Thin–Walled Structures 151 (2020) 106713 Contents lists available at ScienceDirect Thin-Walled Structures journal homepage: http://www.elsevier.com/locate/tws Full length article Performance of a 3D printed cellular structure inspired by bone Abdallah Ghazlan **, Tuan Nguyen , Tuan Ngo *, Steven Linforth , Van Tu Le University of Melbourne, Australia A R T I C L E I N F O A B S T R A C T Keywords: Bioinspired 3D printing Trabecular bone Thin-walled cellular structure Numerical analysis Biological thin-walled cellular structures have intricate arrangements that facilitate lightweight and high energy absorption. A prime example is trabecular bone, which possesses a unique thin-walled cellular structure of connected rods or plates, to minimise weight whilst meeting the loading demands from the body. For example, the femur has a closed cell structure of plates to transmit heavy loads to the ground, whereas a carpal bone has an open cell structure of connected rods. Although existing lightweight thin-walled cellular structures with controlled arrangements have been investigated extensively, such as those with re-entrant geometries, asym­ metric instability due to local buckling can hinder their energy absorption capacity. Mimicking the features of trabecular bone can offer the designer a greater degree of control over the buckling and collapse mechanisms of thin-walled cellular structures. This can lead to the development of high-performance protective systems with superior energy absorption capabilities. This study employs 3D printing and finite element analysis techniques to mimic and investigate several key features of the plate-like thin-walled cellular structure of trabecular bone. The performance of the developed bioinspired structure is benchmarked against traditional hexagonal and re-entrant designs. The controlled and progressive buckling and collapse mechanisms observed in the bioinspired structure result in superior energy absorption over its re-entrant and hexagonal counterparts. 1. Introduction The intricate arrangements of biological thin-walled cellular struc­ tures facilitate lightweight and high energy absorption. These include thin-walled cellular structures that have been optimised over many years of evolution, including those of porous or trabecular bone [1–4], porcupine quills [5–8], turtle shells [9–12] and toucan beak [13–16]. In particular, trabecular bone (Fig. 1) shows a unique cellular arrangement that minimises weight whilst meeting the loading demands of the human body. Engineered thin-walled cellular structures, such as those with honeycomb, re-entrant, spiral and hexachiral geometries, to name a few, have been extensively investigated for numerous applications, including extreme loading (blast and impact) [17–20] and crashwor­ thiness [21–24]. Although auxetic (or negative Poisson’s ratio) cellular structures, such as those with re-entrant geometries, have been found to show the best performance in terms of lightweight and energy absorp­ tion, asymmetric instability due to local buckling has been found to hinder their energy absorption capacity [17,18]. Mimicking the buck­ ling and collapse mechanisms in the intricate structure of trabecular bone can guide the development of superior lightweight thin-walled cellular structures for protective applications. Bone is a sandwich structure that consists of a soft core (trabecular or spongy bone) and a dense outer shell (compact bone). Bone grows in response to the loads applied to it. As such, the density of bone in a particular location of the body depends on the magnitude of the applied loads. In this study, the closed thin-walled cellular structure of a trabecular bone (see Fig. 1) is mimicked for energy absorption appli­ cations. Similar to man-made sandwich structures, the mechanical behaviour of bone depends on the properties of its components and their geometry [25–27]. Generally, trabecular bone has a closed-cell plate-­ like structure, an open-cell strut-like structure or a hybrid of the two. Plate-like structures (Fig. 1b) can be found in denser bones that can support high loads, such as the human femur. Some of the plate-like elements have small openings in them to allow for the interconnection of marrow spaces. Open cell strut-like structures can be found in other types of bone, such as the carpal bone, which is not typically subjected to high loads. Schilling et al. [28] predicted the relative volume of carpal bone by CT scanning a spherical volume of interest (VOI). They defined the relative volume as the ratio of the volume of bone (trabeculae) to the total volume of the VOI. The thickness of the strut-like elements (e.g., in * Corresponding author. Department of Infrastructure Engineering, The University of Melbourne, Victoria, 3010, Australia. ** Corresponding author. Department of Infrastructure Engineering, The University of Melbourne, Victoria, 3010, Australia. E-mail addresses: ghazlana@unimelb.edu.au (A. Ghazlan), dtngo@unimelb.edu.au (T. Ngo). https://doi.org/10.1016/j.tws.2020.106713 Received 26 August 2019; Received in revised form 17 February 2020; Accepted 4 March 2020 Available online 19 March 2020 0263-8231/© 2020 Elsevier Ltd. All rights reserved. A. Ghazlan et al. Thin-Walled Structures 151 (2020) 106713 Fig. 1. a) Bone sandwich structure; b) Closed cell plate-like structure of trabecular bone, which is composed of concave, convex and hybrid (both concave and convex) cells (adapted from Ref. [25]); and c) 3D printed hybrid thin-walled cellular structure that mimics the cell geometries of plate-like trabecular bone. the carpal bones of a human) is approximately 200 μm with a relative volume of 17.31 [29]. However, researchers have observed variabilities in the thickness of the struts and relative volumes among different species. For example, the carpal bone of a gorilla is 370 μm thick with a relative volume of 34.09 [28]. Hybrid plate-like and strut-like structures can be found at the transition zone in bone, namely the interface be­ tween the compact shell and the thin-walled cellular core. Trabecular bone typically has a relative density that is less than 0.7 [25]. Compact bone has a higher relative density than 0.7. The relative density of open cell rod-like structures is typically less than 0.13. In contrast, the relative density of closed cell plate-like structures is greater than 0.2. At intermediate relative densities, the structure of a trabecular bone is composed of a combination of rod- and plate-like elements [25]. Concave and convex cell geometries can be observed in the plate-like thin-walled cellular structure of trabecular bone (Fig. 1b). Mimicking these structural characteristics can provide a method for controlling the Fig. 2. a) Unit cell arrangements obtained from the cell walls of different Voronoi diagrams: a) Hexagons; b) Pentagons; c) Hybrid quads-hexagons; and d) Hybrid oriented hexagons. e) Procedure for obtaining a re-entrant unit cell (concave) from a hexagonal cell (convex). 2 A. Ghazlan et al. Thin-Walled Structures 151 (2020) 106713 Fig. 3. A graphical representation of the numerical and manufacturing framework for generating the finite element model and 3D printed sample of the bio­ inspired structure. buckling collapse mechanisms of thin-walled cellular structures, which can thereby enhance their energy absorption capacity. In trabecular bone, only about 20% of the volume is filled with bone material and the remainder with bone marrow [27,29]. At the nanoscale, it is composed of Type 1 collagen/apatite building blocks [2,3]. Trabecular bone has been reported to possess several hierarchical levels of porosity, from the nano-scale to the macro scale: collagenapatite (10 nm), canalicular (100 nm), lacunar (up to 8 μm), vascular (50 μm), and intertrabecular (up to 1 mm) [2,30]. These facilitate several biological functions such as fluid transport. Voronoi diagrams have been extensively used to model biomimetic structures [31–35], foams [36,37] and polycrystalline solids [38,39]. Given their controlled randomness, Voronoi diagrams have been used to model the longitudinal and transverse trabeculae of a trabecular bone to assess age-related losses [1]. Given that a trabecular bone is a thin-walled cellular material, its stress-strain curve has three distinct regions. In the linear elastic region, the cell walls bend or compress axially. This is followed by a plateau region, which is roughly constant, where the cells begin to collapse by elastic buckling, plastic yielding or brittle fracture of the cell walls. In the densification regime, which is represented by the steep portion of the stress-strain curve, there is contact between the cell walls [19,40]. Advancements in 3D printing technologies have enabled the fabri­ cation of complex prototypes with high accuracy, including cellular structures and bi-material composites [33,41]. Consequently, 3D print­ ing is the dominant manufacturing method employed by researchers for fabricating prototypes of cellular structures [22–24,42]. Extrusion-based methods are quite popular due to their effectiveness in fabricating polymeric prototypes with intricate geometries from a wide range of materials, including Nylon, acrylonitrile butadiene styrene (ABS) and polyurethane. Extrusion-based 3D printing is thereby employed in this research to develop a thin-walled