 Research
 Open access
 Published:
Wrist accelerometer shape feature derivation methods for assessing activities of daily living
BMC Medical Informatics and Decision Making volume 18, Article number: 124 (2018)
Abstract
Background
There has been an increasing interest in understanding the usefulness of wristbased accelerometer data for physical activity (PA) assessment due to the ease of use and higher user compliance than other body placements. PA assessment studies have relied on machine learning methods which take accelerometer data in forms of variables, or feature vectors.
Methods
In this work, we introduce automated shape feature derivation methods to transform epochs of accelerometer data into feature vectors. As the first step, recurring patterns in the collected data are identified and placed in a codebook. Similarities between epochs of accelerometer data and codebook’s patterns are the basis of feature calculations. In this paper, we demonstrate supervised and unsupervised approaches to learn codebooks. We evaluated these methods and compared them with the standard statistical measures for PA assessment. The experiments were performed on 146 participants who wore an ActiGraph GT3X+ accelerometer on the right wrist and performed 33 activities of daily living.
Results
Our evaluations show that the shape feature derivation methods were able to perform comparably with the standard wrist model (F1score: 0.89) for identifying sedentary PAs (F1scores of 0.86 and 0.85 for supervised and unsupervised methods, respectively). This was also observed for identifying locomotion activities (F1scores: 0.87, 0.83, and 0.81 for the standard wrist, supervised, unsupervised models, respectively). All the wrist models were able to estimate energy expenditure required for PAs with low error (rMSE: 0.90, 0.93, and 0.90 for the standard wrist, supervised, and unsupervised models, respectively).
Conclusion
The automated shape feature derivation methods offer insights into the performed activities by providing a summary of repeating patterns in the accelerometer data. Furthermore, they could be used as efficient alternatives (or additions) for manually engineered features, especially important for cases where the latter fail to provide sufficient information to machine learning methods for PA assessment.
Background
Physical activity (PA) assessment has been widely pursued in a variety of research studies including determining relationship with health status [1], detecting future hazardous events (e.g., major mobility disability) [2], and evaluating the performance of interventional studies aimed to increase PA [3]. For PA assessment, wearable accelerometers have been the main devices for data collection, which are minimally intrusive and provide objectively accurate measurements. Most of the studies have been conducted with the accelerometer attached to the hip, since the information obtained from this body placement was highly correlated with ambulation [4]. There has been a recent interest in understanding the usefulness of wristbased accelerometer data collection due to ease of use and higher compliance. In particular, smartwatches play an important role in this change, since they are popular and have necessary resources, e.g., sensor monitors and connectivity means, to make realtime mobility monitoring possible. There have been several remote health monitoring frameworks proposed by researchers that are dependent on wristaccelerometer PA assessment models [5].
PA assessment approaches include two main parts: 1) PA identification, which is a classification task and 2) energy expenditure estimation for performing the PA, which is a regression problem. In both areas, it has been shown that machine learning methods perform better than statistical regressionbased approaches [6]. There are two most widely used approaches to define a physical activity in the PA assessment studies. While some works focused on recognizing homogeneous activities, such as sitting, standing, and walking [7], there have been other works that attempted to detect activities of daily living, e.g., grocery shopping and yard work, which are composites of homogeneous activities [8]. Each approach has unique advantages; however, the latter definition of physical activity has been more closely investigated to assess lifestyles of individuals [6].
Most machine learning methods require data in the form feature vectors, and therefore, their performance depends on the feature derivations. Statistical summaries of accelerometer data have been the most popular choice for feature derivation in PA assessment studies. This type of feature derivation is a manual procedure, which requires domain expertise and sufficient knowledge about the relation between the data in hand and the target variable. To assess activities of daily using wrist accelerometer data, a set of seven summary statistics for short epochs (12.8 or 15 s) has been introduced [9]. The feature vectors obtained from this approach has been shown to be effective measurements for detecting sedentary and locomotion activities [6, 10].
