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Boundary conditions of the specimens greatly affected the results in terms of maximum pullout force, dissipated energy, and strength degradation.
Maximum pullout force was recorded.
The pullout strength was calculated by dividing the maximum pullout force by the interface contact area using the following formula: pullout strength (N/mm) = maximum pullout force (N /interface contact area (mm).
The differences of maximum pullout force among the 3 groups reached statistical significance (p <0.001) (Table 2).
No significant correlation was observed between the sum of the two level scores and maximum pullout force (Spearman's rho rs = -0.17, p = 0.94).
The maximum pullout force of the expandable device unexpanded was significantly greater than of the common screw (2333.49 N vs. 1827.38 N, respectively, p =0.006).
Similar(48)
While expandable pedicle screws produced maximum pullout forces less than or comparable to standard screws, they required a higher amount of energy to be fully removed from both models.
Maximum pullout forces and the tunnel lengths measured by micro-CT were 39.3 ± 13.3 N and 5.4 ± 0.7 mm, respectively, in the OMCS group, and 29.2 ± 7.6 N and 5.2 ± 0.7 mm, respectively, in the control group.
Maximum pullout forces in the thoracic spine occurred with 1.0 cc of bone cement augmentation (186% over the nonaugmented control) and in the lumbar with 1.5 cc of cement (264% over the nonaugmented control).
The peak force recorded during the pullout test was defined as the maximum pullout strength for comparison.
ROM, maximum insertion torque, and maximum pullout strength were presented by mean and standard deviation.
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