Assessment methods in human locomotion often involve the description of normalised graphical profiles and/or the extraction of discrete variables. Whilst useful, these approaches may not represent the full complexity of gait data. Multivariate statistical methods, such as Principal Component Analysis (PCA) and Discriminant Function Analysis (DFA), have been adopted since they have the potential to overcome these data handling issues. The aim of the current study was to develop and optimise a specific machine learning algorithm for processing human locomotion data. Twenty participants ran at a self-selected speed across a 15m runway in barefoot and shod conditions. Ground reaction forces (BW) and kinematics were measured at 1000 Hz and 100 Hz, respectively from which joint angles (°), joint moments (N.m.kg-1) and joint powers (W.kg-1) for the hip, knee and ankle joints were calculated in all three anatomical planes. Using PCA and DFA, power spectra of the kinematic and kinetic variables were used as a training database for the development of a machine learning algorithm. All possible combinations of 10 out of 20 participants were explored to find the iteration of individuals that would optimise the machine learning algorithm. The results showed that the algorithm was able to successfully predict whether a participant ran shod or barefoot in 93.5% of cases. To the authors’ knowledge, this is the first study to optimise the development of a machine learning algorithm.
Citation: Bisele M, Bencsik M, Lewis MGC, Barnett CT (2017) Optimisation of a machine learning algorithm in human locomotion using principal component and discriminant function analyses. PLoS ONE 12(9): e0183990. https://doi.org/10.1371/journal.pone.0183990
Editor: Yih-Kuen Jan, University of Illinois at Urbana-Champaign, UNITED STATES
Received: March 2, 2017; Accepted: August 15, 2017; Published: September 8, 2017
Copyright: © 2017 Bisele et al. This is an open access article distributed under the terms of the Creative Commons Attribution License, which permits unrestricted use, distribution, and reproduction in any medium, provided the original author and source are credited.
Data Availability: Data and code from the current study is located here: https://github.com/sci3bencsm/brood_cycle_matlab_code/tree/master. Due to ethical restrictions, participant data including participant identifiers, are not available without restriction. However, all interested researchers can request and obtain the raw .qtm files by contacting the corresponding author (email@example.com). The contact information for the ethics authority enforcing compliance is SST.Ethics@ntu.ac.uk.
Funding: The authors would like to thank Nottingham Trent University for funding Maria Bisele's Ph.D studentship.
Competing interests: The authors have declared that no competing interests exist.
Abbreviations: DF, Discriminant Function; DFA, Discriminant Function Analysis; FN, False negative; FP, False positive; FFT, Fast Fourier Transform; GRF, Ground reaction forces; HS, Heel strike; LDA, Linear Discriminant Analysis; PCs, Principal Components; PCA, Principal Component Analysis; SEN, Sensitivity; SPM, Spatial Parameter Mapping; SPC, Specificity; TO, Toe off; TN, True negative; TP, True positive; TPR, True positive rate
Gait analysis attempts to describe the characteristics of human locomotion [1, 2]. From a clinical perspective, it is often used to assess the effects of conditions on gait, such as cerebral palsy , and lower limb amputation , and has led to improved diagnoses, enhanced treatment recommendations and enabled the evaluation of treatment outcomes [2, 5]. During gait analysis, data acquisition tools such as motion capture systems, force plates and electromyography are used to assess the biomechanical and physiological characteristics of gait. Kinematic and kinetic data, such as joint angles and ground reaction forces (GRF) are often reported, however subsequent analysis, such as inverse dynamic calculations, can be conducted to assess further aspects of gait such as joint moments and powers [6, 7]. These variables are often presented in temporal waveforms or time-series throughout the gait cycle [7, 8].
As data acquisition tools used to collect gait data and the subsequent procedures for calculating novel variables continuously advance, they provide an ever increasing volume of data [7, 8]. This presents a hindrance to clinicians and researchers when trying to interpret this data and/or forming clinically useful information . A widely used approach to analyse and interpret movement data is through the description of graphical profiles of temporal waveforms and reinforcement of this information through the use of discrete variable extraction [8, 9]. Research has also attempted to summarise waveforms of gait data using indices and summary scores [10–13]. However, the interpretation of graphical profiles may be researcher-dependent, meaning results may differ between patients and/or laboratories. Similarly, the choice of data collected is dependent upon equipment availability, and researchers’ selection of variables. This can be an issue in a clinical environment as variables assessed in a patient may not be the cause of a problem, thus results may show no significant difference with the primary problem remaining undetected and untreated. Therefore, data collection, analysis and interpretation are somewhat subjective and prone to researcher bias.
