http://orcid.org/0000-0003-0497-7356
Figures
Abstract
Running-related overuse injuries can result from a combination of various intrinsic (e.g., gait biomechanics) and extrinsic (e.g., running surface) risk factors. However, it is unknown how changes in environmental weather conditions affect running gait biomechanical patterns since these data cannot be collected in a laboratory setting. Therefore, the purpose of this study was to develop a classification model based on subject-specific changes in biomechanical running patterns across two different environmental weather conditions using data obtained from wearable sensors in real-world environments. Running gait data were recorded during winter and spring sessions, with recorded average air temperatures of -10° C and +6° C, respectively. Classification was performed based on measurements of pelvic drop, ground contact time, braking, vertical oscillation of pelvis, pelvic rotation, and cadence obtained from 66,370 strides (~11,000/runner) from a group of recreational runners. A non-linear and ensemble machine learning algorithm, random forest (RF), was used to classify and compute a heuristic for determining the importance of each variable in the prediction model. To validate the developed subject-specific model, two cross-validation methods (one-against-another and partitioning datasets) were used to obtain experimental mean classification accuracies of 87.18% and 95.42%, respectively, indicating an excellent discriminatory ability of the RF-based model. Additionally, the ranked order of variable importance differed across the individual runners. The results from the RF-based machine-learning algorithm demonstrates that processing gait biomechanical signals from a single wearable sensor can successfully detect changes to an individual’s running patterns based on data obtained in real-world environments.
Citation: Ahamed NU, Kobsar D, Benson L, Clermont C, Kohrs R, Osis ST, et al. (2018) Using wearable sensors to classify subject-specific running biomechanical gait patterns based on changes in environmental weather conditions. PLoS ONE 13(9): e0203839. https://doi.org/10.1371/journal.pone.0203839
Editor: Yih-Kuen Jan, University of Illinois at Urbana-Champaign, UNITED STATES
Received: May 8, 2018; Accepted: August 28, 2018; Published: September 18, 2018
Copyright: © 2018 Ahamed 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: Relevant data are included with the submission, any additional data (e.g., remaining 5 runners data) will be available upon request from the Running Injury Clinic and University of Calgary Institutional Data Access / Ethics Committee (CHREB) by contacting Dr. Stacey A. Page, chair of CHREB at omb@ucalgary.ca.
Funding: This study was partially funded by the Natural Sciences and Engineering Research Council of Canada (NSERC: Discovery Grant 1028495, Accelerator Award 1030390, and Idea-2 Innovation Awared I2IPJ 493875-16), a University of Calgary Eyes High Postdoctoral Research award, and a Strategic Research Grant from the Vice-President (Research) at the University of Calgary. The funders had no role in study design, data collection and analysis, decision to publish, or preparation of the manuscript.
Competing interests: The authors have declared that no competing interests exist.
Introduction
Running is one of the most common recreational activities around the world but despite its popularity, each year approximately 50% of runners experience a running-related musculoskeletal injury [1–3]. The etiology of overuse running injuries is multifactorial, and can result from the interaction of many extrinsic factors, such as environmental conditions, running surface, footwear, and weekly training mileage, as well as intrinsic risk factors such as age, foot strike pattern, and gait biomechanics [1–4]. Prolonged exposure to these intrinsic and extrinsic risk factors may lead to overuse running injury [5]. One risk factor that has received very little attention in the literature is whether gait biomechanical patterns change as a result of environmental weather conditions.
Previous investigations of injury risk, based on ambient temperature, have suggested that tissue damage may occur due to a lack of proper warm up. For example, Milgrom et al. reported an increased risk of Achilles paratendinitis among infantry recruits in winter conditions, as compared to summer [6]. On the other hand, cold weather has been shown to reduce shoe-surface traction, resulting in a reduced risk of acute knee and ankle injuries among football players [7, 8]. Only a handful of studies have investigated the effect of environmental weather conditions on running performance, but none have investigated whether gait biomechanics change as a result of environmental weather. For example, Ely et al., [9] reported a progressive reduction in marathon performance as temperatures increased from 5 to 25 degrees C, for both males and females and across competitive and recreational runners, but performance was more negatively affected for slower runners. These studies suggest that weather can affect both physiological and mechanical aspects of running gait. Thus, it is possible that different weather conditions may be associated with concomitant changes in gait biomechanical running patterns, however, to our knowledge no study has directly investigated this hypothesis.
