joint or segment angle at 1 time point. In particular, frontal plane pelvis–frontal plane thigh and frontal plane thigh–transverse plane shank coordination patterns affect hip and knee motion. In addition, frontal plane hip–transverse plane hip coordination patterns illustrate coupled hip motions during
Eric Foch and Clare E. Milner
Yumeng Li, Rumit S. Kakar, Marika A. Walker, Li Guan and Kathy J. Simpson
Interest in intersegmental coordination during locomotion (eg, between the low back and pelvis or between foot segments) has continued to increase. 1 – 6 Investigating intersegmental coordination of different types of locomotor movements can provide more insight into the processes used by the
James J. Hannigan, Louis R. Osternig and Li-Shan Chou
alter hip and pelvis kinematics during running, 12 , 17 , 18 possibly even increasing hip adduction range of motion. 16 Thus, decreased pain after rehabilitation does not appear to be a result of changing hip kinematics during running. To better understand these findings, some studies have attempted
Hans Kainz, Hoa X. Hoang, Chris Stockton, Roslyn R. Boyd, David G. Lloyd and Christopher P. Carty
Queensland Human Research Ethics Committee. Data Collection MRIs of the pelvis and lower limbs were collected using a 1.5T magnetic resonance scanner (MAGNETOM Avanto, Siemens, Berlin/Munic, Germany) with a modified 3D PD SPACE sequence (slice thickness 1.1 mm, slice increments 1.1 mm, voxel size 0
Rasool Bagheri, Ismail Ebrahimi Takamjani, Mohammad R. Pourahmadi, Elham Jannati, Sayyed H. Fazeli, Rozita Hedayati and Mahmood Akbari
rigid coordination variability in the transverse plane 3 , 8 (meaning that there was a decreased SD of continuous relative phase between trunk and pelvis during repeated trials) 9 – 11 for the movement of the pelvis and trunk in participants with NCLBP compared with healthy controls. Therefore
Danielle L. Gyemi, Charles Kahelin, Nicole C. George and David M. Andrews
15 extremities, respectively. To date, comparable equations and tissue mass data are not yet available for the head, neck, trunk, and pelvis. Therefore, the purpose of this study was to generate and validate (using DXA) tissue mass prediction equations for the head, neck, trunk, and pelvis
Aiko Sakurai, Kengo Harato, Yutaro Morishige, Shu Kobayashi, Yasuo Niki and Takeo Nagura
noncontact ACL injury during landing tasks. Moreover, the model-based image-matching method revealed that rapid valgus and internal rotational development immediately after IC was associated with ACL injury. 12 – 14 Clinically, trunk and pelvis controls are linked to lower-extremity valgus based on more
David W. Keeley, Gretchen D. Oliver, Christopher P. Dougherty and Michael R. Torry
The purpose of this study was to better understand how lower body kinematics relate to peak glenohumeral compressive force and develop a regression model accounting for variability in peak glenohumeral compressive force. Data were collected for 34 pitchers. Average peak glenohumeral compressive force was 1.72% ± 33% body weight (1334.9 N ± 257.5). Correlation coefficients revealed 5 kinematic variables correlated to peak glenohumeral compressive force (P < .01, α = .025). Regression models indicated 78.5% of the variance in peak glenohumeral compressive force (R2 = .785, P < .01) was explained by stride length, lateral pelvis flexion at maximum external rotation, and axial pelvis rotation velocity at release. These results indicate peak glenohumeral compressive force increases with a combination of decreased stride length, increased pelvic tilt at maximum external rotation toward the throwing arm side, and increased pelvis axial rotation velocity at release. Thus, it may be possible to decrease peak glenohumeral compressive force by optimizing the movements of the lower body while pitching. Focus should be on both training and conditioning the lower extremity in an effort to increase stride length, increase pelvis tilt toward the glove hand side at maximum external rotation, and decrease pelvis axial rotation at release.
Richard W. Bohannon and Jason Smutnick
Motion of the femur and pelvis during hip flexion has been examined previously, but principally in the sagittal plane and during nonfunctional activities. In this study we examined femoral elevation in the sagittal plane and pelvic rotation in the sagittal and frontal planes while subjects flexed their hips to ascend single steps. Fourteen subjects ascended single steps of 4 different heights leading with each lower limb. Motion of the lead femur and pelvis during the flexion phase of step ascent was tracked using an infrared motion capture system. Depending on step height and lead limb, step ascent involved elevation of the femur (mean 47.2° to 89.6°) and rotation of the pelvis in both the sagittal plane (tilting: mean 2.6° to 9.7°) and frontal plane (listing: mean 4.2° to 11.9°). Along with maximum femoral elevation, maximum pelvic rotation increased significantly (p < .001) with step height. Femoral elevation and pelvic rotation during the flexion phase of step ascent were synergistic (r = .852–.999). Practitioners should consider pelvic rotation in addition to femoral motion when observing individuals’ ascent of steps.
Yoichi Iino and Takeji Kojima
This study investigated the validity of the top-down approach of inverse dynamics analysis in fast and large rotational movements of the trunk about three orthogonal axes of the pelvis for nine male collegiate students. The maximum angles of the upper trunk relative to the pelvis were approximately 47°, 49°, 32°, and 55° for lateral bending, flexion, extension, and axial rotation, respectively, with maximum angular velocities of 209°/s, 201°/s, 145°/s, and 288°/s, respectively. The pelvic moments about the axes during the movements were determined using the top-down and bottom-up approaches of inverse dynamics and compared between the two approaches. Three body segment inertial parameter sets were estimated using anthropometric data sets (Ae et al., Biomechanism 11, 1992; De Leva, J Biomech, 1996; Dumas et al., J Biomech, 2007). The root-mean-square errors of the moments and the absolute errors of the peaks of the moments were generally smaller than 10 N·m. The results suggest that the pelvic moment in motions involving fast and large trunk movements can be determined with a certain level of validity using the top-down approach in which the trunk is modeled as two or three rigid-link segments.