Abstract:During quiet standing the human 'inverted pendulum' sways irregularly. In previous work where subjects balanced a real inverted pendulum, we investigated what contribution the intrinsic mechanical ankle stiffness makes to achieve stability. Using the results of a plausible model, we suggested that intrinsic ankle stiffness is inadequate for providing stability. Here, using a piezoelectric translator we applied small, unobtrusive mechanical perturbations to the foot while the subject was standing freely. These … Show more
“…During quiet standing, measurement of low intrinsic ankle stiffness (Loram & Lakie, 2002a), analysis of ballistic character of sways (Loram & Lakie, 2002b) and investigations of balance in an analogous task using a weak spring (Lakie, Caplan et al, 2003) provide increasing evidence that intermittent ballistic-like adjustments in muscle length (Loram & Lakie, 2002b) It is important to note that, although MG activity with the unstable shoe did not differ from barefoot measurements after 8 weeks of training in the experimental group, venous return did not decrease when compared to measurements made before the training period (Figure 3). Moreover, measurements made with the unstable test shoe after training revealed significantly higher venous return than barefoot measurements.…”
Purpose: To quantify the effect of unstable shoe wearing on muscle activity and haemodynamic response during standing.Methods: Thirty volunteers were divided into 2 groups: the experimental group wore an unstable shoe for 8 weeks, while the control group used a conventional shoe for the same period. Muscle activity of the medial gastrocnemius, tibialis anterior, rectus femoris and biceps femoris and venous circulation were assessed in quiet standing with the unstable shoe and barefoot.Results: In the first measurement there was an increase in medial gastrocnemius activity in all volunteers while wearing the unstable shoe. On the other hand, after wearing the unstable shoe for eight weeks these differences were not verified. Venous return increased in subjects wearing the unstable shoe before and after training.
Conclusions:The unstable shoe produced changes in electromyographic characteristics which were advantageous for venous circulation even after training accommodation by the neuromuscular system.
“…During quiet standing, measurement of low intrinsic ankle stiffness (Loram & Lakie, 2002a), analysis of ballistic character of sways (Loram & Lakie, 2002b) and investigations of balance in an analogous task using a weak spring (Lakie, Caplan et al, 2003) provide increasing evidence that intermittent ballistic-like adjustments in muscle length (Loram & Lakie, 2002b) It is important to note that, although MG activity with the unstable shoe did not differ from barefoot measurements after 8 weeks of training in the experimental group, venous return did not decrease when compared to measurements made before the training period (Figure 3). Moreover, measurements made with the unstable test shoe after training revealed significantly higher venous return than barefoot measurements.…”
Purpose: To quantify the effect of unstable shoe wearing on muscle activity and haemodynamic response during standing.Methods: Thirty volunteers were divided into 2 groups: the experimental group wore an unstable shoe for 8 weeks, while the control group used a conventional shoe for the same period. Muscle activity of the medial gastrocnemius, tibialis anterior, rectus femoris and biceps femoris and venous circulation were assessed in quiet standing with the unstable shoe and barefoot.Results: In the first measurement there was an increase in medial gastrocnemius activity in all volunteers while wearing the unstable shoe. On the other hand, after wearing the unstable shoe for eight weeks these differences were not verified. Venous return increased in subjects wearing the unstable shoe before and after training.
Conclusions:The unstable shoe produced changes in electromyographic characteristics which were advantageous for venous circulation even after training accommodation by the neuromuscular system.
“…Such passive stiffness acts similar to an "elastic" opposed to the torque of gravitational force, which has the tendency to cause a forward fall of the body. Although the estimative of the contribution of the restoring torque due to the passive stiffness varies widely in the literature, it is estimated that this torque ranges about 65% to 90% from the magnitude of the gravitational torque 7,8 . Therefore, more than half of the torque responsible for maintaining our erect posture would be generated by a purely passive component, independent of the direct participation of the nervous system.…”
“…Maintaining upright balance is controlled primarily by the calf muscle that counteracts the destabilizing effect of gravity (Johansson et al 1988). Recent reports indicate that passive stiffness and open loop mechanisms contribute to the generation of the muscle activity required for stance control (Loram and Lakie 2002) which depends on a coordinated effort of the sensory systems (visual, vestibular, and proprioceptive systems). Deficits in these systems result in impaired balance control.…”
Older individuals have impaired balance control, particularly those that are frail and/or have sensory deprivations. Obese individuals show faster body sway during upright stance than normal weight individuals, suggesting that they also have difficulty controlling balance even if they do not have the same sensory issues as the older people. Therefore, the objective of this study was to examine if obesity is associated to a decreased balance control in older women. Postural sway of normal weight (n 015, age070.8±5.5 years; BMI022.2±1.9 kg/m 2 ), overweight (n 015, age 071.7 ± 4.3 years; BMI 027.3 ± 1.3 kg/m 2 ), and obese (n015, age071.1±4.3 years; BMI033.1±3.4 kg/m 2 ) women was measured with a force platform for normal quiet stance lasting for 30 s in opened and closed eyes conditions. The obese group oscillated at a faster speed than the normal weight group (vision 0.99 ± 0.29 cm/s vs. 0.70 ± 0.16 cm/s, p<0.01; no vision 1.43± 0.50 cm/s vs. 0.87±0.23 cm/s, p<0.01). The obese group exhibited greater range in both axes without vision compared to the normal weight group (p<0.05). When observing sway density parameters, the obese group also spent less time in stability zones (2 mm radius area in which the center of pressure is relatively stable), and the distance between these stability zones are greater than the normal weight group in both visual conditions (p< 0.01 and p<0.05, respectively). Obesity clearly affects postural control in older women. Our results suggest that obesity has a negative impact on the capacity of older woman to adequately use proprioceptive information for posture control. As postural instability or balance control deficits are identified as a risk factor for falling, our results also suggest that obesity in older women could be considered as another potential contributing factor for falling.
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