The main reason the inter-relationship between environmental weather conditions and gait biomechanics has not been investigated is most likely due to the inability to collect such data in a laboratory setting. However, due to the availability and utility of modern portable inertial measurement units (IMUs) and global positioning system (GPS), it is now possible to collect data outside of the laboratory setting [10–12]. Since large quantities of data can be collected using wearable devices, machine learning (ML) techniques are also needed to better understand the complexities of gait biomechanics and how concomitant changes in biomechanical patterns may be related to injury or performance [13, 14]. Furthermore, traditional biomechanics research generally investigates potential differences between two groups using group-based analyses. For example, several researchers have identified differences in running patterns based on different age groups, gender and/or injury status [15–17]. In contrast, more recent research has shown that group-based comparisons are not efficacious due to the existence of sub-groups [18, 19], and other studies have shown that subject-specific models are necessary to understand individual differences and risk factors [20–23]. Several authors have also used different ML algorithms to develop these sub-group-based models, including principal component analysis, support vector machine and hierarchical cluster analysis [17–19]. However, to our knowledge no study has directly investigated whether a subject-specific model provide deeper insight into emerging IMU-based biomechanical investigations based on changes in environmental weather conditions.
Therefore, the purpose of this study was to develop a classification model based on subject-specific changes in biomechanical running patterns across two different environmental weather conditions using data obtained from wearable sensors in out-of-laboratory environments. We hypothesized that we could classify changes in subject-specific running patterns based on weather conditions with a classification accuracy greater than 80% and that the ranked order of variable importance would be based on subject-specific ML models. A secondary objective was to determine the ranking of the biomechanical variables, based on their importance in the classification margin, in order to better understand changes in subject-specific running patterns.
Methods
Participants
Six recreational runners (Five females: age = 47.5±9.69 years, height = 169.17±6.56 cm, weight = 67.42±11.5 kg; and one male: age = 29 years, height = 170 cm, weight = 75 kg) volunteered to participate in the study. The runners were free of any neuromuscular diseases or musculoskeletal injuries and they were registered for a half-marathon training program managed by a local running group. This protocol was approved by the University of Calgary Conjoint Health Research Ethics Board (REB 16–2035) and all runners provided their written informed consent.
Instrumentation
Biomechanical gait variables from each runner were recorded using the Lumo Run® (Lumo Bodytech Inc., Mountain View, CA) wearable inertial measurement unit (IMU), consisting of a 3-dimensional (3D) accelerometer, magnetometer, and gyroscope. (dimension: 4.98cm x 2.84cm x 0.99cm). The Lumo Run IMU was attached to the posterior aspect of either the runner’s waistband or running belt as per the manufacturer’s instructions [24] (Fig 1). This wearable sensor device measured and recorded data for six different biomechanical variables [24] and averaged these data for each ten-strides (Table 1) and a complete description of these variables can be found on the manufacturer’s website [24]. A GPS watch (Garmin vívoactive® HR; Garmin International Inc., KS, USA) was attached to each runner’s preferred wrist (Fig 1) and recorded running speed (m/s), distance (kilometers (km)), and global positioning data, including latitude, longitude and altitude, every second.
Data collection
Gait variables from winter runs were recorded from mid-February to mid-March, while spring runs were recorded from late April to mid-May. Each runner performed two training runs during each weather condition for a total of four runs used in this analysis. Each run began at 8:30 AM on a Sunday, and was completed outdoors on pavement, and along a similar route. Data corresponding to the temperature (degrees Celsius), snow depth (cm), precipitation (mm), and humidity (%) for each run were derived from three different International Air Transport Association-affiliated weather stations in Calgary, AB: Canada Olympic Park (WDU), Calgary International Airport (YYC), and Calgary INT'L CS Alberta (PCI).
For each run, data from km 0 to 1 were discarded, as this was considered a warmup period, and any data following 6-km was also not used in the analysis in order to minimize the effects of fatigue, if any. Therefore, only 5-km of data (i.e., from km 1 to 6) were analyzed from each run and in total, the input data consisted of 66,370 strides (~11,000/runner) across the four runs. Altitude, latitude and longitude data from the Garmin watch were used to ensure the elevation profile for each of the four runs were similar, and that the data from each run were collected from a route with minimal changes in elevation, in order to minimize the effect of running on uphill and/or downhill.
