 Research
 Open Access
 Published:
Machinelearningbased children’s pathological gait classification with lowcost gaitrecognition system
BioMedical Engineering OnLine volume 20, Article number: 62 (2021)
Abstract
Background
Pathological gaits of children may lead to terrible diseases, such as osteoarthritis or scoliosis. By monitoring the gait pattern of a child, proper therapeutic measures can be recommended to avoid the terrible consequence. However, lowcost systems for pathological gait recognition of children automatically have not been on market yet. Our goal was to design a lowcost gaitrecognition system for children with only pressure information.
Methods
In this study, we design a pathological gaitrecognition system (PGRS) with an 8 × 8 pressuresensor array. An intelligent gaitrecognition method (IGRM) based on machine learning and pure plantar pressure information is also proposed in static and dynamic sections to realize high accuracy and good realtime performance. To verifying the recognition effect, a total of 17 children were recruited in the experiments wearing PGRS to recognize three pathological gaits (toein, toeout, and flat) and normal gait. Children are asked to walk naturally on level ground in the dynamic section or stand naturally and comfortably in the static section. The evaluation of the performance of recognition results included stratified tenfold crossvalidation with recall, precision, and a time cost as metrics.
Results
The experimental results show that all of the IGRMs have been identified with a practically applicable degree of average accuracy either in the dynamic or static section. Experimental results indicate that the IGRM has 92.41% and 97.79% intrasubject recognition accuracy, and 85.78% and 78.81% intersubject recognition accuracy, respectively, in the static and dynamic sections. And we find methods in the static section have less recognition accuracy due to the unnatural gesture of children when standing.
Conclusions
In this study, a lowcost PGRS has been verified and realize feasibility, highly average precision, and good realtime performance of gait recognition. The experimental results reveal the potential for the computer supervision of nonpathological and pathological gaits in the plantarpressure patterns of children and for providing feedback in the application of gaitabnormality rectification.
Background
Children are prone to have pathological gaits when starting toddling, which may cause osteoarthritis, scoliosis, or other debilitating diseases. To monitoring the pathological gait pattern of a human, various biosignals are adopted among which kinematics information and plantarpressure show more potential for their easy to measure and explain [1, 2]. These highdimensional biosignals indicate complex states of human muscles and joints [3], which cause difficulty to interpret directly by conventional kinematics or kinetics. However, machine learning (ML) recently has more potential to deal with the largedatadriven patternrecognition problems with the development of computer technology [1, 4].
Employing computervision technology, kinematics information can be easily acquired. Elham et al. acquired gait features including angles, velocity, and acceleration of the joints based on Kinect skeletal tracking sequences [5]. Two ML approaches, an instancebased discriminative classifier and a dynamical generative classifier, were examined to distinguish between healthy and pathological gaits. F1score of the former can reach up to 96% when walking at a fast pace. Javier et al. developed visionbased gaitimpairment analysis for aided diagnosis [6]. A number of semantic and normalized gait features were computed from a single video to provide samples under eight different walking styles: one normal and seven impaired patterns. Several statistical studies were carried out to prove the sensitivity of features in measuring the expected pathologies. Zakaria et al. [7] classified Autism Spectrum Disorder (ASD) children’s gait from normal gait. Gait features were the absolute or relative Cartesian coordinates of 20 joints of the subject measured by a depth camera. Various methods were used to classify these two gaits, among which support vector machine (SVM) classifier has the lowest accuracy, 98.67%, and Naives Bayes classifier has the highest accuracy, 99.66%. Chen et al. [8] proposed a gait classification and develop a simple and efficient method for the quantification method for parkinsonian gait from monocular video imaging based on kernelbased principal component analysis. Faragó et al. [9, 10] proposed a framework for classifying normal walking, heelwalking, and toewalking based on the crosscorrelation of plantar pressures with corresponding lowerlimb EMG signals.