bio-mimetic cellular structure that is targeted at energy absorption applications. To this effect, several key features of plate-like trabecular bone are mimicked. An example is shown in Fig. 1c, where a bone-like structure is 3D printed using hybrid concave and convex cell geometries. Experimental in­ vestigations are conducted to benchmark the performance of the bone-like structure against well-known re-entrant and honeycomb ge­ ometries, using the peak load and energy absorption as the key perfor­ mance criteria. A finite element (FE) model is then developed and validated to simulate the buckling and collapse mechanisms of the bone-like structure to pave a path for the development of design pa­ rameters. The FE method is employed for simulating the behaviour of cellular structures due to the availability of commercial software. 2. Numerical and manufacturing framework 2.1. Generating the bone-like unit cell designs To generate a thin-walled cellular structure based on the architecture of a trabecular bone, several unit cells were extracted from different Voronoi diagrams (see Fig. 2a–d). The Voronoi approach is a powerful tool to generate the bioinspired and benchmark (hexagonal and reentrant, Fig. 2a,e) structures. These designs were quickly obtained by manipulating the sites (or points) of the Voronoi diagram. The locations of the sites control the boundaries of the Voronoi polygons. The math­ ematical description of a Voronoi diagram is given in Ref. [41] and more comprehensive proofs are provided in textbooks on computational ge­ ometry [43]. Although Voronoi diagrams can only produce convex re­ gions, a unit cell can be extracted and transformed to obtain concave geometries, which is demonstrated in Fig. 2e. The unit cell in Fig. 2d was chosen as the representative bioinspired structure because it has two different sub-cells that can be manipulated simultaneously. Therefore, the hybrid thin-walled cellular features of trabecular bone can be mimicked more closely (see Fig. 1b). The hexagonal (Fig. 2a) and the re-entrant configurations (Fig. 2e) were chosen as the benchmark cases 3 A. Ghazlan et al. Thin-Walled Structures 151 (2020) 106713 Fig. 4. The hybrid oriented hexagonal design. The design parameters that were manipulated to obtain the 3D printed bioinspired structure (see Fig. 3) are also presented. for assessing the performance of the bioinspired structure. Importantly, re-entrant and hexagonal geometries have been extensively studied for extreme loading applications, where energy absorption is of paramount importance [17–19,40,44]. � Generate a pattern of the unit cell to obtain a vertical scaffold. This will ensure that a uniform 2D finite element mesh is generated in subsequent steps, which is extruded in the out-of-plane direction � Export the geometry of the scaffold into the International Graphics Exchange Specification (IGES) CAD format and import it into the finite element software (ABAQUS) for meshing � Mesh half the scaffold due to its symmetry about the vertical plane � Copy the mesh and scaffold to obtain the final finite element model and 3D printed structure. 2.2. Constructing the numerical model and 3D printed bioinspired structure Fig. 3 illustrates a flow chart of the numerical and manufacturing framework that was used to generate the finite element model and 3D printed sample of the bioinspired structure. The key steps of the framework are summarised as follows: 2.3. The bioinspired structure with simplified design parameters The meshed finite element model and 3D printed sample of the bioinspired structure (Fig. 3) were obtained by manipulating the pa­ rameters of the hybrid oriented hexagonal design (Fig. 2d). These design parameters are presented in Fig. 4 and described as follows: � Generate a Voronoi diagram of the desired biomimetic design (hybrid oriented hexagons in this case) � Extract the edges of a unit cell from the Voronoi diagram and export the geometry to a format that is compatible with a commercial computer-aided design (CAD) program � Thicken the unit cell walls and modify its design parameters as necessary (e.g., cell angles, lengths of the struts and ties, and wall thickness) � W ¼ 20 mm,H ¼ 20 mm: Width and height of the unit cell, respectively � lut ¼ 8 mm, llt ¼ 4 mm: Length of the upper and lower tie, respectively � tw ¼ 2 mm: Thickness of the cell walls Fig. 5. 