Data analysis
A robust, and non-linear machine learning classifier, called Random Forest (RF), was used to develop the classification model which measured the accuracy and importance of gait biomechanical variables in classifying runs of differing environmental weather conditions. The RF classifier has been shown to provide a higher classification accuracy than other existing ML classifiers with a faster computation speed, while facilitating complex interactions among predictor variables and providing information about the importance of each predictor variable [25–27]. In other word, RF provides variable importance measures to rank predictors according to their predictive power [28]. Two validation methods (Method 1: one-against-another and Method 2: partitioning datasets) were used to ensure that the proposed RF-based subject-specific classification approach was robust and that the data were not overfit [29]. With Method 1 (one-against-another) data combining one winter run and one spring run were considered the training dataset, and the testing dataset consisted of the remaining winter and spring runs. With Method 2 (partitioning datasets), 70% of each runner’s total strides performed in both weather condition were randomly selected for training, and the remaining 30% were used for testing purposes. Individual training and test sets were generated for each subject. Each classification method was applied using the standalone Python programming language (version 3.6, www.python.org) [30]. The developed RF model was trained and cross-validated using the built-in Anaconda distribution of Python with notable packages including matplotlib, numpy, scipy, and scikit-learn (“sklearn.ensemble.RandomForestClassifier”) [31, 32]. The number of trees in the RF was set to 100, as previous research has shown this is a sufficient number for obtaining high accuracy solutions to similar classification problems [33, 34]. Additionally, the RF used a Gini index to calculate the impurity of a node from the CART (classification and regression tree) learning system in order to construct the decision trees [26]. The RF trees compute a heuristic for determining how significant a variable (6 Lumo Run gait variables) is in predicting a target (weather). Statistical analyses were performed using repeated measures ANOVA (P<0.05) and Cohen's d effects size estimates were calculated for each difference on the outcome measures between each weather condition.
Results
Fig 2 presents an overview of the RF-based classification accuracy obtained with test data generated using the two validation methods. Using Method 2 (partitioning datasets), the RF-based model demonstrated an excellent overall mean classification accuracy of 95.42%. In fact, all runners yielded a classification accuracy higher than 90% with the exception of Runner 5, who exhibited a classification accuracy of 89.06%. In contrast, the overall mean classification accuracy obtained with Method 1 (one-against-another) was 87.18%, and all the runners yielded a classification accuracy higher than 85% except for Runner 5, who exhibited an accuracy of 70.47%. Significant differences (P<0.05) in the overall classification accuracies were also found between the methods. Overall, for all runners, Method 2 yielded a higher classification accuracy than Method 1. Moderate differences in classification accuracy were also observed between Methods 1 and 2 for Runner 5 (18.59%) and Runner 6 (14.37%), but the differences in classification accuracy between the methods were slight for Runner 3 (8.0%) and Runner 4 (6.14%), and non-existent for Runner 1 (2.16%), and Runner 2 (0.45%).
Overall, the ranking of the variables, based on their importance in the classification margin, differed across all runners and classification methods (Table 2 and Fig 3). For example, although vertical oscillation of pelvis was the most important variable, using both methods, for Runners 2 and 5, it ranked lower for Runner 1, wherein pelvic drop was the most important variable across both methods. Similarly, pelvic rotation was the second-ranked variable for both methods for Runners 2 and 4 but was less significant for the other runners. Overall, cadence was less important for all runners, with the exception of for Runner 3, wherein it was the second most important variable using Method 2. Another notable difference was found for braking where for Runner 4 it was the most important variable using Method 1 but only the third most important variable with Method 2. A similar inconsistency was found for pelvic rotation, which was identified as the most important variable with Method 1 but was ranked fourth with Method 2. The remaining three variables, braking, ground contact time, and cadence, were not found to be important for the classification task and were consistently ranked third, fifth and sixth across both methods, respectively (Fig 4).
All the variables in this stacked bar graph are shown in the same vertical order for both methods (VOP, PD, PR, braking, GCT and cadence).
Each point is equivalent to five strides. Data from both the training and testing sets are shown.