Plantar pressure contains abundant gaitpattern information, which can be used to reasonably predict and explain human physiological diseases [2]. However, it has high dimensionality, temporal dependence, high variability, complex correlations between curves, and high nonlinear relationship features [4]. Mei et al.[11, 12] analyzed the force of center of pressure (CoP) sample entropy characteristics among the four types, pes cavus, pes valgus, hallux valgus, and normal feet, using the Footscan system. The study showed that dynamic characteristics of CoP progression contain information of the foot type. Zhu et al. [13] developed an umbilical dataacquisition system to measure the pressure between the foot and shoe during walking that had seven forcesensitive resistors (FSRs) on the surface of each insole of a pair of extradepth shoes. The team found that a shuffling gait with short steps would increase the period of foot flat and thus minimize any excessive local plantar pressures [14]. Lin et al. [15] employed dynamic features derived from tracking gait to recognize individuals. The selforganizingmap (SOM) neural network (NN) algorithm and SVM were used in both schemes for data classification. Experiments showed that a higher recognition rate was achieved with the method using all of the plantar pressure sensorcell values during walking regardless of the algorithm used, which suggested that the footpressure distribution of gait is a suitable feature for gait recognition. Sazonov et al. [16] built a NN to predict geriatric patterns using plantar pressure and heel acceleration information, whose classification accuracy was 91.6% on average. Data for training the NN were collected by sensor shoes with 34 pressuresensing elements uniformly distributed across the foot and a 2D accelerometer. Based on a shoeintegrated system with an inertial measurement unit (IMU), four FSRs, and a bend sensor, Chen et al. [17] applied principal component analysis (PCA) and SVM for multipattern classification (toein, toeout, oversupination, heelwalking, and normal pattern). A total of four subjects tested the shoeintegrated device in outdoor environments. Experimental results of the four subjects demonstrated that the proposed method was robust and highly accurate up to 90%. More interestingly, the study showed that insole sensors played a more important role in solving classification problems than IMUs.
Here, three foot types of children including toein, toeout, and flat feet are concerned. Toein, toeout, and flat feet are the most common reasons for parental concerns and referral for a specialist opinion about their children’s gait [18]. The vast majority of pathological gait may correct spontaneously if left untreated [19,20,21,22,23] due to the underdeveloped skeleton of children, which makes it more of a concern to the parents than to the podiatrist. However, since the theoretical explanation and analysis for the selfhealing capability is unclear, the child's gait still needs constant attention. Thus, designing a device for parents to watch children’s gait periodically at home is of high necessity. Many underlying causes leading to in or outtoeing gait lies in the hip joint, femur, or tibia or the hindfoot or forefoot [18]. The most straightforward physical examination method is measuring foot progression angle (FPA) which describes the orientation of the child’s foot to the direction of progression. For a normal child, FPA is slightly outtoed (+ 10°) with a range from −3° to + 20° [24, 25]. If FPA is less than −3°, a child is considered to have an intoeing gait and if it is more than 20°, a child is considered to have an outtoeing gait. And FPA can influence the distribution of the plantar pressure. Rosenbaum [26] found that intoeing increasingly loads the lateral aspects of the midfoot and forefoot by as much as 61% and 49%, respectively, whereas outtoeing intensifies the load on the medial aspect, i.e., predominantly the medial midfoot and medial forefoot by as much as 72% and 52%. Traditionally, a flat foot can also be diagnosed by measuring the area of contact between the foot and the ground [22, 27]. However, as far as we are concerned, there is no related lowcost system for pathological gait recognition of children automatically for ordinary parents with only pressure information. The contributions of this study are the following:

1)
A lowcost pathological gaitrecognition system (PGRS) with an 8 × 8 pressure sensor array is built. With this system, parents can watch children’s gait state daily without the need to consult a podiatrist frequently in hospital. This not only reduces the worry and anxiety of parents, but also improves the efficiency of podiatrists, reducing the pointless counseling for childhood gait.

2)
A highly accurate and fast intelligent gaitrecognition method (IGRM) is realized in static and dynamic situations utilizing only plantarpressure data.

3)
The effects of the algorithm with plantar pressure data collected in both static and dynamic sections are compared. And the research shows that the IGRMs in the dynamic section have higher average accuracy than those in the static section.
Methods
To deal with the gait data with high dimensionality, temporal dependence, high variability, correlations between curves, and nonlinear relationships [4], the proposed gaitrecognition algorithm has three steps: feature extraction, feature reduction, and classification. Figure 1 shows an overview of the abnormal gaitrecognition algorithm and corresponding gait patterns. Firstly, the data are transformed from time domain to orthogonal domain to handle the gait’s temporal dependence and get data features. Here, several transformations can be used, for example, fast Walsh transform (FWT), discrete cosine transform (DCT), and fast Fourier transform (FFT), among which FFT, used in the proposed IGRM, is the most common and effective one [17, 28,29,30,31,32,33]. After feature extraction by FFT, feature combination and feature reduction algorithms, PCA and LDA, are done to make gaitdata dimensionality lower to apply it in realtime situations. Finally, to handle the highvariability problem, correlations between curves, and nonlinear relationships, a robust classification algorithm is used.