Gait data is also governed by a set of well-defined characteristics namely 1. high dimensionality, 2. time-dependence, 3. high variability, and 4. nonlinear correlations residing between the variables independently measured [14, 15]. During data processing, these characteristics are important to consider, however, while previously mentioned methods such as gait indices, summary scores and the extraction of discrete variables may be adequate to provide enough information in some investigations, in others they may not be suitable since temporal information is lost . For example, measurements are often repeated for a given individual in order to account for intra-subject variations. Such variations may result in specific discrete variables that take place at different timings of the measurements for each repeat. These would be neglected in methods where the time-series of the data is ignored/removed. In instances where the time-series of the data is accounted for, careful phasing of the waveforms is required to access the information relating to the absolute gait cycle. Also, certain features reside in the shape of the gait time-series, e.g. in pathological gait [8, 17] where distortions result from pathology and thus are not picked up in methods using purely scalar quantities. Recent studies introduced the use of Spatial Parameter Mapping (SPM) technique considering entire gait waveform thus preserving temporal characteristics of data during statistical analysis [18, 19]. In addition, usually, there will not be fixed linear relationships between variables and each variable may affect or be affected by one or more other variables differently [14, 17]. Therefore, the problem of high dimensionality will often prompt the researcher to identify the variable(s), also known as informative features that change the most as the most important/relevant. However, changes in this variable may reflect the summation of multiple smaller changes in other variables, some of which are sometimes unmeasured, which scale it and infer it is the underlying cause for the difference in gait. For example, when reporting net muscle moments, the individual muscle forces, which drive these moments, are not routinely reported. Hence, there is a need for effective quantification methods to reduce dimensionality sets and establish relationships between variables while retaining temporal information.
Principal Component Analysis (PCA) is a well-established multivariate analysis used for data reduction and sometimes classification, first applied to human locomotion by Deluzio et al. . Typically, it has been used in lieu of statistical comparisons to classify data while maintaining the variance in the structure of the original data. It has had many applications in the comparison of able-bodied gait and pathological gaits such as amputee gait [20–23], osteoarthritis gait [16, 24] and Parkinsonian gait [25–27]. Linear PCA is a strong algorithm that is able to detect patterns in certain structures, without user supervision. Therefore it deduces informative features for classification from the structures without direction, lead purely by the variance within the data  and it seeks the most efficient representation of the original database using Principal Components (PCs). Discriminating factors of interest to the user may go undetected if they are of small magnitude, and/or if they end up being shared between too many Principal Components. Thus, to identify subtle discrimination features that exist between experimental groups, a supervised algorithm such as Discriminant Functional Analysis (DFA) is required. The multivariate statistical method of DFA seeks out linear combinations of the input variables, the PCA scores in our case, in order to best discriminate between groups and therefore highlight differences in the detailed structure of the data where PCA only discriminates between gross structures . Together the combination of unsupervised and supervised numerical search algorithms create a powerful machine learning algorithm, which refers to the ability of a device to independently conduct discrimination on a database without the input of a researcher [22, 29]. In a clinical setting, a machine learning algorithm can provide an objective method to conduct analyses and thus eliminating researcher bias when assessing gait data . Previous studies have used machine learning algorithms to identify gait differences between young and older adults [30–33], males and females , pathological and non-pathological gait [22, 24, 29, 35, 36] and high discrimination results have been obtained such as 91.7% or 95.8% between older and younger individuals [30, 31, 36], between males and females with 98–100%, and 100% between pathological and non-pathological gait . However, in less challenging environments, where differences between distinct groups (e.g. males vs. females) are more easily detected, previous studies have not considered how the quality of data used to train the machine learning algorithm, can deteriorate the quality of the outcome. Different individuals will exploit features in different manners and will not necessarily train the computer in the way that will work best for other individuals that the automated system will analyse later in its predictive stage. At the training stage, it is therefore important to supply the algorithm with a training database that has been carefully selected for its aptitude to reveal the best, highly generic, discriminating features. Furthermore, the PCA algorithm outputs information in a new space defined by a set of axes necessarily orthogonal to each other, causing features of interest too often reside within more than one PCA score. How successful the DFA algorithm will be in pulling out the important discriminating features will, therefore, depend on the extent to which these features have blurred out onto multiple PCA axes.
Therefore, the specific individuals that have been chosen and used to develop the training database for the machine learning algorithm will strongly affect its predictive abilities. Using increasingly larger database for the training stage is of no help, as the feature blurring into multiple PCA scores will only become worse, which we will attempt to address in the current study.
It is, however, possible to work with a smaller sample and try to optimise predictive accuracy by implementing an iterative process where the individuals contributing to the training stage are systematically permuted. In our current study, we find hidden groupings using all possible permutations for resampling our database. We develop, demonstrate and evaluate such a resampling procedure for processing human locomotion data, using power spectra of temporal waveforms as an efficient compromise to keep temporal information without the need to either phase the data or compute user-defined discrete variables.
A convenience sample of twenty recreationally active participants (14 males and 6 females; age 24±4 years; height 1.75±0.086m; mass 72.0±8.5 kg) were drawn from the University community. These individuals who had no lower limb pathologies, and were free of injury during the time of the study, provided informed consent to participate. Ethical approval was granted by the Nottingham Trent University Ethics Committee (Humans).