3D printed thin-walled cellular structures with the same number of cells across the width and depth: a) Hexagonal; b) Re-entrant; c) Bioinspired. The specific energy absorption (kJ/kg) is compared to assess their performance (see Table 1) as the structures do not have an identical mass. 4 A. Ghazlan et al. Thin-Walled Structures 151 (2020) 106713 Fig. 6. Tensile engineering stress-strain curve for Markforged Tough Nylon. Fig. 7. Force-displacement curves for the 3D printed bioinspired and benchmark (hexagonal and reentrant) structures under displacement controlled uniaxial compression. The dimensions of the tested specimens (60 � 60 mm) can be visualised in Fig. 4. The values of the ends of the linear-elastic and plateau regions for each structure are labelled by L and P on the displacement axis, respectively. C1 and C2 signify a minimum and maximum in the plateau region, which are referred to later in the text. Fig. 8. Buckling and collapse mechanisms of the hexagonal structure. 5 A. Ghazlan et al. Thin-Walled Structures 151 (2020) 106713 Fig. 9. Buckling and collapse mechanisms of the re-entrant structure. � α ¼ 63� , β ¼ 45� : Angle of the upper and lower cell strut, respectively � ws: The distance between the upper and lower struts, which is identical at the top and bottom of the cell due to its periodicity. This parameter is determined by the above design parameters. Table 1 Comparing the mechanical performance of the bioinspired thin-walled cellular structure with the benchmark cases (hexagonal and re-entrant). The average values between the two tests are presented for each structure. The out-of-plane thickness of the model was chosen as 30 mm to ensure that only in-plane buckling occurs. 3. Sample fabrication and experimental parameters The CAD files of the bioinspired and benchmark structures (hexag­ onal and re-entrant), which were generated using the manufacturing framework (see Section 2), were converted to the Standard Triangle Language or stereolithography (STL) format. The STL files were subse­ quently converted to 3D printing instructions. The 3D printed samples (Fig. 5) were fabricated using the Markforged Mark Two desktop 3D printer, which has a build volume of 320 � 132 � 154 mm. Two samples were fabricated for each type of structure to assess the repeatability of the test results. To print the geometry illustrated in Fig. 4, a heated filament of Markforged Tough Nylon, a standard plastic material, was extruded layer-by-layer through a 200 μm nozzle onto a heated print bed at 250� C. Each printed layer has a thickness of 200 μm and the total height of the printed model is 30 mm, which corresponds to its overall thickness. This popular 3D printing technique is well-known as layer-bylayer deposition [45]. Each layer of the cellular structure was printed using a random pattern to reduce the directional dependence of the mechanical response. The tensile engineering stress-strain curve of the material is presented in Fig. 6, which was obtained from quasi-static tension tests conducted at the University of Melbourne, Australia. The 3D printed samples were subjected to quasi-static compression at a displacement-controlled loading rate of 3 mm/min. Structure Relative Density Peak Load (kN) Stiffness (N/mm) Energy absorption (J) Specific energy absorption (kJ/kg) Hexagonal Re-entrant Bioinspired 0.33 0.47 0.38 2.1 2.6 1.5 478.9 849.3 418.2 57.5 19.6 97.3 8.91 2.11 12.97 elastic, plateau and densification), which demonstrates that the 3D printing quality is consistent. As per the typical force-displacement behaviour of cellular structures reported in the literature, several re­ gions of interest can be observed, namely linear-elastic, followed by a plateau region and a final densification region. It can be observed that once the peak load is reached in the benchmark structures (hexagonal and re-entrant), the load carrying capacity diminishes before the initi­ ation of the plateau region. In contrast, the bioinspired structure maintains a relatively increasing load carrying capacity throughout the experiment. This results in a larger area under the force-displacement curve before the onset of densification, which demonstrates its supe­ rior energy absorption capacity over the benchmark structures. Impor­ tantly, densification initiates in the bioinspired and hexagonal structures at a similar displacement of around 33 mm. In contrast, the re-entrant structure is highly unstable (see Fig. 9) and thereby reaches densifica­ tion much earlier (at a displacement of around 18 mm). The unstable behaviour of the re-entrant structure results in a relatively smooth plateau region. In contrast, several peaks can be observed in the plateau regions of the bioinspired and hexagonal structures due to progressive buckling and collapse. This behaviour is further investigated by ana­ lysing the collapse mechanisms in each structure individually. The energy absorption capacity of thin-walled cellular structures is typically quantified