Trabecular,Prostheses,Introduc health Trabecular Prostheses

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IntroductionToday used orthopedic prostheses are mainly made of metals and ceramics materials with outstanding strength and rigidity properties but high physiological invasiveness. These systems, while guarantying biomechanical functional tenure, they often strongly interfere with human bone physiology.This invasiveness is particularly evident for hip joint replacements using rigid full metal prostheses. Human bipedal gait and vertical posture have lead to unique and considerable evolution and adaptations of the femur, pelvis, hip and lumbar vertebrae osseous systems (Aversa et al., 2016 a-o, 2017 a-e; Petrescu et al., 2015, 2016 a-e; Petrescu and Calautit, 2016 a-b; Mirsayar et al., 2016-2017).The complex evolution of the trabecular bone positioning and morphology in human proximal femur has been primarily determined by stress patterns where bone was retained only in the areas where it underwent sufficient straining mechanical stimulus and it was lost when not (Lovejoy 1988, 2002, 2005).Therefore, clinical efficiency and long-term reliability of hip joint prosthesization needs a more deep understanding of the biomechanical invasiveness of the current restorative replacements. These products, which are made from traditional technologies such as melting and mechanical machining, do not hold flexible design solutions that permit good biomechanical bone integration in the biologically complex femur bone structure. Moreover, these traditional solutions are not adequate for younger patients who have high life expectations and then high prostheses requirements in terms of duration and biomechanical osseointegration.New generation of prostheses with better biomechanical osseointegration with the living bone are then needed.In particular, additive technologies using Titanium or Cobalt Chrome alloys, due to their process eclecticism in generating high strength complex trabecular structures, can represent the future new new generation of flexible trabecular bio-prosthetic components productions.Studies on prostheses biomimetics involving these innovative fabrication processes (Annunziata et al., 2006; Apicella et al., 2010; Aversa et al., 2009, 2016) have opened to the definition of new design criteria for more biomechanically compatible prostheses production. Figure 1 illustrates the biomimetic approach using in silico, in vitro, and in vivo validation steps for biofidel bone modeling.The biofidel models of the mandible and of the femur have been presented in previous publications (Apicella et al., 2010; Gramanzini et al., 2016; Perillo et al., 2010; Sorrentino et al., 2007; 2009).The Authors, starting from these studies, have investigated the still not fully exploited potential of additive manufacturing technologies. Moreover, the advances of our biomimetic design procedures, which have already enabled us to conceptually develop new biomimetic dental implant (Aversa et al 2009) and new trabecular prostheses, could lead to new prosthetic systems that better mimic the femur biomechanical behavior (Aversa et al 2016).Human femur has an internal light trabecular structure that, through its evolutionary optimization of the mass and morphology of the cortical and trabecular bone types (Walker et al 1985, Bruno et al 1999, Oh and Harris, 1978; Tamar and Hashin, 1980), has been able to develop mechanical properties that can bear high external stresses (Ashman et al., 1984; Dalstra et al., 1993).Human bipedal gait and vertical posture have lead to unique and considerable adaptations of the femur, pelvis, hip and lumbar vertebrae osseous systems. In particular, the hip joint acquired a much more extended position. The human femur, which is principally loaded in the vertical position, has evolved lighter and longer than for other primates where it is loaded horizontally.This morphological evolution was due because femoral neck of the limb in vertical stand is loaded as a cantilevered beam, and it can be then related to the smaller bending moments that are generated in humans.The evolutionary path of the human hip have been extensively reviewed (Lovejoi 2005) to explain the uncommon cortico-trabecular structure of the proximal femur, which presents definitely thickened cortical bone only in specific locations (Figure 2 right).In particular, as reported by Lovejoy et al (1988), the femur head thickens the cortex only near its lower portion while it exhibits a practically complete cortex absence in its upper portion as reported in Figure 2 right).Conversely, very high cortical bone is apposed in the medial diaphysis where flexural stresses are predominant (figure 2). The complexity of the human proximal femur morphological positioning of the trabecular bone in the proximal femur Figure 2 and 3) is primarily determined by rearrangements where bone is retained only in the regions where it reaches a sufficient straining stimulus and, conversely, it is lost when not (Sim and Martin 2014).Gluteus abductors reduce extension strain in the upper part of the femoral neck to such an extent that trabeculae coalesced by progressive loss of arcing trabeculae forming the Ward’s Triangle which is less radiopaque than in other primates.The morphology of the trabecular bone in the region of the proximal epiphysis (femur head) depends on the stress state. Figure 3 (left) shows the epiphysis radiographic image where a clearly visible the trabecular orientation patterns for compressed (blue lines) and tensioned regions (red lines). The morphologies of the trabeculae in these two regions are completely different (figure 3, right side): spherical pores are observed for compression while they appear elongated in the tensioned regions. The