Table 2 also presents the results of the statistical analyses of the individual and overall results from both weather conditions. All runners, except Runner 4, demonstrated lower vertical oscillation of the pelvis in winter than in spring. The pelvic drop of two runners (Runner 2 and Runner 3) and the pelvic rotation of three runners (Runner 3, 4 and 6) were higher in winter than in spring. There was no clear difference in braking between winter and spring because three runners (Runners 1, 3 and 4) exhibited the same values during both conditions, two runners (Runners 4 and 6) had lower braking values in winter, and one runner (Runner 2) presented a higher braking value in winter. Two runners (Runners 1 and 2) had lower ground contact time values in winter, whereas two runners (Runners 3 and 4) had a higher ground contact time in winter, and the remaining two runners (Runners 5 and 6) had a similar value during both weather conditions. Finally, with the exception of Runner 4, all runners demonstrated a higher cadence during winter. Overall, five biomechanical variables (excluding cadence) demonstrated lower values during winter runs as compared to spring runs. However, no significant differences were found between the two weather conditions for any of the six variables (P>0.05). Cohen’s d effect size and 95% confidence intervals [95%CI] are presented in Table 2 and reveal the effect sizes between winter and spring runs were small (i.e., d<0.5), except for vertical oscillation of the pelvis, pelvic drop, and cadence, which were moderate (i.e., 0.5<d<0.8).
The results of the environmental weather conditions are presented in Table 3 and show the average temperature, humidity and snow depth were significantly different between winter and spring runs, along with no differences in precipitation.
The speed and overall route were similar between sessions, as presented in Table 4. In addition, the speed, heart rate, altitude, latitude and longitude showed no significant differences between the two weather conditions (Table 4).
Discussion
The objective of this study was to classify changes in subject-specific running gait patterns based on the environmental weather (winter vs. spring) conditions using an RF classifier. The findings of the current study support our hypotheses and demonstrate that an RF-approach was a robust method for accurately classifying large datasets collected using wearable sensors in real-world settings. Interestingly, each subject’s classification method had different important predictor variables based on the RF evaluation. Therefore, each individual runner exhibited different changes in overall gait biomechanics, and changes in the weather conditions affected the mechanics of individual runners differently. To our knowledge, this study constitutes the first examination of changes in subject-specific gait biomechanics based on environmental weather conditions. These findings also support the efficacy of wearable technology, and subsequent data science approaches for understanding the complexities of running gait patterns based on collecting data in out-of-laboratory environments [29, 35].
Overall, the results of this investigation demonstrate that the presence of snow and colder temperatures results in runner-specific changes in biomechanical gait patterns, possibly in an effort to reduce the risk of falling due to the slippery surface [36]. These assumptions are supported by previous studies that also indicated injury rates were higher in colder weather conditions compared to warmer weather due to running on icy and slippery running paths [37–39]. Moreover, the results of the current study also indicate that the changes in running biomechanical patterns between weather conditions may contribute to overuse running-related injuries [5]. For example, when pelvic drop was important for classification (e.g. Runner 1), there was greater pelvic drop in spring than winter, but when it was not important (e.g. Runners 2 and 3), it was lower in spring than winter. A similar pattern was observed in vertical oscillation of the pelvis: when it was important (e.g. Runners 2 and 5), there was greater amounts of oscillation in spring than winter, but when it was less important (e.g. Runner 4), there was greater oscillation in winter than spring. These results suggest that the runners involved in the current study adjusted to different weather conditions by reducing vertical or frontal plane motion accompanied by slight increases in running cadence and shorter stride length. However, it is important to note that all of the participants were injury-free and these aforementioned gait changes were not necessary to mitigate symptoms of injury. On the other hand, adopting a more constrained running pattern may, over time, may contribute to an overuse running injury [40]. Future prospective research is therefore necessary to help understand the inter-relationship between environmental weather conditions, concomitant and subject-specific changes in gait patterns, and the etiology of injury.
The RF classifier has received increasing attention within the gait-related research community due to its ability to yield excellent classification results and its fast-computational processing speed [41, 42]. In addition, this classifier provides consistent classifications using predictions derived from an ensemble of decision trees as well as a ranking of the variables according to their ability to differentiate between the target classes [41, 43]. The results of the current study are largely consistent with previous RF-based gait biomechanics studies involving wearable sensors (40,41). However, while research has investigated how IMUs systems can be used for the assessment of running biomechanics in laboratory and clinical settings [44], very few studies have been conducted in real-world settings [45, 46]. Therefore, to provide insights into this knowledge gap and open new research directions, the current study developed and evaluated subject-specific methods, using an RF classifier using data from a single IMU, and achieved excellent classification accuracy results. Interestingly, the slight differences in classification accuracy obtained between the two tested RF-methods suggest that the inclusion of information from multiple runs is beneficial for building a successful model. In addition, the current study demonstrates that the RF algorithm was able to accurately classify and determine the relative importance of each input variable for an individual runner [47, 48].
