Biomechanical evaluation of individual 3D-printed vertebrae

Biomechanical evaluation of individual 3D-printed vertebrae | Research Square window.SnipcartSettings = { analytics: { enabled: false } }; (function() { var accessVector = localStorage.getItem('access_vector') || ''; window.dataLayer = window.dataLayer || []; if (accessVector) { window.dataLayer.push({ user: { profile: { profileInfo: { snid: accessVector } } } }); } })(); (function(w,d,s,l,i){w[l]=w[l]||[];w[l].push({'gtm.start':new Date().getTime(),event:'gtm.js'});var f=d.getElementsByTagName(s)[0],j=d.createElement(s),dl=l!='dataLayer'?'&l='+l:'';j.async=true;j.src='https://www.googletagmanager.com/gtm.js?id='+i+dl;f.parentNode.insertBefore(j,f);})(window,document,'script','dataLayer','GTM-K279D39R'); Browse Preprints In Review Journals COVID-19 Preprints AJE Video Bytes Research Tools Research Promotion AJE Professional Editing AJE Rubriq About Preprint Platform In Review Editorial Policies Our Team Advisory Board Help Center Sign In Submit a Preprint Cite Share Download PDF Research Article Biomechanical evaluation of individual 3D-printed vertebrae Florian Metzner, Stefan Schleifenbaum, Christoph-Eckhard Heyde, and 1 more This is a preprint; it has not been peer reviewed by a journal. https://doi.org/ 10.21203/rs.3.rs-7710013/v1 This work is licensed under a CC BY 4.0 License Status: Published Journal Publication published 06 Mar, 2026 Read the published version in BMC Biomedical Engineering → Version 1 posted 10 You are reading this latest preprint version Abstract Background Personalized 3D-printed bone models are becoming increasingly popular in clinical care. Common applications include the visualization of idiopathic deformities or complex joint fractures. Functionalizing such printed replicas in terms of individual mechanical properties holds great potential for clinical training and research but is challenging due to the complexity of the bone structure. This study aims at developing a parametrizable structure as a substitute for spongious bone in order by simplifying 3D reconstruction and printing. Methods 43 vertebrae from 6 body donors aged 86.8 ± 7.8 years were examined. Each spine underwent a clinical computed tomography scan. Cylindrical samples (Ø6 x 12 mm) were randomly taken from the left or right side of the vertebral body using a core drill in the superior-inferior direction. Specific software was used for determining the volumetric Hounsfield-Units of the spongious bone in each vertebral hemisphere. In parallel, a parametric hexagonal grid structure was designed using engineering software. All rods within the lattice have a variable length L and a fixed diameter of t = 0.4 mm. By varying the ratio t/L, six different porosities were defined. For each of these, five cylindrical lattice samples (diameter/length = 1/2) from two different synthetic resins were manufactured using the stereolithography printing process. All samples were mechanically characterized by uniaxial compressive testing. Curve fitting based on power functions (y = ax b ) allowed the determination of correlations between mechanical parameters and Hounsfield-Units (bone) as well as the lattice parameter t/L (3D-printed lattice). Finally, three vertebrae with varying bone quality were printed with their respected parameterized lattice and evaluated by comparing the axial screw pullout forces of the human and the respective printed bones. Results There is a significant correlation between the mechanical properties of the bone specimens and the determined Hounsfield-Units. Furthermore, the mechanical properties of the lattice can be excellently described by the ratio t/L. The printed vertebrae showed pull-out forces similar to those of osteoporotic bone. Conlusion The mechanical behavior of vertebral human spongious bone can be well reproduced by a 3D-printed generic lattice structure. Patient-specific bone models can be generated by integrating the parameterizable lattice structure into the specific bone contours. These models can help in improving patient care, for instance by enabling highly realistic surgical approaches for particularly complex anatomies. cancellous bone 3D-printing lattice additive manufacturing stereolithography compressive test bone osteoporosis bone density Figures Figure 1 Figure 2 Figure 3 Figure 4 Figure 5 Figure 6 Figure 7 Figure 8 1. Background Patient-specific bone models are often used as visual support in the planning and execution of complex operations [ 1 – 4 ]. They are used, for example, in oral and maxillofacial surgery [ 5 ], spinal surgery [ 6 – 8 ] and trauma surgery [ 9 – 11 ]. Both operating time and blood loss can be significantly reduced by using individual 3D-printed models [ 6 ] and they can be produced with minimal shape deviations [ 12 – 14 ]. However, the mechanical properties of the printed models vary greatly depending on shape, printing process, printing settings (part orientation, infill), model material and the interaction between the above parameters [ 15 – 17 ]. Functionalizing patient-specific anatomical models in terms of their mechanical properties holds promising application potential, not only in medical training for learning surgical techniques [ 4 , 18 ], but also in biomechanical research as a reproducible test material with individual characteristics[ 4 ]. The extrusion process, for example, makes it very easy to adjust the internal infill pattern and wall thickness of the models. Some research groups used this method and carried out a qualitative evaluation of the material properties by having experienced orthopedic surgeons carry out various surgical activities (drilling, sawing, screw implantation) and evaluating the haptics using questionnaires [ 19 , 20 ]. Although the models can be produced in a simple and cost-effective manner, their subjective approach prevents them from providing reliable evidence about the actual mechanical behavior of the model bones or the infill structure. A different approach is the fabrication of real trabecular architecture. For this purpose, the geometry information was reconstructed from micro computed tomography (µCT) data and produced in different scales utilizing various 3D-printing processes. Both uniaxial compression tests and screw pull-out tests were performed for analyzing the mechanical behavior and the printability [ 21 , 22 ]. Current model approaches are not practicable for manufacturing patient-specific bone models capable of replicating the mechanical behavior of the original bone, as either their mechanical properties were not objectively determined or they are based on µCT data, which cannot be performed on patients due to the high radiation intensity. This work therefore aims to mechanically characterizing vertebral spongious bones via compressive tests and comparing their mechanical parameters with their local Hounsfield-Units (HU) from diagnostic computed tomography (CT). This data is then used for generating a lattice structure mimicking the mechanical behavior of the spongious bone, which can be parameterized by adapting the lattice dimensions to the individual mechanical behavior of the corresponding bones. Whole vertebrae will finally be replicated to analyze their interactions with pedicle screws and compare them against human bones. This leads to two hypotheses. Based on diagnostic CT data, a lattice structure with bone-like mechanical material behavior can be generated and specifically adapted to the required mechanical strength. Individual bones can be reproduced by substituting the spongious bone inside the vertebral body with the hexagonal lattice structure, allowing them to interact realistically with implanted pedicle screws. 2. Methods The methodology is structured into two distinct phases. The first phase involves the collection of comparative data from human donor specimens through uniaxial compression testing and axial pullout tests of pedicle screws. Subsequently, the second phase encompasses a detailed description of the lattice design, its mechanical characterization, and the comparative evaluation of fully 3D-printed vertebrae. Human bone characterization 43 vertebrae from 6 human body donors (2 females, 4 males) aged 86.8 ± 7.8 (mean ± standard deviation) years were obtained in fresh and anatomically unfixed condition from levels T7 to L5. All body donors gave their informed and written consent to the donation of their bodies for teaching and research purposes while alive. Being part of the body donor program regulated by the Saxonian Death and Funeral Act of 1994 (third section, paragraph 18 item 8), institutional approval for the use of the post-mortem tissues of human body donors was obtained from the Institute of Anatomy, University of Leipzig (ethical approval No. 129/21-ck). The authors declare that all experiments were conducted according to the principles of the Declaration of Helsinki. All bones were stored fresh frozen at -80°C until further preparation. CT scans (Voltage: 120 kV; slice thickness 1 mm; s. Figure 1 , Clinical Imaging) as well as Dual-Energy-X-Ray (DXA) scans were conducted on the frozen whole spines. Before testing all vertebrae were thawed one time to separate each bone from surrounding soft tissues and other bony anatomy. Afterwards the individual bones were freezed again at -80° C until testing. On the test day, the vertebrae were thawed overnight at 4° C and then a polyaxial pedicle screw (M.U.S.T. Pedicle Screw, Medacta International, Castel San Pietro, Switzerland) was randomly instrumented on one side using the classic trajectory with the freehand technique. This involved pre-drilling with a 2.5 mm diameter and tapping using the respective tools. Each vertebra was aligned in aluminum cylinders using 3D-printed clamps and spacers to align the transverse plane of the vertebra orthogonal to the cylinder axis. The vertebral body was then embedded using a cold-curing cast resin system (RenCast FC 52/53, Huntsman Advanced Materials, Basel, Switzerland). Additional fixing screws were embedded to prevent the casting material from shifting and twisting within the cylinder (s. Figure 1 , Specimen Preparation). Now the aluminum cylinder got aligned and secured with screws. This is done by inserting a K-wire into the cannulated screw to visualize the longitudinal axis of the screw. A wire rope was then looped into the screw head and connected to the machine's crosshead using the matching locking screw (s. Figure 1 , Pedicle-Screw Pullout). The whole fixture was mounted on a xy-table within the testing machine (Allroundline Z10, Zwick/Roell GmbH & Co. KG, Ulm, Germany), equipped with a 2.5 kN lead cell, to eliminate transverse loads. All pull-out tests were carried out with a preload of 5 N and a test speed of 5 mm/min according to ASTM F543 [ 23 ] to determine the maximum pull-out force F max . Testing was stopped after 60% of F max had been reached. The embedded vertebra was then extracted from the cylinder and the 3D-printed spacer removed (s. Figure 1 , Specimen extraction). The spacer forms a free space above the vertebra which minimizes tool wear and also creates a flat surface below the vertebra, enabling the vertebra to be aligned in a cranio-caudal direction within the stationary drilling machine. A drill core of Ø6 mm is extracted via a tenon cutter (FAMAG Series 1616, FAMAG Werkzeugfabrik GmbH & Co. KG, Remscheid, Germany) after explanting the pedicle screw. The cylinder was then cut to a 12 mm length using a band saw (EXAKT 310, EXAKT Advanced Technologies GmbH, Norderstedt, Germany) equipped with a specially designed and 3D-printed cutting device [ 24 ]. Brass plates were glued to the end faces of each specimen with cyanoacrylate to minimize end-artifacts (s. Figure 1 , Compressive Test). Subsequent uniaxial compression testing was also performed using the above-mentioned testing machine, whereby the test load was applied via polished stainless steel test platens. A hysteresis loop between 0.16 MPa and 0.33 MPa is applied as preconditioning. These limits come from pre-tests and are set to avoid irreversible damage to the samples. Afterwards, the samples were tested to a maximal compression of 40%. The determined parameters are Modulus E (maximum slope in the quasilinear range; s. Figure 2 , A), compressive stress σ y (failure stress at 0.2% offset of the E; s. Figure 2 B) and the plateau stress σ p (mean value of all stress values in the 20–40% strain range; s. Figure 2 C) [ 24 , 25 ]. Between all steps, the samples were stored in 0.9% saline solution to prevent dehydration. Each vertebra was tested within one day. The determined mechanical parameters were then correlated with the corresponding HU from the CT data of their respective vertebral hemisphere. HU is determined using segmentation software (Mimics Innovation Suite V.23, Materialise, Leuven, Belgium) in accordance with the preliminary work of [ 26 ]. A filled mask is created for each vertebra using the threshold method. The created mask is then thinned using the Erode function so that a new mask is created containing only cancellous bone tissue. Next, this mask is divided into its left and right sides and the average HU of each mask was exported. Modeling and characterizing the lattice structure A hexagonal lattice structure replaces the complex architecture of the cancellous bone within the bone. It was created using the computer-aided-design (CAD) software (Rhino 7, Robert McNeel & Associates, Seattle, WA, USA) and consists of equilateral and equiangular hexagons in one plane, the corners of which are in turn connected with vertical bars between the individual planes. The lattice can thus be clearly defined and customized by a single parameter which is the ratio of strut thickness t and strut length L (s. Figure 3 ). The average trabecular thickness in lumbar vertebral bodies is approximately .12 mm with an average bone volume fraction of 8.15% [ 27 ]. Such small struts cannot be reliably printed by stereolithography (SLA). Initial tests determined a minimum printable strut thickness of t = .4 mm for the SLA-process. This was done by producing cylindrical test specimens with increasing rod thickness, starting at .2 mm, on the SLA printer (Form 3B, Formlabs, Sommerville, MA, USA). The test specimens were then analyzed for printing defects. Since the average trabecular thickness of human cancellous bone in the vertebral body is around .1 mm, the smallest rod diameter of .4 mm that could be reproducibly printed was selected. Cylindrical specimens with a diameter to length ratio of 1:2 were printed for the mechanical characterization (analogous to the bone specimens; s. Figure 4 right) [ 15 , 24 , 28 , 29 ]. The specimen diameter is generally defined to be ten times larger than the largest lattice spacing. This ensures the structural integrity of the sample [ 29 ]. Mechanical stability of the structure is therefore ultimately defined by the ratio of t/L (strut diameter/strut length) and is therefore independent of the selected t. Changing t/L means a variation in the solid content and thus a change in the structural behavior. The relationship between t/L and the resulting relative density (solid content) of the lattice structure is shown in (Fig. 3 , right). The grid is fused with 1 mm thick plates at the end faces of each cylinder for preventing end artefacts during the compression tests [ 30 ]. Additionally, these plates provide an attachment surface for support structures during printing. Six samples of each of the selected t/L ratios were printed from each of two resins (Clear V4 and Tough 2000, Formlabs, Sommerville, MA, USA). The material characteristics of the resins are shown in Table 1 . Table 1 Tensile properties of the used resin materials given by the manufacturer (Formlabs, Sommerville, MA, USA) Material Elastic modulus (GPa) Ultimate tensile strength (MPa) Elongation at break (%) Clear V4 2.8 65 6 Tough 2000 2.2 46 48 One sample from each sample group was used for a preliminary test, so that a total of 90 samples were available for characterizing the lattice structure [ 29 ]. Characterization of the 3D-printed specimens followed the same procedure as the human bone compressive tests (s. Fig. Figure 4 ). The parameterization of the grid structure is based on the mathematical relationships between HU and the mechanical parameters of the human print samples (1), as well as the relationship between t/L and the mechanical properties (2) of the printed grid samples. All correlations are carried out by curve fitting of the experimental data by means of power law relations. Parameterization can be performed via two equations and one unknown for each of the three mechanical parameters (E, σ y , σ p ). The relationship (3) is obtained by inserting and rearranging equations ( 1 ) and ( 2 ). $$\:y=a{\bullet\:\left(HU\right)}^{b}$$ 1 $$\:y=u{\bullet\:\left(\raisebox{1ex}{$t$}\!