Determination of the Modulus of Elasticity by Bending Tests of Specimens with Nonuniform Cross Section

In medical practice and research, numerical simulations of the mechanical behavior of human organs are of increasing interest; for example, finite element simulations of the buildup of stresses in the human pelvis [1‐4]. Reliable experimental identification of relevant material properties is an important precondition to achieve appropriate simulation results. Of predominant importance in this context are the stiffness properties of human tissue, including those of cortical and cancellous bone. Whereas systematic location-dependent stiffness differences should be considered in numerical models to obtain adequate simulation results, random variations may normally be neglected. In many numerical simulation models, human tissues are reproduced by homogeneous components, the effective properties of which need to be determined experimentally, especially those characterizing the material’s stiffness. The focus of this paper is on the experimental determination of the modulus of elasticity of human cortical bone. Samples taken from the human lumbo-pelvic system were subjected to flexural loading. Assuming homogeneity of the material, an effective modulus of elasticity was determined on the basis of deformations measured in the bending tests. The obtained results may then be assigned to finite element models for simulating the stress-dependent deformation of the human pelvis. At present, the database of material properties of the human lumbo-pelvic system appears to be insufficient. One of the goals of this research is to expand this database by applying a reliable testing procedure.

The bending test appears to be a suitable method for testing cortical bone. Direct tension or compression tests are more problematic from the technical point of view because applying a load to the specimen leads to a multiaxial and hard-to-predict state of stress in the vicinity of the specimens’ end faces. In the case of tensile tests, this multiaxiality results from lateral clamping forces, and in the case of compression, it results from lateral frictional forces. These problems complicate the determination of the modulus of elasticity characterizing the material’s stiffness under a uniaxial state of stress. Theoretically, the influence of the lateral forces at the specimens’ end faces vanishes with increasing specimen length, but the maximum size of the bone specimens is commonly limited for anatomical and statistical reasons. The specimens should be small enough to justify the averaging of the local material stiffness. It is undisputed that random variations of the local material properties are larger in biological tissues than in many technical materials. However, if systematic, i.e., anatomically explainable, variations in the stiffness within the specimen are negligible, then the determination of an average modulus of elasticity and the assignment of the value to the corresponding location in a finite element model are justified. In bending tests, this condition can be met because only comparatively small specimen sizes are needed. Another reason for choosing the bending test as the experimental approach is that bone specimens do not necessarily have a straight axis. In direct tension or compression tests, a curved axis leads to significant deviations from the assumed uniform strain distribution in the cross sections of the specimen. However, moderate curvature of beams subjected to bending does not cause significant deviations from basic flexural theory. When the radius of curvature of the beam axis is at least four times the height of the beam, as was the case in the experiments reported here, a straight beam axis may be assumed for the mechanical analysis.

It must be considered that the flexural loading imposed on cortical bone specimens leads to stress concentrations and indentations at the load application point as well as at the supports. However, it is possible to determine the elastic curve of the specimen by measuring the deflection at multiple positions along the beam axis; thus flexural theory can be applied. In this way, the influence of the indentations is eliminated.

A major difference between biological and engineered specimens is the irregularity of the specimen geometry. In the case of the human lumbo-pelvic system, the cross-sectional properties of the beam-like bone specimen may vary markedly along the beam axis mainly due to the natural variation of the cortical layer thickness. When determining the modulus of elasticity on the basis of the measured deformations, it is necessary to consider this variation of the cross-sectional properties and, in this way, to separate its influence from the one of the unavoidable variation of the local material properties. An alternative would be a more invasive processing of the samples to produce strictly rectangular cuboid specimens. However, in this study, the intention was to limit cutting or grinding processes to mitigate their effects on the mechanical behavior of the specimens.

