Response and movement times for tennis and tennis like movements were enhanced by the proper choice of knee angle during the preparatory stance phase
(Cotton and Denning, 1970; Yamamoto, 1996).
These alterations were associated with a higher generated ankle power at the end of the stance phase
and a higher generated hip power at the beginning of the stance phase
For the HNP, hip extensor stimulation was deactivated between 40 and 60 percent of the gait cycle at the end of the stance phase
when the hip was fully extended for both sides.
Fluid-controlled mechanisms for the stance phase
are also to be expected.
The purpose of the study was to examine the patterns and variability in sEMG activity of hip joint muscles, vertical ground reaction force (GRF), and hip joint angles during the stance phase
of walking in individuals with TFA with OFs.
In the stance phase
, knee control is required in the subphases of loading response (Figure 6(a)), midstance (Figure 6(b)), and late stance.
The first system to be introduced clinically for gait compensation was a mechanical structure that locked or limited joint movement during the stance phase
of gait, such as the ankle-foot orthosis (AFO), the knee-AFO (KAFO), or the hip-KAFO (HKAFO), depending on the specific joint weakness.
The required functionality of a transtibial prosthesis during the stance phase
of gait can be summarized as (1) providing early stance shock absorption during load acceptance, (2) adapting to the ground surface by plantar-flexing to a stable foot flat position, (3) providing close to normal shank kinematics during stance by replicating the loaded roll-over shape of the normal foot, and (4) contributing to push-off and a close to normal transition into swing phase.
To ensure identification of those peak pressures associated with shock absorption during loading response phase, we analyzed the magnitudes of peak pressures at each of the measurement sites during the first 40 percent of stance phase
The stance phase
on the nondisabled limb is prolonged, while on the spatial level, the lateral stability margin of stepping is increased on the side of the prosthetic limb by placing the foot farther outside, thereby making walking with a prosthesis more stable .
Therefore, a prosthetic ankle unit that increases ankle motion during stance phase
may produce different ankle-foot roll-over shape characteristics than the prosthetic foot alone.
A considerable effort has been made to dev elop and integrate a controllable knee mechanism in lower-limb bracing that supports the knee during the stance phase
of gait and allows for free movement during swing.