The worldwide population aged over 65 rises exponentially according to recent reports of the United Nations . Amongst others the mobility problems prevail in the elder society. Ageing and many pathologies invoke changes in walking speed and stability , while 30% of the aged population is reported to have fallen every year. Especially, changes in gait speed are related to the functional independence and mobility impairment of the elderly , and are closely connected to fall incidents.
In the last 15 years robotics research has focused on walking assistive robotic devices that will aim to provide postural support and walking assistance [4, 5, 6, 7, 8], as well as sensorial and cognitive assistance to the elderly . Their goal is to increase the user mobility, while avoiding the anxiety and frustration imposed by the common walking aids. In our previous work [10, 11], we have shown that for a robotic rollator, aiming to support patients of different mobility status, user-adaptation is important.
Specifically, a handy system should be able to assess the mobility state of the user and adapt the control strategies accordingly, and also monitor the rehabilitation progress and provide fall prevention. Although computing various gait parameters and the on-line classification of the pathological gait status of the user plays a significant role in the adaptation of a context-aware controller, there are also issues of gait stability that should be addressed.
The purpose of this paper is to present, analyse and evaluate a novel and robust method for on-line gait stability analysis of elderly subjects walking with a mobility assistant platform (Fig. 1), fusing the information from an RGB-D camera that captures the upper body and a LRF monitoring the legs motion in the sagittal plane. Specifically, we use a DL approach for detecting the upper body pose and track the respective CoM through time along with an augmented gait state estimation from the LRF 
. We propose a LSTM-based network for predicting the stability state of the patient, by classifying his gait as safe or fall-risk at each instance. This aims to present a new method for predicting the gait stability state of robotic rollator users with variable pathological gait conditions, using only non-wearable sensors, in order to provide the robotic system with an alarm regarding fall risk episodes. The main goal is to integrate this information into a user-adaptive context-aware robot control architecture for the robotic assistant platform that would prevent possible falls.
I-B Related Work
Fall detection and prevention is a hot topic in the field of assistive robotics . Most of the proposed control strategies for robotic assistive platforms in literature do not deal with the problem of fall prevention and research works focus on navigation and obstacle avoidance [14, 15, 16]. However, there exist some targeted research focusing on incorporating strategies for preventing or detecting fall incidents and facilitating user’s mobility. In [17, 18] the authors developed an admittance controller for a passive walker with a fall-prevention function considering the position and velocity of the user, utilizing data from two LRFs. They model the user as a solid body link, in order to compute the position of the center of gravity , based on which they applied a braking force on the rollator to prevent falls. A fall detection for a cane robot was presented in [20, 21]
, that computes the zero moment point stability of the elderly, using on shoe sensors that provide ground force reactions.
. Gait analysis can be achieved by using Hidden Markov Models for modelling normal and pathological human gait , and extracting gait parameters . Recently, we have developed a new method for online augmented human state estimation, that uses Interacting Multiple Model Particle Filters with Probabilistic Data Association , which tracks the users’ legs using data from a LRF, while it provides real-time gait phase estimation. We have also presented a new human-robot formation controller that utilizes the gait status characterization for user adaptation towards a fall preventing system .
Gait stability is mostly analysed by using wearable sensors , like motion markers placed on the human body to calculate the body’s CoM and the foot placements , and force sensors to estimate the center of pressure of the feet . Gait stability analysis for walking aid users can be found in . Regarding stability classification, an early approach can be found in , where the authors use the body skeleton provided by the RGB-D Kinect sensor as input and perform action classification to detect four classes of falling scenarios and sitting. However, the system in tested only with a physical therapist performing different walking problems.
Human pose estimation is a challenging topic due to the variable formations of the human body, the parts occlusions, etc. The rise of powerful DL frameworks along with the use of large annotated datasets opened a new era of research for optimal human pose estimation . Most approaches provide solutions regarding the detection of the 2D pose from color images by detecting keypoints or parts on the human body [33, 34] achieving high accuracy. The problem of 3D pose estimation is more challenging , as the detected poses are scaled and normalized. Recent approaches aim to solve the ambiguity of 2D-to-3D correspondences by learning 3D poses from single color images [36, 37]. Another relevant research topic concerns the tracking of human poses , but while achieving improved levels of accuracy compared to previous methods, due to the contribution of DL, the high estimation error makes it prohibitive to integrate it into a robotic application that requires high accuracy and robustness. A recent application of pose estimation for a robotic application can be found in .