The study investigated participants under two different experimental conditions; running with (shod) and without shoes (barefoot) with trial conditions being counterbalanced between participants.
Participants completed all activities wearing their own shorts and running shoes. To measure kinematic data, 36 spherical 14mm, retro-reflective markers were placed directly onto the skin or clothing using bi-adhesive tape. Markers were attached bilaterally and used to define trunk  and lower limb segments .
Participants warmed-up with a five minute run on a treadmill at self-selected speed. After the warm-up, participants proceeded to the experimental trials, which required them to run at self-selected speed along a 15m runway making contact with a force plate. This process was repeated until five successful trials (force plate contacts) had been recorded for each condition. Once completed, the process was repeated for the second condition of experimental trials. Ground reaction force (GRF) was measured at 1000Hz using one floor-mounted strain gauge force plate (AMTI, Watertown, MA, USA) and kinematics were measured at 100 Hz using a nine-camera motion capture system (Qualisys, Gothenburg, SE).
The raw marker trajectories and force data were exported as .c3d files and processed in Visual 3D v5 (C Motion, Inc., Germantown, MD, USA). Kinematic data were interpolated using a cubic-spline algorithm with kinematic and GRF data being subsequently filtered using 4th order, zero-lag Butterworth low-pass filters with 6Hz and 30Hz cut-off frequencies respectively. Medial and lateral landmarks defined anatomical frames from which segment co-ordinate systems were defined following the right-hand rule . A flexion-extension, abduction-adduction and longitudinal cardan rotation sequence was used to define the order of rotations to calculate joint kinematics. Gait events of heel strike (HS) and toe off (TO) were determined using GRF data and data all were normalized to 100% gait cycle.
Joint angles (°), joint moments (N.m.kg-1) and joint powers (W.kg-1) for the hip, knee and ankle joints, as well as the GRF (multiples of body weight; BW) were computed using Visual 3D (C-Motion, Inc, Germantown, USA). Results were reported in all three anatomical planes, thus thirty temporal waveforms were reported for a single trial, which was considered to start when the right limb hits the force plate at heel strike and finished at the consecutive heel strike on the same limb. Processed data were exported from Visual3D in .c3d files and individual signals from the .c3d files were imported to MATLAB® R2013a (MathWorks Inc., MA, USA).
Machine learning algorithm
In our study, we optimise a specific machine learning algorithm that would distinguish between two experimental conditions of barefoot and shod running. The development of the machine learning algorithm, using PCA and DFA was done in three stages of dimensionality reduction, informative feature extraction and classification. Prior to conducting PCA or DFA, the data were linearly interpolated to the same digital length to allow the power spectrum (modulus of FFT) to be computed for all variables. This allowed us to remove the absolute phasing of kinetic and kinematic waveforms which would affect the discrimination process since any error in the phase correction required to obtain the absolute gait cycle would be spuriously identified as a discriminating feature between the trials, compromising the outcome of the machine learning algorithm. Apart from the absolute phasing of different frequency components of the data, the rest of the temporal information of the waveforms is kept intact in the power spectra.
An input matrix M was established which contained the power spectra of the kinetic and kinematic waveforms extracted from each experimental trial. The matrix was ordered as follows: for each subject five trials of each condition existed (twenty subjects resulted in 200 trials) and every trial was made of 30 columns with 50 row vectors, where each column represented a variable and each row vector represented the frequency of the 3D coordinate measure of the variable. The input matrix M, originally 3D with 200 x 30 x 50 points, was rearranged to be 2D, with 200 x 1500 points, in order to undertake the PCA on a collection of 200 trials each comprising of 1500 points.
First, the data were summarised using PCA and thus high dimensionality was reduced from the original 1500 points (for each trial) to 8, 10 or 12 points. Our numerical analysis was made immune to overfitting artefacts originating from the over-exploitation of small details, by choosing the highest explored rank (12th) well below the one still carrying information (20th) (see supplementary material S3 Fig). Principal Component Analysis (PCA) is an orthogonal transformation turning dependent variables of a multivariate database to a small set of independent new variables or Principal Components Z, which are used to represent the variance observed in the original variables X . Components Z make up the columns of the correlation/covariance matrix (covariance in the current study) and are eigenvectors, also referred to as loading vectors. The Principal Components (PCs) are ordered in terms of decreasing variance such that the majority of variation in the data can usually be described by the first couple of PCs and therefore the remaining PCs can be ignored reducing the dimensionality of the data which commonly reduces the noise in the input data X. However, depending on the research question this may not hold true and medium or lower ordered PCs may provide the necessary information rather than higher ordered PCs .