Gait feature extraction from gait cycle
In the dynamic situation where subjects walk naturally on the level ground wearing PGRS, the detailed gait featureextraction process is shown in Fig. 2. For lengthL data, the kth feature of the FFT \(S(k)\) can be obtained through
where k is the integer between 0 (included) and L1 (included); \(W\) is \(e^{{  j2\pi /L}}\); n is the time series and \(t(n)\) \(t(n)\) represents the data value at time n.
Simple data sampling strategy with the sliding window method is used to make a proper classification on the assumption that the stochastic process related to the features is stationary over the window interval. We find that if a window interval L is chosen wide enough to include multiple gait periods, then the assumption can be acceptable. Consequently, in this step, the temporal dependence is removed through FFT. In this paper, the sliding window is Hanning window with a width of 512 sample intervals (50 Hz sample frequency, corresponding to about 10 gait periods). A 512length vector \(S(k)\) can be got by transforming the plantarpressure data in the sliding window to frequency domain using FFT. The vector denotes the energy information distribution on the frequency domain of a pressure sensor block during walking. Therefore, vectors \(S_{{i,j}} (k)\), where \(i\) = 1…8 and \(j\) = 1…8, including all 8 × 8 sensor blocks’ frequency information can describe the entire foot energy information distribution. Since the experiments show that the major information of children’s gait data is between 0 and 10 Hz, gait data are divided into five groups which are 0 (exclude)–2 Hz, 2 (exclude)–4 Hz, 4 (exclude)–6 Hz, 6 (exclude)–8 Hz, and 8 (exclude)–10 Hz. This division of groups is optimized by conducting repeatedly the experiments with different number of groups to get the best performance of prediction accuracy, prediction accuracy variation, prediction time cost on the overall classification task. Summing all of the amplitude of frequency components in each group, the 512length vector \(S(k)\) is transformed to a fiveelement feature vector. To denote the information of the entire foot, 30 fiveelement feature vectors from 30 sensors are joined together, obtaining a 150element vector as a training sample. Note that bodyweight is different for different children, the 0 Hz pressure information is excluded and the 150element training sample is normalized to a unit vector to eliminate the weight information influence when classifying the foot types.
In the static situation where subjects stand naturally on the level ground wearing PGRS, the 0 Hz pressure information is kept only and the feature number of a plantar pressure sensor is no longer five but one. The final training sample for gait recognition becomes a 30element vector. Normalization is also used to vanish the influence of the bodyweight of the subjects.
Feature reduction
In this step, plantarpressure information is further compressed and keeps effectiveness at the same time. As a quite effective and common unsupervised method in signal processing, PCA keeps the variance of the original data during the dimension reduction. However, PCA may cause a mixup of differentlabel data in some situations, as Fig. 3a shows. In these situations, another supervised method, LDA, is more efficient. LDA maximizes the average differences among class projections while minimizing average projections of each class (intraclass) after feature reduction. In mathematics, the main idea of LDA can be described as maximizing \(J\left( W \right)\):
where \(S_{B}\) and \(S_{W}\) are the dispersion between two different classes and within a class, respectively; i and j represent the class number; symbol \(\sim\) represents the variable after dimensional reduction and \({\mathbf{W}}^{T}\) is defined as the corresponding transformation matrix.
Gaitclassification model
Our goal in this step is to classify the gaits into different classes, i.e., toein, toeout, flat, and normal according to the feature vectors. Many algorithms in the machine learning field can be used for binary classification problems. In this paper, NN and SVM are used to perform the gaitclassification function.