Our contributions presented in this work is the design of a novel deep-based framework for on-line human gait stability state prediction using the detection of the upper body 3D pose and the respective CoM estimation from an RGB-D camera and the augmented human gait states estimated from LRF data. Differing from the common gait stability analysis methods in literature, we propose an LSTM-based network for fusing the multi-modal information, in order to decode the hidden interaction of the body’s CoM with the legs motion and the gait phases, in order to predict the gait stability of the elderly considering two possible classes: safe and fall-risk walking. The proposed on-line LSTM-based human gait stability predictor is evaluated using multi-modal data from real patients. To justify the model selection, we present an exploratory study regarding the network architecture, the selected hyperparameters and compare the performance of our framework with baseline methods. The results demonstrate the great efficiency of the LSTM-based approach to provide robust predictions of the human stability state, and show its potential to be integrated into a general user-adaptive control architecture as a fall-risk alarm.
Ii Human Gait Stability
During walking the body is in a continuous state of instability . Gait stability is described by the interaction of the position and velocity of the CoM w.r.t. the Base of Support (BoS) in the horizontal plane. The BoS is the imaginary parallelogram formed by the contact of at least one foot with the ground. During double support phases the BoS covers its largest area, while in single leg support phases (one foot in stance phase while the other swings through) the BoS covers smaller areas. Biomechanics considers an inverted pendulum model to describe the CoM-BoS interaction .
When the projection of the CoM lies inside the BoS the body is stable. However, during gait the CoM is outside the BoS for the single leg support phases, for the most time in a gait cycle. Each foot contact, initiating a new gait cycle, prevents a potential fall . One indicator of human stability is the distance of the CoM to the boundaries of the BoS, which is also the stability measure used in this study.
When the CoM is inside the BoS their respective distance is called stability margin, and when the CoM lies outside the BoS the distance is called CoM separation. The measures of these distances are indicative of the stability of a person while walking. Although a human supported by a walking aid has an enlarged BoS, the reported high fall incidents of walking aid users , along with the fact that users often disengage their hands from the aid to perform several actions, led us to consider the general notion of the BoS in this particular paper.
In Fig. 2 an overview of the proposed LSTM-based on-line human gait stability prediction framework is presented. The proposed method uses multimodal RGB-D and LRF data. The RGB-D data are employed for a deep-based pose detection and the estimation of the CoM position. The LRF data are used in an augmented gait state estimation framework for estimating the legs’ position and the gait phase. These estimated human-motion related parameters constitute the features of the LSTM-based Network for predicting the gait stability state at each time instance, using a binary description of the user’s state as “Safe” or “Risk Fall” state. The components of the whole framework are descried below.
Iii-a Deep-based Pose Detection and CoM Estimation
For the upper body pose estimation, we estimate the body keypoints relative to the camera sensor coordinate system. A Kinect v1 camera provides the RGB images and the respective depth maps. The 2D positions of the keypoints are detected by using the Open Pose (OP) Library 
with fixed weights. OP uses a bottom-up representation of associations of the locations and orientations of the limbs through the images and a two branch multi-stage convolutional neural network to predict the keypoints’ 2D positions. The third dimension of the keypoints is obtained by depth maps. The depth maps need to be transformed to the image plane using the calibration matrix of the camera. For this purpose we have applied the method of.
Despite the high performance of the OP framework, the close proximity of the human body to the Kinect sensor, the occlusions of body parts, such as the head or large part of the arms, from the camera’s field of view (Fig. 2), or even the high reflectivity due to ambient light, leads to many detection losses and misdetections. Thus, tracking is required. When the pose is detected, we use the torso keypoints to compute the 3D position of the center of the torso, as the median of the keypoints. We use information learned from motion markers, which were used in experiments, about the actual placement of the CoM inside the human body and we translate the detected torso center in a position inside the body to represent the detected body’s CoM position.
The detected CoM positions are the observations of an UKF that tracks and estimates the CoM state through time. The UKF servers many purposes; it is used to model and predict the nonlinear CoM motion [43, 44], it filters the noisy observations, it compensates the different frame rates between the Kinect and the LRF sensor by giving predictions of the CoM states during the periods when the sensor does not transmit measurements, and also provides estimates when we do not get/accept the corrupted keypoints detections. Since we aim to examine the interactions of the CoM with the legs states, the CoM state, noted as , includes the CoM position in the sagittal plane w.r.t. a global coordinate system on the rollator (Fig. 1) denoted as , the linear velocity in the walking plane (-plane, Fig. 1) noted as and finally the angular velocity in the axis perpendicular to the walking plane (-axis), denoted as . The CoM state to be estimated is: .