Using the reduced database, DFA was further applied to a selection of PC scores (up to the eighth, up the tenth and up to the twelfth score), in order to identify generic discriminating features between the two experimental conditions, and cluster the data as required by the goal of the study (shod versus barefoot). Discriminant Function Analysis (DFA), also known as Linear Discriminant Analysis (LDA), is a statistical analysis which works to attain the maximum discrimination between classes. To achieve maximum separation, the ratio of inter-class and intra-class variance for any given database is computed. This results in linear class boundaries thus grouping the various class clusters in a given subspace .
All previous stages were combined to develop the machine learning algorithm which is also referred to as a predictive algorithm, when applied to data that did not contribute to the learning stage. To optimise its development, the process was divided into two stages of training and predictive (see Fig 1). During the training stage, data from ten participants was used to direct the search for generic features and identify which of these provided the greatest discrimination between the two experimental conditions. During the predictive stage, data of the remaining ten participants that had not contributed to the training of the machine learning algorithm were used to assess whether it could correctly assign data to the group with the same generic features.
To identify which ten participants would best train the algorithm and result in the best overall classification, allowing the most predominate, generic discriminating features to be identified between the two experimental conditions, all possible combinations of 10 out of 20 participants were explored (see Fig 2); a total of 184,756 iterations were identified and assessed therefore optimising the algorithm. An error rate was computed for each individual iteration (see Fig 3) and the one yielding the combination of participants with the lowest error rate revealed the strongest generic discriminating features.
An iteration consisted of a different combination of 10 participants out of 20 for each the training and predicted database. The error is the percentage of variables that end up in the wrong category (shod or barefoot).
The error rate was calculated as follows: each trial was projected onto a two-dimensional DF space, yielding a set of two DF scores. In this space, the coordinates of the two centroids were calculated, and for each trial, the Euclidean distances to both centroids were further calculated. The ratio of these two distances was used to assess whether the trial ended up in the ‘shod’ or ‘barefoot’ category, with a value of 1 corresponding to the threshold dictating the membership. The trials ending up with the incorrect membership were expressed as a percentage error rate, over all the 200 trials (20 individuals each undertaking 5 shod and 5 barefoot runs).
Classification evaluation and performance measure
A confusion matrix has been used to evaluate the performance of the machine learning algorithm. In a two classes problem, positive and negative, as it is the case in the current study, there are four possible outcomes of classification, namely true positive (TP), false negative (FN), true negative (TN), and false positive (FP). In the current study, positive instances relate to shod running trials and negative instances relate to barefoot running trials. The sensitivity and specificity (see Eqs 1 and 2) respectively refer to positive and negative instances which have been correctly identified.
The outcome of all possible iterations, as shown in the histogram of Fig 3, indicates that the error rates of trials which could not be correctly classified ranged from 6.5% to 47.5% and the majority of iteration were identified to have an error rate of 22.5%. This clearly demonstrates how much the algorithm can be helped by careful selection of the training database. As previously mentioned the lowest error rate indicated the highest predictive ability, and thus the iteration corresponding to 6.5% was used as the input for the optimised machine learning algorithm.
Increasing the rank of the PCA scores fed to the DFA algorithm from 8 to 12 did not improve the outcome, and the data we show was obtained using 10 PCA scores. Using the entire database as the training database for the discrimination exercise yielded an error rate of 24% as seen in Fig 4.
The optimum iteration was further used to identify the most discriminating features between the two experimental groups of barefoot and shod running using DFA as illustrated in Fig 5. The different bar charts correspond to different DF curves integrated over all spectral frequencies (full frequency-resolved DF curves are shown in the supplementary material S1 Fig), where each bar represents a variable. The fact that they are dissimilar justifies the benefit of undertaking the discrimination in two dimensions rather than one. The length of each bar emphasises the weight factors of individual kinetic and kinematic variables (averaged over all frequencies). Long and short bars had a high and a low contribution to the discrimination process, respectively. Since the analysis was conducted for thirty variables, there are thirty bars for each integrated DF curve. Variables corresponding to individual bars have been ordered, in decreasing order of contribution, and displayed in supplementary material S2 Fig. High contribution variables included ankle angle and power in the transverse plane, ankle angle in the sagittal plane and ankle moment in the coronal plane whereas low contribution variables corresponded to knee angle and moment in coronal plane, and medial-lateral and the anterior/posterior GRFs. An example of a highly discriminating, and a low discriminating variable is shown in Fig 6.
Abbreviations are knee (KNE), ankle (ANK), angle (ANG), moment (MOM), power (POW), anterior-posterior (AP), medial-lateral (ML) and vertical (VERT).
Dashed lines represent the instance in the gait cycle that the illustrations are taken from.
The outcome of the PCA search (Fig 7) alone results in severely overlapping clouds, demonstrating the fact that the discrimination that was sought for is not residing in the main deviations found in the data, illustrating the challenging nature of the conditions of interest. Instead, the discrimination required (shod/barefoot) resides in subtle details of the spectra, necessitating the second stage numerical search, DFA, to be applied to the data after reduction of PCA. We also undertook visual examination of both the time courses and the spectra of our ‘barefoot’ and ‘shod’ conditions, and no clear common discriminating patterns emerged in spite of careful inspection.
