Technical noteShod wear and foot alignment in clinical gait analysis
Introduction
Ankle angle is often a key variable in clinical gait analysis. Dorsiflexion and plantar flexion are calculated as the angular rotation of the foot around the lateral axis of tibia [1]. Therefore, the ankle angle is affected by foot alignment in the sagittal plane. The conventional gait model describes the foot as a rod defined by a marker at the heel and dorsal surface of the foot [2], [3]. The assessors visually align these markers to the sole of the foot in the sagittal plane and parallel to the long axis of the foot in the coronal plane [3]. The aid of a striped transparent Perspex board may be used (Fig. 1A). However, visual alignment is a subjective and time consuming process as assessors often lay prone on the floor at foot height to minimise parallax error.
Software alignment is an alternative method when the patient can stand barefoot with flat feet, i.e. with the sole of the foot parallel to the ground. Software alignment adjusts the height of the heel marker to match the height of the forefoot marker above the ground [4]. This eliminates the need for sagittal plane alignment and only leaves coronal plane alignment during marker placement. In shod gait analysis, sagittal foot alignment within the shoe is more complex and shod studies may constrain shoe wear to a particular model or have cut outs to improve consistency and accuracy of marker placement [5], [6]. In a clinical setting, this approach is impractical and visual alignment is used.
Software alignment in shod analysis may still be possible if the patient can stand with their shoes flat on the ground and the change in shoe sole thickness across the length of the shoe is measured and entered as a parameter, sole delta (Plug-in-Gait, VICON, [4]). Measurement of sole delta is taken at the two major points of contact of the foot within the shoe (Fig. 1B), estimated to be at the metatarsal heads and the centre of the heel [7], [8]. However, this may introduce a small dorsiflexion bias since sole delta is applied to the heel marker rather than at the centre of the heel (Fig. 1C). Adjusting sole delta (sadj) to remove the bias requires a measure of the distance between the centre of the heel and the heel marker (dheel). Alternatively, the projection of the ankle joint centre on the sole of the foot may be used as a proxy for the position of the rear contact point.
The aim of this technical note was to quantify the magnitude of the bias and to evaluate the accuracy of the visual and software foot alignment methods during shod analysis. We also proposed and evaluated an adjusted software alignment method.
Section snippets
Materials and methods
Sole delta (s) is the height difference at the rear and front of the shoe (Fig. 1B). The adjusted sole delta (sadj) value is calculated for greater foot alignment accuracy using the principle of similar triangles (Fig. 1C):
Where dfoot is the distance between the heel and toe markers projected on the floor and dheel is the distance between the heel marker and rear contact point projected on the floor. The location of the rear contact point is a visual estimation. The
Results
The expected error for a given individual was graphed by holding constant and plotting the bias over a range of rear contact point () and sole delta (s) values. Fig. 2 provides an example of the expected error for average 6 year old (A) and adult (B) females.
Fig. 2 highlights that three factors exaggerate dorsiflexion angles: increased distance between the heel marker and the rear contact point, increased sole delta, and decreased foot length. As a result, careful analysis is
Discussion and conclusion
Our aim was to evaluate the accuracy of sagittal plane alignment during shod gait analysis. Our results show that visual and adjusted software alignments did not introduce a significant bias in ankle dorsiflexion angle, however standard software alignment did.
Our study assumed that ankle dorsiflexion angle was identical between the shoe and shoeless conditions. To verify this, we calculated AFO deformation during stance phase in gait using the model described in Ridgewell et al. [11]. Minimal
Acknowledgement
We would like to acknowledge Jessica Pascoe, Jill Rodda and Pam Thomason senior physiotherapists at the Hugh Williamson Gait Analysis Laboratory, for their help with data collection.
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