The tracking framework employs the well-known prediction and update equations of the UKF, described in . Given the state the kinematic equations are:
where is the discrete time, is the time interval in which we make predictions and
are the linear and angular velocity noises modelled as zero-mean white Gaussians with standard deviationrespectively.
The observation model is linear , with being the observation matrix: , where
is the 2x2 identity matrix,
is the 2x2 zero matrix and
contains the measurement noises for the observation variables, i.e. the CoM position coordinates. These noise vectors are also modelled as white Gaussians with standard deviationsm for the variable and m for the variable, learned from experiments (higher variability in measuring the from the camera’s depth map). Only the estimated CoM position from the UKF is fed to the LSTM-based network (Fig. 2); let us denote it as .
Iii-B Augmented Gait State Estimation
For the augmented human gait state estimation, we have proposed in  a novel framework for efficient and robust leg tracking from LRF data along with predicting the human gait phases (Fig. 2). This approach uses two Particle Filters (PF) and Probabilistic Data Association (PDA) with an Interacting Multiple Model (IMM) scheme for a real-time selection of the appropriate motion model of the PFs according to the human gait analysis and the use of the Viterbi algorithm for an augmented human gait state estimation. The gait state estimates also interact with the IMM as prior information that drives the Markov sampling process for the selection of the appropriate motion model, while the PDA ensures that the legs of the same person are coupled. A thorough analysis of the methodology is provided in . From this method the augmented state , consisting of the estimated legs’ positions and the respective gait phase, is used in the LSTM-based network (Fig. 2).
Iii-C LSTM-based Network for Gait Stability Prediction
In our learning based method for gait stability prediction we employ a Neural Network (NN) architecture based on LSTM units . LSTM constitutes a recurrent NN that can effectively learn long-term dependencies by incorporating memory cells that allow the network to learn when to forget previous hidden states and when to update hidden states given new information. The overall architecture is an encoder-decoder sequence-to-sequence model, considering only past input vectors to make predictions. It consists of two Fully Connected (FC) layers, two LSTM layers and a last FC layer followed by Softmax (Fig. 2).
Input representation: Let
, be the standardised observations (with zero mean and unit variance) at each time instantt and the sequence of our observations in a temporal window of length . These observations are transformed to the LSTM inputs by feeding them to a network with two FC layers:
where and are the weight and the biases of the two linear layers and. These two fully connected layers have the role of an encoder of the features, helping to encode the nonlinear function of the CoM and the legs for preserving or not stability. In this way, we learn a static transformation and find a better representation for the observations before feeding them to the LSTM unit that models time dependencies.
LSTM Unit: LSTM is composed of an input gate , an input modulation gate , a memory cell , a forget gate and an output gate . LSTM takes the computed inputs at each time step , the previous estimations for the hidden state and the memory cell state , in order to update their states using the equations:
|average RMSE (cm)||2,65||6,13||1,2||6,09||2,5||3,71|
where we have the equations of the four gates: input gate , forget gate , output gate , input modulation gate ) that modulates the memory cell and the hidden state with hidden units. Symbol represents element-wise multiplication, the function is the sigmoid non-linearity and is the hyperbolic tangent non-linearity. , with are the weight matrices of the input and recurrent connection of each gate and
denotes the bias vectors for each gate. The parameters of theand constitute parameters which need to be learned during the training of the NN.
In the last layer (Fig. 2), we estimate the classes of gait stability at each time step ,
with “0” being the Safe class and “1” the Fall Risk class, by learning a linear transformation from the hidden statesto the output state , described by: , where again is the weight matrix and
the bias vector of the output layer. Then, the probability of having a Fall Risk gait is given by taking the softmax:
where denote the trainable parameters of the whole network and are the observations until time .