As many researchers have proved, SVM can work very well for multidimensional data[34, 35]. More importantly, sma3ll computation is needed for the final decision function of SVM which comprised only a few support vectors. As shown in Fig. b, it obtains a hyperplane, \({\mathbf{\omega }}^{{\mathbf{T}}} {\mathbf{x}} + b{\text{ = }}0\), to classify two classes by maximizing the margin to the closest data from two classes separately. The decision function can be described as
where \({\mathbf{x}}\) is the feature vector, \({\mathbf{\omega }}\) is the normal vector to the hyperplane, \(\frac{b}{{\left\ {\mathbf{\omega }} \right\}}\) determines the offset of the hyperplane, and \(y\) are either 1 or −1, each indicating the class to which the feature vector belongs. A linear SVM’s goal is to minimize the risk function:
where the term \({\mathbf{\omega }}^{{\mathbf{T}}} {\mathbf{\omega }}\) \({\omega }^{T}\omega \) is called the regularization term and \(C\sum\limits_{{i = 1}}^{N} {\xi _{i} }\) is empirical tolerance [36]. Empirical tolerance is not only used to remove data noise, but also to deal with data nonlinearly separable. To obtain the linear inseparable classification model, the penalty parameter \(C\) calculates the penalties for errors by determining the tradeoff between the empirical tolerance and regularized term. The larger \(C\) is, the stronger penalties are assigned to errors.
To solve the nonlinear classification problem effectively, a kernel function is introduced to the decision function:
where \(\phi \left( {{\mathbf{x}}_{{\mathbf{i}}} ,{\mathbf{x}}} \right)\) is a kernel function that maps \({\mathbf{x}}\) \(\boldsymbol{x}\) space to a higherdimensional space so that a hyperplane can be found to classify samples. In this paper, linear or RBF kernel is used in our classification model. To solve this formulation, SVM can be trained by Platt's sequential minimal optimization (SMO) algorithm [37].
NN is a network of neurons and the connections of biological neurons are modeled as weights. Training the weight using the backpropagation algorithm, NN can learn the mapping relationship between input and output. Regardless of its powerful ability for solving nonlinear problems, NN is a black box comparing with explainable and intuitive SVM.
Results
In this part, a lowcost PGRS is built to measure children’s plantarpressure data during walking, and children's experiments in dynamic and static sections are designed to verify the performance of recall, precision, and time cost of the IGRM. Several typical gaits, namely, toein, toeout, flat, and normal, are involved. All of the subjects signed informed consent forms before experiments.
Pathological gaitrecognition system
As shown in Fig. 4, a PGRS consists of an 8 × 8 pressuresensor array, a signalcollecting circuit, a microcomputing unit, and a wearable shoeintegrated mechanism is designed.
The plantar pressure of adults is in the range of 0–1000 kPa during walking [38], and the maximal pressure can up to approximately 1400 kPa when doing sports. Based on weight conversion, children's plantar pressure is estimated to be in the range of 0 to 700 kPa. Therefore, the pressuredetection range of the sensor array is chosen as 0–1000 kPa. The 8 × 8 piezoresistive sensor array structure and parameter characteristics of this series (Changzhou Roxi Electronic Technology Co. LTD, China) are shown in Fig. 5a and b. The relationship of load pressure \(P\) \(P\) onto the sensor and its resistance \(R_{x}\) \({R}_{x}\) can be described as:
where \(K_{{p  r}}\) is the sensor characteristic constant.
In sensor calibration process, a set of standard weights are used to load on the sensor block. The load is added from 0 to 11 kg and then reduced from 11 to 0 kg for each sensor block twice, and linear regression was applied to the data by least square method to get the calibration line. All the test results of the 8 × 8 sensors’ performance using the control circuit mentioned below are shown in Fig. 5c, indicating its good repeatability and linearity.
For the signalcollecting circuit and the microcomputing unit, as the schematic is shown in Fig. 6a, a microcontroller (STM32F103C8T6 with CortexM3 core and a maximum CPU speed of 72 MHz; STMicroelectronics Corp., USA) was chosen as its control core. Noninverting amplifier converts resistor of the sensor \(R_{x}\) to voltage \(V_{{out}}\). The charging resistor \(R_{0}\) used to stable the ADC output is 1 KΩ [39]. We use two pieces of quad bilateral switch HCF4066B chip (STMicroelectronics Corp., USA) to compose one 8:1 analog switch. The state of the switch is controlled by the logic level of I/O from the microcontroller. The microcontroller is programmed to select the sensor block one by one using two 8:1 analog switches and to read the sensor block’s output. Two 4.2V Liion batteries provide power, generating 5 V with LM7805 (KIA7805AP, threeterminal positive voltage regulator of 5 V, KEC, China) for the signalcollecting circuit and 3.3 V with AMS117 (lowdropoutvoltage regulator with fixed 3.3 V, Advanced Monolithic Systems, Inc.) for the microcontroller.