before the onset of densification. The peak load, 4. Experimental results and discussion The stress-strain curves for the hexagonal, re-entrant and bioinspired designs under uniaxial compression are presented in Fig. 7. Similar mechanical behaviour can be observed for each sample (i.e., linear 6 A. Ghazlan et al. Thin-Walled Structures 151 (2020) 106713 Fig. 10. Buckling and collapse mechanisms of the bioinspired structure at prominent displacements. These prominent deformations of the structure were observed in the experiment at different displacements to those in Figs. 8 and 9. stiffness and energy absorption of the three structures are summarised in Table 1. It can be deduced that the bioinspired structure shows the softest response in the linear elastic region (418.2 N/mm), reaches the lowest peak load (1.5 kN) before the initiation of the plateau region (i.e., the end of the linear-elastic region labelled in Fig. 7) and has the highest energy absorption capacity (97.3 J). This equates to a 29% reduction in the peak load and 69% increase in energy absorption (area under the curve before the end of the plateau region labelled in Fig. 7) compared to the hexagonal structure. Furthermore, from the force-displacement curve, it can be observed that the load in the bioinspired structure does not diminish in the plateau region but shows a relatively monotonic increase, which results in superior energy absorption over the bench­ mark structures. The mechanisms that may be attributed to these su­ perior performance enhancements are further analysed below using experimental observations. The buckling and collapse mechanisms of the hexagonal structure can be observed in Fig. 8. At a displacement of u ¼ 4:5 mm, the structure is relatively stiff and the cells can be observed to deform uniformly. This corresponds to a peak force of 2 kN on the force-displacement curve. At u ¼ 7:5 mm, the lower cells rotate counter-clockwise and begin to collapse, whilst the upper cells rotate clockwise. At u ¼ 10:5 mm, the lower cells completely collapse, which corresponds to the first minimum observed in the plateau region of the force-displacement curve (labelled as C1 in Fig. 7). This process repeats, whereby the upper cells begin to buckle at a displacement of u ¼ 13:5 mm, which corresponds to a peak in the plateau region of the force-displacement curve (labelled as C2 in Fig. 7). This mechanism of progressive buckling and collapse repeats until densification initiates at a displacement of u ¼ 33 mm. Impor­ tantly, the complementary rotations of the upper and lower cells induce a torsional effect that tends to stabilise the structure. Contrary to the reentrant structure analysed further below, the hexagonal structure does not buckle in one direction due to these complementary stabilising effects. The buckling and collapse mechanisms of the re-entrant structure can be observed in Fig. 9. At a displacement of u ¼ 3 mm, the structure begins to buckle inwards due to the negative Poisson’s ratio (auxetic) effect, which is activated by the re-entrant geometry of the unit cells. At this stage, the structure is behaving linear elastically. At u ¼ 4:5 mm (see Figs. 7 and 9), instability is evident in the structure, which begins to buckle towards the left. This asymmetric buckling is attributed to the higher stiffness (Table 1) of the re-entrant structure compared to that of the bioinspired and hexagonal structures. In effect, the horizontal ties between the re-entrant unit cells provide relatively rigid lateral re­ straints that nullify the auxetic effect (see Fig. 9). This deformation mechanism repeats through a displacement of u ¼ 7:5 mm and up to u ¼ 13:5 mm, which corresponds to the minimum load reached in the plateau region. Consequently, the plateau region in the forcedisplacement curve appears smooth, as the auxetic mechanism is not activated due to the asymmetric buckling of the structure. This behav­ iour also causes the re-entrant structure to densify much earlier than the hexagonal and bioinspired structures (see Fig. 7). Introducing more unit cells across the width of the re-entrant sample may result in a wider and more stable structure. However, this has been found to diminish the auxetic (negative Poisson’s ratio) effect, which is not desired [17,18,20, 46]. Re-entrant structures are intended for activating the auxetic energy absorption mechanism. The buckling and collapse mechanisms of the bioinspired structure can be observed in Fig. 10. At a displacement of u ¼ 4:5 mm and through to u ¼ 9 mm, the structure is seen to buckle in the re-entrant regions of the hybrid cells. These cells have a narrow re-entrant region and a convex