Search

Older adults exhibit reductions in push-off power that are often attributed to deficits in plantarflexor force-generating capacity. However, growing evidence suggests that the foot may also contribute to push-off power during walking. Thus, age-related changes in foot structure and function may contribute to altered foot mechanics and ultimately reduced push-off power. The purpose of this paper was to quantify age-related differences in foot mechanical work during walking across a range of speeds and at a single fixed speed with varied demands for push-off power. 9 young and 10 older adults walked at 1.0, 1.2, and 1.4 m/s, and at 1.2 m/s with an aiding or impeding horizontal pulling force equal to 5% BW. We calculated foot work in Visual3D using a unified deformable foot model, accounting for contributions of structures distal to the hindfoot's center-of-mass. Older adults walked while performing less positive foot work and more negative net foot work (p 0.05). Further, we found that the effect of age on mechanical work performed by the foot and the ankle-foot complex increased with increased locomotor demand (p 0.05). Our findings suggest that during walking, age-related differences in foot mechanics may contribute to reduced push-off intensity via greater energy loss from distal foot structures, particularly during walking tasks with a greater demand for foot power generation. These findings are the first step in understanding the role of the foot in push-off power deficits in older adults and may serve as a roadmap for developing future low-cost mobility interventions.

This study investigated the stepping boundary – the force that can be resisted without stepping – for force-controlled perturbations of different durations. Twenty-two healthy young adults (19–37 years old) were instructed to try not to step in response to 86 different force/time combinations of forward waist-pulls. The forces at which 50% of subjects stepped (F50) were identified for each tested perturbation durations. Results showed that F50 decreased hyperbolically when the perturbation’s duration increased and converged toward a constant value (about 10% BW) for longer perturbations (over 1500 ms). The effect of perturbation duration was critical for the shortest perturbations (less than 1 s). In parallel, a simple function was proposed to estimate this stepping boundary. Considering the dynamics of a linear inverted pendulum + foot model and simple balance recovery reactions, we could express the maximum pulling force that can be withstood without stepping as a simple function of the perturbation duration. When used with values of the main model parameters determined experimentally, this function replicated adequately the experimental results. This study demonstrates for the first time that perturbation duration has a major influence on the outcomes of compliant perturbations such as force-controlled pulls. The stepping boundary corresponds to a constant perturbation force-duration product and is largely explained by only two parameters: the reaction time and the displacement of the center of pressure within the functional base of support. Future work should investigate pathological populations and additional parameters characterizing the perturbation time-profile such as the time derivative of the perturbation.

Biological composite materials, such as bone, tooth and nacre, are comprised of a mixture of nano-sized hard components (e.g. mineral platelets) and soft components (e.g. protein molecules). Their mechanical behaviour greatly depends on the protein–mineral interfaces. This paper investigates the effects of mineral surface nanostructures on the interfacial interaction and mechanical behaviour of protein–mineral nanocomposites. Interfacial shear between osteopontin (OPN) and hydroxyapatite (HA) mineral layers with surface nanostructures is investigated using the atomistic molecular dynamics (MD) simulations. The results indicate that the OPN residues can be attached to HA surfaces but the surface nanostructures greatly affect the interfacial interaction and mechanical behaviour. The HA layers with a higher number of nano-sized grooves (defects) increase the surface roughness but reduce the pulling force and energy dissipation.

Treatment of excessive hair growth is an important issue in both dermatological and cosmetic practice. In contrast to treatments with medication, most physical methods are treatments that focus on the hair follicle. To obtain insight in the failure behavior of the anchorage of hairs, hairs were extracted (in vitro) from pig skin at a speed of 0.1 mm/s, one at a time. The pulling force and tweezers displacement were recorded. The extracted hairs were classified with respect to the phase in the growing cycle: anagen (growing phase), telogen (resting phase) or other (catagen phase or unable to determine). The anagen hairs showed a different relation between the tweezers displacement and the pulling force than the telogen hairs. Moreover, the maximum force that could be applied before a hair was extracted proved to be lower for anagen hairs than for telogen hairs (0.36 N, 1.8 N, respectively). The extracted hair length, defined as the part of the hair that had been embedded in the skin which was extracted, was higher for anagen hairs than for telogen hairs (4.8 mm, 3.0 mm, respectively). Removing proximal skin tissue and the embedded parts of the anagen hair (root) resulted in a change of the extraction curves. The results indicate that two phenomena play a role in the anchorage of anagen hairs. We have proposed a model for the extraction of an anagen hair that has been based on these results: first the interface between hair and skin that is located around the inner root sheath (IRS) starts to fail, followed by failing of the hair itself in the region where the hair keratinizes.

RESULTS AND DISCUSSION Table 1 shows the results for typical 2 throwers. Their performances were almost the same (0.4%) although their body weights were quite different (24%). Throwing distance and initial velocities were similar in two throwers. However, maximum pulling forces per body weight were quite different. Therefore the relationship between the pulling force and body weight should be examined in detail. The hammer throwing motion can be compared with two-body problem in mechanics between a thrower’s body and a hammer head. Therefore, it can be considered that body and hammer head rotate each other around the common center of gravity of these two bodies. In this study, the body weight of thrower-B was larger than that of thrower-A about 24%. Then radius of gyration from the common center of gravity to hammer head in thrower-B was longer than in thrower-A. As the velocity of the hammer head at release were almost the same in two throwers, maximum pulling force of thrower-A was larger than that of thrower-B because the centrifugal force (= the maximum pulling force) was inversely proportional to the radius of gyration. Fig.1 shows relationship between throwing distance and maximum pulling force for all the throwers. Thrower's body weight was shown in frames. The multiple linear regression analysis was done by choosing MPF as dependent variable and throwing distance and body weight as independent variables. Figure 1: Relationship between throwing distance and maximum pulling force.