\left/\:\!\raisebox{-1ex}{$L$}\right.\right)}^{v}$$ 2 $$\:\raisebox{1ex}{$t$}\!\left/\:\!\raisebox{-1ex}{$L$}\right.=\sqrt[v]{\frac{a\bullet\:{HU}^{b}}{u}}$$ 3 Since the variables a, b, u and v differ for each mechanical parameter, three different values for t/L are calculated for each printed resin. Averaging these three values gives the corresponding ratio of t/L for the bone model. In this way, all gathered mechanical parameters are included in the model. 3D-printed vertebral models Three lumbar vertebrae from different donors were selected for replicating whole vertebral bones to cover different bone densities and different lumbar levels. Both the outer and inner contours of the cortical bone were segmented using the threshold method. Care was taken to prevent overlapping contours (see Fig. 5 , a). Necessary corrections were made using the ‘Edit Contours’ software tool. The contours were exported from the segmentation software as STL-files and imported into the CAD-software for further processing. First, the models were remeshed with an element size of .8 mm (Fig. 5 , b). Model contours were checked again by re-importing the models into the segmentation software. This was followed by generating the parametrized unit cell (Fig. 5 , c) via HU of the vertebra (Fig. 5 , d). The lattice is then merged with the cortical bone using Boolean operations. Drain holes were integrated into the cover surfaces and the vertebral processes to ensure proper cleaning of the non-polymerized resin. The resulting 3D models (Fig. 5 ,e) were then prepared for printing using preprinting software (PreForm®, Formlabs, Sommerville, MA, USA) and sent to the printer. After printing, the models were thoroughly cleaned with isopropanol and post-cured under ultraviolet radiation and temperature according to the manufacturer's instructions. As a pre-test for the pull-out tests, several vertebrae were made from the two previously analyzed resins and instrumented with pedicle screws. The vertebrae made with ClearV4 resin exhibited such brittle behavior that the models failed locally during instrumentation (pre-drilling, tapping, screw insertion). For this reason, whole vertebral models were printed out of Tough2000 V2 resin, which has a higher ultimate strain to avoid these issues (s. Table 1 ). One lumbar vertebra with normal bone quality and two vertebrae with osteoporosis from different donors and different levels of the lumbar spine were selected for the final pull-out tests of the 3D-printed bones (s. Table 2 ). Each of these three human vertebrae was printed five times from Tough2000 V2 resin. The drain holes were sealed with adhesive tape to prevent penetration of the casting resin into the printed vertebrae during embedding. Table 2 Specifications of the three lumbar vertebrae which were selected for 3D-printing. The selection is justified by ensuring the representation of different bone qualities and different vertebral levels. Donor Level Spongious HU Spongious HU (screw side) 1 L3 118 93 3 L1 303 343 4 L4 62 58 Statistical analyses Descriptive statistics were examined using IBM SPSS Statistics 28 (IBM Corporation, Armonk, NY, USA). Statistical significance is defined with P < .05. Curve estimation based on power law was used to determine relationships between the compressive properties (E, σ y , σ p ) and the HU or the lattice parameter t/L. Linear as well as nonlinear (power, exponential) curve estimations were furthermore applied for analysing the dependence of pullout force and HU. Kruskal-Wallis test for independent samples were used to distinct between the of normal, osteopenic and osteoporotic vertebrae. 3. Results For better comprehensibility, first the results of all compression tests are described followed by the results from the pullout tests on both the human vertebrae and the 3D-printed bones. The individual human vertebrae were classified as osteoporotic, osteopenic and normal based on DXA analysis (s. Table 3 ). Significant differences were found between normal and osteopenic (P < .001) as well as between normal and osteoporotic vertebrae (P < .001), but not between osteopenic and osteoporotic bones. Table 3 Specifications of each body donor including age, sex, T-Score from Dual-Energy X-Ray imaging as well as the resulting osteoporosis classification as defined by the Word Health Organization. One vertebra of each marked (*) donor was selected for parametrization and 3d-printing. Donor (#) Age (years) Sex T-score Bone quality 1 97 female -2.4 osteopenia 2* 79 female -3.2 osteoporosis 3 81 male 0.8 normal 4 95 male -3.2 osteoporosis 5* 78 male 1.1 normal 6* 91 male -3.4 osteoporosis Compressive tests The cancellous HU on the compressive specimen side ranges between 61 and 364 HU. An increase in the mechanical parameters was observed with increasing HU. The compressive modulus lies between 3.3 and 420.9 MPa, the compression limit between 2.0 and 4.3 MPa and the plateau stress between .1 and 4.2 MPa. According to Table 4 , statistical correlations between the mechanical parameters and the HU were demonstrated via curve fittings based on power law functions. A correlation between the mechanical parameters of the printed lattice specimens was verified using the same method. For the ClearV4 material, E lies between 19.9 and 205.9 MPa, σ y between .2 and 4.9 MPa and σ p between .0 and 1.9 MPa. For the material Tough2000 V2, E lies between 16.2 and 144.3 MPa, the σ y between .2 and 3.0 MPa and σ p between .1 MPa 4.8 MPa. E of the samples made of Tough2000 V2 for t/L = .4 is approximately 100 MPa, which is around 10% below the average modulus of the samples with t/L = .35 (s. Figure 6 , top right). Furthermore, no σ p could be determined for the samples made of ClearV4 for t/L = .4, as the samples bursted during the testing. Table 4 Summary of all mechanical tests including human bone samples and 3D-printed lattice specimen made from photopolymer resins (Clear V4 and Tough2000 V2) using stereolithography. Non-linear regression analysis by means of power laws were calculated for each mechanical parameter and the Hounsfield-Units (bone samples) and fraction of strut diameter/strut length t/L (3D-printed specimens). Constant a Exponent b Regression Coeffizient R² P-Value Human Bone vs. HU Compressive Modulus .094 1.25 .42 < .001 Yield Stress .001 1.34 .62 < .001 Plateau Stress .000 1.54 .58 < .001 Clear V4 vs. t/L Compressive Modulus 1168.59 2.06 .96 < .001 Yield Stress 71.83 2.91 .96 < .001 Plateau Stress 67.13 3.65 .91 < .001 Tough2000 vs. t/L Compressive Modulus 609.53 1.66 .87 < .001 Yield Stress 33.32 2.51 .93 < .001 Plateau Stress 58.88 3.05 .96 < .001 Pull-out tests The HU of the instrumented vertebra hemispheres (N = 24) range between 58 and 343 HU. Corresponding F max were between 183 and 1567 N (s. Figure 7 ). Regression analysis containing linear as well as nonlinear curve fittings (s. Table 5 ) confirm statistically significant relationships between side specific cancellous HU and F max . Table 5 Summary of curve fits summarizing the relationship between maximum screw pull-out force and the HU of their corresponding vertebral half. Curve Fit a b R² P-value Linear (y = a*x + b) 5.65 3.56 0.73 < 0.000 Power (y = a*x b ) 2.77 1.04 0.83 < 0.000 Exponential (y = a*e b ) 177.75 0.01 0.78 < 0.000 The averaged F max of the 3D-printed replicas (donor #1, L3 and donor #4, L4) are 200 N higher than their respective human original. The mean F max of the replicas of donor #3 L1 is 600 N lower compared to their human originals (s. Figure 8 ). 4. Discussion Compressive tests Vertebral cancellous bone HU ranges from 61 to 364 HU. The distribution of HU indicates a distinction between the two main groups. Those above 200 HU represent vertebrae with normal bone density and those below 200 HU are assumed to be either osteopenic or osteoporotic. This is consistent with previous studies investigating the relationship between bone quality and HU from diagnostic CT [ 31 – 36 ]. The DXA analysis was only able to assess bone density in the lumbar vertebral bodies. Based on the DXA results, bone quality evaluation across all six donors revealed that two had normal bone quality, one was classified as osteopenic, and three were osteoporotic. Our mechanical parameters show strong concordance with comparable data reported in the literature [ 37 – 40 ]. Öhman-Mägi et al. [ 41 ] reviewed data on the mechanical properties of cancellous bone from vertebral bodies. They found elastic moduli ranging from 1 to 976 MPa. They also found yield stresses ranging from .1 to 14 MPa. Our values are relatively low, likely due to the geriatric age of our body donors and the consequently reduced bone quality. σ y and σ p (R² = .62 and R² = .58 respectively) could be better described mathematically than E (R² = .42) (s. Table 4 ). However, the variance in our data could be due to the fact that we did not measure the exact HU of the samples, but the averaged HU of the vertebral halves from which the samples were taken. The exponent of the power equation lies within 1.3 and 1.5 which corresponds well with experimental findings comparing HU and compressive mechanical properties of human bone from various anatomical sites [ 42 ]. So, plausible and practically useful correlations for lattice dimensioning can be derived by using power functions for predicting the mechanical properties of spongious bone. Strong correlations between the lattice parameter t/L and the mechanical properties of the lattice samples were demonstrated based on power functions (s. Table 4 ). Both material properties matched the properties of the human samples very well. Figure 6 shows that the mechanical parameters scatter more with increasing t/L. Initial tests showed that cylindrical specimens could be printed best when aligned horizontally on the building platform of the printer, meaning that the longitudinal axis of the cylindrical samples is orthogonal to the printing direction. At higher t/L, component distortion during post-processing could not be completely ruled out, so that the plates on the front sides of the samples (s. Figure 4 , right) are no longer parallel to each other. This was especially noticeable in the samples made of the material Tough2000 V2. Samples made of ClearV4 resin further showed incremental failure of the lattice layers at low values of t/L. There was no constant plastic failure zone at high strains as was the case with the bone samples. Lattice structures are primarily used in lightweight engineering to maximize mechanical properties while minimizing component mass. According to Ashby, lattice structures are classified as tensile or bending-dominated structures depending mainly on the type of unit cell (e.g. octet-truss unit-cell, hexagonal unit cell). The exponent in the relationship between relative density and stiffness allows a distinction between bending and tension-dominated structures [ 43 ]. Vertebral cancellous bone is a largely open-cell structure with a relatively low bone volume content of 8.15% [ 27 ] and is therefore a bending-dominated structure [ 44 ]. Our t/L ratio is proportional to its relative density (s. Figure 3 , right) and closely matches the relative density of vertebral cancellous bone, ranging from 4 to 12% [ 27 ]. We can thus show that the chosen hexagonal lattice structure with its bending-dominated properties is well suited for mimicking vertebral cancellous bones, especially for bones with poor bone quality. Pull-out tests Similar to the compression specimens with previous investigations, we found rather low F max in the human specimens [ 45 – 47 ] Which is related to their poor bone quality [ 48 , 49 ]. The regression analysis of F max vs. HU shows significant models for each curve fit, with the power function showing highest R² = .83. Previous studies could also show significant correlations between HU and screw anchorage. Matsukawa et al. [ 50 ] examined the Regional HU within the screw trajectory in vivo. They found significantly lower summarized HU for the loosened screws compared to the fixed ones. Similar findings were published by Zou et al. [ 51 ]. Another group around Wichmann [ 52 ] measured the mineral content by means of quantitative CT within different regions alongside the screw trajectory and compared it to the maximum pullout force in vivo. Best correlations were found by comparing the pullout force with the mineral content inside the pedicle. Their pullout forces range between roughly 100 and 1300 N which is in good agreement with our data presented in Fig. 7 . The above-mentioned grouping of the data points regarding bone quality is also recognizable here. Our data show that a reduced bone quality can be assumed for F max of less than 500 to 600 N. While instrumenting the printed vertebral replicas, it was determined in preliminary tests that post-processing (cleaning with isopropanol and post-curing according to the manufacturer's specifications under temperature and ultraviolet radiation) of the vertebrae significantly influenced the print quality. This may explain the variance in F max . We found on average 200 N higher F max on the replicas of vertebrae #1, L3 and #4, L4 than compared to their human counterparts, which both had low bone quality. In our opinion, the most plausible explanation for this is that the cortical bone in the pedicle is too thick, which could be caused by errors during segmentation or during post-processing. Since the pull-out force mainly depends on the cortical fixation of the screw within the pedicle [ 53 , 54 ], the unintended decrease of the pedicle diameter within the vertebral replicas increased their F max . Conversely, the high pull-out force of specimen #3, L1 failed to be replicated by the printed resin, even though it has an appropriately dimensioned lattice. These observations confirm the argument of cortical anchorage. These lower pull-out forces in comparison to the human model can therefore be explained by the difference in strength between synthetic resin (modulus of elasticity 1.9 GPa, s. Table 1 ) and cortical bone (modulus of elasticity around 18 GPa [ 55 ]). Thus, we conclude that the chosen model approach is well suited for the replication of bones with low bone quality. For the replication of healthy bones or bones with pathologically increased mechanical properties (e.g. due to osteoarthritis, necrosis, tumors), other model materials or material combinations (e.g. short fiber reinforcements) should be investigated. Limitations The presented bone models were based on HU from opportunistic CT-scans. For this reason, a major limitation of our study is the transferability of parameterization results to other clinical CT-scans, since HU from CT depends on the machine type, tube voltage or current used. A quantification of the HU could be performed retrospectively for bone replications based on other scanners/parameters, e.g. by external calibration of the scans. High t/L specimens in particular showed warping during printing, which may have an influence on the internal stress conditions within the specimens affecting the mechanical properties. All overhanging structures require reinforcement with support structures during SLA printing. These supports must be removed after printing, which, depending on the orientation within the build volume, can potentially damage the cylindrical specimens. Positioning the specimens horizontally offered the best compromise between reliable printing and minimal post-processing. Besides part geometry, warping is also highly influenced by the material used. Each human specimen was printed five times and underwent a pull-out test, so we tested the in vitro structure five times per vertebral body with the same (replicated) bone geometries by using the pull-out test. We found large variations in F max , which can be explained by irregularities in printing, which are estimated to be rather small, as the lattice in the vertebrae is supported from all sides in contrast to the compression specimens. However, we believe that the greatest influence on the variation of F max is the chosen freehand implantation technique. In the future, deviations in the screw trajectories could be avoided by using individualized drilling templates. 