Several investigations involving flexural tests of beam-like cortical bone specimens are reported in the literature. Normally, the determination of the modulus of elasticity is based on the measured midspan deflection of rectangular cuboid beams [5‐7]. Lotz et al. [8] tested flat plate cortical bone specimens and determined the modulus of elasticity under consideration of the load point indentation. The consideration of nonuniform cross-sectional properties in flexural tests of beam-like cortical bone specimens has not been reported in the literature before. As far as shear deformation and support indentation in flexural tests are concerned, their effects on the determined moduli of elasticity were extensively studied for other materials. Mujika [9] tested carbon/epoxy composite and Brancheriau et al. [10] wooden samples. It was found in both cases that the before-mentioned influences are not always negligible.

In the “Bending Tests and Deflection Measurements” and “Elastic Curve Determination based on the Optical Displacement Measurement” sections, the applied test setup as well as data acquisition and processing are described. Different evaluation methods for processing the experimental results are presented in the “Methods for Evaluating the Test Results” section, and their suitability is discussed in the “Comparison of the Evaluation Methods” section. It should be noted that the applicability of the evaluation methods proposed in this paper is not limited to the human pelvis or other cortical bone tissue. Possible applications also include naturally grown structural materials. However, the samples of cortical bone from the human lumbo-pelvic complex were a suitable example for the application and comparison of the evaluation methods described here. Due to the natural shape of the pelvis, the samples were characterized by comparatively large variability in thickness and curvature, which made them more realistic than artificially produced samples.

The specimens of cortical bone were taken from the pelvises of three female and two male human donors. The donors were 76.8 ± 13.4 (53–89) years old. Being part of the body donor program regulated by the Saxonian Death and Funeral Act of 1994 (3rd section, paragraph 18, item 8), the Institute of Anatomy of Leipzig University obtained institutional approval for the use of postmortem tissues of human body donors. All experiments were performed according to the ethical principles of the Declaration of Helsinki.

Specimen acquisition as well as preparation and storage of the samples were performed according to a standardized procedure proposed by the first author. It was intended to acquire the specimens as less invasive as possible in order to investigate their mechanical properties largely close to nature. The targeted dimensions of the beam-like specimens with intended rectangular cross sections resulted from the geometry of the human pelvis and from the requirements for flexural testing. The selection of the sampling locations was made from an anatomical point of view and by means of computed tomography (CT) scans of the individual donor pelvises. The cortical bone was cut in the deep-frozen state using a diamond thin-cutting band saw, without water cooling. Cancellous bone was removed by sawing and by means of a Stille-Ruskin bone rongeur. For the removal of soft tissue, where possible, served a scalpel. The omission of further post-processing, in particular sawing or grinding on the upper or lower face of the beam-like specimens, resulted in the before-mentioned variation of the cross-sectional properties along the beam axis.

The specimens had approximately rectangular cross sections. The average specimen dimensions were approximately 2.26 × 9.52 × 35.4 mm³ (height × width × length). The height was the dimension in the loading direction and corresponds to the natural thickness of the cortical bone. A total of 145 samples were successfully harvested, and 138 qualified for inclusion in the examination described below. Reasons for exclusion were strong anatomical abnormality, either geometrical or due to impurity, and, in the case of four samples, failed tests due to accidental dislocation or unacceptable twisting. Table 1 contains information on the variation of the cross-sectional dimensions along the span of the individual specimens as well as within the whole population of all 138 samples. The variation of the height is noticeably greater than that of the width. Graphical representations of the corresponding distributions are shown in the supplementary material.

Figure 1 shows the experimental setup with the loading device made of stainless steel. The circular-cylindrical roller bearings at midspan and at the supports had a diameter 2 mm. The upper roller bearing was rotatable about an axis parallel to the beam axis. Complete design drawings of the experimental setup may be found in the supplementary material.