Through an amplifier and feedback resistance \(R_{f}\) \({R}_{f}\), the output voltage \(V_{{out}}\) of the amplifier is linear to the pressure sensor received. Defining \(D_{{{\text{output}}}}\),\(V_{{{\text{adc\_ref}}}}\) and \(m\) as the digital value received by the analogtodigital converter (ADC), the reference voltage and resolution of the ADC, respectively, \(V_{{out}}\) \({V}_{out}\) is related to the resistance of a specific sensor. We have
where \(V_{{{\text{adc\_ref}}}}\) is 5 V, \(V_{{ref}}\) is 0.5 V and m is 10 in the experiments, so that the load pressure \(P\) can be reflected by \(D_{{{\text{output}}}}\).
During the test, it was found that the pressure on one sensor would lead to an unexpected output of the rest of the sensors. Crosstalk is found between sensor blocks caused by current path 2 and path 3 when measuring the sensor value at (1,1), where (No. 1, No. 2) means the sensor block at row channel No. 1 and column channel No. 2, as shown in Fig. 6a. The closer the distance between two sensors is, the stronger their interactions are. To extract individual sensor resistor value one after another from the 8 × 8 sensor array and eliminate the crosstalk between each sensor, as shown in Fig. 6b [40, 41], the active sensor during readout was selected by grounding one of the 8:1 analog switch channels on the column, while other channels are pulling up to \(V_{{{\text{ref}}}}\) \({V}_{ref}\). The same control operation is applied to row pins of the 8 × 8 sensor array at the same time, so that the current path except path 1 such as path 2 will be cut off. The sampling result shown in Fig. 6c indicates that the ADC output value (maximum is 1024) of a certain sensor influenced by other sensors is within 10 (32.2 mV output, corresponding to 0.282 kg loaded), which is much better than the previous maximum, almost 70 (225 mV output, corresponding to 1.977 kg loaded).
Gaitpressure data collection
A GUIbased program using MatLab R2016a (MathWorks, USA) was designed to make the pressure information more available and more visual. Its flowchart is shown in Fig. 7 , which has functions of filtering the pressure data, showing the realtime pressure data curve of a specific plantarpressure sensor, saving pressure data in the computer, and obtaining the gaitpattern results.
To meet the expected situation where people normally want to have low disturbance in slow signals and low lag in fast signals, the filter used in the aforementioned program is One Euro filter [42]. And [41] has found that a straightforward linear relationship between cutoff frequency and the absolute speed of the input signal works well. To construct One Euro filter, the frequency spectrum information of input is studied. Based on the experiment data collected at the Children's Hospital, Zhejiang University School of Medicine, the frequency spectrum of plantarpressure data of the children shows almost all information is located in 0–10 Hz, which is similar to the features found by Hangqi Wei [43] about adult plantar pressure.
As shown in Table 1, 17 subjects who had undergone gait diagnosis by a specialist were recruited to participate in the experiment. The experiments are divided into two sections: dynamic and static section. The experimental procedures of the dynamic section are shown in Fig. 8. Subjects are asked to walk naturally for 10 m two times with a 2min gap on level ground. In the static section, children are expected to stand naturally and comfortably for about 10 s five times.
One example of the collected plantarpressure data in the dynamic section is shown in Fig. 9a. The plantarpressure curve can be divided into several gait phases: initial contact (IC), loading response (LR), midstance (MS), terminal stance (TS), preswing (PS), and swing phase (SP). And typical toein, toeout, and normal footpressure distribution in static section is shown in Fig. 9b.
Gaitrecognition results
The IGRM is coded in Python with scikitlearn library. PCA or linear discriminant analysis (LDA) is used to reduce plantarpressure data dimension in both dynamic and static sections. Coefficient gamma of RBF kernel in SVM is chosen as 1/(features × variance of data) and penalty parameter C is 1. The layer of the NN is 3 and the neuron number of the hidden layer is 10. The total experiment samples are 20,000 in which normal, toein, toeout, and flat have 5000 samples, respectively, in the dynamic section and 1308 in which normal, toein, toeout, and flat have 327 samples, respectively, in the static section. The scheme of evaluation included stratified tenfold crossvalidation with recall, precision, and a time cost as metrics. All statistical analysis was performed using SPSS version 22 (SPSS Inc., Chicago, IL, USA). the time cost is calculated by predicting 2000 samples in the dynamic section or 130 samples in the static section using the same computer.
Experimental performances of dynamic and static sections, respectively, are shown in Tables 2 and 3. Figure 10 shows the distribution of the accuracy of different types of algorithms which are evaluated by tenfold crossvalidation and the average time cost per fold. The classification result of classification models to all the samples is shown in the average confusion matrix in Fig. 11.
