Target leg ankle power was derived from kinematic and kinetic data and calculated using inverse dynamics (Visual3D Version 6, C-Motion, Germantown, MD). Ankle power in the sagittal plane was identified as the product of ankle joint moment and angular velocity47 (link). The second peak of ankle power, A2, was calculated for each subject. Muscle Synergy Analysis (MSA) was performed using data derived from a minimum of ten but up to twenty gait cycles. Gait cycles including or immediately following either TMS or Estim events were disregarded for the MSA analysis. Raw EMG data were gain-corrected, converted to millivolts, demeaned, and filtered using a fourth-order zero-lag Butterworth bandpass filter (10–450 Hz). To perform MSA, EMG data were rectified and smoothed using a low-pass, fourth-order zero phase-lag Butterworth filter with a cutoff frequency of 7 Hz divided by the participant’s average stride time. Data were also time interpolated using force plate-derived gait events to obtain 101 samples per cycle15 (link).
Visual3d version 6
Manufactured by C-Motion
Sourced in United States
Visual3D Version 6 is a software application for biomechanical analysis and modeling. It provides tools for processing and visualizing motion capture data from various sources.
Automatically generated - may contain errors
Lab products found in correlation
4 protocols using visual3d version 6
1
Inverse Dynamics for Ankle Power
2
Kinetic Analysis of Lower Extremity Biomechanics
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Lower extremities’ kinetic data were collected at 100 Hz using a 3D motion capture system equipped with eight infrared cameras (Vicon Motion Analysis, United Kingdom) by tracking 18 infrared-reflective balls (reflective markers) of 14 mm diameter. Ground reaction force data were sampled at 1000 Hz using a 3D Kistler force measuring platform (model: 9287B, 90 cm × 60 cm×10 cm, Kistler, Inc., Switzerland). The plug-in gait was modeled using Visual3D (Version 6, C-Motion, Inc., United States) to calculate joint kinetics.
The following kinetic data were analyzed: ground reaction force (GRF, including vertical GRF [vGRF], medial GRF [mGRF], and lateral GRF [lGRF]), time to peak GRF (T_GRF, including time to peak vertical GRF [T_vGRF], time to peak medial GRF [T_mGRF], and time to peak lateral GRF [T_lGRF]), loading rate (LR), joint torque in the sagittal plane and the frontal plane, hip joint vertical length variation (ΔL), lower extremity stiffness (Kleg), and ankle stiffness. LR was calculated using Eq.1 . Kleg was calculated using Eq. 2 .
The following kinetic data were analyzed: ground reaction force (GRF, including vertical GRF [vGRF], medial GRF [mGRF], and lateral GRF [lGRF]), time to peak GRF (T_GRF, including time to peak vertical GRF [T_vGRF], time to peak medial GRF [T_mGRF], and time to peak lateral GRF [T_lGRF]), loading rate (LR), joint torque in the sagittal plane and the frontal plane, hip joint vertical length variation (ΔL), lower extremity stiffness (Kleg), and ankle stiffness. LR was calculated using Eq.
3
Kinematic Modeling Approach Comparison
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All data were processed using Visual 3D version 6 (C-Motion, Inc.). Kinematic and force plate data were filtered at 18 Hz using a zero-lag 4 th order low-pass Butterworth filter following residual analysis (Yu et al., 1999) . Three IK models were created from the same conditioned data, the only difference between models being the magnitude of the joint constraints applied (Table 2). All trials were processed using each of the three models described in Table 2. Model IK3 allowed 3DoF at each joint; flexion/extension, abduction/adduction and internal/external rotation with no translation permitted. Model IK6 allowed 6DoF without joint constraints; flexion/extension, abduction/adduction, internal/external rotation, medial/lateral translation, anterior/posterior translation and inferior/superior translation. Model IK6Constrained also allowed 6DoF but with specified joint translation constraints derived from the literature (Section 2.2.1).
4
Biomechanical Analysis of Jump-Landing Kinematics
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The kinematic and force plate data were filtered using a fourth-order zero-lag Butterworth digital filter at cut-off frequencies of 6 Hz and 40 Hz, respectively. The cut-off frequency was determined by the residual analysis technique (Winter, 2005) . A three-dimensional model was constructed using Visual3D version 6 (C-Motion Inc., USA). The average of three successful trials in each direction for each limb was analysed. The landing phase was identified from the initial contact to 300 ms after initial contact. Knee and hip joint kinematics were calculated based on the cardan sequence of XYZ, equivalent to the joint coordinate system proposed by Grood and Suntay (1983) . Knee-hip angle-angle plots, knee velocity-angle plots, knee flexion excursion, and knee angular velocity at initial contact and at peak VGRF were reported. Knee flexion excursion was calculated from an angular displacement from an initial contact to peak knee flexion during landing phase.
Statistical analysis was performed using SPSS version 17. Repeated-measure ANOVA (2 × 4, side × jump-landing direction) were used to determine the effect of limb jump-landing direction and knee side. In addition, post hoc pairwise comparisons were performed to compare the landing directions. The statistical significance was set at an alpha level of 0.05.
Statistical analysis was performed using SPSS version 17. Repeated-measure ANOVA (2 × 4, side × jump-landing direction) were used to determine the effect of limb jump-landing direction and knee side. In addition, post hoc pairwise comparisons were performed to compare the landing directions. The statistical significance was set at an alpha level of 0.05.
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