Each dot represents a trial of a participant and since each participant has conducted 10 trials (5 shod and 5 barefoot) and there was a total of 10 participants the figure illustrates the discrimination of 100 trials.
The quality of the discrimination obtained with our optimised DFA is illustrated in Figs 8, 9 and 10. The quality in discrimination is evidenced by the minimal amount of overlap between the two conditions; two well-discriminated groups will not occupy the same space. The outcome of the training database alone, used to develop the algorithm is shown in Fig 8. Once developed the predictive ability of the algorithm was assessed as illustrated in Fig 9. It can be seen that even though there is a slightly greater scatter in the predictive outcome it does not compromise the quality of discrimination: when the software has been given a chance to be trained with the ideal training data base, Figs 8 and 9 suggest that the computer is further able to correctly discriminate those individuals that have a rather ‘unique’ or ‘rare’ way to run shod and barefoot. Combining both the outcomes from the training database and the predictive data (Fig 10), it is clear that both experimental conditions of barefoot and shod running are clustered in separate clouds which are shifted to the left and right side respectively, with minimal overlap between the two clouds and a slight vertical slant between the two centroids. The overlap is representative of 6.5% of the trials which could not be correctly discriminated (5% and 8% overlap respectively when considering the predicted data only, and the training data only). The discrimination occurs mostly horizontally with a slight angle indicating that the discrimination is mostly achieved through the DF score 1. Projection onto a higher dimensional space did not yield any significant discrimination. The classification evaluation reinforces these results and shows that sensitivity i.e. true positives (shod and truly identified as shod) would be correctly identified in 90% of cases and specificity i.e. true negatives (barefoot and truly identified as barefoot) would be correctly identified in 91%.
The scatter slightly greater than in Fig 3, but an excellent reliability in terms of correct discrimination.
In our study, we optimised the predictive accuracy of a specific machine learning algorithm to distinguish between two experimental conditions of barefoot and shod running. This was done by implementing an iterative process, where the individuals contributing to the training stage were systematically permuted, using an iterative process to explore all possible iterations of 10 participants out of 20 in order to identify generic discriminating features between the two experimental conditions. The optimised algorithm yielded a high discrimination accuracy of 93.5%, typically 17.5% higher than when using a standard analysis.
We achieved high improvement in the software’s performance by using half of our data for training, and the other half for prediction. In instances where the machine learning algorithm is facing the challenge of a mixture of highly ‘generic’ and highly ‘singular’ trials in its training database, we suggest that by homing onto the highly generic individuals, at the stage of training the computer, substantial improvements may be achieved over the entire group, including the highly ‘singular’ individuals. The relatively small group size of our study prevents us from estimating the extent to which accidental spurious information may also have been harvested in the process but limiting ourselves to only 10 PCA scores severely limits the likelihood of such phenomena.
An interesting question is whether it might be possible, in any study similar to ours, to identify the best group size to be used when optimising the training. Unfortunately, the extent to which specific volunteers provide a generic enough feature and the extent to which features of interest become spread between several PCA scores will depend on the specific study undertaken so that no general method can be recommended.
For very large studies, one way forward is perhaps to start by following our optimisation procedure with the same group sizes for training and predicting, and then further refine the collection of ‘ideal’ individuals by swapping one of the ten individuals with a new one to see whether improved discrimination could be obtained. This way the collection of ‘ideal’ generic individuals could gradually be further improved. Using a larger sample then presented in the current study would provide the option to validate the machine learning algorithm since individuals who did not contribute to the training and prediction stages could be used. In such large studies, it is also possible to somewhat reduce the effect of a second possible source of overfitting artefact, that coming from (possibly high magnitude) information accidentally helping the clustering and therefore biasing it. It is possible to quantitate and minimise such overfitting artefacts  by splitting the individuals who did not contribute to the training into two groups respectively called ‘validation’ and ‘test’ sets. The trained algorithm can be optimised on the ‘validation’ set only, and those iterations yielding a performance much lower on the ‘test’ set can be deemed as suffering from overfitting and dismissed. Unfortunately, such method is not reliable on the relatively small group size of our study, and the high performance of the optimised outcome of our work suggests that we would have reached the same result if we had implemented it, as both ‘validation’ and ‘test’ sets would have benefitted from a similar performance. Our method systematically tests the algorithm’s performance on data that has not contributed (or biased) the learning of the computer and is therefore inherently minimising overfitting artefacts.