The simply supported beam-like specimens had a span of 20 mm. During the tests, the periosteum of the cortical bone was directed upward, and its cancellous (inner) side was directed downward. This orientation was chosen to minimize the stiffening effect of residual material adhering to the cortical bone specimen. The remains of the periosteum on the upper side and of the cancellous bone on the lower side have a comparatively small stiffness under compression and tension, respectively. These different behaviors result from the internal structure of the two types of tissue. The periosteum consists mainly of flexible collagen fibers that evade compressive stress. In contrast to that, the cancellous bone has a trabecular structure consisting of small beam-like members with the hollow spaces between them filled with rather liquid bone marrow. In comparison to the cortical bone tested here, the stiffness of cancellous bone is significantly smaller [11]. In addition, the trabecular structure of the latter is damaged in the cutting process, further reducing its tensile stiffness.

At midspan, a transverse force was applied under displacement control by using a 10 kN test frame of an electromechanical testing machine (walter + bai AG - LFEM 600/100/10). A 200 N load cell (Bosche - S40S-G3-0020) served as the force measurement device. The loading velocity was chosen in accordance with a physiologically justifiable strain rate of \(\dot{\varepsilon } = 0.005\;{\text{s}}^{ - 1}\) [12]. Based on flexural theory, the resulting midspan deflection rate is obtained by \(v = {{\left( {\dot{\varepsilon } \cdot l^{2} } \right)} \mathord{\left/ {\vphantom {{\left( {\dot{\varepsilon } \cdot l^{2} } \right)} {\left( {6 \cdot h} \right)}}} \right. \kern-0pt} {\left( {6 \cdot h} \right)}}\) for the span \(l\) of the beam and the height \(h\) at midspan.

The deflection was measured by digital image correlation (DIC) with a Dantec Dynamics Q400 DCM 12.0 (2 × 12 MP sensor, 65 mm focal length, ~100 px/mm resolution, and 4 Hz sampling rate). For evaluating the displacement components, the software Istra4D (version 4.4.7.527) was utilized with the grid spacing set to 35 px and the facet size to 39 px. Figure 1 shows in the bottom a full-field map of the vertical displacement component, i.e., of the displacement in the loading direction. The white circles are the evaluation points for the DIC measurement of the 3D coordinates. The intention was to acquire as much information as possible on the deformed state of each specimen.

In addition to the DIC, the load point displacement was measured by linear variable displacement transformers (LVDTs, type W10K from Hottinger Brüel & Kjaer GmbH) as displacement sensors. The LVDTs were applied to two opposite sides of the loading device, not directly to the specimen. Due to the relatively small compliance of the loading device compared to the specimen deformability, the measured load point displacement may be regarded as the midspan deflection of the beam. However, a portion of the deflection measured in this way results from indentation at the load point and at the supports.

The 3D displacement components of seven evaluation points on the specimen surface, see Fig. 1 (bottom), were measured by DIC and then projected onto the loading plane. The vertical displacements of these points, i.e., those parallel to the loading direction, are the local deflection values, which were approximated by a continuous function for the elastic curve by conducting a weighted multi-constraint nonlinear least-square fit. The applied constraints are physically justifiable by means of flexural theory and include zero curvature of the elastic curve at the supports and negative curvature along the beam’s span. Adequate fits were achieved with a Fourier series having four sine terms and additional linear and constant elements. The applied approximation function and its derivatives are given in equations (1) through (3), which are based on the coordinate system shown in Fig. 2 and contain the Fourier coefficients \(b_{i}\) as well as \(c\) and \(d\) as additional parameters. The second derivative is zero at the supports, i.e., at \(x = x_{\min } = - {l \mathord{\left/ {\vphantom {l 2}} \right. \kern-0pt} 2}\) and \(x = x_{\max } = + {l \mathord{\left/ {\vphantom {l 2}} \right. \kern-0pt} 2}\), thus satisfying the abovementioned zero-curvature constraint.

The total lateral (i.e., vertical) displacement \(w(x)\), approximating the measured displacement, may be subdivided into different contributions that also influence the modulus of elasticity to be determined. These contributions are schematically represented in Fig. 2 and may be summed according to equation (4).