mechanical behavior of these two structures is completely different: isotropic for the spherical trabeculae and orthotropic (directional) for the elongated trabeculae.The solid models of the trabecular structures obtained from Micro Computer Tomography (Micro CT) in compressed (figure 4a) and tensioned (figure 4c) regions clarify the origin of this different mechanical behavior. The structure that is repeating in the trabecular bone of the compressed regions are constituted by repeating tetrahedral/octahedral units (figure 4b). The more complex structure of the tensioned trabeculae (figure 4 c) is characterized by a different orientation and distribution in transversal (figure 4d) and longitudinal (figure 4e) sections. This distribution, which is more continuous and massive in the longitudinal section, leads to a greater strength and rigidity of the bone in the direction of the trabeculae orientation (figure 4 e) than in the transvers direction (figure 4d).Total hip replacements in younger patients (less than 65) should meet higher life span expectation that needs an extended functional permanency of the prosthesis overcoming the actual 15 years. A more biological and biomimetic prosthesis combining the needed strength with modulated stiffness that match that of the bone has to be developed. The prosthesis that replaces the resected portions of the femur head, should be expected to ensure an “equivalent stiffness”, which cab be obtained by combining trabecular morphology and prosthesis shape, that matches that of the missing part and inducing equivalent deformation of the residual osseous region. The higher mechanical compatibility allowing better bio- and osseointegration will increase its service lifespan avoiding implant loosening and any additional surgical revision.Figure 5 shows the adaptive properties of the bone undergoing coupling between bone formation and bone reabsorption. This process relates to bone-forming activity in which the osteocytes reabsorption by osteoclasts and the renewed generations of osteoblasts from precursors replaces in a dynamic equilibrium the bone. Coupling can be then considered a complex dynamic remodelling mechanism involving the interactions of different types of cells and controlling stimuli. Since remodelling of the bone occurs at many sites “asynchronously throughout the skeleton” (Sims and Martin 2014), control mechanisms comprising the mechanical stimulation are locally active (figure 6). The mechanical stimulation should be comprised between physiological strain levels (figure 6) between 50 me and 3000 me (Apicella et al 2011 and 2015, Aversa et al 2009).Osteoblasts under specific biochemical and mechanical stimulations mature and transform in osteocytes that mineralize the bone. The osteoclasts activity in not mechanically stimulated conditions following prosthesization could then induce bone reabsorption in this new mechanical equilibrium state.The traditional full metal implants adopted today, which are characterized by stiffness much higher than those of bone where they are implanted, strongly alters the physiological local deformation leading to undesired bone reabsorption. The stiffness mismatching, in fact, leads to the low level of loading, which is know as stress shielding, that reduces the physiological strain needed for healthy bone growth (Frost, 1994, Weinans et al 1992).Conversely, a customized metallic trabecular structure, which combines both strength and elasticity requirements, may produce a beneficial healthy growth physiological mechanical stimulus even in the prosthesized bone.The trabecular metal structure of the new prostheses could be achieved using electron beam  (EB) sintered Titanium alloys. The EB Additive technology melts Titanium powders of about 50 microns forming thin layers one over the other.Moreover, biological hybrid prostheses made using hybrid polymeric materials (Schiraldi et al., 2004) coatings may further favor the growth of the bone and prosthesis biointegration. The new hybrid bio-prosthesis could drastically reduce the stress shielding phenomena while providing an advantageous improvement of prosthesis lifetime compared to traditional solutions. The recovery of optimal joint functionality will lead to the improvement of the quality of life of the patient, who perceives significantly abating the risk of new surgical operation.In this study we analyze the potential of the new additive technologies in the development of trabecular prostheses that better mimics the resected bone mechanical behavior that could lead to a new generation of biomimetic prostheses.Finite Element Models have been presented in previous works where the influence of the morphology of femur and mandible structures has been evaluated (Aversa et al 2016, 2009; Apicella et al 2010, Beaupre and Hayes 1985, Reilly and Burstein 1974, 1975).Methods and DiscussionMedical Image Segmentation has been derived using the Mimics and 3Matic softwares (Materialise, Belgium) to process CT and micro CT medical imaging of a entire femur and its proximal epiphysis lead to the solid models reported in figures 2 and 4 and to the STL files of figure 7.The results of tethraedric element material distribution are shown in Fig. 2. The yellow-green elements correspond to cortical bone while light and dark blues are relative the trabecular bone.The same procedure was applied from Micro CT segmentation of a sectioned proximal epiphysis (figure 4) to the preparation of solid models of the trabecular bone types, which characterize the micro morphology of the femur head trabecular bone types.Modeling of trabecular bone structures from Micro TAC segmentation was carried out on a section of a dry femur (figure 2 and 3). The trabecular bone of the femoral head, in fact, is characterized by