While it is important to note that the combination of multiple variables was needed to achieve a high classification accuracy and fully understand the multidimensional characteristics of the subject-specific running biomechanics associated with different weather conditions, the current findings can be compared to previous studies that have either addressed the effects of temperature on running performance [9, 49, 50] or injury rates [51]. For example, our findings are consistent with previous work demonstrating the usefulness of multidimensional analyses to better understand the complex patterns and inter-relationships between multiple biomechanical variables when classifying runners based on subtle differences in gait patterns that may be indicative of performance and/or injury [52–55]. Moreover, in the current study, regardless of the classification method, all runners exhibited slightly lower values for all biomechanical gait variables, except cadence, during winter as compared to spring. These findings support previous research indicating a more economical running technique with a lower risk of overuse injury during winter (colder) weather conditions [56–58]. Reduced pelvic drop has also been considered a protective factor for patellofemoral pain [59, 60], as well as a gait retraining strategy to reduce pain associated with this common running-related injury [61]. Future research is therefore necessary using wearable sensors in real-world situations to help better elucidate these inter-relationships.
To our knowledge, this is the first study to quantify subject-specific changes in real-world running gait biomechanics as a result of changes in environmental weather conditions. Moreover, the current study also represents one of the first investigations to analyse data from a runner’s actual training run. Specifically, a recent systematic review [62] suggested that future studies should involve long-term data collections, across multiple running bouts, and in a runner’s natural environment, thus enabling prospective studies and the development of subject-specific models of gait. Considering that the etiology of overuse running injuries is multifactorial, and can result from the interaction of many extrinsic factors such as environmental conditions, the results of the current study are an important contribution to help to better understand injury etiology.
Limitation and future directions
The stated findings should be considered with respect to limitations. First, although there was a small number of runners (n = 6), the method employed is generalizable considering that we used subject-specific models to measure changes in gait parameters across 66,370 strides. Regardless, further investigation using a larger sample size is necessary to determine if homogenous sub-groups, or clusters, will form as a result of consistent within-group biomechanical changes (18,58). Second, we did not include any non-weather-related factors such as changes in runner’s clothing, footwear, nutrition, sleep, or daily mood state profile. Future research should consider these factors in order to gain a more complete understanding of how external factors can influence running gait biomechanics. Third, although the present study examined two different weather conditions, these results of the present study may only be applicable to these weather conditions and temperatures. As well, the temperatures in the present study (i.e., -10°C to +6°C) were lower than those of Ely et al., [9] (i.e., +5°C to +25°C) and Knapik et al., [51] (i.e., +15°C to +35°C). Lastly, a limited number of spatiotemporal and biomechanical variables obtained from a commercially available wearable sensor device were used for the current study. While it is likely that additional or more complex variables from one or more wearable sensors could improve the classification accuracy of the current study, we posit that the simplicity and translatability to the current market of wearable sensors is a significant advantage that should not be overlooked. Regardless, future research should include a broader range of variables, and possibly more wearable sensor devices, in order to gain a deeper understanding for subject-specific changes in gait patterns during out-of-laboratory data collections.
Conclusion
In summary, our developed RF-based subject-specific classification model demonstrated excellent mean classification accuracies (87.18% and 95.42%) based on a large set of running gait data from a small group of runners. These novel results support the use of a robust machine learning approach for determining subject-specific changes in running gait patterns based on differences in external weather conditions using a single IMU device. We believe that our RF-based method may provide a more in-depth understanding of changes in gait biomechanics in response to extrinsic injury-risk factors and therefore conclude that the relationship between environmental weather conditions and gait biomechanics is subject-specific and multifactorial and involves unique interactions between intrinsic and extrinsic factors.
Supporting information
S1 File. Validation for Runner 4 (R-4) using Method 1 (one-against-another); classification accuracy: 91.42%.
https://doi.org/10.1371/journal.pone.0203839.s001
(XLSX)
S2 File. Validation for Runner 4 (R-4) using Method 2 (partitioning datasets in two sets at a ratio of 7:3); classification accuracy: 97.56%.
https://doi.org/10.1371/journal.pone.0203839.s002
(XLSX)
Acknowledgments
This study was partially funded by the Natural Sciences and Engineering Research Council of Canada (NSERC) Idea-2-Innovation Award (grant #I2IPJ 493875–16), a University of Calgary Eyes High Postdoctoral Research award, and a Strategic Research Grant from the Vice-President (Research) at the University of Calgary.