The contribution of the indentation at the supports \(w_{L} (x)\) is considered by the linear and constant terms in equation (1) and can easily be quantified on the basis of the displacements of the beam axis measured at the supports. By subtracting \(w_{L} (x)\) from the total displacement, the deflection due to the internal forces along the beam’s axis is obtained. The deflection \(w_{V} (x)\) due to the shear force is in the case of slender beams significantly smaller than that due to the bending moment \(w_{M} (x)\). Due to the constant shear force in both half-spans, i.e., to the left and right of the load point, the resulting inclination of the beam’s axis will also be constant, leading to the bilinear function \(w_{V} (x)\). In flexural theory, the function of the deflection due to the bending moment \(w_{M} (x)\) is commonly referred to as the elastic curve. The corresponding midspan values for the aforementioned three contributions to the total displacement are denoted as \(f_{L}\), \(f_{V}\), and \(f_{M}\) (see Fig. 2).

Since the contribution of the shear force is considerably smaller than that of the bending moment, the contribution of the shear force may be estimated under the assumption of uniform cross-sectional properties along the beam axis. Under this simplifying assumption, a theoretical ratio of the midspan displacements, \(f_{V}\) and \(f_{M}\), i.e., of those due to the shear force and the bending moment, respectively, may be determined. Their theoretical values arewhere \(E\) is the modulus of elasticity, \(\nu\) is Poisson’s ratio, \(G = E/(2(1 + \nu ))\) is the shear modulus, \(I\) is the moment of inertia, and \(A_{S}\) is the shear area as a cross-sectional property. Hence,where I and A_S are the average cross-sectional properties along the beam axis. For the rectangular shape of the cross section assumed here (see the “Methods for Evaluating the Test Results” section), the shear area A_S is equal to the total cross-sectional area divided by 1.2. Poisson’s ratio \(\nu\) may be estimated on the basis of uniaxial test results or an assumed value is adopted. This simplification is justifiable because of the non-proportional and, thereby, comparatively small influence of \(\nu\), see equations (5) and (6), and also in view of the shear-induced midspan displacement \(f_{V}\) being only a small portion of the total midspan displacement \(f_{V} + f_{M}\). For the dimensions of the individual specimens tested here, this portion amounts to 4.16% ± 2.61%. Wirtz et al. [11] proposed assuming a value of \(\nu\) = 0.3 for cortical bone. A reduction of this value by 20% would lead to a reduction of the calculated total midspan displacement \(f_{V} + f_{M}\) by only about 0.2%.

Using equation (6), we estimated the contribution of the shear deformation to the midspan displacement resulting from the internal forces. The bilinear function of the displacement due to the shear force was then

The contributions of the shear deformation and of the indentation at the supports may be deducted from the measured total displacements of the beam axis, yielding the displacements resulting from the bending moment only. To obtain a continuous function \(w_{M} (x)\), these modified displacement values along the beam axis were again approximated by a Fourier series but now without additional linear and constant terms because the deflections at the supports are zero.

There are several methods to retrieve an average modulus of elasticity of the material of a beam-shaped specimen. In the following, a total of seven methods, A through G, are presented (see Table 2). Each of these methods includes multiple submethods, which will be explained later. All methods are based on the following assumptions:

In view of the particular set of specimens referred to in the present paper, two of the above assumptions require further explanation. First, the midspan curvature of the unloaded specimens was smaller than 0.05 mm⁻¹ for more than 95% of all specimens, and the curvature of a circle put through center and supported points of the respective beam axis is even smaller, see distributions in the supplementary material. Consequently, the minimum ratio of the radius of curvature to the average specimen height is larger than about 8. This leads to a deviation of less than 1.5% in the total strain energy of the deflected beam as well as in the calculated midspan deflection. Therefore, the neglect of the curvature is justified for these particular specimens. The strain energy is only slightly underestimated and statistical analyses did not reveal a significant correlation between initial curvature and the determined modulus of elasticity, see Spearman coefficients in the supplementary material. Second, the neglect of the anticlastic curvature on the measured deflections is justified for the present experiments, but is not generalizable. For the present experiments and a Poisson’s ratio of 0.3, linear-elastic Finite Element simulations conducted by the authors have shown that the maximum deviation between the deflections in the beam’s centerline and at the side faces amounts to less than 3% of the midspan deflection, justifying the neglect of anticlastic curvature. For other specimen geometries and test setups, it might be appropriate to consider both the initial curvature of the beam axis and the anticlastic curvature of the middle surface. It might also become necessary to consider cross sections the shape of which deviates from the rectangular shape assumed here.