When summarizing a dataset into a few summary statistics, it is possible that two different activities exhibit similar features. In this method, we lose certain details and information that might be useful to identify other types of activities. Therefore, for a new target variable (e.g., a new activity of interest), another set of features might be required. The present work, which builds on a previous paper presented by Kheirkhahan et al. [11], proposes two shape feature derivation methods for PA assessment that are based on detecting representative accelerometer patterns in a dataset containing activities of daily living. The representative patterns are called atoms and gathered in a codebook. The learned codebook is used to calculate feature vectors based on similarities of subsequences within a PA accelerometer data and atoms.
The main contributions of the present work are:

We introduce an unsupervised method to learn a comprehensive codebook from the wrist accelerometer data. We obtain a bagofwords representation of the data by replacing the subsequences of data with their most similar atoms. We apply a term frequencyinverse document frequency function on bagofwords representations to obtain feature vectors suitable to be passed to PA assessment models.

Leveraging the idea of motif detection [12], we propose a supervised shape feature derivation method that identifies recurring patterns for an activity of interest. We show that this method results in a more specialized codebook with fewer atoms, and therefore, the distance of subsequences of data to atoms are directly used as new features.

We evaluate the three different feature derivation methods for PA assessment, which are 1) standard wrist model relying on statistical summaries, 2) bagofwords approach, and 3) supervised shape feature. The present work shows that the shape features perform with high accuracy for identifying sedentary and locomotion PAs. There accuracies are comparable with the statistical features that were defined for this problem. However, they provide further information that contribute to models with higher accuracy than the standard wrist model for new activities of interest.

The current study also investigates whether performing additional steps of activity identification improve the energy expenditure estimation for all three models.
Methods
Data Collection
Participants
One hundred and forty six adults with ages ranging between 20 and 89 years participated in a study of metabolic costs of daily activity [13]. Table 1 shows the participant characteristics. The participants were community dwelling adults, who were required to understand and speak English, had stable body weight for at least three months, and willing to undergo all testing procedures. They provided written informed consents approved by the Institutional Review Board at the University of Florida.
They were asked to perform a list of 33 tasks mimicking daily chores in four visits, including exercise and sedentary type physical activities, in a clinic laboratory setting (see Table 2). An ActiGraph GT3X+ (ActiGraph, Pensacola, FL) triaxial accelerometer was mounted on their right wrist. Locomotion tasks were performed during the first visit, while the fourth visit was dedicated to sedentary tasks (e.g., TV watching and standing still). During the other two visits, participants engaged in tasks where ambulation was necessary for some parts. For computer work, TV watching, and strength exercises, participants were asked to remain seated throughout the activity.
Instrumentation
The ActiGraph GT3X+ monitors were mounted on participants’ right wrists. These lightweight accelerometers record accelerations in units of gravity (1 g) in perpendicular, anteriorposterior, and mediolateral axes. They were configured to collect data at 100 Hz sampling rate. Energy expenditures was measured in parallel using a portable indirect calorimetry system, Cosmed K4b2 [14]. Respiratory gas exchange data were collected breathbybreath through a fitted mask. Data were converted to MET values defined as the oxygen uptake (VO_{2} = ml/min.kg) during steady state rate expressed as a function of 3.5 ml/min.kg.
Wrist Accelerometer Models
A conventional accelerometer model for activity recognition consists of modules for feature vector calculations from the timeseries data and machine learning methods for predicting activity labels. In this work, we present three different approaches for feature representations; 1) statistical summaries of accelerometer data, which has been the standard feature vectors for physical activity assessments, 2) a bagofwords approach, which is an unsupervised method for detecting recurring patterns of accelerations in the unprocessed timeseries data, and 3) a supervised shape feature derivation, which identifies epochs of acceleration data that are repeated within an activity of interest. Details for each method are presented in the following:
Standard Statistical Wrist Feature Representation
We develop the wrist model (i.e., set of variables) using which have been widely used for activity recognition and physical activity assessment using highfrequency accelerometer data collected on the wrist [6, 9, 15]. Briefly, the constructed variables are:

Timedomain variables: the mean and standard deviation vector magnitude (MVM and SDVM, respectively), where the vector magnitude is calculated using x, y, and zaxes of the accelerometer as follows:
$$VM = \sqrt{x^{2} + y^{2} + z^{2}}$$ 
Frequencydomain variables: after obtaining the frequency representation of the vector magnitude using the Fast Fourier Transform [16], the following variables are calculated: 1) the dominant frequency (DF), 2) its fraction of power (FPDF), and 3) the fraction of power within human movement frequencies, i.e., 0.6 Hz to 2.5 Hz (P625).