5. Conclusion This study presents a method for replicating individual human vertebrae using 3D-printing. A hexagonal lattice structure was designed with mechanical properties that can be precisely tuned by adjusting the ratio of rod thickness to rod length. Uniaxial testing established mathematical relationships between the mechanical properties, the HU from diagnostic CT data, and the lattice parameter t/L. By integrating these lattice structures within CT-reconstructed bone geometry, entire vertebrae can be accurately reproduced using SLA printing. This individualized approach was validated through uniaxial pull-out tests of pedicle screws on both human specimens and their printed replicas, demonstrating its utility in simulating implant anchorage in vertebrae with low bone quality. Unlike generic bone models, our method enables the creation of anatomically specific, reproducible replicas directly from patient CT data, allowing for precise in vitro testing and the development of customized treatment strategies tailored to each unique anatomy. Abbreviations 3D three dimensional t Rod thickness of the lattice L Rod length of the lattice μCT Mocir computed tomography HU Hounsfield-Unit CT Computed tomography T7 Seventh thoracal vertebrea L5 Fifth lumbal vertebrea DXA Dual-Energy-X-Ray Fig. Figure F max Maximum pullout force MPa Megapascal E Compressive modulus σ y Compressive stress σ p Plateau stress CAD Computer aided design SLA Stereolithography y Algebraic Variable x Algebraic Variable a Product within power equation b Exponent within power equation Tab. Table p Statisical p-value vs. Versus N Number R² Regression coefficient e.g. For example Declarations Ethics approval and consent to participate The authors are accountable for all aspects of the work in ensuring that questions related to the accuracy or integrity of any part of the work are appropriately investigated and resolved. All body donors gave their informed and written consent to the donation of their bodies for teaching and research purposes while alive. Being part of the body donor program regulated by the Saxonian Death and Funeral Act of 1994 (third section, paragraph 18 item 8), institutional approval for the use of the post-mortem tissues of human body donors was obtained from the Institute of Anatomy (University of Leipzig) by the Ethics Committee of the University of Leipzig Medical Center (ethical approval No. 129/21-ck). The authors declare that all experiments were conducted according to the principles of the Declaration of Helsinki (as revised in 2013). Consent for publication Not applicable. Availability of data and materials The datasets used and/or analysed during the current study are available from the corresponding author on reasonable request. Competing interests The authors have no conflicts of interest to declare. Funding This research was funded by Roland Ernst Stiftung für Gesundheitswesen (Funding Number: ROLAND ERNST STIFTUNG/ 01/21). This article was funded by the Open Access Publishing Fund of Leipzig University, which is supported by the German Research Foundation within the program Open Access Publication Funding. Authors' contributions FM – Conception and design, data acquisition, analyzation and interpretation, lattice design and parametrization, original draft and revision SS – Conception and design, data analyzation and manuscript revision C-EH – Conception and design NvdH – Conception and design, data acquisition and interpretation, manuscript revision Acknowledgements We want to thank all body donors for giving their bodies for research and the Institute of Anatomy, Faculty of Medicine, Leipzig University for acquiring the donor tissue. Furthermore I want to thank Robin Heilmann for the support in designing the lattice structure. Declaration of 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. 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17:48:42","extension":"xml","order_by":18,"title":"","display":"","copyAsset":false,"role":"acdc-reference","size":152130,"visible":true,"origin":"","legend":"","description":"","filename":"ecf65c21b6a447f097752b5ce003ad571structuring.xml","url":"https://assets-eu.researchsquare.com/files/rs-7710013/v1/8795500ecd3684b7e1bf9052.xml"},{"id":93804382,"identity":"395abc2a-507f-4d0c-83e4-89f970fd8184","added_by":"auto","created_at":"2025-10-17 17:48:42","extension":"html","order_by":19,"title":"","display":"","copyAsset":false,"role":"acdc-reference","size":162726,"visible":true,"origin":"","legend":"","description":"","filename":"earlyproof.html","url":"https://assets-eu.researchsquare.com/files/rs-7710013/v1/ef7a681664d88936e07949e1.html"},{"id":93804356,"identity":"e3475b22-14d5-4e37-a62d-476f886bbeb1","added_by":"auto","created_at":"2025-10-17 17:48:41","extension":"png","order_by":1,"title":"Figure 1","display":"","copyAsset":false,"role":"figure","size":120623,"visible":true,"origin":"","legend":"\u003cp\u003eTesting protocol for data acquisition frum human donor tissues\u003c/p\u003e","description":"","filename":"1.png","url":"https://assets-eu.researchsquare.com/files/rs-7710013/v1/eb902e281db23dbe3876151d.png"},{"id":93804357,"identity":"928dd6c3-18d9-4c37-a54c-5f06e3116bee","added_by":"auto","created_at":"2025-10-17 17:48:41","extension":"png","order_by":2,"title":"Figure 2","display":"","copyAsset":false,"role":"figure","size":101457,"visible":true,"origin":"","legend":"\u003cp\u003eExemplary stress-strain-curve of a compressive bone specimen from the second lumbar vertebrae of donor #5 (left). The corresponding sample is shown on the right-hand side at that moment when each mechanical parameter is determined. The compressive modulus E is determined at A, the compressive stress σ\u003csub\u003e0.2\u003c/sub\u003e at B and the plateau stress σ\u003csub\u003ep\u003c/sub\u003e at C.\u003c/p\u003e","description":"","filename":"2.png","url":"https://assets-eu.researchsquare.com/files/rs-7710013/v1/c3aa987e3a88dc9d980a4b0c.png"},{"id":93805259,"identity":"4f37a2a2-0deb-48a1-bc47-7a2620e49123","added_by":"auto","created_at":"2025-10-17 17:56:41","extension":"png","order_by":3,"title":"Figure 3","display":"","copyAsset":false,"role":"figure","size":39480,"visible":true,"origin":"","legend":"\u003cp\u003eUnit-cell of the hexagonal lattice (left). All struts within the lattice have the same length L and a constant strut diameter t of 0.4mm. The dependence of the relative density and the ratio t/L is shown on the right side.\u003c/p\u003e","description":"","filename":"3.png","url":"https://assets-eu.researchsquare.com/files/rs-7710013/v1/eb6b346641324a058428f014.png"},{"id":93804358,"identity":"7ec9b210-40fb-47de-9c13-3a08aeb4b888","added_by":"auto","created_at":"2025-10-17 17:48:41","extension":"png","order_by":4,"title":"Figure 4","display":"","copyAsset":false,"role":"figure","size":131742,"visible":true,"origin":"","legend":"\u003cp\u003eExemplary stress-strain-curve of a compressive lattice made of Tough 2000 resin with t/l = 0.2 (left). The corresponding sample is shown on the right-hand side at that moment when each mechanical parameter is determined. The compressive modulus E is determined at A, the compressive stress σ\u003csub\u003e0.2\u003c/sub\u003e at B and the plateau stress σ\u003csub\u003ep\u003c/sub\u003e at C.\u003c/p\u003e","description":"","filename":"4.png","url":"https://assets-eu.researchsquare.com/files/rs-7710013/v1/c59b15636f899749f1a67b2a.png"},{"id":93805898,"identity":"07ef5abd-f57d-4a58-8f9a-1b20d0b02832","added_by":"auto","created_at":"2025-10-17 18:04:41","extension":"png","order_by":5,"title":"Figure 5","display":"","copyAsset":false,"role":"figure","size":143612,"visible":true,"origin":"","legend":"\u003cp\u003eWorkflow for creating the whole bone models of selected vertebrae. After segmentation (a) of the outer and inner cortical contours the two separate models are exported as STL files. The models were then imported and remeshed (b) in the CAD-Software Rhino (Rhino 7, Robert McNeel \u0026amp; Associates, Seattle, WA, USA). The unit cell (c) was then created using the calculated ratio of truss diameter and truss length (t/L) and the inner cortical contour is voxelized with the unit cells (d). Finally lattice and cortical shell were unified and exported as STL for 3D-Printing using stereolithography (e).\u003c/p\u003e","description":"","filename":"5.png","url":"https://assets-eu.researchsquare.com/files/rs-7710013/v1/e5a8868cbc68e311e6bfb877.png"},{"id":93805256,"identity":"21c38cdb-571b-473c-86e5-40d9e0cc65c9","added_by":"auto","created_at":"2025-10-17 17:56:41","extension":"png","order_by":6,"title":"Figure 6","display":"","copyAsset":false,"role":"figure","size":41472,"visible":true,"origin":"","legend":"\u003cp\u003eScatterplots showing the compressive properties (Compressive Modulus, Yield stress and Plateau stress) of human bone specimens as functions of their Hounsfield-Units (left) and printed lattice specimens as functions of the ratio of truss diameter and truss length (right). All fittings are based on power laws. The lattice specimens were printed with two different resin materials (Clear V4 and Tough 2000 V2, Formlabs, Sommerville, MA, USA.\u003c/p\u003e","description":"","filename":"6.png","url":"https://assets-eu.researchsquare.com/files/rs-7710013/v1/ec90ca4a6a976b349c73c60e.png"},{"id":93804364,"identity":"41169860-fc52-40d5-bae8-14eb86e5bf11","added_by":"auto","created_at":"2025-10-17 17:48:41","extension":"png","order_by":7,"title":"Figure 7","display":"","copyAsset":false,"role":"figure","size":23844,"visible":true,"origin":"","legend":"\u003cp\u003eScatter plot of the spongious Hounsfield-Unit of the instrumented vertebral hemispheres and their respective pullout forces.\u003c/p\u003e","description":"","filename":"7.png","url":"https://assets-eu.researchsquare.com/files/rs-7710013/v1/f4f02fcde0abb9c4a5b51b6f.png"},{"id":93806463,"identity":"c1fe32fd-df70-4bda-a7f1-0d158b86ab6a","added_by":"auto","created_at":"2025-10-17 18:12:41","extension":"png","order_by":8,"title":"Figure 8","display":"","copyAsset":false,"role":"figure","size":9701,"visible":true,"origin":"","legend":"\u003cp\u003ePullout forces of 3 selected human vertebrae and the mean value (error bars show standard deviation) of each group of their replicas (N=5).\u003c/p\u003e","description":"","filename":"8.png","url":"https://assets-eu.researchsquare.com/files/rs-7710013/v1/4fa58196432d589f812651f0.png"},{"id":104250785,"identity":"241520c3-54fb-4969-b1bf-bede16cc9a55","added_by":"auto","created_at":"2026-03-09 16:08:28","extension":"pdf","order_by":0,"title":"","display":"","copyAsset":false,"role":"manuscript-pdf","size":1533048,"visible":true,"origin":"","legend":"","description":"","filename":"manuscript.pdf","url":"https://assets-eu.researchsquare.com/files/rs-7710013/v1/ef14ce99-55f5-4961-9bce-7efe5d7c2b7b.pdf"}],"financialInterests":"No competing interests reported.","formattedTitle":"Biomechanical evaluation of individual 3D-printed vertebrae","fulltext":[{"header":"1. Background","content":"\u003cp\u003ePatient-specific bone models are often used as visual support in the planning and execution of complex operations [\u003cspan additionalcitationids=\"CR2 CR3\" citationid=\"CR1\" class=\"CitationRef\"\u003e1\u003c/span\u003e\u0026ndash;\u003cspan citationid=\"CR4\" class=\"CitationRef\"\u003e4\u003c/span\u003e]. They are used, for example, in oral and maxillofacial surgery [\u003cspan citationid=\"CR5\" class=\"CitationRef\"\u003e5\u003c/span\u003e], spinal surgery [\u003cspan additionalcitationids=\"CR7\" citationid=\"CR6\" class=\"CitationRef\"\u003e6\u003c/span\u003e\u0026ndash;\u003cspan citationid=\"CR8\" class=\"CitationRef\"\u003e8\u003c/span\u003e] and trauma surgery [\u003cspan additionalcitationids=\"CR10\" citationid=\"CR9\" class=\"CitationRef\"\u003e9\u003c/span\u003e\u0026ndash;\u003cspan citationid=\"CR11\" class=\"CitationRef\"\u003e11\u003c/span\u003e]. Both operating time and blood loss can be significantly reduced by using individual 3D-printed models [\u003cspan citationid=\"CR6\" class=\"CitationRef\"\u003e6\u003c/span\u003e] and they can be produced with minimal shape deviations [\u003cspan additionalcitationids=\"CR13\" citationid=\"CR12\" class=\"CitationRef\"\u003e12\u003c/span\u003e\u0026ndash;\u003cspan citationid=\"CR14\" class=\"CitationRef\"\u003e14\u003c/span\u003e]. However, the mechanical properties of the printed models vary greatly depending on shape, printing process, printing settings (part orientation, infill), model material and the interaction between the above parameters [\u003cspan additionalcitationids=\"CR16\" citationid=\"CR15\" class=\"CitationRef\"\u003e15\u003c/span\u003e\u0026ndash;\u003cspan citationid=\"CR17\" class=\"CitationRef\"\u003e17\u003c/span\u003e]. Functionalizing patient-specific anatomical models in terms of their mechanical properties holds promising application potential, not only in medical training for learning surgical techniques [\u003cspan citationid=\"CR4\" class=\"CitationRef\"\u003e4\u003c/span\u003e, \u003cspan citationid=\"CR18\" class=\"CitationRef\"\u003e18\u003c/span\u003e], but also in biomechanical research as a reproducible test material with individual characteristics[\u003cspan citationid=\"CR4\" class=\"CitationRef\"\u003e4\u003c/span\u003e].