different morphologies that are influenced by their of position. In particular, a structure characterized by asymmetric pores elongated in the direction of the lines of tension is evident in areas subject to tension while in the areas subject to compression the trabeculae follow symmetrical arched structure.The objective of modeling these regions was aimed to identify the exact morphology and properties of the trabecular structures to mimic successive replication of equivalent structures obtained by additive technology (see figure 7 and 8).Orthotropic trabecular bone (Figure 7 right side)The CAD solid model and solid meshes of the asymmetric trabecular bone, which is expected to show mechanical properties of an orthotropic structure, have been obtained from MicroTac of a trabecular segment 4,5x4,5x4,5 mm processed with Materialise Mimics and 3Matic softwareDetailed surface mesh (about 300,000 units) of the trabecular structure volume mesh (reduced size) of about 1200 solid elements (4 knots tetrahedrons elements) are reported in figure 7 (right side).The apparent density of the trabecular bone, which has been evaluated as the ratio between the volume occupied by trabeculae (36.5 mm3) and the total volume occupied (103.7 mm3) is 0.665 grams per cm3 (this has been evaluated by considering a limiting density for the cortical bone  of 1.9 g/cm3).Isotropic Trabecular bone (Figure 7 left side)Analogously, the CAD solid model and mesh of the symmetric trabecular bone, which is expected to show isotropic mechanical properties, have been obtained from MicroTac segmentation of a trabecular segment 16x16x16 mm processed with Materialise Mimics and 3Matic softwares.From this surface CAD model it was generated the STL file and the solid model FEM with the operation of 3matic volume mesh. The volume generated contains approximately 1900 tetrahedral elements and 31700 nodes. The bulk density of the isotropic trabecular bone, which has been derived from the ratio between the volume occupied by the trabeculae (33,167 mm3) and the overall occupied volume (2340 mm3) size with an apparent density of 0.070 g/cm3).The equivalent isotropic and orthotropic structures in Titanium will have apparent densities of 1.3 and 0.15 g/cm3. The equivalent structures to be used in the EB additive sintering of Ti powder (figure 8) are illustrated in figure 9. Namely, an equivalent octahedral repeating unit has been chosen for the isotropic trabecular bone (figure 9 left side) and an octaedroid with the ratio between the three principal orthogonal directions 1 2 1 (figure 9 right side) has been chosen for the orthotropic trabecular structure.Variable Rigidity Ti Prostheses DesignIn order to reduce the rigidity of the prosthesis stem, a trabecular structure has been properly designed to match the specific rigidity of each diaphysis section interested by the prosthesization.The proposed model of the hip proximal epiphysis follows the isostatic lines that characterizes the oriented trabecular systems (Kummer 1986) and it is shown in Figure 9 (lower side). Details of the trabecular prosthesis are given in figure 10.The five regions of the prosthesis decreasing rigidities are contained in the red lines reported in the right low side of Fig. 10 along with isotension black lines. These regions are characterized by different rigidities that progressively decrease from the highly rigid head (region 1 in Fig. 10) down to the lower rigidity one (region 5 in Fig. 9).The orientation and shape of the trabecular porosity of the prosthesis is evident in the details of the internal structure reported in the transverse and longitudinal sections reported in Figure 10b and10c.Isorigidity trabecular structure obtained by Ti alloy powder sintering by Electron Beam is reported in Fig. 10d. The apparent elastic moduli of the trabecular structures are summarized in Table 1.Table 1: Elastic moduli distribution in the isorigidity regionsRegion12345E, GPa20.011.08.04.01.0ConclusionThe proposed paper illustrates the new concept of biomimetic prostheses obtained using trabecular structure in substitution of full metal implants. The currently used prosthesis while restoring the hip functionality, do not preserve the physiological beneficial strain distribution in the remaining bone surrounding the prosthesis. The new more biological and flexible prostheses are able to be completely biomimetic since they are mimicking and recovering the physiological strain distribution of the bone.It could be expected that the new average life of these flexible prosthesis could overcome the limits of 10/15 years of the current prosthetic systemsThis work has identified design criteria and manufacturing technologies to exploit the potential of new customized health care. The new class of implants may be extended to the orthopedics of the ankle, the hip, and the knee.The new flexible prosthetic system allows better functional recovery and bone regeneration due to their biomechanical activity.Application of the product is surgical oncology is also possible in the restoring of removed bone section of primitive and metastatic tumors.ReferencesAnnunziata, M., R. Aversa, A. Apicella, A. Annunziata and D. Apicella et al., 2006. In vitro biological response to a light-cured composite when used for cementation of composite inlays. Dental Mater., 22: 1081-1085. DOI: 10.1016/j.dental.2005.08.009Apicella D., R. Aversa, E. Ferro, D. Ianniello and A. Apicella, 2010. The importance of cortical bone orthotropicity, maximum stiffness direction and thickness on the reliability of mandible numerical models. J. Biomed. Mater. Res. Part B Applied Biomater., 93: 150-163. DOI: 10.1002/jbm.b.31569Apicella D., M. Veltri, P. Balleri, A. Apicella and M. Ferrari, 2011. 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