[b] AUC FScore Accuracy Test dataset: 1 2 3 4 5 mean 1 2 3 4 5 mean 1 2 3 4 5 mean window size: T=100 LSTM, 1, N=256 71,78 65,82 96,67 48,29 53,77 66,87 56,25 65,10 80,74 52,71 63,09 63,58 60,45 55,26 83,20 43,73 52,02 58,93 FC1+FC2+LSTM, , N=256 96,33 69,31 98,88 94,63 92,97 90,61 86,75 78,17 90,42 85,45 89,64 86,13 89,48 67,59 92,77 83,64 85,53 83,60 FC1+FC2+LSTM, , N=128 96,51 66,98 99,01 94,20 93,33 90,01 87,95 80,42 89,52 86,10 89,96 86,79 90,83 69,69 91,70 83,35 86,25 84,36 FC1+FC2+LSTM, , N=256 96,36 67,50 99,08 94,69 93,79 90,28 87,71 79,05 89,76 86,67 89,21 86,48 90,51 68,24 91,92 83,90 85,44 84,00
denotes the layers
|FC1+FC2+LSTM, , N=128|
|window size: T=50||97,26||63,46||98,79||93,90||92,78||89,24||86,97||77,74||88,07||87,84||88,90||85,09||89,43||66,35||90,38||85,13||85,03||83,26|
|window size: T=100||96,51||66,98||99,01||94,20||93,33||90,01||87,95||80,42||89,52||86,10||89,96||86,79||90,83||69,69||91,70||83,35||86,25||84,36|
|window size: T=200||96,11||68,49||98,99||91,99||93,02||89,72||86,56||79,57||90,33||83,06||89,50||85,80||89,53||68,80||92,42||79,84||85,53||83,22|
Iv Experimental Analysis and Results
Iv-a Experimental Setup
Data Collection: The data used in this work were collected in Agaplesion Bethanien Hospital - Geriatric Center with the participation of real patients. The participants presented moderate to mild mobility impairment, according to clinical evaluation. The subjects walked with physical support of a passive robotic rollator, used for the purpose of data collection, in a specific hospital area, while wearing a set of MoCap markers. The visual markers data are used for ground truth extraction. The data for the Gait Stability Prediction were provided by a Kinect v1 camera for capturing the upper body, and a Hokuyo rapid LRF for detecting the legs, which were mounted on the rollator (Fig. 1).
Ground truth extraction from visual markers: For extracting the ground truth labels of the Gait Stability Prediction framework, we followed the methodology described in  for extracting the CoM from visual markers. In our previous work  we have thoroughly described the process of detecting the gait phases from the planar foot impact. As explained in Section II for specifying the body stability we have to analyze the CoM-BoS interaction. Therefore, we detect the BoS according to the respective gait phase and measure the distance of the planar CoM position and evaluate the respective margins of stability. Given the respective average measures of the stability margins found in literature , we label each walking instance as Safe or Fall Risk state. Those two states constitute the ground truth labels used for training the proposed network. We have also conducted statistical analysis on the CoM motion for tuning the UKF used in our framework, and we found the statistics of the BoS size and position w.r.t. the users’ tibia (the level at which the LRF scans the user’s legs) which were used for a baseline rule-based method described below.
Dataset statistics & Data Augmentation: We use a dataset containing data from five patients, resulting in about 11000 frames corresponding to more than 300sec of walking. The dataset consists of 73% safe states, leading to a largely unbalanced dataset. To avoid overfitting, we applied data augmentation by applying on the ground truth CoM data additive random noise exploiting the statistics extracted for the CoM position by initial experimentation, i.e. zero mean and standard deviations in the x-direction and in the y-direction, thus populating the Fall Risk states. The same noise vector was also applied on the pose-based CoM. The final dataset consists of about 22000 frames, with about 46% Fall-Risk labels. We employ a leave-one-out strategy for training/testing, i.e. data from four subjects in training and one in testing iteratively for cross-validation.
Iv-B Evaluation Strategy
For the evaluation of the predicted gait stability labels, we present a thorough analysis regarding different LSTM architectures and other baseline methods by reporting the FScore, Accuracy, Precision and Recall metrics. We also evaluate the Area Under Curve (AUC), which is defined as the area under the Receiver Operating Characteristic (ROC) curve[48, 49]. The ROC curve plots true positive rates vs. false positive rates at different classification thresholds, while AUC helps evaluating the classifier’s performance across all possible classification thresholds. We also demonstrate a brief validation of the CoM position estimation w.r.t. the respective extracted ground truth CoM employing the Root Mean Square Error (RMSE).