region. Given that the re-entrant region is narrow, the neigh­ bouring unit cells support the convex region of the hybrid cell when it collapses. In effect, once the initial peak load (1.5 kN) is reached, the load carrying capacity of the structure does not diminish at the initiation of the plateau region. This is a key advantage over the re-entrant and hexagonal structures, which are stiffer and reach a higher peak load that diminishes near the onset of the plateau region. At u ¼ 16:5 mm, the convex regions of the hybrid cells collapse onto the concave regions, which induces a hardening effect in the plateau region i.e. the peak load is seen to increase in a relatively monotonic manner up to the onset of densification. After these hybrid cells densify, the lower cells at the base of the structure collapse and densify at u ¼ 19:5 mm, which causes a minor jump in the force-displacement curve. At u ¼ 25:5 mm, the convex unit cells buckle and collapse until the onset of densification at 7 A. Ghazlan et al. Thin-Walled Structures 151 (2020) 106713 Fig. 11. The densified structures: a) Hexagonal; b) Re-entrant; c) Bioinspired. u ¼ 33 mm. Importantly, the progressive buckling and collapse mech­ anisms of the bioinspired structure are sequential, and the stable cells effectively support the unstable cells. Essentially, the convex cells pro­ vide stability whilst the hybrid cells collapse and densify. These mech­ anisms result in a significant increase in energy absorption over the hexagonal and re-entrant structures. The final densified structures are shown in Fig. 11 for completeness, and to provide further insight into the stability of the bioinspired structure compared to the benchmark cases (hexagonal and re-entrant). It can be observed that the hexagonal structure (Fig. 11a) is reasonably stable, with relatively uniform densification throughout its structure. The re-entrant structure does not densify effectively, as it buckles to­ wards the left, which compromises the load carrying capacity of the perimeter cells. The bioinspired structure is observed to be the most stable due to the progressive buckling and collapse mechanisms described earlier. Hence, a hybrid cell that utilises the benefits of a soft and stiff thin-walled cellular structure is required to maximise energy absorption. By strategically arranging the hybrid and convex cells, the energy absorption of thin-walled cellular structures can be amplified significantly whilst enhancing their maximum load carrying capacity. 5. Validated numerical model A finite element (FE) model of the bioinspired structure was devel­ oped using the commercial software package ABAQUS, and validated using the experimental results reported and discussed in Section 4. The purpose of this preliminary model is to capture the load-displacement behaviour and deformation mechanisms of the bio-inspired cellular Fig. 12. Finite element models of the bio-inspired cellular structure with different mesh densities. 8 A. Ghazlan et al. Thin-Walled Structures 151 (2020) 106713 Fig. 13. Results from the mesh convergence study. Fig. 14. Force-displacement curves for the finite element model and 3D printed samples of the bioinspired structure. structure in the elastic and plateau regions. The model will be exten­ sively calibrated and validated under different loading conditions in a future work to be used as a design tool for bioinspired protective cellular structures under extreme loads, such as blast and impact. The stress-strain curve for Markforged Tough Nylon (Fig. 6), which has a Poisson’s ratio of 0.4, was input into ABAQUS to simulate the mechanical response of the bioinspired cellular structure. The model was assembled from hexagonal brick elements with reduced integration (C3D8R). A displacement-controlled compressive load was applied to the structure using ABAQUS explicit, which was chosen over the implicit approach due to its stability in modelling large deformations and contact problems. The simulation was terminated at a displacement of 42 mm i. e., when the densification region in the experiment was adequately captured. The ABAQUS explicit contact model was used to capture the interactions between the cell walls: hard contact to predict the normal behaviour; and the penalty formulation with a friction coefficient of 0.3 to predict the tangential behaviour. No interpenetration was observed (see Fig. 15). A convergence study was conducted using an element side length (l) of 0.5 mm, 0.25 mm and 0.125 mm as shown in Fig. 12, with 6, 12 and 24 elements through the thickness, respectively. It can be observed from Fig. 13 that the three models exhibit an identical elastic response, with slight