Orientationrelated variables: the mean and standard deviation of the existing angle between the perpendicular axis (x) and vector magnitude (MANGLE and SDANGLE, respectively), where the angle is calculated as follows:
$$\text{angle} = \frac{180}{\pi} \times sin^{1} \frac{x}{VM}$$
We calculate the abovementioned variables from nonoverlapping 15s epochs of acceleration data.
BagofWords Feature Representation
Every observation (i.e., accelerometer data for a PA) is considered a time series sequence. The bagofwords time series model is a threepronged process, which is depicted in Fig. 1. At the first step, we find ksecond accelerometer patterns that are representative of vector magnitudes in the collected data. These representative patterns are often called atoms [17] and in the physical activity literature, the duration for such patterns (k) is usually less than 6 s [18]. Atoms are gathered into a datom codebook. After finding the codebook, we convert every ksecond subsequence of accelerometer data to a word using the label of the atom which resembles that subsequence the most. Using the word representation of the accelerometer data, we calculate normalized word frequency variables to obtain numeric vectors suitable for the machine learning methods. Details of this method is presented in the following paragraphs.
Codebook learning
To find a comprehensive codebook containing the representative acceleration patterns, we divide each time series data into subsequences. Subsequences are ksecond subintervals of the original time series instance, where the two adjacent subsequences have k−1 s of overlapping parts. These subsequences are obtained using a ksecond sliding window, which slides 1 s after each subsequence subtraction. For a sampling rate of s Hz (s acceleration values for every second), each subsequence has k^{′}=k×s data points. More specifically, from the i^{th} timeseries data with t_{i} s duration, we extract t_{i}−k+1 subsequences, each having k^{′} data points. Therefore, for a dataset containing n observations we will obtain \({\sum \nolimits }_{i = 1}^{n}(t_{i}  k + 1)\) subsequences. Next, we apply clustering algorithms to obtain d representative acceleration patterns and learn the codebook. For a study with 150 participants, each performing thirty 10min long PAs and the subsequence length (k=) 3 s, we obtain more than 2.5 billion subsequences. To be able to cluster this large number of subsequences, we use Apache Spark Big Data framework for partitionbased clustering (Spark MLlib [19]). The implicit parallelism of this framework provides efficient calculations suitable for large datasets. We calculate the silhouette values for clusters to find the best cluster fits [20]. The silhouette variable for the i^{th} cluster is defined as follows:
where a(i) represents the average distance between the samples within i^{th} cluster and b(i) is the minimum average distance of i^{th} cluster’s samples to other clusters. sl(i) values close to 1 indicate clusters with homogenous and uniformly distributed samples. For a datom codebook, each cluster centroid is an atom with k^{′} sample points in the codebook \(C \in \mathbb {R}^{k^{\prime }\times d}\). Figure 2 shows the process of learning the codebook.
Feature calculation
Once the codebook is learned, we convert every timeseries observation to a bag of words using the procedure depicted in Fig. 3. First, each subsequence of the timeseries data is replaced by the most resembling atom in the codebook. Next, we replace each subsequence with its corresponding atom’s label to obtain the bagofwords representation of the data. Finally, we calculate a normalized term frequency variable for the present words.
There are three major challenges in finding the most similar atom for each subsequence. First, acceleration patterns’ differences might be due to highfrequency noises, and not because of human movements. Second, the source of dissimilarity might be due to a phase delay, such that one acceleration pattern is identical to another one but shifted in time. Third, due to the difference in participants’ movements speed, an acceleration pattern obtained from one participant might be a scaled version of the other one. To address the first challenge, we apply a lowpass filter to exclude data irrelevant to human movement (i.e., >5 Hz). We also use overlapping subsequences, such that they have one second nonoverlapping parts to overcome the phasedelay issue. Lastly, we employ dynamic time warping method [21] to calculate the similarity of a subsequence to codebook’s atoms. This is a dynamic programming approach which is robust to small shifts (in our case, it is <1 second) and the scaling problem.