As baseline methods we use the nonlinear Support Vector Machine (SVM) classifier with gaussian kernel and the same inputs as the LSTM-based method, as well as a rule-based approach. The rule-based approach follows the biomechanics rules also employed for the ground truth extraction. From the augmented gait state estimation we get the leg’s positions (at knee height) and the respective gait phase. We define the BoS in the horizontal plane employing the statistics learned by the visual markers analysis. Subsequently, we apply the same thresholds for evaluating the stability margins, which were used in the ground truth labels extraction.
Implementation: We trained from scratch the proposed network with
hidden layers in PyTorch using an Nvidia Titan X GPU. The output units of the FC layers FC1, FC2 wereand respectively. For training we employed the Adam optimizer with the Logistic Cross-Entropy Loss for binary classification:
where are the batched training samples, is the binary gait stability label of , and and are the positive safe and fall risk labelled sample sets. is obtained by the softmax activation of the final layer (Eq. 4). We used mini-batches of 256 clips, with initial learning rate , momentum and weight decay
. The learning rate is divided by 10 after half of the epochs. For better regularization and faster training we also have applied dropout with probability
in the FC1 layer and batch normalization after the first two FC layers and the LSTM unit. All subsystems were integrated in ROS .
Iv-C Experimental Results
Validation of CoM estimation: Table I reports the average position RMSE for the CoM w.r.t. the ground truth CoM positions extracted by the visual markers. Only subjects 2 and 4 present higher errors about 6cm error. Fig. 3 depicts the forward CoM displacement, as this is estimated by the UKF (blue line) given the detected CoM from the pose (orange line) w.r.t. the extracted ground truth (red line). We aim to show the difficulty of the dataset, since the ambiguity in the proximal pose detection leads to many occlusions and misdetections which are handled well by the UKF approach.
Evaluation of the LSTM-based prediction model: Table III explores the performance of different network architectures for fixed window size sequences of 100 instances across the whole dataset using the metrics AUC, FScore and Accuracy. We observe that the plain architcture of a simple 1-layer LSTM with N=256 hidden states cannot capture the complexity of the body motion and decode the underlying interaction of the CoM with the legs motion per gait phase. On the contrary, the other models that use the two fully connected layers FC1 and FC2 before the LSTM cells can encode the hidden parameters of the whole body motion, achieving high accuracy. More importantly all three architectures achieve high AUC over 90%, while the FScores are over 86% meaning that they can be used for providing precise predictions about the safety of the rollator user. As for per user performance, it is evident that all network architectures perform worse when predicting subject’s stability state. This poor performance is highly influenced by the higher CoM estimation errors as can be seen in Table I, or even a kind of pathological gait unseen to the system, since we only had available data from five patients. However, the existence of patient data in the other four training datasets did not influence the performance; indeed the deep networks could decode the different types of walking and achieve high performance in spite of the estimation noise and errors from the tracking systems.
From this exploratory study, we choose as our main network architecture the FC1+FC2+LSTMs with 2 layers of N=128 hidden variables, as it achieves the best FScore and Accuracy rate, while hitting a 90% mean AUC. In Table III, we explore the influence of the temporal window size on the proposed model. We cross-evaluate the results for all datasets and present the AUC, FScore and Accuracy measures. We observe the most consistent performance across all metrics for input sequences of 100 instances.
The final part of the experimental evaluation presents the cross-examination of the proposed model w.r.t. baseline methods. As described previously, we compare the LSTM-based network with the rule-based method, with an SVM classifier and for the sake of generality with the simple LSTM (no initial FC layers) of Table III. We evaluate the average metrics across all datasets. Inspecting the results, the rule based method achieves an accuracy of 80% and an analogous FScore. This finding is a strong indicator that our analysis about predicting the stability state by fusing the data from the body pose and the gait state estimates is plausible. The rule-based method is a discrete process that does not include probabilities computation like the rest of the methods; thus the AUC could not be evaluated.
On the other hand, we notice that the SVM classifier performs very well. This was well expected, since the SVM classifier with nonlinear kernel is known to work well in binary classification problems with relatively small datasets. However, the proposed network improves the SVM scores as it achieves 4% better FScore and ameliorates the AUC score by 3%. The plain LSTM model achieves again the poorest results, as in Table III, since it is evident that there is an underlying nonlinear relation between the CoM and the gait states, which is encoded by the fully connected layers. For better understanding of the results of this table, we plot the ROC curve for the SVM, LSTM, the proposed network, and the random predictor across all possible classification thresholds. Although, all methods perform better than random predictor, the proposed fully connected LSTM-based network outperform all the other methods at all cases.
