Multibody Computational Biomechanical Model of the Upper Body

Dubowsky, Sarah R.

doi:10.1115/detc2005-84809

Cited by 2 publications

(1 citation statement)

References 67 publications

(131 reference statements)

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“…To provide further insight into muscle forces and joint torques during wheelchair propulsion, biomechanical models have been developed, including: a finite element model developed by van der Helm [21]; a model of glenohumeral joint kinematics by Cooper et al [23,24]; generalised limb segment models proposed by Dumas et al [25,26]; and a generalised model of the upper limb developed by Pennestrì et al [28]. Furthermore, commercially available multibody computational models have been applied with the objective of realistically accommodating the complexity of the shoulder, for example [27]. These models provide high resolution of three dimensional biomechanics, including dynamic effects.…”

Section: Introductionmentioning

confidence: 99%

A fundamental model of quasi-static wheelchair biomechanics

Leary¹,

Gruijters²,

Mazur³

et al. 2012

Medical Engineering & Physics

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The performance of a wheelchair system is a function of user anatomy, including arm segment lengths and muscle parameters, and wheelchair geometry, in particular, seat position relative to the wheel hub. To quantify performance, researchers have proposed a number of predictive models. In particular, the model proposed by Richter is extremely useful for providing initial analysis as it is simple to apply and provides insight into the peak and transient joint torques required to achieve a given angular velocity. The work presented in this paper identifies and corrects a critical error; specifically that the Richter model incorrectly predicts that shoulder torque is due to an anteflexing muscle moment. This identified error was confirmed analytically, graphically and numerically. The authors have developed a corrected, fundamental model which identifies that the shoulder anteflexes only in the first half of the push phase and retroflexes in the second half. The fundamental model has been extended by the authors to obtain novel data on joint and net power as a function of push progress. These outcomes indicate that shoulder power is positive in the first half of the push phase (concentrically contracting anteflexors) and negative in the second half (eccentrically contracting retroflexors). As the eccentric contraction introduces adverse negative power, these considerations are essential when optimising wheelchair design in terms of the user's musculoskeletal system. The proposed fundamental model was applied to assess the effect of vertical seat position on joint torques and power. Increasing the seat height increases the peak positive (concentric) shoulder and elbow torques while reducing the associated (eccentric) peak negative torque. Furthermore, the transition from positive to negative shoulder torque (as well as from positive to negative power) occurs later in the push phase with increasing seat height. These outcomes will aid in the optimisation of manual wheelchair propulsion biomechanics by minimising adverse negative muscle power, and allow joint torques to be manipulated as required to minimise injury or aid in rehabilitation.

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