Initially, every subsequence is represented by a word; the label of the most similar atom. Next, we construct a delement vector h=(h_{1},h_{2},…,h_{d}). Each element in this vector represents the number of subsequences which were found closest to the i^{th} atom. In the example shown in Fig. 3, we will have h=(1,1,2,0) using a 4atom codebook. In our experiments, we obtain an h vector for every PA and calculate the term frequency (tf) for every word. To prevent a bias towards longer PAs, we use an augmented frequency function, which is the raw frequency of a word divided by the maximum word frequency found in the PA: \(tf(i, h) = 0.5 + 0.5 \cdot \frac {h(i)}{\underset {j}{max}\{h(j)}\)
Also, to detect rare and common words across all the PAs and to obtain a measure of how much information each word provides, we calculate a scaling factor, known as inverse document frequency (idf) as follows:
where H is a \(\mathbb {R}^{n \times d}\) matrix containing h vectors for all n tasks. This function is effective in assigning low weights to the common words. For every PA performed by a participant, we will have d variables, which are calculated by multiplying the values obtained from term frequency and inverse document frequency functions. For the i^{th} word, we obtain a normalized word frequency by multiplying the abovementioned frequency terms, i.e., tfidf(i,h,H)=tf(i,h)·idf(i,H).
Supervised Shape Feature Representation
Similar to the bagofwords approach, this method is also seeking to identify recurring patterns in the raw accelerometer data to form a codebook. To achieve that, this method relies on detecting motifs [12] that are observed within an activity of interest. This method has two major steps. First, for each participant and activity, an initial codebook is learned. Next, for every activity, the initial codebooks are combined and unique acceleration patterns are identified to form the final codebook.
The first step in this approach is to learn an initial codebook for each participant and activity and is outlined in Algorithm 1. The function takes four input arguments; 1) accelerometer timeseries data (denoted as T) that is the vector magnitude calculated from the triaxial data of all participants, 2) the activity of interest, 3) desired length of acceleration patterns to be mined, and 4) the selection rate, which indicates what portion of data (for a participant and activity) should be considered. The algorithm calculates a vector of distance score (denoted as D) for every ksecond subsequence of accelerometer data. To calculate the distance score, we use a sliding window approach where the distance between the selected subsequence and successor subsequences are calculated and the choose the minimum distance. Next, we include the subsequence with the minimum distance score, as an atom, in the initial codebook (denoted as IC). Figure 4 shows selecting a subsequence of data with the lowest distance score. The selected atom is checked to have no overlapping acceleration patterns with the previously selected atoms and after every atom selection, the corresponding subsequences are removed from the selection pool. The process of selecting atoms is repeated until we obtain the desired number of atoms for one participant. If β is set to 1, the initial codebook becomes similar to the pool of data chunks in the bagofwords approach since we would include all subsequences.
When generating the initial codebook, data for each participant are considered individually since every participant performs activities with unique dominant accelerometer patterns; i.e., participants perform activities with different pace and strength. Furthermore, this allows calculating the distance scores, which has a runtime order of O(n^{2}), to be expedited by parallel execution.
To learn the final codebook, we apply a hierarchical clustering method, which uses dynamic time warping as the distance function, to find groups of similar atoms. From each group, we select the medoid as the representative and include that in the final codebook, which is similar to the codebook learning step in the bagofwords approach. To calculate a feature vector for an epoch, we use a sliding window (with 50% overlap) to calculate distances between epoch’s subsequences and atoms. The distances are calculated using the Dynamic Time Warping method. The average value of distances to each atom is used as features calculated for the epoch.