After the flexural load test, the following data were available for further processing:

Based on these data, the average modulus of elasticity in the axial direction was to be determined. In the beginning, a conventional and simplifying method is presented which is referred to as Method A (see Table 2). In addition to the above assumptions, this method is based on a constant moment of inertia I along the beam axis. The external force is related to the midspan deflection. Based on flexural theory, the midspan deflection increment Δf_M is obtained by equation (8).where ΔF is the force increment, I is the constant moment of inertia and E is the sought-for modulus of elasticity averaged over the entire specimen and the respective force increment. The major disadvantages of Method A are the required assumption of a constant moment of inertia and the falsifying influence of the support indentation. A possible improvement is the evaluation of the beam’s midspan curvature increment instead of the midspan deflection increment. This leads to Method B. The deflection values at three points in the midspan region of the beam are retrieved from the elastic curve and used for calculating the curvature of the beam axis in this region (shown in Fig. 3). The center point is located at midspan, and the distance between the outer points is l_b. By using this method, the influence of the indentation at the supports is automatically eliminated. It is also possible to eliminate the influence of the shear strain.

Assuming a constant moment of inertia \(I\) along the beam axis, the elastic curve \(\tilde{w}\left( x \right)\) based on the coordinate system in Fig. 3 can be expressed by

This leads towhere \(s_{b}\) is the sag of the center point relative to the two outer measurement points (see Fig. 3). In case of an asymmetric elastic curve, the average \(\tilde{w}\) value for the two outer measurement points is used. The strain \(\varepsilon_{bottom}\) at the bottom face with the distance \(\tilde{z}_{bottom}\) from the cross section’s centroid is

Because of the rectangular cross section, \(\tilde{z}_{bottom}\) is half of the specimen height. Equations (10) and (11) yield

For a certain load increment, the average modulus of elasticity can then be calculated by

Note that equations (9) through (11) are still based on a constant moment of inertia along the beam axis, although for the stress analysis in equation (13), the one at midspan is used. To consider nonuniform cross-sectional properties, the equivalence between the work W_ext done by the external force F and the internal work U done by the internal forces may be used. This approach is here referred to as Method C. The external and internal work increments arewhere M₀ and F₀ are the bending moment and the external force, respectively, at the beginning of the increment. The bending moment M and the resulting deflection \(w_{M}\) are functions of x with values ranging from -l/2 to l/2. Note that for the internal work the absolute values of bending moment and resulting curvature are multiplied. Under the conditions that equilibrium and compatibility are satisfied at the beginning of the load increment and assuming linear-elastic deformation within the increment, it can be stated that

This leads to

The function of the moment increment ΔM(x), equation (18), is derived from the equilibrium conditions.

Hence,

It is possible to consider the contribution \(\Delta f_{V}\) of the shear deformation to the midspan displacement increment by adding an extra term to equation (17).where \(\Delta V(x)\) is the shear force increment, \(A_{S} (x)\) is the shear area as a cross-sectional property and \(G = E/(2(1 + \nu ))\) is the shear modulus of the material. As stated before, Wirtz et al. [11] proposed adopting a Poisson’s ratio of \(\nu\) = 0.3. An assumption regarding Poisson’s ratio is justifiable since its influence is comparatively small. The midspan deflection, including the shear contribution, can be calculated bywhere \(\Delta f\) is the total midspan displacement increment, measured or obtained from the fitted displacement function (see the “Elastic Curve Determination based on the Optical Displacement Measurement” section), and \(\Delta f_{L}\) is the midspan displacement increment resulting from the indentation at the supports (see Fig. 2). The average modulus of elasticity for the load increment is then

Method C has a fundamental shortcoming. The evaluation of the experimental results is exclusively based on a single displacement value, the one at midspan. It is expected that the consideration of the entire elastic curve would yield a more reliable value of the average modulus of elasticity. This leads to Method D, which is based on the calculation of the theoretical elastic curve and its adjustment to the measured curve. Based on the x, z coordinate system shown in Fig. 2 and on the linearized differential equation of the elastic curve, equation (23), the solution presented in equation (24) is derived for the present problem.