Previous studies have achieved high discrimination results however the quality of data used as a training database for the machine learning algorithms have not been considered which in turn affects the reliability of their predictive outcome [22, 24, 29–35]. Factors affecting the reliability of an algorithm include data from a very limited number of participants since classification results can be high, however, they are not necessarily generic . Unlike other published work our discrimination (see Fig 5) is free from artefacts resulting from training the computer with trials carrying rather rare or unique information. Moreover, the context of the experimental protocol influences the results of a discrimination since some experimental groups or conditions are easier to distinguish than others, in particular in instances where the two groups to be discriminated are necessarily formed from different individuals, e.g. young vs. older individuals, normal vs. pathological gait and males vs. females [24, 29–35]. Thus in the development of the current machine learning algorithm, the same heterogeneous sample of participants repeated both experimental conditions. This creates a more challenging environment, when compared to having clearly discrete homogenous groups e.g. healthy vs. pathology, whose data is independent of one another. Therefore, the outcome of the algorithm presented in the current study was more likely to reflect the ability of the algorithm rather than experimental group differences.
Developing a machine learning algorithm using scalar quantities extracted from the waveforms of kinetic and kinematic variables [29, 30, 32, 33] could result in the dismissal of important temporal data, thus power spectra of full waveforms have been employed [24, 35, 36] since each individual feature provides complementary information . In the current study, the training database used to conduct a numerical search using PCA and DFA included the spectra of thirty full temporal waveforms of kinetic and kinematic variables for each trial thus the entire waveform of a variable was taken into consideration.
In previous studies, ankle kinematic and kinetic variables such as plantar flexion [43,44] have been shown to differ between barefoot and shod running gait [43–45]. Studies have also reported limited differences between barefoot and shod runners in GRFs [46, 47]. Although not the specific focus of the current study, the results of the current study confirmed these findings, suggesting that these variables represent the key differences between shod and barefoot running gait. However, unlike previous research, the choice of variables selected in our study as an input to the machine learning algorithm were generic biomechanical features, and not specifically selected, thus reducing researcher bias and reflecting the true ability of the algorithm to identify the generic discriminating features.
The development of the machine learning algorithm described has many important applications in both clinical and research settings. In clinical settings, it allows for a more comprehensive and consistent assessment process across patients by utilising a wider range of data whilst simultaneously eliminating researcher bias. Furthermore, since all discriminating features are identified, in both a clinical and research setting, it will prevent important factors being neglected and ensure accurate and reliable diagnosis. This will enable analysis methods to be more objective, consistent and reliable across institutions.
A specific machine learning algorithm, using composite PCA and DFA, was developed using power spectra of temporal waveforms to successfully identify barefoot and shod running gait. The predictive accuracy of the algorithm was optimised in a challenging environment by implementing an iterative process. All discriminating features between the two experimental groups were identified and a strong machine learning algorithm was developed with a 93.5% accuracy in discriminating between conditions. This method can be implemented, to find informative features when the sample size is small and heterogeneous, as common in gait analysis.
S1 Fig. Full DFA spectra.
The right-hand side vertical axis is valid for variables 1 to 3, whilst the left-hand side one is valid for all remaining variables. Note that frequencies above 150 Hz do not contribute to the discrimination and the high importance of ultra-low frequencies. In some instances (e.g. variables No. 15 and 24), frequencies as high as 90 Hz contribute to the discrimination. In the main manuscript, the data shown in Fig 4. was obtained by integrating the absolute values of the spectra shown here, over all frequencies. The data shown in Fig 10. is obtained by cross-correlating the spectra shown here with the spectra coming from the raw variables (cross correlating any raw variable spectrum respectively with DF spectra 1 and 2 provide the corresponding DF score 1 and 2).
S2 Fig. Thirty variables in decreasing order of contribution to the discrimination between barefoot and shod runners.
We would like to give a great thanks to Professor Roy Goodacre, Manchester University for providing us with the MATLAB® DFA routine, written by B.K. Alsberg, NTNU, Norway (made available at https://github.com/sci3bencsm/brood_cycle_matlab_code/tree/master).
- 1. Kirtley C. Clinical gait analysis: theory and practice. Elsevier Health Sciences; 2006.
- 2. Levine D, Richards J, Whittle MW. Whittle's Gait Analysis. Elsevier Health Sciences; 2012 Jul 13.
- 3. Novacheck TF, Trost JP, Sohrweide S. Examination of the child with cerebral palsy. Orthopedic Clinics of North America. 2010 Oct;41(4):469–88. pmid:20868879
- 4. Barnett C, Vanicek N, Polman R, Hancock A, Brown B, Smith L et al. Kinematic gait adaptations in unilateral transtibial amputees during rehabilitation. Prosthetics and Orthotics International. 2009 Jun;33(2):135–47. pmid:19367517
- 5. Hamill J, Gorton G, Masso P. Clinical Biomechanics: Contributions to the Medical Treatment of Physical Abnormalities. Kinesiology Review. 2012 Feb;1(1):17–23.
- 6. Winter DA. Biomechanics and motor control of human movement. John Wiley & Sons; 2009 Oct 12.