discrepancies in the plateau and densification regions of the forcedisplacement curve. The model with ρ ¼ 0:125 mm terminates prema­ turely due to excessive distortions. Given the similarities of the plateau and densified response of the dense models, the model with ρ ¼ 0:25 mm was selected for validation with the experiment due to its stability and computational efficiency. It can be observed from Fig. 14 that the FE model captures the prominent regions of the force-displacement curve of the bioinspired thin-walled cellular structure, namely linear-elastic, plateau and densi­ fication. Although the onset of densification is predicted prematurely in the simulation, the elastic stiffness, hardening behaviour in the plateau region and deformation mechanisms were captured with high accuracy. The premature prediction of the onset of densification may be attributed to the 3D printing direction of the extruder, which introduces anisotropy into the structure. It can be observed from Fig. 15 that the buckling and collapse mechanisms observed in the experiment were captured, which are analysed further below. This behaviour will be investigated further in future research by: analysing the effects of several 3D printing pat­ terns and conducting extensive optimisation studies to extract the optimal biomimetic design parameters for the intended loading condi­ tions, namely blast and impact. The deformation mechanisms captured by the FE model are compared with those observed in the experiment hereafter to further validate the model. It can be observed in Fig. 15 that the FE model captures the key buckling and collapse mechanisms in the bioinspired structure that were observed in the experiment. These observations, which were reported and analysed in detail in Section 4, are summarised as follows: � At u ¼ 9 mm, the rotation and buckling mechanisms in the convex regions of the hybrid cells are captured. However, the convex regions collapse prematurely in the FE model, which may be attributed to the artefacts introduced by the 3D printing extrusion process as dis­ cussed previously. � At u ¼ 16:5 mm, the convex regions of the hybrid cells continue to collapse and there is contact between their walls. The cells at the 9 A. Ghazlan et al. Thin-Walled Structures 151 (2020) 106713 Fig. 15. Deformation mechanisms of the bio-inspired thin-walled cellular structure. The fringe of the vertical displacement is presented. base of the structure also collapse. The shapes of the collapsed cells are relatively consistent with experimental observations. � At u ¼ 19:5 mm, the hybrid cells have collapsed further. The convex cells rotate and buckle, and thereby provide stability to the structure. Their hourglass-like shapes are consistent with experimental observations. � At u ¼ 25:5 mm, the buckling and collapse mechanism discussed above progresses through the structure until the onset of densification. 6. Conclusions This research mimicked the concave and convex hybrid cell geom­ etries in the plate-like thin-walled cellular structure of trabecular bone. 10 Thin-Walled Structures 151 (2020) 106713 A. Ghazlan et al. To this effect, a numerical modelling and manufacturing framework was developed to automatically generate a finite element model and 3D printed sample of the bioinspired structure. Due to its automated manufacturing functionality, the framework was also employed for fabricating the 3D printed samples of two benchmark structures. The performance of the bioinspired structure was benchmarked against these two structures (hexagonal and re-entrant), which have been extensively investigated in the literature. Compared to the hexagonal structure, the bioinspired structure showed a 29% reduction in the peak load and a 69% increase in energy absorption. These significant per­ formance enhancements were attributed to the sequential buckling and collapse mechanisms of the bioinspired structure, where the hybrid cells buckled and collapsed whilst the convex cells provided stability. In contrast, the performance of the re-entrant structure was significantly compromised due to asymmetric buckling. These results have positive implications in the design of protective structures, where lightweight and high energy absorption are of paramount importance. In future work, several 3D printing patterns will be analysed extensively to study the effects of anisotropy on the performance of bioinspired thin-walled cellular structures. The design parameters of the bioinspired thinwalled cellular structure will also be optimised for blast and impact loading. [13] R.S. Fecchio, Y. Seki, S.G. Bodde, M.S. Gomes, J. 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