Introduction
Impedance control has been used in prosthetic legs and exoskeletons to provide soft interactions between users and these devices. This soft interaction can elimate injury of users and also can prevent damage of hardware. Despite these advantages, implementing the impedance control include mannually tunning process which is time comsuming. One reason is that there is no good reference of how large the impedance parameters should be. Quasi-stiffness is usually used as the starting point, however it does not represent the real-stiffness that exists in joints.
In this project, we identify the impedance parameters of human leg joints (hip, knee, and ankle) from perturbed walking data. Similar to the step strategy identification, we turn the identification problems into trajectory optimization problems by using closed-loop identification method.
Method
Impedance control is defined in the following equation, which has virtual spring-damper property when reaching the target position.
begin{center} $T = K_p*(theta_{tar} - theta) + K_d*(0 -dot{theta})$ end{center}
where $T$ is the torque generated by the impedance controller; $K_p$, $K_d$, and $theta_{tar}$ are three impedance control parameters: proportional gains, derivative gains, and target joint position; $theta$ and $dot{theta}$ are the current joint position and joint velocity.\
A pilot study have been done to identify ankle joint impedance parameters from 10 seconds walking data. In the pilot study, two sets impedance parameters were identified from two trials walking data of two subjects. For one data trial, only one set impedance parameters ($K_p, K_d, theta_{tar}$) is used to control ankle joint among entire gait cycles including both stance and swing phases. The identified impedance parameters are shown in Table ref{tab:impedance_results}. Fits between identified trajectories and experiment data are shown in Figure ref{fig:impedance_fit}.