According to Table 2, in the dynamic section, LDA + SVMlin reaches the highest average accuracy, 97.79%. In the term of accuracy, independent ttest shows a significant difference between LDA + SVMlin and PCA + SVMlin (Pvalue = 0.007). There is no significant accuracy difference among LDA + SVMrbf, PCA + SVMrbf, and LDA + NN. However, LDA + SVMlin, 4.40 ms per 2000 samples, has a significant smaller time cost than LDA + SVMrbf (Pvalue < < 0.01), PCA + SVMlin (Pvalue < < 0.01), and PCA + SVMrbf (Pvalue < < 0.01). PCA + SVMlin has the largest time cost (Pvalue < < 0.01), 75.2 ms per 2000 samples. In the static section, PCA + SVMrbf reaches the highest average accuracy, 92.41%. However, PCA + SVMrbf has a significantly larger time cost than others (Pvalue < < 0.01), 2.07 ms per 130 samples. Compared with other algorithms, LDA + SVMlin has no significant difference with other algorithms in terms of accuracy, but it has a significantly smaller time cost (Pvalue < < 0.01) than LDA + SVMrbf, PCA + SVMlin, and PCA + SVMrbf.
Taking precision, time cost, and statistical analysis into consideration, LDA + SVMlin and LDA + NN are excellent classifiers in both dynamic and static sections.
Discussion
The results in Fig. 10 prove the feasibility, robustness, and high average accuracy of the proposed approach. All of the IGRMs have been identified with a practically applicable degree of average accuracy either in the dynamic or static section.
From the experimental results above, LDA + SVMlin (97.79% in average precision), LDA + NN (97.38%) are excellent classifiers in both dynamic and static sections. An independent ttest shows no significant difference between LDA + NN and LDA + SVMlin in terms of accuracy (Pvalue = 0.702 in the dynamic section, Pvalue = 0.765 in the static section) and time cost (Pvalue = 0.064 in the dynamic section, P = 0.388 in the static section). However, based on the good interpretability of SVM, a combination of LDA and SVM with linear kernel is our first choice.
The accuracy distribution of the IGRMs shows that LDA is much better than PCA in pathological gait recognition. As shown in dynamic section of Fig. 10 , LDA + SVMrbf and LDA + SVMlin have a significantly smaller variance than PCA + SVMrbf and PCA + SVMlin in the dynamic section, respectively. However, in the static section, the accuracy of LDA + SVMrbf and PCA + SVMrbf, LDA + SVMlin, and PCA + SVMlin has no significant difference. We infer it might be caused by the fact that plantar pressure data in the dynamic section are more complex and efficient than those in the static section. Besides, LDA has higher efficiency in terms of time cost. Results show that PCA + SVM is approximately two to five times the time cost of the LDA + SVM.
According to our prior knowledge, plantar pressure in the static situation have more information about foot types than that in the dynamic situation. More interestingly, we found that the IGRMs in the dynamic section have higher average accuracy than those of the static section. Combined with the corresponding pressure distribution, it can be inferred that children may act more naturally in the dynamic section than in the static section. Regarding preexperiment sections I and II, the walking gestures of children resemble an actual situation in the dynamic section, while in the static section children are prone to stand unnaturally when asked to stand still, which causes the plantar pressure collected by PGRS unable to reflect the actual foot type. Meanwhile, according to the opinion of an experienced clinician, it is quite difficult to judge toein and toeout in the static section unless it is in a serious stage.
To test the methodology of generalization performance to unseen participants, a new simulation under static and dynamic conditions, respectively, is conducted. During the simulation, 17 subjects are divided into two sets, training set containing 16 subjects and testing set containing one subject, taking turns to choose a different subject as testing set. As a result, the accuracy of some subjects can reach up above 95% and the variance of prediction accuracy is quite large. The performance of toein or toeout are quite low, less than 50%. Comparatively speaking, the generalization performance of normal and flat are much better. The average accuracy precision of flat and normal is 85.78% and 84.71%, respectively, and the maximum can both reach up above 95% in dynamic section. Corresponding accuracy precision in static section is, 73.48% and 78.10%, respectively, and the maximum can both reach up above 95%. We think it is caused by the small number of subjects and the dataset is not large enough. Due to the lack of patients with toein or toeout, this dataset lets the model falls into subjects’ specific walking patterns, causing the accuracy precision below 50%. With more subjects involved in our dataset, we think the generalization performance could converge to much better results, despite the difficulty to collect enough subjects. However, the experiment also shows the efficiency of our method in children gait monitoring scenarios.
