137 0.146 5.69 5.34 5.71 0.146 0.0583 0.0623 Maximum displacement (mm) The designers must consider the manufacturability and cost while suggesting any new materials for the biomedical applications. Considering cost and manufacturability, AZ31 is best suited material for Bone implants. It has low stress and displacement in comparison to natural Bone and CP Ti [24–27]. 4. Conclusions The current study elaborates the behaviour of Human femur bone for different loading conditions. There was a slight variation in the stresses due to modelling errors. This work mainly focuses on understanding the behaviour of Femur bone for daily life activities, which were assumed as boundary conditions for analysis and muscle effect on femoral bone is neglected to understand behaviour of the bone for different loading conditions. If muscle effect is considered, then stresses will decrease by 30% [24–27]. Obtained results in above analysis could be utilized to find the displacement, stress and frequency at which fracture occurs in femur bone and also helps to decide thickness and type of material required for implantation. The Weight of natural Femur bone is 1.28 kg, AZ31 materials 1.14 kg and whereas CP Ti the weight is 2.89 kg. AZ31 is the best materials for the artificial bone implants and also it degrades over the time in the body. The CAD model developed from CT-scan data will be used to in making exact femur bone for an individual. Declaration of Competing Interest The authors declare that they have no known competing financial interests or personal relationships that could have appeared to influence the work reported in this paper. Acknowledgements The authors are thankful to Management of Graphic Era Deemed to be University, Dehradun for their motivation towards the publication of this work. References 5 [2] Amrita Francis, Ashwini Shrivastava, Chetna Masih, Nidhi Dwivedi, Priyanka Tiwari, Raji Nareliya, Veerendra Kumar, Biomechanical analysis of human femur: a review, J. Biomed. Bioeng. 3 (1) (2012) 67–70. [3] Pradosh Pritam Das, Kaushal Kishor, S.K.Panda, ‘‘Biomechanical Stress Analysis Of Human Femur Bone”, Department Of Mechanical Engineering, Nit Rourkela, Odisha, India. 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