References
- 1. Saragiotto BT, Di Pierro C, Lopes AD. Risk factors and injury prevention in elite athletes: a descriptive study of the opinions of physical therapists, doctors and trainers. Brazilian journal of physical therapy. 2014;18(2):137–43. pmid:24845023
- 2. Saragiotto BT, Yamato TP, Junior LCH, Rainbow MJ, Davis IS, Lopes AD. What are the main risk factors for running-related injuries? Sports medicine. 2014;44(8):1153–63. pmid:24809248
- 3. van Gent BR, Siem DD, van Middelkoop M, van Os TA, Bierma-Zeinstra SS, Koes BB. Incidence and determinants of lower extremity running injuries in long distance runners: a systematic review. British journal of sports medicine. 2007;41:469–80. pmid:17473005
- 4. Meeuwisse WH. Assessing causation in sport injury: A multifactorial model. LWW; 1994.
- 5. Hreljac A. Impact and overuse injuries in runners. Medicine and science in sports and exercise. 2004;36(5):845–9. pmid:15126720
- 6. Milgrom C, Finestone A, Zin D, Mandel D, Novack V. Cold weather training: a risk factor for Achilles paratendinitis among recruits. Foot & ankle international. 2003;24(5):398–401.
- 7. Orchard JW, Powell JW. Risk of knee and ankle sprains under various weather conditions in American football. Medicine and science in sports and exercise. 2003;35(7):1118–23. pmid:12840631
- 8. Orchard J, Seward H, McGivern J, Hood S. Intrinsic and extrinsic risk factors for anterior cruciate ligament injury in Australian footballers. The American journal of sports medicine. 2001;29(2):196–200. pmid:11292045
- 9. Ely MR, Cheuvront SN, Roberts WO, Montain SJ. Impact of weather on marathon-running performance. Medicine and Science in Sports and Exercise. 2007;39(3):487–93. pmid:17473775
- 10. Giandolini M, Pavailler S, Samozino P, Morin J-B, Horvais N. Foot strike pattern and impact continuous measurements during a trail running race: proof of concept in a world-class athlete. Footwear Science. 2015;7(2):127–37.
- 11. Giandolini M, Horvais N, Rossi J, Millet GY, Samozino P, Morin J-B. Foot strike pattern differently affects the axial and transverse components of shock acceleration and attenuation in downhill trail running. Journal of biomechanics. 2016;49(9):1765–71. pmid:27087676
- 12. Meardon SA, Hamill J, Derrick TR. Running injury and stride time variability over a prolonged run. Gait & posture. 2011;33(1):36–40.
- 13. Schöllhorn W, Nigg B, Stefanyshyn D, Liu W. Identification of individual walking patterns using time discrete and time continuous data sets. Gait & Posture. 2002;15(2):180–6.
- 14. Kiernan D, Hawkins DA, Manoukian MA, McKallip M, Oelsner L, Caskey CF, et al. Accelerometer-based prediction of running injury in National Collegiate Athletic Association track athletes. Journal of Biomechanics. 2018.
- 15. Bus SA. Ground reaction forces and kinematics in distance running in older-aged men. Medicine & Science in Sports & Exercise. 2003;35(7):1167–75.
- 16. Ferber R, Davis IM, Williams Iii DS. Gender differences in lower extremity mechanics during running. Clinical biomechanics. 2003;18(4):350–7. pmid:12689785
- 17. Phinyomark A, Hettinga BA, Osis ST, Ferber R. Gender and age-related differences in bilateral lower extremity mechanics during treadmill running. PLoS One. 2014;9(8):e105246. pmid:25137240
- 18. Phinyomark A, Osis S, Hettinga BA, Ferber R. Kinematic gait patterns in healthy runners: A hierarchical cluster analysis. Journal of biomechanics. 2015;48(14):3897–904. pmid:26456422
- 19. Watari R, Osis ST, Phinyomark A, Ferber R. Runners with patellofemoral pain demonstrate sub-groups of pelvic acceleration profiles using hierarchical cluster analysis: an exploratory cross-sectional study. BMC musculoskeletal disorders. 2018;19(1):120. pmid:29673341
- 20. Bates BT, Stergiou N. Performance Accomodation to Midsole Hardness During Running. Journal of Human Movement Studies. 1996;31(4):189–210. Epub 210.