V Conclusions & Future Work
In this work have presented and experimentally evaluated a novel and robust method for on-line gait stability analysis of elderly subjects walking with a mobility assistant platform. The proposed method is fusing the information from an RGB-D camera which captures the upper body and a LRF which monitors the legs motion. We use the OP framework for detecting the upper body pose, we track the respective CoM, while we exploit the LRF data in an augmented gait state estimation framework for extraction the legs’ position and the respective gait phase. Our main contribution is the proposal of a novel LSTM-based network for predicting the stability state of the elderly, by classifying walking as safe or fall-risk at each instant.
In the future, we plan to increase our datasets for training and evaluation of the proposed model and integrate it into a user-adaptive context-aware robot control architecture with a fall-prevention functionality for an intelligent robotic assistant platform.
-  T. W. Bank, “Population ages 65 and above,” 2017.
J. M. Hausdorff, “Gait dynamics, fractals and falls: Finding meaning in the stride-to-stride fluctuations of human walking,”Human Movement Science 2007.
-  F. Garcia-Pinillos et. al, “Gait speed in older people: an easy test for detecting cognitive impairment, functional independence, and health state,” Psychogeriatrics, 2016.
-  S. D. et.al., “Pamm - a robotic aid to the elderly for mobility assistance and monitoring: A ’helping-hand’ for the elderly,” in IEEE Int’l Conf. on Robotics and Automation, 2000, pp. 570–576.
-  B. Graf, M. Hans, and R. D. Schraft, “Mobile robot assistants,” IEEE Robotics Automation Magazine, vol. 11, no. 2, pp. 67–77, June 2004.
-  D. Rodriguez-Losada, F. Matia, A. Jimenez, R. Galan, and G. Lacey, “Implementing map based navigation in guido, the robotic smartwalker,” in Proceedings of the 2005 IEEE International Conference on Robotics and Automation, April 2005, pp. 3390–3395.
-  V. Kulyukin, A. Kutiyanawala, E. LoPresti, J. Matthews, and R. Simpson, “iwalker: Toward a rollator-mounted wayfinding system for the elderly,” in 2008 IEEE International Conference on RFID, April 2008, pp. 303–311.
-  T. Ohnuma et. al., “Particle filter based lower limb prediction and motion control for jaist active robotic walker,” in 2014 RO-MAN.
-  S. Jenkins et. al, “Care, monitoring, and companionship: Views on care robots from older people and their carers,” International Journal of Social Robotics, 2015.
-  G. Chalvatzaki, X. S. Papageorgiou, and C. S. Tzafestas, “Towards a user-adaptive context-aware robotic walker with a pathological gait assessment system: First experimental study,” in 2017 IEEE/RSJ International Conference on Intelligent Robots and Systems (IROS), Sept 2017, pp. 5037–5042.
-  ——, “User-adaptive human-robot formation control for an intelligent robotic walker using augmented human state estimation and pathological gait characterization,” in 2018 IEEE/RSJ International Conference on Intelligent Robots and Systems (IROS), Oct 2018.
-  G. Chalvatzaki, X. S. Papageorgiou, C. S. Tzafestas, and P. Maragos, “Augmented human state estimation using interacting multiple model particle filters with probabilistic data association,” IEEE Robotics and Automation Letters, vol. 3, no. 3, pp. 1872–1879, July 2018.
-  Y. S. Delahoz and M. A. Labrador, “Survey on fall detection and fall prevention using wearable and external sensors,” Sensors, vol. 14, no. 10, pp. 19 806–19 842, 2014. [Online]. Available: http://www.mdpi.com/1424-8220/14/10/19806
-  O. Chuy et. al, “Environment feedback for robotic walking support system control,” in 2007 IEEE International Conference on Robotics and Automation (ICRA), April 2007, pp. 3633–3638.
-  C. A. Cifuentes and A. Frizera, Development of a Cognitive HRI Strategy for Mobile Robot Control. Springer International Publishing, 2016.
-  M. Geravand et. al, “An integrated decision making approach for adaptive shared control of mobility assistance robots,” Int’l J. of Social Robotics, 2016.