\u003c/p\u003e\u003cp\u003eThe extrusion process, for example, makes it very easy to adjust the internal infill pattern and wall thickness of the models. Some research groups used this method and carried out a qualitative evaluation of the material properties by having experienced orthopedic surgeons carry out various surgical activities (drilling, sawing, screw implantation) and evaluating the haptics using questionnaires [\u003cspan citationid=\"CR19\" class=\"CitationRef\"\u003e19\u003c/span\u003e, \u003cspan citationid=\"CR20\" class=\"CitationRef\"\u003e20\u003c/span\u003e]. Although the models can be produced in a simple and cost-effective manner, their subjective approach prevents them from providing reliable evidence about the actual mechanical behavior of the model bones or the infill structure. A different approach is the fabrication of real trabecular architecture. For this purpose, the geometry information was reconstructed from micro computed tomography (\u0026micro;CT) data and produced in different scales utilizing various 3D-printing processes. Both uniaxial compression tests and screw pull-out tests were performed for analyzing the mechanical behavior and the printability [\u003cspan citationid=\"CR21\" class=\"CitationRef\"\u003e21\u003c/span\u003e, \u003cspan citationid=\"CR22\" class=\"CitationRef\"\u003e22\u003c/span\u003e]. Current model approaches are not practicable for manufacturing patient-specific bone models capable of replicating the mechanical behavior of the original bone, as either their mechanical properties were not objectively determined or they are based on \u0026micro;CT data, which cannot be performed on patients due to the high radiation intensity.\u003c/p\u003e\u003cp\u003eThis work therefore aims to mechanically characterizing vertebral spongious bones via compressive tests and comparing their mechanical parameters with their local Hounsfield-Units (HU) from diagnostic computed tomography (CT). This data is then used for generating a lattice structure mimicking the mechanical behavior of the spongious bone, which can be parameterized by adapting the lattice dimensions to the individual mechanical behavior of the corresponding bones. Whole vertebrae will finally be replicated to analyze their interactions with pedicle screws and compare them against human bones.\u003c/p\u003e\u003cp\u003eThis leads to two hypotheses. Based on diagnostic CT data, a lattice structure with bone-like mechanical material behavior can be generated and specifically adapted to the required mechanical strength. Individual bones can be reproduced by substituting the spongious bone inside the vertebral body with the hexagonal lattice structure, allowing them to interact realistically with implanted pedicle screws.\u003c/p\u003e"},{"header":"2. Methods","content":"\u003cp\u003eThe methodology is structured into two distinct phases. The first phase involves the collection of comparative data from human donor specimens through uniaxial compression testing and axial pullout tests of pedicle screws. Subsequently, the second phase encompasses a detailed description of the lattice design, its mechanical characterization, and the comparative evaluation of fully 3D-printed vertebrae.\u003c/p\u003e\n\u003cp\u003e\u003cstrong\u003eHuman bone characterization\u003c/strong\u003e\u003c/p\u003e\n\u003cp\u003e43 vertebrae from 6 human body donors (2 females, 4 males) aged 86.8\u0026thinsp;\u0026plusmn;\u0026thinsp;7.8 (mean\u0026thinsp;\u0026plusmn;\u0026thinsp;standard deviation) years were obtained in fresh and anatomically unfixed condition from levels T7 to L5. All body donors gave their informed and written consent to the donation of their bodies for teaching and research purposes while alive. Being part of the body donor program regulated by the Saxonian Death and Funeral Act of 1994 (third section, paragraph 18 item 8), institutional approval for the use of the post-mortem tissues of human body donors was obtained from the Institute of Anatomy, University of Leipzig (ethical approval No. 129/21-ck). The authors declare that all experiments were conducted according to the principles of the Declaration of Helsinki. All bones were stored fresh frozen at -80\u0026deg;C until further preparation. CT scans (Voltage: 120 kV; slice thickness 1 mm; s. Figure \u003cspan class=\"InternalRef\"\u003e1\u003c/span\u003e, Clinical Imaging) as well as Dual-Energy-X-Ray (DXA) scans were conducted on the frozen whole spines. Before testing all vertebrae were thawed one time to separate each bone from surrounding soft tissues and other bony anatomy. Afterwards the individual bones were freezed again at -80\u0026deg; C until testing.\u003c/p\u003e\n\u003cp\u003eOn the test day, the vertebrae were thawed overnight at 4\u0026deg; C and then a polyaxial pedicle screw (M.U.S.T. Pedicle Screw, Medacta International, Castel San Pietro, Switzerland) was randomly instrumented on one side using the classic trajectory with the freehand technique. This involved pre-drilling with a 2.5 mm diameter and tapping using the respective tools. Each vertebra was aligned in aluminum cylinders using 3D-printed clamps and spacers to align the transverse plane of the vertebra orthogonal to the cylinder axis. The vertebral body was then embedded using a cold-curing cast resin system (RenCast FC 52/53, Huntsman Advanced Materials, Basel, Switzerland). Additional fixing screws were embedded to prevent the casting material from shifting and twisting within the cylinder (s. Figure \u003cspan class=\"InternalRef\"\u003e1\u003c/span\u003e, Specimen Preparation). Now the aluminum cylinder got aligned and secured with screws. This is done by inserting a K-wire into the cannulated screw to visualize the longitudinal axis of the screw. A wire rope was then looped into the screw head and connected to the machine\u0026apos;s crosshead using the matching locking screw (s. Figure \u003cspan class=\"InternalRef\"\u003e1\u003c/span\u003e, Pedicle-Screw Pullout). The whole fixture was mounted on a xy-table within the testing machine (Allroundline Z10, Zwick/Roell GmbH \u0026amp; Co. KG, Ulm, Germany), equipped with a 2.5 kN lead cell, to eliminate transverse loads. All pull-out tests were carried out with a preload of 5 N and a test speed of 5 mm/min according to ASTM F543 [\u003cspan class=\"CitationRef\"\u003e23\u003c/span\u003e] to determine the maximum pull-out force F\u003csub\u003emax\u003c/sub\u003e. Testing was stopped after 60% of F\u003csub\u003emax\u003c/sub\u003e had been reached.\u003c/p\u003e\n\u003cp\u003eThe embedded vertebra was then extracted from the cylinder and the 3D-printed spacer removed (s. Figure \u003cspan class=\"InternalRef\"\u003e1\u003c/span\u003e, Specimen extraction). The spacer forms a free space above the vertebra which minimizes tool wear and also creates a flat surface below the vertebra, enabling the vertebra to be aligned in a cranio-caudal direction within the stationary drilling machine.\u003c/p\u003e\n\u003cp\u003eA drill core of \u0026Oslash;6 mm is extracted via a tenon cutter (FAMAG Series 1616, FAMAG Werkzeugfabrik GmbH \u0026amp; Co. KG, Remscheid, Germany) after explanting the pedicle screw. The cylinder was then cut to a 12 mm length using a band saw (EXAKT 310, EXAKT Advanced Technologies GmbH, Norderstedt, Germany) equipped with a specially designed and 3D-printed cutting device [\u003cspan class=\"CitationRef\"\u003e24\u003c/span\u003e]. Brass plates were glued to the end faces of each specimen with cyanoacrylate to minimize end-artifacts (s. Figure \u003cspan class=\"InternalRef\"\u003e1\u003c/span\u003e, Compressive Test). Subsequent uniaxial compression testing was also performed using the above-mentioned testing machine, whereby the test load was applied via polished stainless steel test platens. A hysteresis loop between 0.16 MPa and 0.33 MPa is applied as preconditioning. These limits come from pre-tests and are set to avoid irreversible damage to the samples. Afterwards, the samples were tested to a maximal compression of 40%. The determined parameters are Modulus E (maximum slope in the quasilinear range; s. Figure \u003cspan class=\"InternalRef\"\u003e2\u003c/span\u003e, A), compressive stress \u0026sigma;\u003csub\u003ey\u003c/sub\u003e (failure stress at 0.2% offset of the E; s. Figure \u003cspan class=\"InternalRef\"\u003e2\u003c/span\u003eB) and the plateau stress \u0026sigma;\u003csub\u003ep\u003c/sub\u003e (mean value of all stress values in the 20\u0026ndash;40% strain range; s. Figure \u003cspan class=\"InternalRef\"\u003e2\u003c/span\u003eC) [\u003cspan class=\"CitationRef\"\u003e24\u003c/span\u003e, \u003cspan class=\"CitationRef\"\u003e25\u003c/span\u003e]. Between all steps, the samples were stored in 0.9% saline solution to prevent dehydration. Each vertebra was tested within one day.\u003c/p\u003e\n\u003cp\u003eThe determined mechanical parameters were then correlated with the corresponding HU from the CT data of their respective vertebral hemisphere. HU is determined using segmentation software (Mimics Innovation Suite V.23, Materialise, Leuven, Belgium) in accordance with the preliminary work of [\u003cspan class=\"CitationRef\"\u003e26\u003c/span\u003e]. A filled mask is created for each vertebra using the threshold method. The created mask is then thinned using the Erode function so that a new mask is created containing only cancellous bone tissue. Next, this mask is divided into its left and right sides and the average HU of each mask was exported.\u003c/p\u003e\n\u003cp\u003e\u003cstrong\u003eModeling and characterizing the lattice structure\u003c/strong\u003e\u003c/p\u003e\n\u003cp\u003eA hexagonal lattice structure replaces the complex architecture of the cancellous bone within the bone. It was created using the computer-aided-design (CAD) software (Rhino 7, Robert McNeel \u0026amp; Associates, Seattle, WA, USA) and consists of equilateral and equiangular hexagons in one plane, the corners of which are in turn connected with vertical bars between the individual planes. The lattice can thus be clearly defined and customized by a single parameter which is the ratio of strut thickness t and strut length L (s. Figure \u003cspan class=\"InternalRef\"\u003e3\u003c/span\u003e).\u003c/p\u003e\n\u003cp\u003eThe average trabecular thickness in lumbar vertebral bodies is approximately .12 mm with an average bone volume fraction of 8.15% [\u003cspan class=\"CitationRef\"\u003e27\u003c/span\u003e]. Such small struts cannot be reliably printed by stereolithography (SLA). Initial tests determined a minimum printable strut thickness of t\u0026thinsp;=\u0026thinsp;.4 mm for the SLA-process. This was done by producing cylindrical test specimens with increasing rod thickness, starting at .2 mm, on the SLA printer (Form 3B, Formlabs, Sommerville, MA, USA). The test specimens were then analyzed for printing defects. Since the average trabecular thickness of human cancellous bone in the vertebral body is around .1 mm, the smallest rod diameter of .4 mm that could be reproducibly printed was selected.\u003c/p\u003e\n\u003cp\u003eCylindrical specimens with a diameter to length ratio of 1:2 were printed for the mechanical characterization (analogous to the bone specimens; s. Figure \u003cspan class=\"InternalRef\"\u003e4\u003c/span\u003e right) [\u003cspan class=\"CitationRef\"\u003e15\u003c/span\u003e, \u003cspan class=\"CitationRef\"\u003e24\u003c/span\u003e, \u003cspan class=\"CitationRef\"\u003e28\u003c/span\u003e, \u003cspan class=\"CitationRef\"\u003e29\u003c/span\u003e]. The specimen diameter is generally defined to be ten times larger than the largest lattice spacing. This ensures the structural integrity of the sample [\u003cspan class=\"CitationRef\"\u003e29\u003c/span\u003e]. Mechanical stability of the structure is therefore ultimately defined by the ratio of t/L (strut diameter/strut length) and is therefore independent of the selected t. Changing t/L means a variation in the solid content and thus a change in the structural behavior. The relationship between t/L and the resulting relative density (solid content) of the lattice structure is shown in (Fig. \u003cspan class=\"InternalRef\"\u003e3\u003c/span\u003e, right). The grid is fused with 1 mm thick plates at the end faces of each cylinder for preventing end artefacts during the compression tests [\u003cspan class=\"CitationRef\"\u003e30\u003c/span\u003e]. Additionally, these plates provide an attachment surface for support structures during printing. Six samples of each of the selected t/L ratios were printed from each of two resins (Clear V4 and Tough 2000, Formlabs, Sommerville, MA, USA). The material characteristics of the resins are shown in Table\u0026nbsp;\u003cspan class=\"InternalRef\"\u003e1\u003c/span\u003e.\u003c/p\u003e\n\u003cdiv class=\"gridtable\"\u003e\n \u003ctable id=\"Tab1\" border=\"1\"\u003e\n \u003ccaption language=\"En\"\u003e\n \u003cdiv class=\"CaptionNumber\"\u003eTable 1\u003c/div\u003e\n \u003cdiv class=\"CaptionContent\"\u003e\n \u003cp\u003eTensile properties of the used resin materials given by the manufacturer (Formlabs, Sommerville, MA, USA)\u003c/p\u003e\n \u003c/div\u003e\n \u003c/caption\u003e\n \u003cthead\u003e\n \u003ctr\u003e\n \u003cth align=\"left\"\u003e\n \u003cp\u003eMaterial\u003c/p\u003e\n \u003c/th\u003e\n \u003cth align=\"left\"\u003e\n \u003cp\u003eElastic modulus (GPa)\u003c/p\u003e\n \u003c/th\u003e\n \u003cth align=\"left\"\u003e\n \u003cp\u003eUltimate tensile strength (MPa)\u003c/p\u003e\n \u003c/th\u003e\n \u003cth align=\"left\"\u003e\n \u003cp\u003eElongation at break (%)\u003c/p\u003e\n \u003c/th\u003e\n \u003c/tr\u003e\n \u003c/thead\u003e\n \u003ctbody\u003e\n \u003ctr\u003e\n \u003ctd align=\"left\"\u003e\n \u003cp\u003eClear V4\u003c/p\u003e\n \u003c/td\u003e\n \u003ctd align=\"char\"\u003e\n \u003cp\u003e2.8\u003c/p\u003e\n \u003c/td\u003e\n \u003ctd align=\"char\"\u003e\n \u003cp\u003e65\u003c/p\u003e\n \u003c/td\u003e\n \u003ctd align=\"char\"\u003e\n \u003cp\u003e6\u003c/p\u003e\n \u003c/td\u003e\n \u003c/tr\u003e\n \u003ctr\u003e\n \u003ctd align=\"left\"\u003e\n \u003cp\u003eTough 2000\u003c/p\u003e\n \u003c/td\u003e\n \u003ctd align=\"char\"\u003e\n \u003cp\u003e2.2\u003c/p\u003e\n \u003c/td\u003e\n \u003ctd align=\"char\"\u003e\n \u003cp\u003e46\u003c/p\u003e\n \u003c/td\u003e\n \u003ctd align=\"char\"\u003e\n \u003cp\u003e48\u003c/p\u003e\n \u003c/td\u003e\n \u003c/tr\u003e\n \u003c/tbody\u003e\n \u003c/table\u003e\n\u003c/div\u003e\n\u003cp\u003eOne sample from each sample group was used for a preliminary test, so that a total of 90 samples were available for characterizing the lattice structure [\u003cspan class=\"CitationRef\"\u003e29\u003c/span\u003e]. Characterization of the 3D-printed specimens followed the same procedure as the human bone compressive tests (s. Fig. Figure \u003cspan class=\"InternalRef\"\u003e4\u003c/span\u003e).