- 7. Robertson G, Caldwell G, Hamill J, Kamen G, Whittlesey S. Research methods in biomechanics, 2E. Human Kinetics; 2013 Sep 25.
- 8. Deluzio KJ, Wyss UP, Zee B, Costigan PA, Serbie C. Principal component models of knee kinematics and kinetics: normal vs. pathological gait patterns. Human Movement Science. 1997 Apr 30;16(2):201–17.
- 9. Deluzio KJ, Wyss UP, Costigan PA, Sorbie C, Zee B. Gait assessment in unicompartmental knee arthroplasty patients: Principal component modelling of gait waveforms and clinical status. Human Movement Science. 1999 Oct 31;18(5):701–11.
- 10. Schutte LM, Narayanan U, Stout JL, Selber P, Gage JR, Schwartz MH. An index for quantifying deviations from normal gait. Gait & Posture. 2000 Feb 29;11(1):25–31.
- 11. Cretual A, Bervet K, Ballaz L. Gillette gait index in adults. Gait & Posture. 2010 Jul 31;32(3):307–10.
- 12. Barton GJ, Hawken MB, Scott MA, Schwartz MH. Movement Deviation Profile: A measure of distance from normality using a self-organizing neural network. Human Movement Science. 2012 Apr 30;31(2):284–94. pmid:20728953
- 13. Baker R, McGinley JL, Schwartz MH, Beynon S, Rozumalski A, Graham HK et al. The gait profile score and movement analysis profile. Gait & Posture. 2009 Oct 31;30(3):265–9.
- 14. Chau T. A review of analytical techniques for gait data. Part 1: fuzzy, statistical and fractal methods. Gait & Posture. 2001 Feb 28;13(1):49–66.
- 15. Chau T. A review of analytical techniques for gait data. Part 2: neural network and wavelet methods. Gait & Posture. 2001 Apr 30;13(2):102–20.
- 16. Deluzio KJ, Astephen JL. Biomechanical features of gait waveform data associated with knee osteoarthritis: an application of principal component analysis. Gait & Posture. 2007 Jan 31;25(1):86–93.
- 17. Daffertshofer A, Lamoth CJ, Meijer OG, Beek PJ. PCA in studying coordination and variability: a tutorial. Clinical Biomechanics. 2004 May 31;19(4):415–28. pmid:15109763
- 18. Ardestani MM, Ferrigno C, Moazen M, Wimmer MA. From normal to fast walking: Impact of cadence and stride length on lower extremity joint moments. Gait & Posture. 2016 May 31;46:118–25.
- 19. Ardestani MM, Wimmer MA. Can a linear combination of gait principal component vectors identify hip OA stages?. Journal of Biomechanics. 2016 Jul 5;49(10):2023–30. pmid:27255606
- 20. Mouchnino L, Mille ML, Martin N, Baroni G, Cincera M, Bardot A et al. Behavioral outcomes following below-knee amputation in the coordination between balance and leg movement. Gait & Posture. 2006 Aug 31;24(1):4–13.
- 21. Gao F, Zhang F, Huang H. Investigation of sit-to-stand and stand-to-sit in an above knee amputee. InEngineering in Medicine and Biology Society, EMBC, 2011 Annual International Conference of the IEEE 2011 Aug 30 (pp. 7340–7343). IEEE.
- 22. LeMoyne R, Mastroianni T, Hessel A, Nishikawa K. Implementation of machine learning for classifying prosthesis type through conventional gait analysis. In Engineering in Medicine and Biology Society (EMBC), 2015 37th Annual International Conference of the IEEE 2015 Aug 25 (pp. 202–205). IEEE.
- 23. Soares DP, de Castro MP, Mendes EA, Machado L. Principal component analysis in ground reaction forces and center of pressure gait waveforms of people with transfemoral amputation. Prosthetics and Orthotics International. 2016 Dec;40(6):729–38. pmid:26598512
- 24. Kobsar D, Osis ST, Hettinga BA, Ferber R. Gait biomechanics and patient-reported function as predictors of response to a hip strengthening exercise intervention in patients with knee osteoarthritis. PloS One. 2015 Oct 7;10(10):e0139923. pmid:26444426
- 25. Dillmann U, Holzhoffer C, Johann Y, Bechtel S, Gräber S, Massing C et al. Principal Component Analysis of gait in Parkinson's disease: relevance of gait velocity. Gait & Posture. 2014 Mar 31;39(3):882–7.
- 26. Jeon HS, Han J, Yi WJ, Jeon B, Park KS. Classification of Parkinson gait and normal gait using spatial-temporal image of plantar pressure. In Engineering in Medicine and Biology Society, 2008. EMBS 2008. 30th Annual International Conference of the IEEE 2008 Aug 20 (pp. 4672–4675). IEEE.