-  Y. Hirata et. al, “Motion control of intelligent passive-type walker for fall-prevention function based on estimation of user state,” in 2017 IEEE International Conference on Robotics and Automation (ICRA).
-  Y. Hirata, S. Komatsuda, and K. Kosuge, “Fall prevention control of passive intelligent walker based on human model,” in 2008 IEEE/RSJ International Conference on Intelligent Robots and Systems, Sept 2008, pp. 1222–1228.
-  M. Takeda, Y. Hirata, K. Kosuge, T. Katayama, Y. Mizuta, and A. Koujina, “Human cog estimation for assistive robots using a small number of sensors,” in 2017 IEEE International Conference on Robotics and Automation (ICRA), May 2017, pp. 6052–6057.
-  P. Di, J. Huang, S. Nakagawa, K. Sekiyama, and T. Fukuda, “Fall detection and prevention in the elderly based on the zmp stability control,” in 2013 IEEE Workshop on Advanced Robotics and its Social Impacts, Nov 2013, pp. 82–87.
-  P. Di, Y. Hasegawa, S. Nakagawa, K. Sekiyama, T. Fukuda, J. Huang, and Q. Huang, “Fall detection and prevention control using walking-aid cane robot,” IEEE/ASME Transactions on Mechatronics, vol. 21, no. 2, pp. 625–637, April 2016.
-  J. Bae and M. Tomizuka, “Gait phase analysis based on a hidden markov model,” Mechatronics, 2011.
-  C. Nickel et. al., “Using hidden markov models for accelerometer-based biometric gait recognition,” in CSPA 2011.
-  X. S. Papageorgiou, G. Chalvatzaki, C. S. Tzafestas, and P. Maragos, “Hidden markov modeling of human normal gait using laser range finder for a mobility assistance robot,” in 2014 IEEE International Conference on Robotics and Automation (ICRA), May 2014, pp. 482–487.
-  ——, “Hidden markov modeling of human pathological gait using laser range finder for an assisted living intelligent robotic walker,” in 2015 IEEE/RSJ International Conference on Intelligent Robots and Systems (IROS), Sept 2015, pp. 6342–6347.
-  X. S. Papageorgiou, G. Chalvatzaki, K. N. Lianos, C. Werner, K. Hauer, C. S. Tzafestas, and P. Maragos, “Experimental validation of human pathological gait analysis for an assisted living intelligent robotic walker,” in 2016 6th IEEE International Conference on Biomedical Robotics and Biomechatronics (BioRob), June 2016, pp. 1086–1091.
-  S. Page, K. Mun, Z. Guo, F. A. Reyes, H. Yu, and V. Pasqui, “Unbalance detection to avoid falls with the use of a smart walker,” in 2016 6th IEEE International Conference on Biomedical Robotics and Biomechatronics (BioRob), June 2016, pp. 1000–1005.
-  V. Lugade, V. Lin, and L.-S. Chou, “Center of mass and base of support interaction during gait,” Gait and Posture, vol. 33, no. 3, pp. 406 – 411, 2011. [Online]. Available: http://www.sciencedirect.com/science/article/pii/S096663621000442X
-  C.-W. Huang, P.-D. Sue, M. F. Abbod, B. C. Jiang, and J.-S. Shieh, “Measuring center of pressure signals to quantify human balance using multivariate multiscale entropy by designing a force platform,” Sensors, vol. 13, no. 8, pp. 10 151–10 166, 2013. [Online]. Available: http://www.mdpi.com/1424-8220/13/8/10151
-  E. Costamagna, S. Thies, L. Kenney, D. Howard, A. Liu, and D. Ogden, “A generalisable methodology for stability assessment of walking aid users,” Medical Engineering and Physics, vol. 47, pp. 167 – 175, 2017. [Online]. Available: http://www.sciencedirect.com/science/article/pii/S1350453317301510
-  S. Taghvaei, Y. Hirata, and K. Kosuge, “Visual human action classification for control of a passive walker,” in 2017 7th International Conference on Modeling, Simulation, and Applied Optimization (ICMSAO), April 2017, pp. 1–5.
-  M. Andriluka, L. Pishchulin, P. Gehler, and B. Schiele, “2d human pose estimation: New benchmark and state of the art analysis,” in
-  S. Wei, V. Ramakrishna, T. Kanade, and Y. Sheikh, “Convolutional pose machines,” in 2016 IEEE Conference on Computer Vision and Pattern Recognition (CVPR), June 2016, pp. 4724–4732.