\u003c/p\u003e\n\u003cp\u003eThe parameterization of the grid structure is based on the mathematical relationships between HU and the mechanical parameters of the human print samples (1), as well as the relationship between t/L and the mechanical properties (2) of the printed grid samples. All correlations are carried out by curve fitting of the experimental data by means of power law relations. Parameterization can be performed via two equations and one unknown for each of the three mechanical parameters (E, \u0026sigma;\u003csub\u003ey\u003c/sub\u003e, \u0026sigma;\u003csub\u003ep\u003c/sub\u003e). The relationship (3) is obtained by inserting and rearranging equations (\u003cspan class=\"InternalRef\"\u003e1\u003c/span\u003e) and (\u003cspan class=\"InternalRef\"\u003e2\u003c/span\u003e).\u003c/p\u003e\n\u003cdiv id=\"Equ1\" class=\"Equation\"\u003e\n \u003cdiv class=\"mathdisplay\" id=\"FileID_Equ1\" name=\"EquationSource\"\u003e$$\\:y=a{\\bullet\\:\\left(HU\\right)}^{b}$$\u003c/div\u003e\n \u003cdiv class=\"EquationNumber\"\u003e1\u003c/div\u003e\n\u003c/div\u003e\n\u003cdiv id=\"Equ2\" class=\"Equation\"\u003e\n \u003cdiv class=\"mathdisplay\" id=\"FileID_Equ2\" name=\"EquationSource\"\u003e$$\\:y=u{\\bullet\\:\\left(\\raisebox{1ex}{$t$}\\!\\left/\\:\\!\\raisebox{-1ex}{$L$}\\right.\\right)}^{v}$$\u003c/div\u003e\n \u003cdiv class=\"EquationNumber\"\u003e2\u003c/div\u003e\n\u003c/div\u003e\n\u003cdiv id=\"Equ3\" class=\"Equation\"\u003e\n \u003cdiv class=\"mathdisplay\" id=\"FileID_Equ3\" name=\"EquationSource\"\u003e$$\\:\\raisebox{1ex}{$t$}\\!\\left/\\:\\!\\raisebox{-1ex}{$L$}\\right.=\\sqrt[v]{\\frac{a\\bullet\\:{HU}^{b}}{u}}$$\u003c/div\u003e\n \u003cdiv class=\"EquationNumber\"\u003e3\u003c/div\u003e\n\u003c/div\u003e\n\u003cp\u003eSince the variables a, b, u and v differ for each mechanical parameter, three different values for t/L are calculated for each printed resin. Averaging these three values gives the corresponding ratio of t/L for the bone model. In this way, all gathered mechanical parameters are included in the model.\u003c/p\u003e\n\u003ch3\u003e3D-printed vertebral models\u003c/h3\u003e\n\u003cp\u003eThree lumbar vertebrae from different donors were selected for replicating whole vertebral bones to cover different bone densities and different lumbar levels. Both the outer and inner contours of the cortical bone were segmented using the threshold method. Care was taken to prevent overlapping contours (see Fig. \u003cspan class=\"InternalRef\"\u003e5\u003c/span\u003e, a). Necessary corrections were made using the \u0026lsquo;Edit Contours\u0026rsquo; software tool. The contours were exported from the segmentation software as STL-files and imported into the CAD-software for further processing. First, the models were remeshed with an element size of .8 mm (Fig. \u003cspan class=\"InternalRef\"\u003e5\u003c/span\u003e, b). Model contours were checked again by re-importing the models into the segmentation software. This was followed by generating the parametrized unit cell (Fig. \u003cspan class=\"InternalRef\"\u003e5\u003c/span\u003e, c) via HU of the vertebra (Fig. \u003cspan class=\"InternalRef\"\u003e5\u003c/span\u003e, d). The lattice is then merged with the cortical bone using Boolean operations. Drain holes were integrated into the cover surfaces and the vertebral processes to ensure proper cleaning of the non-polymerized resin.\u003c/p\u003e\n\u003cp\u003eThe resulting 3D models (Fig. \u003cspan class=\"InternalRef\"\u003e5\u003c/span\u003e,e) were then prepared for printing using preprinting software (PreForm\u0026reg;, Formlabs, Sommerville, MA, USA) and sent to the printer. After printing, the models were thoroughly cleaned with isopropanol and post-cured under ultraviolet radiation and temperature according to the manufacturer\u0026apos;s instructions. As a pre-test for the pull-out tests, several vertebrae were made from the two previously analyzed resins and instrumented with pedicle screws. The vertebrae made with ClearV4 resin exhibited such brittle behavior that the models failed locally during instrumentation (pre-drilling, tapping, screw insertion). For this reason, whole vertebral models were printed out of Tough2000 V2 resin, which has a higher ultimate strain to avoid these issues (s. Table \u003cspan class=\"InternalRef\"\u003e1\u003c/span\u003e).\u003c/p\u003e\n\u003cp\u003eOne lumbar vertebra with normal bone quality and two vertebrae with osteoporosis from different donors and different levels of the lumbar spine were selected for the final pull-out tests of the 3D-printed bones (s. Table\u0026nbsp;\u003cspan class=\"InternalRef\"\u003e2\u003c/span\u003e). Each of these three human vertebrae was printed five times from Tough2000 V2 resin. The drain holes were sealed with adhesive tape to prevent penetration of the casting resin into the printed vertebrae during embedding.\u003c/p\u003e\n\u003cdiv class=\"gridtable\"\u003e\n \u003ctable id=\"Tab2\" border=\"1\"\u003e\n \u003ccaption language=\"En\"\u003e\n \u003cdiv class=\"CaptionNumber\"\u003eTable 2\u003c/div\u003e\n \u003cdiv class=\"CaptionContent\"\u003e\n \u003cp\u003eSpecifications of the three lumbar vertebrae which were selected for 3D-printing. The selection is justified by ensuring the representation of different bone qualities and different vertebral levels.\u003c/p\u003e\n \u003c/div\u003e\n \u003c/caption\u003e\n \u003cthead\u003e\n \u003ctr\u003e\n \u003cth align=\"left\"\u003e\n \u003cp\u003eDonor\u003c/p\u003e\n \u003c/th\u003e\n \u003cth align=\"left\"\u003e\n \u003cp\u003eLevel\u003c/p\u003e\n \u003c/th\u003e\n \u003cth align=\"left\"\u003e\n \u003cp\u003eSpongious HU\u003c/p\u003e\n \u003c/th\u003e\n \u003cth align=\"left\"\u003e\n \u003cp\u003eSpongious HU (screw side)\u003c/p\u003e\n \u003c/th\u003e\n \u003c/tr\u003e\n \u003c/thead\u003e\n \u003ctbody\u003e\n \u003ctr\u003e\n \u003ctd align=\"left\"\u003e\n \u003cp\u003e1\u003c/p\u003e\n \u003c/td\u003e\n \u003ctd align=\"left\"\u003e\n \u003cp\u003eL3\u003c/p\u003e\n \u003c/td\u003e\n \u003ctd align=\"char\"\u003e\n \u003cp\u003e118\u003c/p\u003e\n \u003c/td\u003e\n \u003ctd align=\"char\"\u003e\n \u003cp\u003e93\u003c/p\u003e\n \u003c/td\u003e\n \u003c/tr\u003e\n \u003ctr\u003e\n \u003ctd align=\"left\"\u003e\n \u003cp\u003e3\u003c/p\u003e\n \u003c/td\u003e\n \u003ctd align=\"left\"\u003e\n \u003cp\u003eL1\u003c/p\u003e\n \u003c/td\u003e\n \u003ctd align=\"char\"\u003e\n \u003cp\u003e303\u003c/p\u003e\n \u003c/td\u003e\n \u003ctd align=\"char\"\u003e\n \u003cp\u003e343\u003c/p\u003e\n \u003c/td\u003e\n \u003c/tr\u003e\n \u003ctr\u003e\n \u003ctd align=\"left\"\u003e\n \u003cp\u003e4\u003c/p\u003e\n \u003c/td\u003e\n \u003ctd align=\"left\"\u003e\n \u003cp\u003eL4\u003c/p\u003e\n \u003c/td\u003e\n \u003ctd align=\"char\"\u003e\n \u003cp\u003e62\u003c/p\u003e\n \u003c/td\u003e\n \u003ctd align=\"char\"\u003e\n \u003cp\u003e58\u003c/p\u003e\n \u003c/td\u003e\n \u003c/tr\u003e\n \u003c/tbody\u003e\n \u003c/table\u003e\n\u003c/div\u003e\n\u003cp\u003e\u003cstrong\u003eStatistical analyses\u003c/strong\u003e\u003c/p\u003e\n\u003cp\u003eDescriptive statistics were examined using IBM SPSS Statistics 28 (IBM Corporation, Armonk, NY, USA). Statistical significance is defined with P\u0026thinsp;\u0026lt;\u0026thinsp;.05. Curve estimation based on power law was used to determine relationships between the compressive properties (E, \u0026sigma;\u003csub\u003ey\u003c/sub\u003e, \u0026sigma;\u003csub\u003ep\u003c/sub\u003e) and the HU or the lattice parameter t/L. Linear as well as nonlinear (power, exponential) curve estimations were furthermore applied for analysing the dependence of pullout force and HU. Kruskal-Wallis test for independent samples were used to distinct between the of normal, osteopenic and osteoporotic vertebrae.\u003c/p\u003e"},{"header":"3. Results","content":"\u003cp\u003eFor better comprehensibility, first the results of all compression tests are described followed by the results from the pullout tests on both the human vertebrae and the 3D-printed bones. The individual human vertebrae were classified as osteoporotic, osteopenic and normal based on DXA analysis (s. Table\u0026nbsp;\u003cspan class=\"InternalRef\"\u003e3\u003c/span\u003e). Significant differences were found between normal and osteopenic (P\u0026thinsp;\u0026lt;\u0026thinsp;.001) as well as between normal and osteoporotic vertebrae (P\u0026thinsp;\u0026lt;\u0026thinsp;.001), but not between osteopenic and osteoporotic bones.\u003c/p\u003e\n\u003cdiv class=\"gridtable\"\u003e\n \u003ctable id=\"Tab3\" border=\"1\"\u003e\n \u003ccaption language=\"En\"\u003e\n \u003cdiv class=\"CaptionNumber\"\u003eTable 3\u003c/div\u003e\n \u003cdiv class=\"CaptionContent\"\u003e\n \u003cp\u003eSpecifications of each body donor including age, sex, T-Score from Dual-Energy X-Ray imaging as well as the resulting osteoporosis classification as defined by the Word Health Organization. One vertebra of each marked (*) donor was selected for parametrization and 3d-printing.\u003c/p\u003e\n \u003c/div\u003e\n \u003c/caption\u003e\n \u003cthead\u003e\n \u003ctr\u003e\n \u003cth align=\"left\"\u003e\n \u003cp\u003eDonor (#)\u003c/p\u003e\n \u003c/th\u003e\n \u003cth align=\"left\"\u003e\n \u003cp\u003eAge (years)\u003c/p\u003e\n \u003c/th\u003e\n \u003cth align=\"left\"\u003e\n \u003cp\u003eSex\u003c/p\u003e\n \u003c/th\u003e\n \u003cth align=\"left\"\u003e\n \u003cp\u003eT-score\u003c/p\u003e\n \u003c/th\u003e\n \u003cth align=\"left\"\u003e\n \u003cp\u003eBone quality\u003c/p\u003e\n \u003c/th\u003e\n \u003c/tr\u003e\n \u003c/thead\u003e\n \u003ctbody\u003e\n \u003ctr\u003e\n \u003ctd align=\"left\"\u003e\n \u003cp\u003e1\u003c/p\u003e\n \u003c/td\u003e\n \u003ctd align=\"char\"\u003e\n \u003cp\u003e97\u003c/p\u003e\n \u003c/td\u003e\n \u003ctd align=\"left\"\u003e\n \u003cp\u003efemale\u003c/p\u003e\n \u003c/td\u003e\n \u003ctd align=\"char\"\u003e\n \u003cp\u003e-2.4\u003c/p\u003e\n \u003c/td\u003e\n \u003ctd align=\"left\"\u003e\n \u003cp\u003eosteopenia\u003c/p\u003e\n \u003c/td\u003e\n \u003c/tr\u003e\n \u003ctr\u003e\n \u003ctd align=\"left\"\u003e\n \u003cp\u003e2*\u003c/p\u003e\n \u003c/td\u003e\n \u003ctd align=\"char\"\u003e\n \u003cp\u003e79\u003c/p\u003e\n \u003c/td\u003e\n \u003ctd align=\"left\"\u003e\n \u003cp\u003efemale\u003c/p\u003e\n \u003c/td\u003e\n \u003ctd align=\"char\"\u003e\n \u003cp\u003e-3.2\u003c/p\u003e\n \u003c/td\u003e\n \u003ctd align=\"left\"\u003e\n \u003cp\u003eosteoporosis\u003c/p\u003e\n \u003c/td\u003e\n \u003c/tr\u003e\n \u003ctr\u003e\n \u003ctd align=\"left\"\u003e\n \u003cp\u003e3\u003c/p\u003e\n \u003c/td\u003e\n \u003ctd align=\"char\"\u003e\n \u003cp\u003e81\u003c/p\u003e\n \u003c/td\u003e\n \u003ctd align=\"left\"\u003e\n \u003cp\u003emale\u003c/p\u003e\n \u003c/td\u003e\n \u003ctd align=\"char\"\u003e\n \u003cp\u003e0.8\u003c/p\u003e\n \u003c/td\u003e\n \u003ctd align=\"left\"\u003e\n \u003cp\u003enormal\u003c/p\u003e\n \u003c/td\u003e\n \u003c/tr\u003e\n \u003ctr\u003e\n \u003ctd align=\"left\"\u003e\n \u003cp\u003e4\u003c/p\u003e\n \u003c/td\u003e\n \u003ctd align=\"char\"\u003e\n \u003cp\u003e95\u003c/p\u003e\n \u003c/td\u003e\n \u003ctd align=\"left\"\u003e\n \u003cp\u003emale\u003c/p\u003e\n \u003c/td\u003e\n \u003ctd align=\"char\"\u003e\n \u003cp\u003e-3.2\u003c/p\u003e\n \u003c/td\u003e\n \u003ctd align=\"left\"\u003e\n \u003cp\u003eosteoporosis\u003c/p\u003e\n \u003c/td\u003e\n \u003c/tr\u003e\n \u003ctr\u003e\n \u003ctd align=\"left\"\u003e\n \u003cp\u003e5*\u003c/p\u003e\n \u003c/td\u003e\n \u003ctd align=\"char\"\u003e\n \u003cp\u003e78\u003c/p\u003e\n \u003c/td\u003e\n \u003ctd align=\"left\"\u003e\n \u003cp\u003emale\u003c/p\u003e\n \u003c/td\u003e\n \u003ctd align=\"char\"\u003e\n \u003cp\u003e1.1\u003c/p\u003e\n \u003c/td\u003e\n \u003ctd align=\"left\"\u003e\n \u003cp\u003enormal\u003c/p\u003e\n \u003c/td\u003e\n \u003c/tr\u003e\n \u003ctr\u003e\n \u003ctd align=\"left\"\u003e\n \u003cp\u003e6*\u003c/p\u003e\n \u003c/td\u003e\n \u003ctd align=\"char\"\u003e\n \u003cp\u003e91\u003c/p\u003e\n \u003c/td\u003e\n \u003ctd align=\"left\"\u003e\n \u003cp\u003emale\u003c/p\u003e\n \u003c/td\u003e\n \u003ctd align=\"char\"\u003e\n \u003cp\u003e-3.4\u003c/p\u003e\n \u003c/td\u003e\n \u003ctd align=\"left\"\u003e\n \u003cp\u003eosteoporosis\u003c/p\u003e\n \u003c/td\u003e\n \u003c/tr\u003e\n \u003c/tbody\u003e\n \u003c/table\u003e\n\u003c/div\u003e\n\u003cp\u003e\u003cstrong\u003eCompressive tests\u003c/strong\u003e\u003c/p\u003e\n\u003cp\u003eThe cancellous HU on the compressive specimen side ranges between 61 and 364 HU. An increase in the mechanical parameters was observed with increasing HU. The compressive modulus lies between 3.3 and 420.9 MPa, the compression limit between 2.0 and 4.3 MPa and the plateau stress between .1 and 4.2 MPa. According to Table \u003cspan class=\"InternalRef\"\u003e4\u003c/span\u003e, statistical correlations between the mechanical parameters and the HU were demonstrated via curve fittings based on power law functions.\u003c/p\u003e\n\u003cp\u003eA correlation between the mechanical parameters of the printed lattice specimens was verified using the same method. For the ClearV4 material, E lies between 19.9 and 205.9 MPa, \u0026sigma;\u003csub\u003ey\u003c/sub\u003e between .2 and 4.9 MPa and \u0026sigma;\u003csub\u003ep\u003c/sub\u003e between .0 and 1.9 MPa. For the material Tough2000 V2, E lies between 16.2 and 144.3 MPa, the \u0026sigma;\u003csub\u003ey\u003c/sub\u003e between .2 and 3.0 MPa and \u0026sigma;\u003csub\u003ep\u003c/sub\u003e between .1 MPa 4.8 MPa. E of the samples made of Tough2000 V2 for t/L\u0026thinsp;=\u0026thinsp;.4 is approximately 100 MPa, which is around 10% below the average modulus of the samples with t/L\u0026thinsp;=\u0026thinsp;.35 (s. Figure \u003cspan class=\"InternalRef\"\u003e6\u003c/span\u003e, top right). Furthermore, no \u0026sigma;\u003csub\u003ep\u003c/sub\u003e could be determined for the samples made of ClearV4 for t/L\u0026thinsp;=\u0026thinsp;.4, as the samples bursted during the testing.\u003c/p\u003e\n\u003cdiv class=\"gridtable\"\u003e\n \u003ctable id=\"Tab4\" border=\"1\"\u003e\n \u003ccaption language=\"En\"\u003e\n \u003cdiv class=\"CaptionNumber\"\u003eTable 4\u003c/div\u003e\n \u003cdiv class=\"CaptionContent\"\u003e\n \u003cp\u003eSummary of all mechanical tests including human bone samples and 3D-printed lattice specimen made from photopolymer resins (Clear V4 and Tough2000 V2) using stereolithography. Non-linear regression analysis by means of power laws were calculated for each mechanical parameter and the Hounsfield-Units (bone samples) and fraction of strut diameter/strut length t/L (3D-printed specimens).