Physical Activity Assessment
Using the derived features explained earlier, we seek to identify activities of daily living for different categories. First, we define two classification problems: 1) detecting sedentary PAs and 2) identifying locomotion activities. Sedentary PAs are defined as the activities that require <1.6 METs [22]. In our dataset, this category contains computer work, TV watching, and standing still activities. Locomotion PAs include walks, stair ascent, and stair descent. For both classification problems, we employ random forest classifier which has been the preferred method for PA assessment using accelerometer data in the previous works [8, 11].
As another step in PA assessment, we also pursue energy expenditure (MET value) estimation to evaluate the performance of the models. We use random forest regression method to estimate the energy expenditure required to perform a PA.
Results
Table 2 shows a summary of standard wrist variables for the performed activities of daily living, their mean (SD) METs, and the labels as sedentary or locomotion PAs. In our experiments, we divided our data into training and test sets. We used the collected from 126 participants for our training set and kept the other 20 for the test set. We tuned our machine learning methods using the training set and applied the trained models on the test set and reported their outcomes.
For activity identification, we used feature vectors for 15second epochs to train the classifier. The classifier predicted labels for epochs of the same size for the test set data. For each activity in the test set, the label assigned to the majority of its epochs was selected as the predicted label. To estimate the energy expenditures for each activity, we used an average feature vector over all 15second epochs for both training the model and estimation.
For the bagofwords variable representations, we tried a variety of combinations for subsequence length (k∈{3 and6} s) and codebook size (d∈{8,16, 32, and64} words). The best performance was obtained using k=3 s for subsequent length and d=32 words for the codebook, and thus, we report the results using this parameter setting. Figure 5 shows the learned codebook with thirtytwo 3second words.
For sedentary PAs, D3 and D7 words (acceleration patterns) had the highest values. These words were representatives of accelerometer patterns with negligible intensities. The other words had values close to 0, which shows they were rarely observed during sedentary PAs and they had no association with PAs belonging to the sedentary category. D8 and D19 had the highest values for the locomotion category, and thus, the top indicators of consistent movements, such as walking. Interestingly, for stair ascending PAs the dominant acceleration patterns were D9 and D10. The combination of these two words yield an acceleration pattern resembling D8 but at a lower pace. This is due to the fact that ambulation in climbing stairs is slower than walks.
We used different atom lengths (k∈{3,6} s) and selection rates (β∈[0.01,0.1]) to learn the codebook using the supervised shape feature approach. Figure 6 shows the selected atoms for locomotion activities for atom length of 3 s and selection rate of 0.01.
We categorized activities of daily living into two classification problems: 1) sedentary versus nonsedentary and 2) locomotion versus stationary activities. Table 3 shows the performance of explained methods for sedentarynonsedentary PA identification on the test set. Since the number of sedentary PAs were only a small fraction of the total number activities (9%), for a better assessment, we report accuracy, sensitivity, precision, and F1score measures, which are calculated as follows:
F1score is the harmonic mean of sensitivity and precision. For sedentarynonsedentary classification problem, sedentary PAs are considered as positive samples.
Similar to the previous case, for locomotionstationary classification problem, the number of samples belonging to each class was not evenly distributed (19% of the PAs belonged to locomotion class). Therefore, we use the abovementioned evaluation metrics to compare the methods. The results are presented in Table 4.
Three PAs in our data were categorized as sedentary tasks; computer work, TV watching (i.e., sitting), and standing still. Figure 7 shows the confusion matrices obtained from each method. The supervised shape feature method provided the best performance for specific activity type identification (accuracy = 96.6%) compared with the standard wrist model (accuracy = 78.9%) and bagofwords method (accuracy = 81.9%). We also obtained confusion matrices for PAs belonging to locomotion category. We considered Leisure Walk and Walk at RPE 1 as slow walks, and Rapid Walk and Walk at RPE 5 as fast walks. Figure 8 shows performance of each method.