The continuity conditions at midspan are automatically satisfied, and the boundary conditionsat the supports lead toallowing the determination of the midspan deflection \(w_{M} (0) = f_{M}\) and corresponding slope \(w^{\prime}_{M} (0)\). Then, using equation (24), the deflection at an arbitrary point x can be calculated and adjusted to the measured values by varying the modulus of elasticity. For a single deflection increment \(\Delta w_{M}\) at position x resulting from the force increment \(\Delta F\), this adjustment leads to

The moduli of elasticity obtained for different positions x are averaged over the beam’s span. In some submethods, a weighted average is calculated. When determining \(w_{M} (x)\), the influences of the indentation at the supports and of the shear deformation may be eliminated, as stated above.

All evaluation methods described thus far are based on displacement values, either directly on the locally measured values or on those calculated from a fitted continuous displacement function. An alternative approach is to differentiate the fitted continuous displacement function twice and to use the obtained curvature \(w^{\prime\prime}_{M} (x)\) for further data processing. In Method E, an axial strain increment at a certain position x and at a certain distance z from the cross section’s centroid is determined according to Bernoulli flexural theory by

The modulus of elasticity in the cross section at position x and within the considered load increment is then obtained by

The position x may be at midspan or at the strain maximum. It is also possible to average over an evaluation length l_e according to equation (30). The corresponding submethods (see Table 2) are explained below.

Method F is also based on the evaluation of the curvature, i.e., of the second derivative of the elastic curve. However, instead of relating a stress increment to a strain increment, the differential equation of the elastic curve, equation (23), is directly applied to relate a curvature increment \(\Delta w^{\prime\prime}_{M} \left( x \right)\) to a bending moment increment \(\Delta M\left( x \right)\). Within the load increment concerned, the modulus of elasticity averaged over an evaluation length l_e is obtained by

The evaluation length l_e may be the total span of the beam or only an inner part of it, symmetric with respect to midspan. In the latter case, perturbations from the low-curvature regions close to the supports may be eliminated.

Method G utilizes the equivalence between the external and internal work, as in Method C. However, the internal work U is calculated on the basis of the curvature and slope of the elastic curve rather than on the basis of the internal forces. Equivalent to equation (20), the following equation describes the equivalence between the external and internal work. The second term on the left-hand side contains the contribution of the shear deformation.

Replacing the internal forces by derivatives of the elastic curve usingyields the following expression of the average modulus of elasticity within the considered load increment.

In curvature-based methods, the indentation at the supports theoretically does not influence the determined modulus of elasticity. It must be considered, however, that the continuous displacement function to be differentiated twice is just an approximation. It is therefore advisable to deduct the contribution of the indentation, in some sub-methods also the contribution of the shear force, from the displacement function prior to differentiation and further processing, as explained in the “Elastic Curve Determination based on the Optical Displacement Measurement” section.

Table 2 gives an overview of the seven evaluation methods (A through G) and their submethods. For systematization and comprehensibility, all submethods are labeled by a combination of four characters, such as “A0Al”. The first letter indicates one of the seven evaluation methods, i.e., Method A through Method G. In the second position, the number (“0” through “4”) specifies the type of data used for retrieving the modulus of elasticity (see Table 2 for definitions). The fitting of a continuous function to the measured displacements (indicated by “2” in the second position) and the differentiation for obtaining a curvature function (indicated by “4” in the second position) are explained in the “Elastic Curve Determination based on the Optical Displacement Measurement” section. The number “3” in the second position applies only to Method G. There, the fitted displacement function is used for retrieving its midspan value, whereas the internal work is determined on the basis of the curvature and slope functions. In submethods A4**, the midspan strain is calculated from the midspan curvature (where “*” represents any character).

