Mechanical behaviour of femoral bones in bending loading

Structural properties of fourth-generation composite femurs and tibias

“…For the exceptions, tibia flexural rigidity with the anterior surface in tension and femur compressive longitudinal strain at the second lowest strain gage location, the third-and fourth-generation average results were within 5% of each other. All measurements were taken by the same author in separate studies using identical methodology; the natural bone values measured previously by the author were in line with those reported by other researchers (Cristofolini and Viceconti, 2000;Cristofolini et al, 1996;Crowninshield et al, 1980;Diegel et al, 1989;Martens et al, 1980Martens et al, , 1986McBeath et al, 1980;Motoshima, 1960;Oh and Harris, 1978;Otani et al, 1993a, b;Papini et al, 2007;Stromsoe et al, 1995). Natural tibia axial stiffness results were not reported, because of unacceptably high setup variability indicating exceptional difficulty in obtaining reproducible bone alignment (Heiner and Brown, 2003); this complication was also reported by Cristofolini and Viceconti (2000).…”

Modifying landing mat material properties may decrease peak contact forces but increase forefoot forces in gymnastics landings

“…Each segment was made of two parts connected by a rigid joint so that moments could be calculated in the middle of the link. Using a twopart link to calculate bending moment is a simple method to determine the magnitude of the loading on the skeletal structure and can be related to the fracture failure of bones from invitro tests (Martens et al, 1986). However, live bone is normally stronger than in vitro bone specimens and also has the advantage that muscle and other soft tissue surround it.…”

The influence of simulation model complexity on the estimation of internal loading in gymnastics landings

“…As vault landings are known to be strenuous and can lead to pain and injury in trained gymnasts, it would seem likely that the loading would approach the maximum seen in average samples. Martens et al (1986) found in vitro femoral failure near 400 Nm whereas for Model One maximum bending moments ranged from 40 Nm to 224 Nm and in Model Three ranged from 260 Nm to 363 Nm, suggesting that the Model Three values were of the correct magnitude. As mentioned earlier this 2D model cannot account for all the complexities of in vivo 3D loadings from multiple muscles and other passive tissues.…”