\u003c/p\u003e\n \u003c/div\u003e\n \u003c/caption\u003e\n \u003cthead\u003e\n \u003ctr\u003e\n \u003cth align=\"left\"\u003e\u0026nbsp;\u003c/th\u003e\n \u003cth align=\"left\"\u003e\u0026nbsp;\u003c/th\u003e\n \u003cth align=\"left\"\u003e\n \u003cp\u003eConstant a\u003c/p\u003e\n \u003c/th\u003e\n \u003cth align=\"left\"\u003e\n \u003cp\u003eExponent b\u003c/p\u003e\n \u003c/th\u003e\n \u003cth align=\"left\"\u003e\n \u003cp\u003eRegression Coeffizient R\u0026sup2;\u003c/p\u003e\n \u003c/th\u003e\n \u003cth align=\"left\"\u003e\n \u003cp\u003eP-Value\u003c/p\u003e\n \u003c/th\u003e\n \u003c/tr\u003e\n \u003c/thead\u003e\n \u003ctbody\u003e\n \u003ctr\u003e\n \u003ctd align=\"left\" rowspan=\"3\"\u003e\n \u003cp\u003e\u003cstrong\u003eHuman Bone\u0026nbsp;\u003c/strong\u003e\u003c/p\u003e\n \u003cp\u003e\u003cstrong\u003evs. HU\u003c/strong\u003e\u003c/p\u003e\n \u003c/td\u003e\n \u003ctd align=\"left\"\u003e\n \u003cp\u003eCompressive Modulus\u003c/p\u003e\n \u003c/td\u003e\n \u003ctd align=\"left\"\u003e\n \u003cp\u003e.094\u003c/p\u003e\n \u003c/td\u003e\n \u003ctd align=\"char\"\u003e\n \u003cp\u003e1.25\u003c/p\u003e\n \u003c/td\u003e\n \u003ctd align=\"left\"\u003e\n \u003cp\u003e.42\u003c/p\u003e\n \u003c/td\u003e\n \u003ctd align=\"left\"\u003e\n \u003cp\u003e\u0026lt;\u0026thinsp;.001\u003c/p\u003e\n \u003c/td\u003e\n \u003c/tr\u003e\n \u003ctr\u003e\n \u003ctd align=\"left\"\u003e\n \u003cp\u003eYield Stress\u003c/p\u003e\n \u003c/td\u003e\n \u003ctd align=\"left\"\u003e\n \u003cp\u003e.001\u003c/p\u003e\n \u003c/td\u003e\n \u003ctd align=\"char\"\u003e\n \u003cp\u003e1.34\u003c/p\u003e\n \u003c/td\u003e\n \u003ctd align=\"left\"\u003e\n \u003cp\u003e.62\u003c/p\u003e\n \u003c/td\u003e\n \u003ctd align=\"left\"\u003e\n \u003cp\u003e\u0026lt;\u0026thinsp;.001\u003c/p\u003e\n \u003c/td\u003e\n \u003c/tr\u003e\n \u003ctr\u003e\n \u003ctd align=\"left\"\u003e\n \u003cp\u003ePlateau Stress\u003c/p\u003e\n \u003c/td\u003e\n \u003ctd align=\"left\"\u003e\n \u003cp\u003e.000\u003c/p\u003e\n \u003c/td\u003e\n \u003ctd align=\"char\"\u003e\n \u003cp\u003e1.54\u003c/p\u003e\n \u003c/td\u003e\n \u003ctd align=\"left\"\u003e\n \u003cp\u003e.58\u003c/p\u003e\n \u003c/td\u003e\n \u003ctd align=\"left\"\u003e\n \u003cp\u003e\u0026lt;\u0026thinsp;.001\u003c/p\u003e\n \u003c/td\u003e\n \u003c/tr\u003e\n \u003ctr\u003e\n \u003ctd align=\"left\" rowspan=\"3\"\u003e\n \u003cp\u003e\u003cstrong\u003eClear V4\u0026nbsp;\u003c/strong\u003e\u003c/p\u003e\n \u003cp\u003e\u003cstrong\u003evs. t/L\u003c/strong\u003e\u003c/p\u003e\n \u003c/td\u003e\n \u003ctd align=\"left\"\u003e\n \u003cp\u003eCompressive Modulus\u003c/p\u003e\n \u003c/td\u003e\n \u003ctd align=\"left\"\u003e\n \u003cp\u003e1168.59\u003c/p\u003e\n \u003c/td\u003e\n \u003ctd align=\"char\"\u003e\n \u003cp\u003e2.06\u003c/p\u003e\n \u003c/td\u003e\n \u003ctd align=\"left\"\u003e\n \u003cp\u003e.96\u003c/p\u003e\n \u003c/td\u003e\n \u003ctd align=\"left\"\u003e\n \u003cp\u003e\u0026lt;\u0026thinsp;.001\u003c/p\u003e\n \u003c/td\u003e\n \u003c/tr\u003e\n \u003ctr\u003e\n \u003ctd align=\"left\"\u003e\n \u003cp\u003eYield Stress\u003c/p\u003e\n \u003c/td\u003e\n \u003ctd align=\"left\"\u003e\n \u003cp\u003e71.83\u003c/p\u003e\n \u003c/td\u003e\n \u003ctd align=\"char\"\u003e\n \u003cp\u003e2.91\u003c/p\u003e\n \u003c/td\u003e\n \u003ctd align=\"left\"\u003e\n \u003cp\u003e.96\u003c/p\u003e\n \u003c/td\u003e\n \u003ctd align=\"left\"\u003e\n \u003cp\u003e\u0026lt;\u0026thinsp;.001\u003c/p\u003e\n \u003c/td\u003e\n \u003c/tr\u003e\n \u003ctr\u003e\n \u003ctd align=\"left\"\u003e\n \u003cp\u003ePlateau Stress\u003c/p\u003e\n \u003c/td\u003e\n \u003ctd align=\"left\"\u003e\n \u003cp\u003e67.13\u003c/p\u003e\n \u003c/td\u003e\n \u003ctd align=\"char\"\u003e\n \u003cp\u003e3.65\u003c/p\u003e\n \u003c/td\u003e\n \u003ctd align=\"left\"\u003e\n \u003cp\u003e.91\u003c/p\u003e\n \u003c/td\u003e\n \u003ctd align=\"left\"\u003e\n \u003cp\u003e\u0026lt;\u0026thinsp;.001\u003c/p\u003e\n \u003c/td\u003e\n \u003c/tr\u003e\n \u003ctr\u003e\n \u003ctd align=\"left\" rowspan=\"3\"\u003e\n \u003cp\u003e\u003cstrong\u003eTough2000\u0026nbsp;\u003c/strong\u003e\u003c/p\u003e\n \u003cp\u003e\u003cstrong\u003evs. t/L\u003c/strong\u003e\u003c/p\u003e\n \u003c/td\u003e\n \u003ctd align=\"left\"\u003e\n \u003cp\u003eCompressive Modulus\u003c/p\u003e\n \u003c/td\u003e\n \u003ctd align=\"left\"\u003e\n \u003cp\u003e609.53\u003c/p\u003e\n \u003c/td\u003e\n \u003ctd align=\"char\"\u003e\n \u003cp\u003e1.66\u003c/p\u003e\n \u003c/td\u003e\n \u003ctd align=\"left\"\u003e\n \u003cp\u003e.87\u003c/p\u003e\n \u003c/td\u003e\n \u003ctd align=\"left\"\u003e\n \u003cp\u003e\u0026lt;\u0026thinsp;.001\u003c/p\u003e\n \u003c/td\u003e\n \u003c/tr\u003e\n \u003ctr\u003e\n \u003ctd align=\"left\"\u003e\n \u003cp\u003eYield Stress\u003c/p\u003e\n \u003c/td\u003e\n \u003ctd align=\"left\"\u003e\n \u003cp\u003e33.32\u003c/p\u003e\n \u003c/td\u003e\n \u003ctd align=\"char\"\u003e\n \u003cp\u003e2.51\u003c/p\u003e\n \u003c/td\u003e\n \u003ctd align=\"left\"\u003e\n \u003cp\u003e.93\u003c/p\u003e\n \u003c/td\u003e\n \u003ctd align=\"left\"\u003e\n \u003cp\u003e\u0026lt;\u0026thinsp;.001\u003c/p\u003e\n \u003c/td\u003e\n \u003c/tr\u003e\n \u003ctr\u003e\n \u003ctd align=\"left\"\u003e\n \u003cp\u003ePlateau Stress\u003c/p\u003e\n \u003c/td\u003e\n \u003ctd align=\"left\"\u003e\n \u003cp\u003e58.88\u003c/p\u003e\n \u003c/td\u003e\n \u003ctd align=\"char\"\u003e\n \u003cp\u003e3.05\u003c/p\u003e\n \u003c/td\u003e\n \u003ctd align=\"left\"\u003e\n \u003cp\u003e.96\u003c/p\u003e\n \u003c/td\u003e\n \u003ctd align=\"left\"\u003e\n \u003cp\u003e\u0026lt;\u0026thinsp;.001\u003c/p\u003e\n \u003c/td\u003e\n \u003c/tr\u003e\n \u003c/tbody\u003e\n \u003c/table\u003e\n\u003c/div\u003e\n\u003cp\u003e\u003cstrong\u003ePull-out tests\u003c/strong\u003e\u003c/p\u003e\n\u003cp\u003eThe HU of the instrumented vertebra hemispheres (N\u0026thinsp;=\u0026thinsp;24) range between 58 and 343 HU. Corresponding F\u003csub\u003emax\u003c/sub\u003e were between 183 and 1567 N (s. Figure \u003cspan class=\"InternalRef\"\u003e7\u003c/span\u003e). Regression analysis containing linear as well as nonlinear curve fittings (s. Table \u003cspan class=\"InternalRef\"\u003e5\u003c/span\u003e) confirm statistically significant relationships between side specific cancellous HU and F\u003csub\u003emax\u003c/sub\u003e.\u003c/p\u003e\n\u003cdiv class=\"gridtable\"\u003e\n \u003ctable id=\"Tab5\" border=\"1\"\u003e\n \u003ccaption language=\"En\"\u003e\n \u003cdiv class=\"CaptionNumber\"\u003eTable 5\u003c/div\u003e\n \u003cdiv class=\"CaptionContent\"\u003e\n \u003cp\u003eSummary of curve fits summarizing the relationship between maximum screw pull-out force and the HU of their corresponding vertebral half.\u003c/p\u003e\n \u003c/div\u003e\n \u003c/caption\u003e\n \u003cthead\u003e\n \u003ctr\u003e\n \u003cth align=\"left\"\u003e\n \u003cp\u003eCurve Fit\u003c/p\u003e\n \u003c/th\u003e\n \u003cth align=\"left\"\u003e\n \u003cp\u003ea\u003c/p\u003e\n \u003c/th\u003e\n \u003cth align=\"left\"\u003e\n \u003cp\u003eb\u003c/p\u003e\n \u003c/th\u003e\n \u003cth align=\"left\"\u003e\n \u003cp\u003eR\u0026sup2;\u003c/p\u003e\n \u003c/th\u003e\n \u003cth align=\"left\"\u003e\n \u003cp\u003eP-value\u003c/p\u003e\n \u003c/th\u003e\n \u003c/tr\u003e\n \u003c/thead\u003e\n \u003ctbody\u003e\n \u003ctr\u003e\n \u003ctd align=\"left\"\u003e\n \u003cp\u003eLinear (y\u0026nbsp;=\u0026nbsp;a*x\u0026thinsp;+\u0026thinsp;b)\u003c/p\u003e\n \u003c/td\u003e\n \u003ctd align=\"char\"\u003e\n \u003cp\u003e5.65\u003c/p\u003e\n \u003c/td\u003e\n \u003ctd align=\"char\"\u003e\n \u003cp\u003e3.56\u003c/p\u003e\n \u003c/td\u003e\n \u003ctd align=\"char\"\u003e\n \u003cp\u003e0.73\u003c/p\u003e\n \u003c/td\u003e\n \u003ctd align=\"char\"\u003e\n \u003cp\u003e\u0026lt;\u0026thinsp;0.000\u003c/p\u003e\n \u003c/td\u003e\n \u003c/tr\u003e\n \u003ctr\u003e\n \u003ctd align=\"left\"\u003e\n \u003cp\u003ePower (y\u0026nbsp;=\u0026nbsp;a*x\u003csup\u003eb\u003c/sup\u003e)\u003c/p\u003e\n \u003c/td\u003e\n \u003ctd align=\"char\"\u003e\n \u003cp\u003e2.77\u003c/p\u003e\n \u003c/td\u003e\n \u003ctd align=\"char\"\u003e\n \u003cp\u003e1.04\u003c/p\u003e\n \u003c/td\u003e\n \u003ctd align=\"char\"\u003e\n \u003cp\u003e0.83\u003c/p\u003e\n \u003c/td\u003e\n \u003ctd align=\"char\"\u003e\n \u003cp\u003e\u0026lt;\u0026thinsp;0.000\u003c/p\u003e\n \u003c/td\u003e\n \u003c/tr\u003e\n \u003ctr\u003e\n \u003ctd align=\"left\"\u003e\n \u003cp\u003eExponential (y\u0026nbsp;=\u0026nbsp;a*e\u003csup\u003eb\u003c/sup\u003e)\u003c/p\u003e\n \u003c/td\u003e\n \u003ctd align=\"char\"\u003e\n \u003cp\u003e177.75\u003c/p\u003e\n \u003c/td\u003e\n \u003ctd align=\"char\"\u003e\n \u003cp\u003e0.01\u003c/p\u003e\n \u003c/td\u003e\n \u003ctd align=\"char\"\u003e\n \u003cp\u003e0.78\u003c/p\u003e\n \u003c/td\u003e\n \u003ctd align=\"char\"\u003e\n \u003cp\u003e\u0026lt;\u0026thinsp;0.000\u003c/p\u003e\n \u003c/td\u003e\n \u003c/tr\u003e\n \u003c/tbody\u003e\n \u003c/table\u003e\n\u003c/div\u003e\n\u003cp\u003eThe averaged F\u003csub\u003emax\u003c/sub\u003e of the 3D-printed replicas (donor #1, L3 and donor #4, L4) are 200 N higher than their respective human original. The mean F\u003csub\u003emax\u003c/sub\u003e of the replicas of donor #3 L1 is 600 N lower compared to their human originals (s. Figure \u003cspan class=\"InternalRef\"\u003e8\u003c/span\u003e).\u003c/p\u003e"},{"header":"4. Discussion","content":"\u003cp\u003e\u003cb\u003eCompressive tests\u003c/b\u003e\u003c/p\u003e\u003cp\u003eVertebral cancellous bone HU ranges from 61 to 364 HU. The distribution of HU indicates a distinction between the two main groups. Those above 200 HU represent vertebrae with normal bone density and those below 200 HU are assumed to be either osteopenic or osteoporotic. This is consistent with previous studies investigating the relationship between bone quality and HU from diagnostic CT [\u003cspan additionalcitationids=\"CR32 CR33 CR34 CR35\" citationid=\"CR31\" class=\"CitationRef\"\u003e31\u003c/span\u003e\u0026ndash;\u003cspan citationid=\"CR36\" class=\"CitationRef\"\u003e36\u003c/span\u003e].\u003c/p\u003e\u003cp\u003eThe DXA analysis was only able to assess bone density in the lumbar vertebral bodies. Based on the DXA results, bone quality evaluation across all six donors revealed that two had normal bone quality, one was classified as osteopenic, and three were osteoporotic.\u003c/p\u003e\u003cp\u003eOur mechanical parameters show strong concordance with comparable data reported in the literature [\u003cspan additionalcitationids=\"CR38 CR39\" citationid=\"CR37\" class=\"CitationRef\"\u003e37\u003c/span\u003e\u0026ndash;\u003cspan citationid=\"CR40\" class=\"CitationRef\"\u003e40\u003c/span\u003e]. \u0026Ouml;hman-M\u0026auml;gi et al. [\u003cspan citationid=\"CR41\" class=\"CitationRef\"\u003e41\u003c/span\u003e] reviewed data on the mechanical properties of cancellous bone from vertebral bodies. They found elastic moduli ranging from 1 to 976 MPa. They also found yield stresses ranging from .1 to 14 MPa. Our values are relatively low, likely due to the geriatric age of our body donors and the consequently reduced bone quality.\u003c/p\u003e\u003cp\u003eσ\u003csub\u003ey\u003c/sub\u003e and σ\u003csub\u003ep\u003c/sub\u003e (R\u0026sup2; = .62 and R\u0026sup2; = .58 respectively) could be better described mathematically than E (R\u0026sup2; = .42) (s. Table\u0026nbsp;\u003cspan refid=\"Tab4\" class=\"InternalRef\"\u003e4\u003c/span\u003e). However, the variance in our data could be due to the fact that we did not measure the exact HU of the samples, but the averaged HU of the vertebral halves from which the samples were taken. The exponent of the power equation lies within 1.3 and 1.5 which corresponds well with experimental findings comparing HU and compressive mechanical properties of human bone from various anatomical sites [\u003cspan citationid=\"CR42\" class=\"CitationRef\"\u003e42\u003c/span\u003e]. So, plausible and practically useful correlations for lattice dimensioning can be derived by using power functions for predicting the mechanical properties of spongious bone. Strong correlations between the lattice parameter t/L and the mechanical properties of the lattice samples were demonstrated based on power functions (s. Table\u0026nbsp;\u003cspan refid=\"Tab4\" class=\"InternalRef\"\u003e4\u003c/span\u003e). Both material properties matched the properties of the human samples very well. Figure\u0026nbsp;\u003cspan refid=\"Fig6\" class=\"InternalRef\"\u003e6\u003c/span\u003e shows that the mechanical parameters scatter more with increasing t/L. Initial tests showed that cylindrical specimens could be printed best when aligned horizontally on the building platform of the printer, meaning that the longitudinal axis of the cylindrical samples is orthogonal to the printing direction.\u003c/p\u003e\u003cp\u003eAt higher t/L, component distortion during post-processing could not be completely ruled out, so that the plates on the front sides of the samples (s. Figure\u0026nbsp;\u003cspan refid=\"Fig4\" class=\"InternalRef\"\u003e4\u003c/span\u003e, right) are no longer parallel to each other. This was especially noticeable in the samples made of the material Tough2000 V2. Samples made of ClearV4 resin further showed incremental failure of the lattice layers at low values of t/L. There was no constant plastic failure zone at high strains as was the case with the bone samples.\u003c/p\u003e\u003cp\u003eLattice structures are primarily used in lightweight engineering to maximize mechanical properties while minimizing component mass. According to Ashby, lattice structures are classified as tensile or bending-dominated structures depending mainly on the type of unit cell (e.g. octet-truss unit-cell, hexagonal unit cell). The exponent in the relationship between relative density and stiffness allows a distinction between bending and tension-dominated structures [\u003cspan citationid=\"CR43\" class=\"CitationRef\"\u003e43\u003c/span\u003e]. Vertebral cancellous bone is a largely open-cell structure with a relatively low bone volume content of 8.15% [\u003cspan citationid=\"CR27\" class=\"CitationRef\"\u003e27\u003c/span\u003e] and is therefore a bending-dominated structure [\u003cspan citationid=\"CR44\" class=\"CitationRef\"\u003e44\u003c/span\u003e]. Our t/L ratio is proportional to its relative density (s. Figure\u0026nbsp;\u003cspan refid=\"Fig3\" class=\"InternalRef\"\u003e3\u003c/span\u003e, right) and closely matches the relative density of vertebral cancellous bone, ranging from 4 to 12% [\u003cspan citationid=\"CR27\" class=\"CitationRef\"\u003e27\u003c/span\u003e]. We can thus show that the chosen hexagonal lattice structure with its bending-dominated properties is well suited for mimicking vertebral cancellous bones, especially for bones with poor bone quality.\u003c/p\u003e\u003cp\u003e\u003cb\u003ePull-out tests\u003c/b\u003e\u003c/p\u003e\u003cp\u003eSimilar to the compression specimens with previous investigations, we found rather low F\u003csub\u003emax\u003c/sub\u003e in the human specimens [\u003cspan additionalcitationids=\"CR46\" citationid=\"CR45\" class=\"CitationRef\"\u003e45\u003c/span\u003e\u0026ndash;\u003cspan citationid=\"CR47\" class=\"CitationRef\"\u003e47\u003c/span\u003e] Which is related to their poor bone quality [\u003cspan citationid=\"CR48\" class=\"CitationRef\"\u003e48\u003c/span\u003e, \u003cspan citationid=\"CR49\" class=\"CitationRef\"\u003e49\u003c/span\u003e]. The regression analysis of F\u003csub\u003emax\u003c/sub\u003e vs. HU shows significant models for each curve fit, with the power function showing highest R\u0026sup2; = .83. Previous studies could also show significant correlations between HU and screw anchorage. Matsukawa et al. [\u003cspan citationid=\"CR50\" class=\"CitationRef\"\u003e50\u003c/span\u003e] examined the Regional HU within the screw trajectory in vivo. They found significantly lower summarized HU for the loosened screws compared to the fixed ones. Similar findings were published by Zou et al. [\u003cspan citationid=\"CR51\" class=\"CitationRef\"\u003e51\u003c/span\u003e]. Another group around Wichmann [\u003cspan citationid=\"CR52\" class=\"CitationRef\"\u003e52\u003c/span\u003e] measured the mineral content by means of quantitative CT within different regions alongside the screw trajectory and compared it to the maximum pullout force in vivo. Best correlations were found by comparing the pullout force with the mineral content inside the pedicle. Their pullout forces range between roughly 100 and 1300 N which is in good agreement with our data presented in Fig.