-  Z. Cao, T. Simon, S. Wei, and Y. Sheikh, “Realtime multi-person 2d pose estimation using part affinity fields,” in 2017 IEEE Conference on Computer Vision and Pattern Recognition (CVPR), July 2017, pp. 1302–1310.
-  J. Martinez, R. Hossain, J. Romero, and J. J. Little, “A simple yet effective baseline for 3d human pose estimation,” in ICCV, 2017.
-  G. Pavlakos, L. Zhu, X. Zhou, and K. Daniilidis, “Learning to estimate 3D human pose and shape from a single color image,” in Proceedings of the IEEE Conference on Computer Vision and Pattern Recognition, 2018.
-  G. Pavlakos, X. Zhou, and K. Daniilidis, “Ordinal depth supervision for 3D human pose estimation,” in Proceedings of the IEEE Conference on Computer Vision and Pattern Recognition, 2018.
-  R. Girdhar, G. Gkioxari, L. Torresani, M. Paluri, and D. Tran, “Detect-and-Track: Efficient Pose Estimation in Videos,” in CVPR, 2018.
-  C. Zimmermann, T. Welschehold, C. Dornhege, W. Burgard, and T. Brox, “3d human pose estimation in rgbd images for robotic task learning,” in IEEE International Conference on Robotics and Automation (ICRA), 2018. [Online]. Available: https://lmb.informatik.uni-freiburg.de/projects/rgbd-pose3d/
-  S. M. Bruijn and J. H. van Dieën, “Control of human gait stability through foot placement,” Journal of The Royal Society Interface, vol. 15, no. 143, 2018. [Online]. Available: http://rsif.royalsocietypublishing.org/content/15/143/20170816
-  Y. chung Pai and J. Patton, “Center of mass velocity-position predictions for balance control.” Journal of biomechanics, vol. 30 4, pp. 347–54, 1997.
-  T. R. de Mettelinge and D. Cambier, “Understanding the relationship between walking aids and falls in older adults: a prospective cohort study.” Journal of geriatric physical therapy, vol. 38 3, pp. 127–32, 2015.
-  M. Jacquelin Perry, Gait Analysis: Normal and Pathological Function, 1st ed., C. Bryan Malas, MHPE, Ed. SLACK Incorporated, 1992.
-  N. Belloto and H. Hu, “People tracking with a mobile robot: A comparison of kalman and particle filters.” IASTED 2007.
-  E. A. Wan et al., “The unscented kalman filter for nonlinear estimation,” in Proc. of IEEE Adaptive Systems for Signal Processing, Communications, and Control Symposium, 2000, pp. 153–158.
-  S. Hochreiter and J. Schmidhuber, “Long short-term memory,” Neural computation, vol. 9, no. 8, pp. 1735–1780, 1997.
-  G. Chalvatzaki, X. S. Papageorgiou, C. S. Tzafestas, and P. Maragos, “Estimating double support in pathological gaits using an hmm-based analyzer for an intelligent robotic walker,” in 2017 26th IEEE International Symposium on Robot and Human Interactive Communication (RO-MAN), Aug 2017, pp. 101–106.
J. Davis and M. Goadrich, “The relationship between precision-recall and roc
Proceedings of the 23rd international conference on Machine learning. ACM, 2006, pp. 233–240.
-  P. Koutras and P. Maragos, “A perceptually based spatio-temporal computational framework for visual saliency estimation,” Signal Processing: Image Communication, vol. 38, pp. 15 – 31, 2015, recent Advances in Saliency Models, Applications and Evaluations. [Online]. Available: http://www.sciencedirect.com/science/article/pii/S0923596515001290
-  S. Ioffe and C. Szegedy, “Batch normalization: Accelerating deep network training by reducing internal covariate shift,” in Proceedings of the 32Nd International Conference on International Conference on Machine Learning - Volume 37, ser. ICML’15. JMLR.org, 2015, pp. 448–456. [Online]. Available: http://dl.acm.org/citation.cfm?id=3045118.3045167
-  M. Quigley, K. Conley, B. P. Gerkey, J. Faust, T. Foote, J. Leibs, R. Wheeler, and A. Y. Ng, “Ros: an open-source robot operating system,” in ICRA Workshop on Open Source Software, 2009.