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234  BIOMECHANICS OF THE HUMAN BODY

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                       TABLE 9.5  Power-Law Regressions Between Ultimate Stress s (in MPa) and Apparent Density r (in g/cm )
                       for Compressive Loading of Human Trabecular Bone Specimens from a Range of Anatomic Sites
                                                Cadavers                           s = ar b
                             Study         Number   Age, years  No. of specimens  a  b      r 2
                       Proximal tibia
                        Linde et al., 1989 151  9    59–82       121         34.2   1.56    0.79
                       Proximal femur
                        Lotz et al., 1990 131  4     25–82        49         25.0   1.80    0.93
                       Lumbar spine
                        Hansson et al., 1987 88  3   71–84       231         50.3   2.24    0.76
                        Mosekilde et al., 1987 78  42  15–87      40         24.9   1.80    0.83



                                       1.0
                                               Compression        Tension *


                                       0.8      *
                                     Yield Strain (%)  0.6  0.35  –0.62  0.67  –0.57





                                       0.4


                                       0.2


                                       0.0
                                            Vertebra  Proximal Tibia  Trochanter  Femoral Neck
                                                        Anatomic Site

                                   FIGURE 9.13 Mean yield strain per anatomic site in both compression and
                                   tension. Error bars indicate 1 standard deviation. Yield strain is only weakly
                                   dependent on apparent density for four of the groups, as indicated by the
                                   Pearson correlation coefficient r in the bar. Compressive yield strains are higher
                                   than tensile yield strains for each anatomic site. Intrasite scatter is on the order
                                   of one-tenth the mean values. (From Ref. 11.)


                         The advent of high-resolution finite-element modeling 94  has led to enormous progress in deter-
                       mining elastic stiffness matrices, multiaxial failure behavior, and as will be seen later, trabecular tis-
                       sue properties. Finite-element models of individual specimens, developed using microcomputed
                       tomography 95,96  and other types of microscopic imaging, 17,97  have been used to compute the full set
                       of elastic constants for specimens from multiple anatomic sites. Results indicate that trabecular bone
                       can be considered orthotropic 98,99  or, in some cases, transversely orthotropic. 100  Poisson’s ratios,
                       which are difficult to measure experimentally for trabecular bone, range from 0.03 to 0.60. 22,99
                         Given the complexity of in vivo loading conditions, there is a need to develop a multiaxial failure
                       criterion for trabecular bone. Results have been reported for bovine bone only. 101–103  These studies
                       indicate that the von Mises criterion does not work well and that expression of the criterion in terms
                       of strain (or nondimensional measures of stress divided by modulus) greatly simplifies the mathe-
                       matical form of the criterion since it eliminates the dependence of the criterion on specimen density.
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