We also pursued energy expenditure estimation as another part of our evaluations. We report the root mean squared error (rMSE) and the goodness of fit (R^{2}) metrics to compare the performance of methods in estimating the energy expenditure required to perform activities of daily living. First, we trained models using the derived features to estimate the energy expenditures. Next, we included the predicted labels obtained from the sedentary and locomotion classifiers as two additional independent variables for regressors. Finally, we added the predicted labels for the specific activity type as 8 additional binary variables (2 sedentary and 4 locomotion PAs) to the energy expenditure estimation models. Table 5 shows rMSE and R^{2} values for energy expenditure (MET value) estimations. Overall, all methods performed similarly well and with low error. The standard wrist model outperformed the two shape feature representations when the original feature vectors were only considered; however, including the additional PA identification steps resulted in less noticeable improvement.
Figure 9 shows the average energy expenditure (MET) estimation for standard wrist model, BagofWords approach, and supervised shape features. Stair ascent, as the only laborintensive PA, was the most challenging activity for the methods to estimate the required energy expenditure.
Discussion
In this study, introduced two shape feature derivation methods, which rely on supervised and unsupervised methods to learn codebooks. We compared the performance of the two new models with the standard wrist accelerometer model for PA recognition and energy expenditure estimation. While the standard wrist model outperforms the other feature representation for locomotion and sedentary PA identification (Tables 3 and 4), the shape feature methods are not far behind. For new target variables, e.g., identifying the specific activity type within sedentary or locomotion PAs, they are able to perform with modestly higher accuracies.
The standard wrist model offers high interpretability since the features are manually crafted. The shape feature methods also provide some level of interpretability; since these methods rely on the learned codebook, by checking the characteristics of the atoms and their weights for each PA insight could be obtained.
By definition, the energy expenditure (MET value) required to perform sedentary PAs is <1.6. Therefore, there is little variation in energy expenditure within this category. Table 2 shows that most of locomotion PAs (e.g., fast walks and stair ascent) require more energy than other activities of daily living, while the rest rank somewhere in the middle. Therefore, one might wonder whether it is possible to improve energy expenditure estimation by identifying the PA type first and training activityspecific energy expenditure models. For smaller datasets (<25 participants), previous works showed that this approach enhances energy expenditure models significantly [11, 23]. The standard wrist model is not able to identify the specific activity types within the locomotion class; for most of the cases, the model misclassifies slow walks as stair descents (or vice versa) and rapid walks as stair ascent (or vice versa). Since the MET ranges for the mentioned locomotion PAs are almost similar, the higher error rate for this model does not prevent it from benefiting from the additional steps. Although including further PA identification steps improves the energy expenditure estimation models, the improvements are not statistically significant. This is due to the fact that we obtain a model with lower bias if sufficient training data is provided. Thus, extra steps to reduce model’s error, which was a result of lack of data, are no longer necessary.
Besides the strengths, there are also limitations to this study. Although it compared three PA assessment models using wrist accelerometer data, it did not cover activitycountbased methods [24]. Another limitation is that the PAs were performed in laboratory settings. It has been shown that machine learning methods trained on such data perform poorly in freeliving condition [25]. Therefore, future studies should consider including accelerometer data for activities of daily living in reallife conditions. This study employed participantindependent models for PA assessment. However, it has been shown that personalized models perform activity recognition with higher accuracy [26] and are subject to future works.
Conclusion
The current study compared three different approaches for PA type identification and energy expenditure estimation using highresolution accelerometer data collected on the wrist. The two shape feature derivation methods result in comparable performance for PA assessment. The standard wrist model provides interpretable features and is well suited for the sedentary and locomotion PA identification. However, it might not be adequate for other PA type identifications; e.g., detecting tasks which require upper/lower body movements. Therefore, depending on the PA type classification careful feature engineering ought to be pursued. Shape feature derivation methods provide feature vectors with less efforts. This is more apparent for the bagofwords approach, which learns a codebook from the accelerometer data, regardless of the activities of interest. Thus, upon any alteration in the target variable (i.e., physical activity), the weights can be adjusted by reapplying the tf−idf method. Thus, when there is a variation in the PA assessment data analysis pipeline (e.g., new target variable) the introduced methods could be practical choices for feature derivation step.