- 21. Stacoff A, Nigg BM, Reinschmidt C, Van Den Bogert AJ, Lundberg A. Tibiocalcaneal kinematics of barefoot versus shod running. Journal of biomechanics. 2000;33(11):1387–95. pmid:10940397
- 22. Stacoff A, Reinschmidt C, Nigg B, van den Bogert AJ, Lundberg A, Denoth J, et al. Effects of foot orthoses on skeletal motion during running. Clinical Biomechanics. 2000;15(1):54–64. pmid:10590345
- 23. Bates B, James C, Dufek J. Single-subject analysis. In Stergiou N (Ed), Innovative analyses of human movement. 2004:3–28.
- 24.
LumoBack. Available from: https://www.lumobodytech.com/science-of-lumo-run/. 2018.
- 25. Cutler DR, Edwards TC, Beard KH, Cutler A, Hess KT, Gibson J, et al. Random forests for classification in ecology. Ecology. 2007;88(11):2783–92. pmid:18051647
- 26. Strobl C, Boulesteix A-L, Kneib T, Augustin T, Zeileis A. Conditional variable importance for random forests. BMC bioinformatics. 2008;9(1):307.
- 27. Ziegler A, König IR. Mining data with random forests: current options for real‐world applications. Wiley Interdisciplinary Reviews: Data Mining and Knowledge Discovery. 2014;4(1):55–63.
- 28. Degenhardt F, Seifert S, Szymczak S. Evaluation of variable selection methods for random forests and omics data sets. Briefings in bioinformatics. 2017.
- 29. Ferber R, Osis ST, Hicks JL, Delp SL. Gait biomechanics in the era of data science. Journal of biomechanics. 2016;49(16):3759–61. pmid:27814971
- 30. Pedregosa F, Varoquaux G, Gramfort A, Michel V, Thirion B, Grisel O, et al. Scikit-learn: Machine learning in Python. Journal of Machine Learning Research. 2011;12(Oct):2825–30.
- 31. Gupta VP, Garton AL, Sisti JA, Christophe BR, Lord AS, Lewis AK, et al. Prognosticating Functional Outcome After Intracerebral Hemorrhage: The ICHOP Score. World Neurosurgery. 2017;101:577–83. pmid:28242488
- 32. Rendeiro AF, Schmidl C, Strefford JC, Walewska R, Davis Z, Farlik M, et al. Chromatin accessibility maps of chronic lymphocytic leukemia identify subtypespecific epigenome signatures and associated transcription regulatory networks. Nature Communications. 2016:1–25.
- 33. Pavey TG, Gilson ND, Gomersall SR, Clark B, Trost SG. Field evaluation of a random forest activity classifier for wrist-worn accelerometer data. Journal of Science and Medicine in Sport. 2017;20(1):75–80. pmid:27372275
- 34. Singh K, Guntuku SC, Thakur A, Hota C. Big data analytics framework for peer-to-peer botnet detection using random forests. Information Sciences. 2014;278:488–97.
- 35. Phinyomark A, Petri G, Ibáñez-Marcelo E, Osis ST, Ferber R. Analysis of Big Data in Gait Biomechanics: Current Trends and Future Directions. Journal of Medical and Biological Engineering. 2017:1–17.
- 36. Cappellini G, Ivanenko YP, Dominici N, Poppele RE, Lacquaniti F. Motor patterns during walking on a slippery walkway. Journal of Neurophysiology. 2010;103(2):746–60. pmid:19955283
- 37. Powell KE, Kohl HW, Caspersen CJ, Blair SN. An epidemiological perspective on the causes of running injuries. The physician and Sportsmedicine. 1986;14(6):100–14. pmid:27463440
- 38. van Mechelen W. Running Injuries. Sports Medicine. 1992;14(5):320–35.
- 39. Renström P, Peterson L. Groin injuries in athletes. British Journal of Sports Medicine. 1980;14(1):30. pmid:7378668
- 40. Hamill J, van Emmerik RE, Heiderscheit BC, Li L. A dynamical systems approach to lower extremity running injuries. Clinical biomechanics. 1999;14(5):297–308. pmid:10521606
- 41.
Reynard F, Terrier P. Determinants of gait stability while walking on a treadmill: a machine learning approach. arXiv preprint arXiv:170505191. 2017.
- 42. Samà A, Rodríguez-Martín D, Pérez-López C, Català A, Alcaine S, Mestre B, et al. Determining the optimal features in freezing of gait detection through a single waist accelerometer in home environments. Pattern Recognition Letters. 2017.