\u0026nbsp;\u003cspan refid=\"Fig7\" class=\"InternalRef\"\u003e7\u003c/span\u003e.\u003c/p\u003e\u003cp\u003eThe above-mentioned grouping of the data points regarding bone quality is also recognizable here. Our data show that a reduced bone quality can be assumed for F\u003csub\u003emax\u003c/sub\u003e of less than 500 to 600 N.\u003c/p\u003e\u003cp\u003eWhile instrumenting the printed vertebral replicas, it was determined in preliminary tests that post-processing (cleaning with isopropanol and post-curing according to the manufacturer's specifications under temperature and ultraviolet radiation) of the vertebrae significantly influenced the print quality. This may explain the variance in F\u003csub\u003emax\u003c/sub\u003e. We found on average 200 N higher F\u003csub\u003emax\u003c/sub\u003e on the replicas of vertebrae #1, L3 and #4, L4 than compared to their human counterparts, which both had low bone quality. In our opinion, the most plausible explanation for this is that the cortical bone in the pedicle is too thick, which could be caused by errors during segmentation or during post-processing. Since the pull-out force mainly depends on the cortical fixation of the screw within the pedicle [\u003cspan citationid=\"CR53\" class=\"CitationRef\"\u003e53\u003c/span\u003e, \u003cspan citationid=\"CR54\" class=\"CitationRef\"\u003e54\u003c/span\u003e], the unintended decrease of the pedicle diameter within the vertebral replicas increased their F\u003csub\u003emax\u003c/sub\u003e.\u003c/p\u003e\u003cp\u003eConversely, the high pull-out force of specimen #3, L1 failed to be replicated by the printed resin, even though it has an appropriately dimensioned lattice. These observations confirm the argument of cortical anchorage. These lower pull-out forces in comparison to the human model can therefore be explained by the difference in strength between synthetic resin (modulus of elasticity 1.9 GPa, s. Table\u0026nbsp;\u003cspan refid=\"Tab1\" class=\"InternalRef\"\u003e1\u003c/span\u003e) and cortical bone (modulus of elasticity around 18 GPa [\u003cspan citationid=\"CR55\" class=\"CitationRef\"\u003e55\u003c/span\u003e]).\u003c/p\u003e\u003cp\u003eThus, we conclude that the chosen model approach is well suited for the replication of bones with low bone quality. For the replication of healthy bones or bones with pathologically increased mechanical properties (e.g. due to osteoarthritis, necrosis, tumors), other model materials or material combinations (e.g. short fiber reinforcements) should be investigated.\u003c/p\u003e\u003cp\u003e\u003cb\u003eLimitations\u003c/b\u003e\u003c/p\u003e\u003cp\u003eThe presented bone models were based on HU from opportunistic CT-scans. For this reason, a major limitation of our study is the transferability of parameterization results to other clinical CT-scans, since HU from CT depends on the machine type, tube voltage or current used. A quantification of the HU could be performed retrospectively for bone replications based on other scanners/parameters, e.g. by external calibration of the scans.\u003c/p\u003e\u003cp\u003eHigh t/L specimens in particular showed warping during printing, which may have an influence on the internal stress conditions within the specimens affecting the mechanical properties. All overhanging structures require reinforcement with support structures during SLA printing. These supports must be removed after printing, which, depending on the orientation within the build volume, can potentially damage the cylindrical specimens. Positioning the specimens horizontally offered the best compromise between reliable printing and minimal post-processing. Besides part geometry, warping is also highly influenced by the material used.\u003c/p\u003e\u003cp\u003eEach human specimen was printed five times and underwent a pull-out test, so we tested the in vitro structure five times per vertebral body with the same (replicated) bone geometries by using the pull-out test. We found large variations in F\u003csub\u003emax\u003c/sub\u003e, which can be explained by irregularities in printing, which are estimated to be rather small, as the lattice in the vertebrae is supported from all sides in contrast to the compression specimens. However, we believe that the greatest influence on the variation of F\u003csub\u003emax\u003c/sub\u003e is the chosen freehand implantation technique. In the future, deviations in the screw trajectories could be avoided by using individualized drilling templates.\u003c/p\u003e"},{"header":"5. Conclusion","content":"\u003cp\u003eThis study presents a method for replicating individual human vertebrae using 3D-printing. A hexagonal lattice structure was designed with mechanical properties that can be precisely tuned by adjusting the ratio of rod thickness to rod length. Uniaxial testing established mathematical relationships between the mechanical properties, the HU from diagnostic CT data, and the lattice parameter t/L. By integrating these lattice structures within CT-reconstructed bone geometry, entire vertebrae can be accurately reproduced using SLA printing. This individualized approach was validated through uniaxial pull-out tests of pedicle screws on both human specimens and their printed replicas, demonstrating its utility in simulating implant anchorage in vertebrae with low bone quality. Unlike generic bone models, our method enables the creation of anatomically specific, reproducible replicas directly from patient CT data, allowing for precise in vitro testing and the development of customized treatment strategies tailored to each unique anatomy.\u003c/p\u003e"},{"header":"Abbreviations","content":"\u003ctable border=\"1\" cellspacing=\"0\" cellpadding=\"0\"\u003e\n \u003ctbody\u003e\n \u003ctr\u003e\n \u003ctd valign=\"top\"\u003e\n \u003cp\u003e3D\u003c/p\u003e\n \u003c/td\u003e\n \u003ctd valign=\"top\"\u003e\n \u003cp\u003ethree dimensional\u003c/p\u003e\n \u003c/td\u003e\n \u003c/tr\u003e\n \u003ctr\u003e\n \u003ctd valign=\"top\"\u003e\n \u003cp\u003et\u003c/p\u003e\n \u003c/td\u003e\n \u003ctd valign=\"top\"\u003e\n \u003cp\u003eRod thickness of the lattice\u003c/p\u003e\n \u003c/td\u003e\n \u003c/tr\u003e\n \u003ctr\u003e\n \u003ctd valign=\"top\"\u003e\n \u003cp\u003eL\u003c/p\u003e\n \u003c/td\u003e\n \u003ctd valign=\"top\"\u003e\n \u003cp\u003eRod length of the lattice\u003c/p\u003e\n \u003c/td\u003e\n \u003c/tr\u003e\n \u003ctr\u003e\n \u003ctd valign=\"top\"\u003e\n \u003cp\u003eμCT\u003c/p\u003e\n \u003c/td\u003e\n \u003ctd valign=\"top\"\u003e\n \u003cp\u003eMocir computed tomography\u003c/p\u003e\n \u003c/td\u003e\n \u003c/tr\u003e\n \u003ctr\u003e\n \u003ctd valign=\"top\"\u003e\n \u003cp\u003eHU\u003c/p\u003e\n \u003c/td\u003e\n \u003ctd valign=\"top\"\u003e\n \u003cp\u003eHounsfield-Unit\u003c/p\u003e\n \u003c/td\u003e\n \u003c/tr\u003e\n \u003ctr\u003e\n \u003ctd valign=\"top\"\u003e\n \u003cp\u003eCT\u003c/p\u003e\n \u003c/td\u003e\n \u003ctd valign=\"top\"\u003e\n \u003cp\u003eComputed tomography\u003c/p\u003e\n \u003c/td\u003e\n \u003c/tr\u003e\n \u003ctr\u003e\n \u003ctd valign=\"top\"\u003e\n \u003cp\u003eT7\u003c/p\u003e\n \u003c/td\u003e\n \u003ctd valign=\"top\"\u003e\n \u003cp\u003eSeventh thoracal vertebrea\u003c/p\u003e\n \u003c/td\u003e\n \u003c/tr\u003e\n \u003ctr\u003e\n \u003ctd valign=\"top\"\u003e\n \u003cp\u003eL5\u003c/p\u003e\n \u003c/td\u003e\n \u003ctd valign=\"top\"\u003e\n \u003cp\u003eFifth lumbal vertebrea\u003c/p\u003e\n \u003c/td\u003e\n \u003c/tr\u003e\n \u003ctr\u003e\n \u003ctd valign=\"top\"\u003e\n \u003cp\u003eDXA\u003c/p\u003e\n \u003c/td\u003e\n \u003ctd valign=\"top\"\u003e\n \u003cp\u003eDual-Energy-X-Ray\u0026nbsp;\u003c/p\u003e\n \u003c/td\u003e\n \u003c/tr\u003e\n \u003ctr\u003e\n \u003ctd valign=\"top\"\u003e\n \u003cp\u003eFig.\u003c/p\u003e\n \u003c/td\u003e\n \u003ctd valign=\"top\"\u003e\n \u003cp\u003eFigure\u003c/p\u003e\n \u003c/td\u003e\n \u003c/tr\u003e\n \u003ctr\u003e\n \u003ctd valign=\"top\"\u003e\n \u003cp\u003eF\u003csub\u003emax\u003c/sub\u003e\u003c/p\u003e\n \u003c/td\u003e\n \u003ctd valign=\"top\"\u003e\n \u003cp\u003eMaximum pullout force\u003c/p\u003e\n \u003c/td\u003e\n \u003c/tr\u003e\n \u003ctr\u003e\n \u003ctd valign=\"top\"\u003e\n \u003cp\u003eMPa\u003c/p\u003e\n \u003c/td\u003e\n \u003ctd valign=\"top\"\u003e\n \u003cp\u003eMegapascal\u003c/p\u003e\n \u003c/td\u003e\n \u003c/tr\u003e\n \u003ctr\u003e\n \u003ctd valign=\"top\"\u003e\n \u003cp\u003eE\u003c/p\u003e\n \u003c/td\u003e\n \u003ctd valign=\"top\"\u003e\n \u003cp\u003eCompressive modulus\u003c/p\u003e\n \u003c/td\u003e\n \u003c/tr\u003e\n \u003ctr\u003e\n \u003ctd valign=\"top\"\u003e\n \u003cp\u003eσ\u003csub\u003ey\u003c/sub\u003e\u003c/p\u003e\n \u003c/td\u003e\n \u003ctd valign=\"top\"\u003e\n \u003cp\u003eCompressive stress\u0026nbsp;\u003c/p\u003e\n \u003c/td\u003e\n \u003c/tr\u003e\n \u003ctr\u003e\n \u003ctd valign=\"top\"\u003e\n \u003cp\u003eσ\u003csub\u003ep\u003c/sub\u003e\u0026nbsp;\u003c/p\u003e\n \u003c/td\u003e\n \u003ctd valign=\"top\"\u003e\n \u003cp\u003ePlateau stress\u0026nbsp;\u003c/p\u003e\n \u003c/td\u003e\n \u003c/tr\u003e\n \u003ctr\u003e\n \u003ctd valign=\"top\"\u003e\n \u003cp\u003eCAD\u003c/p\u003e\n \u003c/td\u003e\n \u003ctd valign=\"top\"\u003e\n \u003cp\u003eComputer aided design\u003c/p\u003e\n \u003c/td\u003e\n \u003c/tr\u003e\n \u003ctr\u003e\n \u003ctd valign=\"top\"\u003e\n \u003cp\u003eSLA\u003c/p\u003e\n \u003c/td\u003e\n \u003ctd valign=\"top\"\u003e\n \u003cp\u003eStereolithography\u003c/p\u003e\n \u003c/td\u003e\n \u003c/tr\u003e\n \u003ctr\u003e\n \u003ctd valign=\"top\"\u003e\n \u003cp\u003ey\u003c/p\u003e\n \u003c/td\u003e\n \u003ctd valign=\"top\"\u003e\n \u003cp\u003eAlgebraic Variable\u003c/p\u003e\n \u003c/td\u003e\n \u003c/tr\u003e\n \u003ctr\u003e\n \u003ctd valign=\"top\"\u003e\n \u003cp\u003ex\u003c/p\u003e\n \u003c/td\u003e\n \u003ctd valign=\"top\"\u003e\n \u003cp\u003eAlgebraic Variable\u003c/p\u003e\n \u003c/td\u003e\n \u003c/tr\u003e\n \u003ctr\u003e\n \u003ctd valign=\"top\"\u003e\n \u003cp\u003ea\u003c/p\u003e\n \u003c/td\u003e\n \u003ctd valign=\"top\"\u003e\n \u003cp\u003eProduct within power equation\u003c/p\u003e\n \u003c/td\u003e\n \u003c/tr\u003e\n \u003ctr\u003e\n \u003ctd valign=\"top\"\u003e\n \u003cp\u003eb\u003c/p\u003e\n \u003c/td\u003e\n \u003ctd valign=\"top\"\u003e\n \u003cp\u003eExponent within power equation\u003c/p\u003e\n \u003c/td\u003e\n \u003c/tr\u003e\n \u003ctr\u003e\n \u003ctd valign=\"top\"\u003e\n \u003cp\u003eTab.\u003c/p\u003e\n \u003c/td\u003e\n \u003ctd valign=\"top\"\u003e\n \u003cp\u003eTable\u003c/p\u003e\n \u003c/td\u003e\n \u003c/tr\u003e\n \u003ctr\u003e\n \u003ctd valign=\"top\"\u003e\n \u003cp\u003ep\u003c/p\u003e\n \u003c/td\u003e\n \u003ctd valign=\"top\"\u003e\n \u003cp\u003eStatisical p-value\u003c/p\u003e\n \u003c/td\u003e\n \u003c/tr\u003e\n \u003ctr\u003e\n \u003ctd valign=\"top\"\u003e\n \u003cp\u003evs.\u003c/p\u003e\n \u003c/td\u003e\n \u003ctd valign=\"top\"\u003e\n \u003cp\u003eVersus\u003c/p\u003e\n \u003c/td\u003e\n \u003c/tr\u003e\n \u003ctr\u003e\n \u003ctd valign=\"top\"\u003e\n \u003cp\u003eN\u003c/p\u003e\n \u003c/td\u003e\n \u003ctd valign=\"top\"\u003e\n \u003cp\u003eNumber\u003c/p\u003e\n \u003c/td\u003e\n \u003c/tr\u003e\n \u003ctr\u003e\n \u003ctd valign=\"top\"\u003e\n \u003cp\u003eR²\u003c/p\u003e\n \u003c/td\u003e\n \u003ctd valign=\"top\"\u003e\n \u003cp\u003eRegression coefficient\u003c/p\u003e\n \u003c/td\u003e\n \u003c/tr\u003e\n \u003ctr\u003e\n \u003ctd valign=\"top\"\u003e\n \u003cp\u003ee.g.\u003c/p\u003e\n \u003c/td\u003e\n \u003ctd valign=\"top\"\u003e\n \u003cp\u003eFor example\u003c/p\u003e\n \u003c/td\u003e\n \u003c/tr\u003e\n \u003c/tbody\u003e\n\u003c/table\u003e"},{"header":"Declarations","content":"\u003cp\u003e\u003cstrong\u003eEthics approval and consent to participate\u003c/strong\u003e\u003c/p\u003e\n\u003cp\u003eThe authors are accountable for all aspects of the work in ensuring that questions related to the accuracy or integrity of any part of the work are appropriately investigated and resolved. All body donors gave their informed and written consent to the donation of their bodies for teaching and research purposes while alive. Being part of the body donor program regulated by the Saxonian Death and Funeral Act of 1994 (third section, paragraph 18 item 8), institutional approval for the use of the post-mortem tissues of human body donors was obtained from the Institute of Anatomy (University of Leipzig) by the Ethics Committee of the University of Leipzig Medical Center (ethical approval No. 129/21-ck). The authors declare that all experiments were conducted according to the principles of the Declaration of Helsinki (as revised in 2013).\u003c/p\u003e\n\u003cp\u003e\u003cstrong\u003eConsent for publication\u003c/strong\u003e\u003c/p\u003e\n\u003cp\u003eNot applicable.\u003c/p\u003e\n\u003cp\u003e\u003cstrong\u003eAvailability of data and materials\u003c/strong\u003e\u003c/p\u003e\n\u003cp\u003eThe datasets used and/or analysed during the current study are available from the corresponding author on reasonable request.\u003c/p\u003e\n\u003cp\u003e\u003cstrong\u003eCompeting interests\u003c/strong\u003e\u003c/p\u003e\n\u003cp\u003eThe authors have no conflicts of interest to declare.\u003c/p\u003e\n\u003cp\u003e\u003cstrong\u003eFunding\u003c/strong\u003e\u003c/p\u003e\n\u003cp\u003eThis research was funded by Roland Ernst Stiftung für Gesundheitswesen (Funding Number: ROLAND ERNST STIFTUNG/ 01/21). This article was funded by the Open Access Publishing Fund of Leipzig University, which is supported by the German Research Foundation within the program Open Access Publication Funding.\u003c/p\u003e\n\u003cp\u003e\u003cstrong\u003eAuthors' contributions\u003c/strong\u003e\u003c/p\u003e\n\u003cp\u003eFM – Conception and design, data acquisition, analyzation and interpretation, lattice design and parametrization, original draft and revision\u003c/p\u003e\n\u003cp\u003eSS – Conception and design, data analyzation and manuscript revision\u003c/p\u003e\n\u003cp\u003eC-EH – Conception and design\u003c/p\u003e\n\u003cp\u003eNvdH – Conception and design, data acquisition and interpretation, manuscript revision\u003c/p\u003e\n\u003cp\u003e\u003cstrong\u003eAcknowledgements\u003c/strong\u003e\u003c/p\u003e\n\u003cp\u003eWe want to thank all body donors for giving their bodies for research and the Institute of Anatomy, Faculty of Medicine, Leipzig University for acquiring the donor tissue. Furthermore I want to thank Robin Heilmann for the support in designing the lattice structure.\u003c/p\u003e\n\u003cp\u003e\u003cstrong\u003eDeclaration of interest\u003c/strong\u003e\u003c/p\u003e\n\u003cp\u003eThe 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.\u003c/p\u003e"},{"header":"References","content":"\u003col\u003e\n \u003cli\u003eJiang M, Coles-Black J, Chen G, Alexander M, Chuen J, Hardidge A. 3D Printed Patient-Specific Complex Hip Arthroplasty Models Streamline the Preoperative Surgical Workflow: A Pilot Study. Front Surg. 2021;8:687379. doi:10.3389/fsurg.2021.687379.\u003c/li\u003e\n \u003cli\u003eDiment LE, Thompson MS, Bergmann JHM. Clinical efficacy and effectiveness of 3D printing: a systematic review. BMJ Open. 2017;7:e016891. doi:10.1136/bmjopen-2017-016891.