References
Migueles JH, CadenasSanchez C, Ekelund U, Nyström CD, MoraGonzalez J, Löf M, Labayen I, Ruiz JR, Ortega FB. Accelerometer data collection and processing criteria to assess physical activity and other outcomes: A systematic review and practical considerations. Sports Med. 2017; 47:1–25.
Kheirkhahan M, TudorLocke C, Axtell R, Buman MP, Fielding RA, Glynn NW, Guralnik JM, King AC, White DK, Miller ME, et al.Actigraphy features for predicting mobility disability in older adults. Physiol Meas. 2016; 37(10):1813.
Manini TM, Carr LJ, King AC, Marshall S, Robinson TN, Rejeski WJ. Interventions to reduce sedentary behavior. Med Sci Sports Exerc. 2015; 47(6):1306–10.
Ellis K, Kerr J, Godbole S, Staudenmayer J, Lanckriet G. Hip and wrist accelerometer algorithms for freeliving behavior classification. Med Sci Sports Exerc. 2016; 48(5):933.
King CE, Sarrafzadeh M. A survey of smartwatches in remote health monitoring. J Healthc Informat Res. 2017:1–24.
Staudenmayer J, He S, Hickey A, Sasaki J, Freedson PS. Methods to estimate aspects of physical activity and sedentary behavior from high frequency wrist accelerometer measurements. J Appl Physiol. 2015; 119:jap–00026.
Kwapisz JR, Weiss GM, Moore SA. Activity recognition using cell phone accelerometers. ACM SigKDD Explor Newsl. 2011; 12(2):74–82.
Ellis K, Kerr J, Godbole S, Lanckriet G, Wing D, Marshall S. A random forest classifier for the prediction of energy expenditure and type of physical activity from wrist and hip accelerometers. Physiol Meas. 2014; 35(11):2191.
Zhang S, Rowlands AV, Murray P, Hurst TL, et al.Physical activity classification using the genea wristworn accelerometer. Ph.D. dissertation.Lippincott Williams and Wilkins; 2012.
Nair S, Kheirkhahan M, Davoudi A, Rashidi P, Wanigatunga AA, Corbett DB, Manini TM, Ranka S. Roamm: A software infrastructure for realtime monitoring of personal health. In: eHealth Networking, Applications and Services (Healthcom), 2016 IEEE 18th International Conference on. IEEE: 2016. p. 1–6.
Kheirkhahan M, Mehta S, Nath M, Wanigatunga AA, Corbett DB, Manini TM, Ranka S. A bagofwords approach for assessing activities of daily living using wrist accelerometer data. In: 2017 IEEE International Conference on Bioinformatics and Biomedicine (BIBM): 2017. p. 678–85.
Vahdatpour A, Amini N, Sarrafzadeh M. Toward unsupervised activity discovery using multidimensional motif detection in time series. IJCAI. 2009; 9:1261–6.
Corbett DB, Wanigatunga AA, Valiani V, Handberg EM, Buford TW, Brumback B, Casanova R, Janelle CM, Manini TM. Metabolic costs of daily activity in older adults (chores xl) study: Design and methods. Contemp Clin Trials Commun. 2017; 6:1–8.
Knaggs JD, Larkin KA, Manini TM. Metabolic cost of daily activities and effect of mobility impairment in older adults. J Am Geriatr Soc. 2011; 59(11):2118–23.
Kheirkhahan M, Das H, Battula M, Davoudi A, Rashidi P, Manini TM, Ranka S. Powerefficient realtime approach to nonwear time detection for smartwatches. In: Biomedical Health and Informatics (BHI), 2017 IEEE 4th Annual International Conference on. IEEE: 2017. p. 3–7.
Welch P. The use of fast fourier transform for the estimation of power spectra: a method based on time averaging over short, modified periodograms. IEEE Trans Audio Electroacoustics. 1967; 15(2):70–3.
Mallat SG, Zhang Z. Matching pursuits with timefrequency dictionaries. IEEE Trans Sig Process. 1993; 41(12):3397–415.
Lin J, Khade R, Li Y. Rotationinvariant similarity in time series using bagofpatterns representation. J Intell Inf Syst. 2012; 39(2):287–315.
