Contributions of muscle forces and toe-off kinematics to peak knee flexion during the swing phase of normal gait: an induced position analysis

Anderson, Frank C.; Goldberg, Saryn R.; Pandy, Marcus G.; Delp, Scott L.

doi:10.1016/j.jbiomech.2003.09.018

Cited by 109 publications

(99 citation statements)

References 25 publications

(41 reference statements)

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“…If we had analyzed a simpler model consisting of only the swing limb, in which the trajectory of the pelvis was prescribed, then gravity would have accelerated the knee toward extension during the extension phase. This explanation has been noted previously (Anderson et al, 2004).…”

Section: Discussionsupporting

confidence: 77%

“…For example, Mena et al (1981) analyzed a planar, three-segment model of the swing limb and showed that when the prescribed trajectory of the hip was exaggerated, the motions of the knee were abnormal. Anderson et al (2004) used a simulation to identify the contributions of muscles and toe-off kinematics to peak knee flexion during early swing, and reported that the net effect of stance-limb muscles, particularly the gluteus maximus and gluteus medius/minimus, was to oppose knee flexion. Wang et al (2005), using a torque-driven simulation, showed that reasonable stepping motions could be generated simply by controlling pelvis motion.…”

Section: Discussionmentioning

confidence: 99%

“…Determining how individual muscles contribute to knee motions is difficult because a muscle can accelerate joints it does not span and segments other than those to which it attaches (Zajac and Gordon, 1989;Zajac et al, 2002). For instance, several studies have shown that knee motions in early swing are influenced not only by muscles that cross the knee, but also by moments generated at other joints (Anderson et al, 2004;Kerrigan et al, 1998;Piazza and Delp, 1996).…”

Section: Introductionmentioning

confidence: 99%

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Muscular coordination of knee motion during the terminal-swing phase of normal gait

Arnold

Thelen

Schwartz

et al. 2007

Journal of Biomechanics

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Children with cerebral palsy often walk with diminished knee extension during the terminal swing phase, resulting in a troublesome "crouched" posture at initial contact and a shortened stride. Treatment of this gait abnormality is challenging because the factors that extend the knee during normal walking are not well understood, and because the potential of individual muscles to limit terminal-swing knee extension is unknown. This study analyzed a series of three-dimensional, muscle-driven dynamic simulations to quantify the angular accelerations of the knee induced by muscles and other factors during swing. Simulations were generated that reproduced the measured gait dynamics and muscle excitation patterns of six typically-developing children walking at self-10 selected speeds. The knee was accelerated toward extension in the simulations by velocity-related forces (i.e., Coriolis and centrifugal forces) and by a number of muscles, notably the vasti in mid-12 swing (passive), the hip extensors in terminal swing, and the stance-limb hip abductors, which accelerated the pelvis upward. Knee extension was slowed in terminal swing by the stance-limb hip flexors, which accelerated the pelvis backward. The hamstrings decelerated the forward motion of the swing-limb shank, but did not contribute substantially to angular motions of the knee. Based on these data, we hypothesize that the diminished knee extension in terminal swing exhibited by children with cerebral palsy may, in part, be caused by weak hip extensors or by impaired hip muscles on the stance limb that result in abnormal accelerations of the pelvis.

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Section: Discussionsupporting

confidence: 77%

Section: Discussionmentioning

confidence: 99%

Section: Introductionmentioning

confidence: 99%

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Muscular coordination of knee motion during the terminal-swing phase of normal gait

Arnold

Thelen

Schwartz

et al. 2007

Journal of Biomechanics

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“…특히, 뇌졸중 편마비 환자들은 운동하기에 충분한 힘을 생성하지 못하여 기능 적인 움직임에 제한을 받고 있다 (Fellows, Kaus, & Thilmann, 1994). 무릎강직 보행의 여러 가지 잠재적 원인들은 유각기 구 간 (Piazza & Delp, 1996;) 또 는 전유각기 동안 (Anderson, Goldberg, Pandy, & Delp, 2004;Reinbolt, Fox, Arnold, Ounpuu, & Delp, 2008;Van Der Krogt, et al, 2010), 대퇴사두근 중 특히 대퇴 직근의 과도한 활성화로 보고되고 있지만 편마비 (hemiplegia) 환자의 10% 정도는 무릎강직 보행 시 대퇴 사두근의 경직으로 보고하고 있다 (Waters, Garland, Perry, Habig & Slabaugh, 1979). 또 다른 잠재 원인은 비복근 의 약화 (Kerrigan, et al, 1991)나 발끝 걷기 (Kerrigan, Burke, Nieto, & Riley, 2001)로 야기된 추진력 감소로 보고하고 있다.…”

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Characteristics of the Compensation for Gait of the Induced Knee Stiffness in Normal Subjects

Woo¹

2013

Korean Journal of Sport Biomechanics

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The purposes of this study were investigated physical compensation for gait on induced knee stiffness in normal subjects. Ten subjects were participated in the experiment(age: 26.0±6.3 yrs, height: 175.5±5.3 cm, weight: 69.1±6.1 kg). The study method adopted 3D analysis with five cameras and ground reaction force with two force-plate. Induced knee stiffness level were classified as gait pattern on ROM of knee(free level, 30° restriction level, fix level). The results were as follows; In angular displacement of hip joint, left hip joint was the more extended in mid-stance on induced right knee stiffness. In angular displacement of knee joint, there was no physical compensation on induced right knee stiffness, but free knee level gait was more flexed in swing phase of right knee joint. In angular displacement of ankle joint, right ankle joint was the more dorsiflexed on induced right knee stiffness, and 30° restriction level and fix level gait were less plantarflexed in TO2. In trunk tilt, free and 30° restriction level gait was more backward tilt on induced right knee stiffness. In ROM of each joint, right knee joint was more larger and trunk tilt was more lower on induced right knee stiffness. In GRF, Fx was more bigger lateral force in free and 30° restriction level gait, and was more bigger medial force in fix level gait. Fy was more bigger propulsion force in free level gait, and was was more bigger braking force in 30° restriction level gait. Left braking force in 30° restriction level gait was more bigger. Fz was no significant.

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“…55 Previous research has shown that in persons with a transtibial (TT) or transfemoral (TF) amputation, significantly less power is generated during the A2 phase in the amputated leg compared with the ankle of an ablebodied person. 48,[56][57][58] Because the generation of energy of the ankle is decreased, persons with TT and TF amputation must adapt the motor strategies used for forward progression of the body, acceleration of the leg, and achievement of sufficient knee flexion during the swing phase.…”

Section: Introductionmentioning

confidence: 99%

Adapting to change : influence if a microprocessor-controlled prosthetic knee on gait adaptations

Prinsen¹

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Contributions of muscle forces and toe-off kinematics to peak knee flexion during the swing phase of normal gait: an induced position analysis

Cited by 109 publications

References 25 publications

Muscular coordination of knee motion during the terminal-swing phase of normal gait

Muscular coordination of knee motion during the terminal-swing phase of normal gait

Characteristics of the Compensation for Gait of the Induced Knee Stiffness in Normal Subjects

Adapting to change : influence if a microprocessor-controlled prosthetic knee on gait adaptations

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