The character in the third position (“A”, “S”, “M”, or “C”) describes which influences on the displacements have been deducted from the measured values (see the “Elastic Curve Determination based on the Optical Displacement Measurement” section). In the case of “A”, “S”, and “M” in the third position, the displacement function, obtained after the corresponding type of elimination, is regarded as resulting from the bending moment only. Although this is incorrect for “A” (no falsifying influences eliminated) and “S” (only support indentation eliminated), the evaluation results may serve for comparisons of the individual evaluation methods (see the “Elimination of Falsifying Influences” section). The character “C” in the third position is used when the shear deformation is directly considered in the expression for the internal mechanical work, rather than by deducting its contribution from the displacement function, as done in the case of “M”.

The character at the fourth position (“l”, “e”, or “g”) specifies which part of the beam’s span is considered for retrieving the modulus of elasticity. In the case of “l” at the fourth position, only values acquired at midspan are used, i.e., at the position of maximum moment, and in the case of “e” at the position of maximum strain. The character “g” is used when input data along the total span of the beam or, in the case of Methods E and F, along a portion of the span are evaluated. The corresponding options for the evaluation length are expressed by the Suffixes “fu”, “ha”, or “th” (see footnotes in Table 2). In Methods D through G, the evaluation length was always equal to the total span. In Method F, the displacement function served as a weighting function for averaging along the evaluation length, whereas in Method D, two different types of weighting were applied (see Suffixes “wt” and “uw” specified in the footnotes of Table 2).

The range of the stress-strain curve used for the evaluation of the modulus of elasticity has also been varied (see first footnote in Table 2). Within this evaluation range, averaging over multiple load increments or, alternatively, fitting a straight line to the load–displacement curve was conducted. More explanation may be found in the “Evaluation Range of the Stress-Strain Curve” section.

It is possible to determine the modulus of elasticity of beam-like specimens with a nonuniform cross section by means of three-point bending tests and appropriate evaluation methods. It is strongly recommended to eliminate the falsifying influence of the support indentation from the results. This requires the measurement of the beam’s displacement at multiple points along its axis, not only at midspan.

In this study, several evaluation methods proved to be suitable for retrieving the average modulus of elasticity of the material from measured displacements. However, Method D is considered the most appropriate. It is based on the fitting of the elastic curve analytically determined by definite integrals to the measured deflections. In comparative evaluations of the experimental results, Method D proved to be less sensitive than the other methods to changes in the evaluation procedure. Neither the type of database, in particular the measurement point displacements (submethods D1**) or a fitted displacement function (submethods D2**), nor the weighting of the displacements had a substantial influence on the obtained modulus of elasticity. It is recommended, however, to use a fitted displacement function for the calculation since the influence of local fluctuations of the measured values is reduced in this way. In addition, measurement points located outside the beam’s span may also be used for the curve fitting.

As stated previously, the elimination of falsifying influences is critical, especially the elimination of support indentations. In this study, the proposed evaluation method yielded on average a 109.9% higher modulus of elasticity than the conventional determination, i.e., determination exclusively based on the midspan displacement (submethod A0Al).

Method C is also attractive for practical applications, in particular submethods C2Ml and C2Cl, which eliminate falsifying influences. It involves much less computational effort and leads to comparable results. This may be because the deflection maximum is, in most cases, not far off midspan, even for beams with a nonuniform cross section. Variation of the cross-sectional properties along the beam’s axis is also considered in Method C.

The evaluation method D2Mgwt was successfully used to determine the modulus of elasticity of human pelvic cortical bone. The complete results and their correlation with harvesting locations as well as with donor-specific and other data will be presented in a forthcoming publication.