Meng X, Bradley J, Yavuz B, Sparks E, Venkataraman S, Liu D, Freeman J, Tsai D, Amde M, Owen S, et al.Mllib: Machine learning in apache spark. J Mach Learn Res. 2016; 17(1):1235–41.
Kaufman L, Rousseeuw PJ. Finding groups in data: an introduction to cluster analysis.Wiley; 2009, p. 344.
Berndt DJ, Clifford J. Using dynamic time warping to find patterns in time series. In: KDD workshop, vol. 10, no. 16.Seattle: 1994. p. 359–70.
Jette M, Sidney K, Blümchen G. Metabolic equivalents (mets) in exercise testing, exercise prescription, and evaluation of functional capacity. Clin Cardiol. 1990; 13(8):555–65.
Albinali F, Intille S, Haskell W, Rosenberger M. Using wearable activity type detection to improve physical activity energy expenditure estimation. In: Proceedings of the 12th ACM international conference on Ubiquitous computing. ACM: 2010. p. 311–20.
Crouter SE, Clowers KG, Bassett DR. A novel method for using accelerometer data to predict energy expenditure. J Appl Physiol. 2006; 100(4):1324–31.
Van Hees VT, Gorzelniak L, Leon ECD, Eder M, Pias M, Taherian S, Ekelund U, Renström F, Franks PW, Horsch A, et al.Separating movement and gravity components in an acceleration signal and implications for the assessment of human daily physical activity. PLoS ONE. 2013; 8(4):e61691.
Weiss GM, Lockhart JW. The impact of personalization on smartphonebased activity recognition. In: AAAI Workshop on Activity Context Representation: Techniques and Languages: 2012. p. 98–104.
Acknowledgments
We thank the reviewers, whose valuable feedback and suggestions substantially improved this paper.
Funding
Publication costs are funded by the National Institutes of Health (NIH)/National Institute on Aging (NIA) (R01AG042525). The research is partially supported by the Claude D. Pepper Older Americans Independence Centers at the University of Florida (1P30AG028740) and University of Florida Informatics Institute. Dr. Amal Wanigatunga is supported by NIH/NIA grants (T32AG000247 and R21AG053198). The funders had no role in study design, data collection and analysis, decision to publish, or preparation of the manuscript.
Availability of data and material
The datasets generated during and/or analysed during the current study are not publicly available due to the restrictions regarding participants confidentiality but are available from the corresponding author on reasonable request.
About this supplement
This article has been published as part of BMC Medical Informatics and Decision Making Volume 18 Supplement 4, 2018: Selected articles from the IEEE BIBM International Conference on Bioinformatics & Biomedicine (BIBM) 2017: medical informatics and decision making. The full contents of the supplement are available online at https://bmcmedinformdecismak.biomedcentral.com/articles/supplements/volume18supplement4.
Author information
Authors and Affiliations
Contributions
All authors contributed to study conception and design. AW and DC were responsible for data collection. MK and AC were responsible for analyzing data. MK drafted the manuscript which was revised by TM and SR. All authors have read and approved the final manuscript.
Corresponding author
Ethics declarations
Ethics approval and consent to participate
Not applicable.
Consent for publication
Not applicable.
Competing interests
The authors declare that they have no competing interests.
Rights and permissions
Open Access This article is distributed under the terms of the Creative Commons Attribution 4.0 International License (http://creativecommons.org/licenses/by/4.0/), which permits unrestricted use, distribution, and reproduction in any medium, provided you give appropriate credit to the original author(s) and the source, provide a link to the Creative Commons license, and indicate if changes were made. The Creative Commons Public Domain Dedication waiver(http://creativecommons.org/publicdomain/zero/1.0/) applies to the data made available in this article, unless otherwise stated.
About this article
Cite this article
Kheirkhahan, M., Chakraborty, A., Wanigatunga, A.A. et al. Wrist accelerometer shape feature derivation methods for assessing activities of daily living. BMC Med Inform Decis Mak 18 (Suppl 4), 124 (2018). https://doi.org/10.1186/s1291101806711
Published:
DOI: https://doi.org/10.1186/s1291101806711