\u003c/li\u003e\n \u003cli\u003eYang M, Li C, Li Y, Zhao Y, Wei X, Zhang G, et al. 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J Orthop Surg Res. 2022;17:376. doi:10.1186/s13018-022-03265-4.\u003c/li\u003e\n \u003cli\u003eMetzner F, Reise R, Heyde C-E, H\u0026ouml;h NH von der, Schleifenbaum S. Side specific differences of Hounsfield-Units in the osteoporotic lumbar spine. J Spine Surg. 2024;10:232\u0026ndash;43. doi:10.21037/jss-23-121.\u003c/li\u003e\n \u003cli\u003eUlrich D, van Rietbergen B, Laib A, R̈uegsegger P. The ability of three-dimensional structural indices to reflect mechanical aspects of trabecular bone. Bone. 1999;25:55\u0026ndash;60. doi:10.1016/S8756-3282(99)00098-8.\u003c/li\u003e\n \u003cli\u003eMetzner F, Fischer B, Heyde C-E, Schleifenbaum S. The effects of force application on the compressive properties of femoral spongious bone. Clin Biomech (Bristol, Avon). 2022;101:105866. doi:10.1016/j.clinbiomech.2022.105866.\u003c/li\u003e\n \u003cli\u003eDIN 50134:2008-10, Pr\u0026uuml;fung von metallischen Werkstoffen_- Druckversuch an metallischen zellularen Werkstoffen. Berlin: Beuth Verlag GmbH. doi:10.31030/1443205.\u003c/li\u003e\n \u003cli\u003eKeaveny TM, Pinilla TP, Crawford RP, Kopperdahl DL, Lou A. Systematic and random errors in compression testing of trabecular bone. J Orthop Res. 1997;15:101\u0026ndash;10. doi:10.1002/jor.1100150115.\u003c/li\u003e\n \u003cli\u003eLenchik L, Weaver AA, Ward RJ, Boone JM, Boutin RD. Opportunistic Screening for Osteoporosis Using Computed Tomography: State of the Art and Argument for Paradigm Shift. Curr Rheumatol Rep. 2018;20:74. doi:10.1007/s11926-018-0784-7.\u003c/li\u003e\n \u003cli\u003eAhmad A, Crawford CH, Glassman SD, Dimar JR, Gum JL, Carreon LY. Correlation between bone density measurements on CT or MRI versus DEXA scan: A systematic review. N Am Spine Soc J. 2023;14:100204. doi:10.1016/j.xnsj.2023.100204.\u003c/li\u003e\n \u003cli\u003ePinto EM, Neves JR, Teixeira A, Frada R, Atilano P, Oliveira F, et al. Efficacy of Hounsfield Units Measured by Lumbar Computer Tomography on Bone Density Assessment: A Systematic Review. Spine (Phila Pa 1976). 2022;47:702\u0026ndash;10. doi:10.1097/BRS.0000000000004211.\u003c/li\u003e\n \u003cli\u003eScheyerer MJ, Ullrich B, Osterhoff G, Spiegl UA, Schnake KJ. \u0026bdquo;Hounsfield units\u0026ldquo; als Ma\u0026szlig; f\u0026uuml;r die Knochendichte \u0026ndash; Anwendungsm\u0026ouml;glichkeiten in der Wirbels\u0026auml;ulenchirurgie. [Hounsfield units as a measure of bone density-applications in spine surgery]. Unfallchirurg. 2019;122:654\u0026ndash;61. doi:10.1007/s00113-019-0658-0.\u003c/li\u003e\n \u003cli\u003eShirley M, Wanderman N, Keaveny T, Anderson P, Freedman BA. Opportunistic Computed Tomography and Spine Surgery: A Narrative Review. Global Spine J. 2020;10:919\u0026ndash;28. doi:10.1177/2192568219889362.\u003c/li\u003e\n \u003cli\u003eZaidi Q, Danisa OA, Cheng W. Measurement Techniques and Utility of Hounsfield Unit Values for Assessment of Bone Quality Prior to Spinal Instrumentation: A Review of Current Literature. Spine (Phila Pa 1976). 2019;44:E239-E244. doi:10.1097/BRS.0000000000002813.\u003c/li\u003e\n \u003cli\u003eKeaveny TM, Hayes WC. A 20-year perspective on the mechanical properties of trabecular bone. J Biomech Eng. 1993;115:534\u0026ndash;42. doi:10.1115/1.2895536.\u003c/li\u003e\n \u003cli\u003eKeaveny TM, Morgan EF, Niebur GL, Yeh OC. Biomechanics of trabecular bone. Annu Rev Biomed Eng. 2001;3:307\u0026ndash;33. doi:10.1146/annurev.bioeng.3.1.307.\u003c/li\u003e\n \u003cli\u003eKeaveny TM, Borchers RE, Gibson LJ, Hayes WC. Trabecular bone modulus and strength can depend on specimen geometry. Journal of Biomechanics. 1993;26:991\u0026ndash;1000. doi:10.1016/0021-9290(93)90059-N.\u003c/li\u003e\n \u003cli\u003eKeller TS. Predicting the compressive mechanical behavior of bone. In Memory of Rik Huiskes. 1994;27:1159\u0026ndash;68. doi:10.1016/0021-9290(94)90056-6.\u003c/li\u003e\n \u003cli\u003e\u0026Ouml;hman-M\u0026auml;gi C, Holub O, Wu D, Hall RM, Persson C. Density and mechanical properties of vertebral trabecular bone-A review. JOR Spine. 2021;4:e1176. doi:10.1002/jsp2.1176.\u003c/li\u003e\n \u003cli\u003eCiarelli MJ, Goldstein SA, Kuhn JL, Cody DD, Brown MB. Evaluation of orthogonal mechanical properties and density of human trabecular bone from the major metaphyseal regions with materials testing and computed tomography. J Orthop Res. 1991;9:674\u0026ndash;82. doi:10.1002/jor.1100090507.\u003c/li\u003e\n \u003cli\u003eAshby MF. The properties of foams and lattices. Philos Trans A Math Phys Eng Sci. 2006;364:15\u0026ndash;30. doi:10.1098/rsta.2005.1678.\u003c/li\u003e\n \u003cli\u003eGibson LJ. The mechanical behaviour of cancellous bone. Journal of Biomechanics. 1985;18:317\u0026ndash;28. doi:10.1016/0021-9290(85)90287-8.\u003c/li\u003e\n \u003cli\u003eBurval DJ, McLain RF, Milks R, Inceoglu S. Primary pedicle screw augmentation in osteoporotic lumbar vertebrae: biomechanical analysis of pedicle fixation strength. Spine (Phila Pa 1976). 2007;32:1077\u0026ndash;83. doi:10.1097/01.brs.0000261566.38422.40.\u003c/li\u003e\n \u003cli\u003eGao M, Lei W, Wu Z, Da Liu, Shi L. Biomechanical evaluation of fixation strength of conventional and expansive pedicle screws with or without calcium based cement augmentation. Clin Biomech (Bristol, Avon). 2011;26:238\u0026ndash;44. doi:10.1016/j.clinbiomech.2010.10.008.\u003c/li\u003e\n \u003cli\u003eKoller H, Zenner J, Hitzl W, Resch H, Stephan D, Augat P, et al. The impact of a distal expansion mechanism added to a standard pedicle screw on pullout resistance. A biomechanical study. Spine J. 2013;13:532\u0026ndash;41. doi:10.1016/j.spinee.2013.01.038.\u003c/li\u003e\n \u003cli\u003eHalvorson TL, Kelley LA, Thomas KA, Whitecloud TS, Cook SD. Effects of bone mineral density on pedicle screw fixation. Spine (Phila Pa 1976). 1994;19:2415\u0026ndash;20. doi:10.1097/00007632-199411000-00008.\u003c/li\u003e\n \u003cli\u003eSoshi S, Shiba R, Kondo H, Murota K. An experimental study on transpedicular screw fixation in relation to osteoporosis of the lumbar spine. Spine (Phila Pa 1976). 1991;16:1335\u0026ndash;41. doi:10.1097/00007632-199111000-00015.\u003c/li\u003e\n \u003cli\u003eMatsukawa K, Abe Y, Yanai Y, Yato Y. Regional Hounsfield unit measurement of screw trajectory for predicting pedicle screw fixation using cortical bone trajectory: a retrospective cohort study. Acta Neurochir (Wien). 2018;160:405\u0026ndash;11. doi:10.1007/s00701-017-3424-5.\u003c/li\u003e\n \u003cli\u003eZou D, Sun Z, Zhou S, Zhong W, Li W. Hounsfield units value is a better predictor of pedicle screw loosening than the T-score of DXA in patients with lumbar degenerative diseases. E Spine J. 2020;29:1105\u0026ndash;11. doi:10.1007/s00586-020-06386-8.\u003c/li\u003e\n \u003cli\u003eWichmann JL, Booz C, Wesarg S, Bauer RW, Kerl JM, Fischer S, et al. Quantitative dual-energy CT for phantomless evaluation of cancellous bone mineral density of the vertebral pedicle: correlation with pedicle screw pull-out strength. Eur Radiol. 2015;25:1714\u0026ndash;20. doi:10.1007/s00330-014-3529-7.\u003c/li\u003e\n \u003cli\u003eHirano T, Hasegawa K, Takahashi HE, Uchiyama S, Hara T, Washio T, et al. Structural characteristics of the pedicle and its role in screw stability. Spine (Phila Pa 1976). 1997;22:2504-9; discussion 2510. doi:10.1097/00007632-199711010-00007.\u003c/li\u003e\n \u003cli\u003eCho W, Cho SK, Wu C. The biomechanics of pedicle screw-based instrumentation. J Bone Joint Surg Br. 2010;92:1061\u0026ndash;5. doi:10.1302/0301-620X.92B8.24237.\u003c/li\u003e\n \u003cli\u003eCarter, Hayes WC. The compressive behavior of bone as a two-phase porous structure. JBJS. 1977;59.\u003c/li\u003e\n\u003c/ol\u003e"}],"fulltextSource":"","fullText":"","funders":[],"hasAdminPriorityOnWorkflow":false,"hasManuscriptDocX":true,"hasOptedInToPreprint":true,"hasPassedJournalQc":"","hasAnyPriority":false,"hideJournal":false,"highlight":"","institution":"","isAcceptedByJournal":true,"isAuthorSuppliedPdf":false,"isDeskRejected":"","isHiddenFromSearch":false,"isInQc":false,"isInWorkflow":false,"isPdf":false,"isPdfUpToDate":true,"isWithdrawnOrRetracted":false,"journal":{"display":true,"email":"[email protected]","identity":"bmc-biomedical-engineering","isNatureJournal":false,"hasQc":true,"allowDirectSubmit":false,"externalIdentity":"bbme","sideBox":"Learn more about [BMC Biomedical Engineering](http://bmcbiomedeng.biomedcentral.com)","snPcode":"","submissionUrl":"https://www.editorialmanager.com/bbme/default.aspx","title":"BMC Biomedical Engineering","twitterHandle":"BMC_series","acdcEnabled":true,"dfaEnabled":false,"editorialSystem":"em","reportingPortfolio":"BMC Series","inReviewEnabled":true,"inReviewRevisionsEnabled":true},"keywords":"cancellous bone, 3D-printing, lattice, additive manufacturing, stereolithography, compressive test, bone, osteoporosis, bone density","lastPublishedDoi":"10.21203/rs.3.rs-7710013/v1","lastPublishedDoiUrl":"https://doi.org/10.21203/rs.3.rs-7710013/v1","license":{"name":"CC BY 4.0","url":"https://creativecommons.org/licenses/by/4.0/"},"manuscriptAbstract":"\u003cp\u003e\u003cstrong\u003eBackground\u003c/strong\u003e\u003c/p\u003e\n\u003cp\u003ePersonalized 3D-printed bone models are becoming increasingly popular in clinical care. Common applications include the visualization of idiopathic deformities or complex joint fractures. Functionalizing such printed replicas in terms of individual mechanical properties holds great potential for clinical training and research but is challenging due to the complexity of the bone structure. This study aims at developing a parametrizable structure as a substitute for spongious bone in order by simplifying 3D reconstruction and printing.\u003c/p\u003e\n\u003cp\u003e\u003cstrong\u003eMethods\u003c/strong\u003e\u003c/p\u003e\n\u003cp\u003e43\u0026nbsp;vertebrae from 6\u0026nbsp;body donors aged 86.8\u0026nbsp;±\u0026nbsp;7.8 years were examined. Each spine underwent a clinical computed tomography scan. Cylindrical samples (Ø6\u0026nbsp;x\u0026nbsp;12\u0026nbsp;mm) were randomly taken from the left or right side of the vertebral body using a core drill in the superior-inferior direction. Specific software was used for determining the volumetric Hounsfield-Units of the spongious bone in each vertebral hemisphere. In parallel, a parametric hexagonal grid structure was designed using engineering software. All rods within the lattice have a variable length L and a fixed diameter of t\u0026nbsp;=\u0026nbsp;0.4\u0026nbsp;mm. By varying the ratio t/L, six different porosities were defined. For each of these, five cylindrical lattice samples (diameter/length\u0026nbsp;=\u0026nbsp;1/2) from two different synthetic resins were manufactured using the stereolithography printing process. All samples were mechanically characterized by uniaxial compressive testing. Curve fitting based on power functions (y\u0026nbsp;=\u0026nbsp;ax\u003csup\u003eb\u003c/sup\u003e) allowed the determination of correlations between mechanical parameters and Hounsfield-Units (bone) as well as the lattice parameter t/L (3D-printed lattice). Finally, three vertebrae with varying bone quality were printed with their respected parameterized lattice and evaluated by comparing the axial screw pullout forces of the human and the respective printed bones.\u003c/p\u003e\n\u003cp\u003e\u003cstrong\u003eResults\u003c/strong\u003e\u003c/p\u003e\n\u003cp\u003eThere is a significant correlation between the mechanical properties of the bone specimens and the determined Hounsfield-Units. Furthermore, the mechanical properties of the lattice can be excellently described by the ratio t/L. The printed vertebrae showed pull-out forces similar to those of osteoporotic bone.\u003c/p\u003e\n\u003cp\u003e\u003cstrong\u003eConlusion\u003c/strong\u003e\u003c/p\u003e\n\u003cp\u003eThe mechanical behavior of vertebral human spongious bone can be well reproduced by a 3D-printed generic lattice structure. Patient-specific bone models can be generated by integrating the parameterizable lattice structure into the specific bone contours. These models can help in improving patient care, for instance by enabling highly realistic surgical approaches for particularly complex anatomies.\u003c/p\u003e","manuscriptTitle":"Biomechanical evaluation of individual 3D-printed vertebrae","msid":"","msnumber":"","nonDraftVersions":[{"code":1,"date":"2025-10-17 17:48:37","doi":"10.21203/rs.3.rs-7710013/v1","editorialEvents":[{"type":"communityComments","content":0},{"type":"decision","content":"Revision requested","date":"2025-10-31T04:54:43+00:00","index":"","fulltext":""},{"type":"editorInvitedReview","content":"","date":"2025-10-30T10:29:24+00:00","index":"hide","fulltext":""},{"type":"reviewerAgreed","content":"297244513613412340117312053637346870386","date":"2025-10-20T08:43:58+00:00","index":"hide","fulltext":""},{"type":"reviewerAgreed","content":"170644441863082192848479408053172335993","date":"2025-10-05T06:57:29+00:00","index":"hide","fulltext":""},{"type":"editorInvitedReview","content":"","date":"2025-10-03T11:36:42+00:00","index":"hide","fulltext":""},{"type":"reviewerAgreed","content":"252793255752161349639863276952493523488","date":"2025-10-03T07:10:07+00:00","index":"hide","fulltext":""},{"type":"reviewersInvited","content":"","date":"2025-10-03T06:50:23+00:00","index":"","fulltext":""},{"type":"editorAssigned","content":"","date":"2025-09-29T13:52:39+00:00","index":"","fulltext":""},{"type":"checksComplete","content":"","date":"2025-09-29T13:51:47+00:00","index":"","fulltext":""},{"type":"submitted","content":"BMC Biomedical Engineering","date":"2025-09-25T07:23:18+00:00","index":"","fulltext":""}],"status":"published","journal":{"display":true,"email":"[email protected]","identity":"bmc-biomedical-engineering","isNatureJournal":false,"hasQc":true,"allowDirectSubmit":false,"externalIdentity":"bbme","sideBox":"Learn more about [BMC Biomedical Engineering](http://bmcbiomedeng.biomedcentral.com)","snPcode":"","submissionUrl":"https://www.editorialmanager.com/bbme/default.aspx","title":"BMC Biomedical Engineering","twitterHandle":"BMC_series","acdcEnabled":true,"dfaEnabled":false,"editorialSystem":"em","reportingPortfolio":"BMC Series","inReviewEnabled":true,"inReviewRevisionsEnabled":true}}],"origin":"","ownerIdentity":"540a82b6-03da-4a56-8e5a-c8fc5fc503da","owner":[],"postedDate":"October 17th, 2025","published":true,"recentEditorialEvents":[],"rejectedJournal":[],"revision":"","amendment":"","status":"published-in-journal","subjectAreas":[],"tags":[],"updatedAt":"2026-03-09T16:04:17+00:00","versionOfRecord":{"articleIdentity":"rs-7710013","link":"https://doi.org/10.1186/s42490-026-00107-w","journal":{"identity":"bmc-biomedical-engineering","isVorOnly":false,"title":"BMC Biomedical Engineering"},"publishedOn":"2026-03-06 15:57:40","publishedOnDateReadable":"March 6th, 2026"},"versionCreatedAt":"2025-10-17 17:48:37","video":"","vorDoi":"10.1186/s42490-026-00107-w","vorDoiUrl":"https://doi.org/10.1186/s42490-026-00107-w","workflowStages":[]},"version":"v1","identity":"rs-7710013","journalConfig":"researchsquare"},"__N_SSP":true},"page":"/article/[identity]/[[...version]]","query":{"redirect":"/article/rs-7710013","identity":"rs-7710013","version":["v1"]},"buildId":"XKTyCvWXoU3ODBz1xrDgd","isFallback":false,"isExperimentalCompile":false,"dynamicIds":[84888],"gssp":true,"scriptLoader":[]}