- 43. Breiman L. Random forests. Machine learning. 2001;45(1):5–32.
- 44. Wundersitz DW, Josman C, Gupta R, Netto KJ, Gastin PB, Robertson S. Classification of team sport activities using a single wearable tracking device. Journal of biomechanics. 2015;48(15):3975–81. pmid:26472301
- 45.
Buckley C, O'Reilly M, Whelan D, Farrell AV, Clark L, Longo V, et al., editors. Binary classification of running fatigue using a single inertial measurement unit. Wearable and Implantable Body Sensor Networks (BSN), 2017 IEEE 14th International Conference on; 2017: IEEE.
- 46.
Ahmadi A, Mitchell E, Destelle F, Gowing M, O'Connor NE, Richter C, et al., editors. Automatic activity classification and movement assessment during a sports training session using wearable inertial sensors. Wearable and Implantable Body Sensor Networks (BSN), 2014 11th International Conference on; 2014: IEEE.
- 47. Nandy A, Chakraborty R, Chakraborty P. Cloth invariant gait recognition using pooled segmented statistical features. Neurocomputing. 2016;191(Supplement C):117–40. https://doi.org/10.1016/j.neucom.2016.01.002.
- 48. Langs G, Menze BH, Lashkari D, Golland P. Detecting stable distributed patterns of brain activation using gini contrast. NeuroImage. 2011;56(2):497–507. pmid:20709176
- 49. Vihma T. Effects of weather on the performance of marathon runners. International journal of biometeorology. 2010;54(3):297–306. pmid:19937453
- 50. Suping Z, Guanglin M, Yanwen W, Ji L. Study of the relationships between weather conditions and the marathon race, and of meteorotropic effects on distance runners. International journal of biometeorology. 1992;36(2):63–8. pmid:1634282
- 51. Knapik JJ, Canham-chervak M, Hauret K, Laurin MJ, Hoedebecke E, Craig S, et al. Seasonal variations in injury rates during US Army Basic Combat Training. Annals of occupational hygiene. 2002;46(1):15–23. pmid:12005127
- 52. Clermont CA, Osis ST, Phinyomark A, Ferber R. Kinematic Gait Patterns in Competitive and Recreational Runners. Journal of Applied Biomechanics. 2017:1–26.
- 53. Clermont CA, Phinyomark A, Osis ST, Ferber R. Classification of higher-and lower-mileage runners based on running kinematics. Journal of Sport and Health Science. 2017.
- 54. Phinyomark A, Osis S, Hettinga B, Leigh R, Ferber R. Gender differences in gait kinematics in runners with iliotibial band syndrome. Scandinavian journal of medicine & science in sports. 2015;25(6):744–53.
- 55. Ahamed NU, Benson L, Clermont C, Osis ST, Ferber R. Fuzzy Inference System-based Recognition of Slow, Medium and Fast Running Conditions using a Triaxial Accelerometer. Procedia Computer Science. 2017;114:401–7.
- 56. Wellenkotter J, Kernozek T, Meardon S, Suchomel T. The effects of running cadence manipulation on plantar loading in healthy runners. International journal of sports medicine. 2014;35(09):779–84.
- 57. Hobara H, Sato T, Sakaguchi M, Nakazawa K. Step frequency and lower extremity loading during running. International journal of sports medicine. 2012;33(04):310–3.
- 58. Schubert AG, Kempf J, Heiderscheit BC. Influence of stride frequency and length on running mechanics: a systematic review. Sports health. 2014;6(3):210–7. pmid:24790690
- 59. Dierks TA, Manal KT, Hamill J, Davis IS. Proximal and distal influences on hip and knee kinematics in runners with patellofemoral pain during a prolonged run. Journal of Orthopaedic & Sports Physical Therapy. 2008;38(8):448–56.
- 60. Willson JD, Davis IS. Lower extremity mechanics of females with and without patellofemoral pain across activities with progressively greater task demands. Clinical biomechanics. 2008;23(2):203–11. pmid:17942202
- 61. Willy RW, Scholz JP, Davis IS. Mirror gait retraining for the treatment of patellofemoral pain in female runners. Clinical Biomechanics. 2012;27(10):1045–51. pmid:22917625
- 62. Benson LC, Clermont CA, Bošnjak E, Ferber R. The Use of Wearable Devices for Walking and Running Gait Analysis Outside of The Lab: A Systematic Review. Gait & Posture. 2018;63:124–38.