- 27. Muniz AM, Liu H, Lyons KE, Pahwa R, Liu W, Nadal J. Quantitative evaluation of the effects of subthalamic stimulation on gait in Parkinson's disease patients using principal component analysis. International Journal of Neuroscience. 2010 Aug 1;120(9):609–16. pmid:20707636
- 28. von Tscharner V, Enders H, Maurer C. Subspace identification and classification of healthy human gait. PLoS One. 2013 Jul 8;8(7):e65063. pmid:23861736
- 29. Alaqtash M, Sarkodie-Gyan T, Yu H, Fuentes O, Brower R, Abdelgawad A. Automatic classification of pathological gait patterns using ground reaction forces and machine learning algorithms. InEngineering in Medicine and Biology Society, EMBC, 2011 Annual International Conference of the IEEE 2011 Aug 30 (pp. 453–457). IEEE.
- 30. Begg R, Kamruzzaman J. A machine learning approach for automated recognition of movement patterns using basic, kinetic and kinematic gait data. Journal of Biomechanics. 2005 Mar 31;38(3):401–8. pmid:15652537
- 31. Eskofier BM, Federolf P, Kugler PF, Nigg BM. Marker-based classification of young—elderly gait pattern differences via direct PCA feature extraction and SVMs. Computer Methods in Biomechanics and Biomedical Engineering. 2013 Apr 1;16(4):435–42. pmid:22149087
- 32. Wu J, Wang J, Liu L. Feature extraction via KPCA for classification of gait patterns. Human Movement Science. 2007 Jun 30;26(3):393–411. pmid:17509708
- 33. Chan H, Yang M, Zheng H, Wang H, Sterritt R, McClean S et al. Machine learning and statistical approaches to assessing gait patterns of younger and older healthy adults climbing stairs. InNatural Computation (ICNC), 2011 Seventh International Conference on 2011 Jul 26 (Vol. 1, pp. 588–592). IEEE.
- 34. Phinyomark A, Osis ST, Hettinga BA, Kobsar D, Ferber R. Gender differences in gait kinematics for patients with knee osteoarthritis. BMC Musculoskeletal Disorders. 2016 Apr 12;17(1):157.
- 35. Federolf P, Tecante K, Nigg B. A holistic approach to study the temporal variability in gait. Journal of Biomechanics. 2012 Apr 30;45(7):1127–32. pmid:22387120
- 36. Reid SM, Graham RB, Costigan PA. Differentiation of young and older adult stair climbing gait using principal component analysis. Gait & Posture. 2010 Feb 28;31(2):197–203.
- 37. Leardini A, Biagi F, Merlo A, Belvedere C, Benedetti MG. Multi-segment trunk kinematics during locomotion and elementary exercises. Clinical Biomechanics. 2011 Jul 31;26(6):562–71. pmid:21419535
- 38. Cappozzo A, Catani F, Della Croce U, Leardini A. Position and orientation in space of bones during movement: anatomical frame definition and determination. Clinical Biomechanics. 1995 Jun 30;10(4):171–8. pmid:11415549
- 39. Phinyomark A, Hettinga BA, Osis S, Ferber R. Do intermediate-and higher-order principal components contain useful information to detect subtle changes in lower extremity biomechanics during running?. Human Movement Science. 2015 Dec 31;44:91–101. pmid:26340274
- 40. Sugavaneswaran L, Umapathy K, Krishnan S. Ambiguity domain-based identification of altered gait pattern in ALS disorder. Journal of Neural Engineering. 2012 Jun 25;9(4):046004. pmid:22732899
- 41. Lever J, Krzywinski M, Altman N. Points of significance: Model selection and overfitting. Nature Methods. 2016 Sep 1;13(9):703–4.
- 42. Ali S, Shah M. Human action recognition in videos using kinematic features and multiple instance learning. IEEE Transactions on Pattern Analysis and Machine Intelligence. 2010 Feb;32(2):288–303. pmid:20075459
- 43. Lieberman DE, Venkadesan M, Werbel WA, Daoud AI, D’Andrea S, Davis IS et al. Foot strike patterns and collision forces in habitually barefoot versus shod runners. Nature. 2010 Jan 28;463(7280):531–5. pmid:20111000
- 44. Williams DB III, Green DH, Wurzinger B. Changes in lower extremity movement and power absorption during forefoot striking and barefoot running. International Journal of Sports Physical Therapy. 2012 Oct;7(5):525. pmid:23091785
- 45. Braunstein B, Arampatzis A, Eysel P, Brüggemann GP. Footwear affects the gearing at the ankle and knee joints during running. Journal of Biomechanics. 2010 Aug 10;43(11):2120–5. pmid:20462583
- 46. Divert C, Mornieux G, Baur H, Mayer F, Belli A. Mechanical comparison of barefoot and shod running. International Journal of Sports Medicine. 2005 Sep;26(07):593–8.
- 47. Kerrigan DC, Franz JR, Keenan GS, Dicharry J, Della Croce U, Wilder RP. The effect of running shoes on lower extremity joint torques. PM&R. 2009 Dec 31;1(12):1058–63.