Conclusions
In this paper, an effective IGRM for pathological gait recognition with dimensional reduction and a classification algorithm is put forward. Also, a lowcost and wearable PGRS with an 8 × 8 pressure sensor array was built. The experimental results show that the proposed IGRM (LDA + SVMlin) has both high accuracy and low prediction time cost in the dynamic section, that is, 97.79% average accuracy and a 4.4ms prediction time per 2000 samples, while in the static section 90.90% average accuracy and a 0.5ms prediction time per 130 samples were realized. Additional generalization performance experiment shows IGRM has 85.78% and 78.81% intersubject recognition accuracy, respectively, in the static and dynamic sections. Another phenomenon found in the experiments is that pathological gait is detected more effectively in the dynamic section since children act more naturally in walking than just standing.
In conclusion, a lowcost PGRS has been verified and realize feasibility, highly average precision, and good realtime performance of gait recognition. Furthermore, the experimental results reveal the potential for the computer supervision of nonpathological and pathological gaits in the plantarpressure patterns of children and for providing feedback in the application of gaitabnormality rectification.
In this study, the implementation of the IGRM is mainly done via a GUI program on a computer. Thus, a PC is still the indispensable device used in pathological gait recognition. In the future, all of the PGRS components should be integrated into an embedded, wearable system to constitute a more powerful, practical PGRS. Besides, more subjects must be involved, and more plantarpressure data should be collected to build a pathological dataset for more complex pathological gait research.
Availability of data and materials
The datasets used and/or analyzed during the current study are available from the corresponding author on reasonable request.
References
Figueiredo J, Santos CP, Moreno JC. Automatic recognition of gait patterns in human motor disorders using machine learning: A review. Med Eng Phys. 2018;53:1–12. https://doi.org/10.1016/j.medengphy.2017.12.006.
Titianova EB, Mateev PS, Tarkka IM. Footprint analysis of gait using a pressure sensor system. J Electromyogr Kinesiol. 2004;14:275–81. https://doi.org/10.1016/S10506411(03)000774.
Salarian A, Russmann H, Vingerhoets FJG, Dehollain C, Blanc Y, Burkhard PR, et al. Gait Assessment in Parkinson’s disease: toward an ambulatory system for longterm monitoring. IEEE Trans Biomed Eng. 2004;51:1434–43. https://doi.org/10.1109/TBME.2004.827933.
Chau T. A review of analytical techniques for gait data Part 1: Fuzzy, statistical and fractal methods. Gait Posture. 2001;13:49–66. https://doi.org/10.1016/s09666362(00)000941.
Dolatabadi E, Taati B, Mihailidis A. An automated classification of pathological gait using unobtrusive sensing technology. IEEE Trans Neural Syst Rehabil Eng. 2017;25:2336–46. https://doi.org/10.1109/tnsre.2017.2736939.
Ortells J, HerreroEzquerro MT, Mollineda RA. Visionbased gait impairment analysis for aided diagnosis. Med Biol Eng Comput. 2018;56:1553–64. https://doi.org/10.1007/s1151701817952.
Zakaria NK. ASD Children gait classification based on principal component analysis and linear discriminant analysis. IJETER 2020;8:2438–45. https://doi.org/10.30534/ijeter/2020/38862020.
Chen SW, Lin SH, Liao LD, Lai HY, Pei YC, Kuo TS, et al. Quantification and recognition of parkinsonian gait from monocular video imaging using kernelbased principal component analysis. BioMed Eng OnLine. 2011;10:99. https://doi.org/10.1186/1475925X1099.
Faragó P, Grama L, Farago MA, Hintea S. A novel wearable foot and ankle monitoring system for the assessment of gait biomechanics. Appl Sci. 2021;11:268. https://doi.org/10.3390/app11010268.
Faragó P, Cirlugea M, Hintea S. A Novel SmartShoe Architecture for Podiatric Monitoring. 2020 43rd International Conference on Telecommunications and Signal Processing (TSP), 2020, p. 180–3. https://doi.org/10.1109/TSP49548.2020.9163549.
Mei Z, Ivanov K, Zhao G, Li H, Wang L. An explorative investigation of functional differences in plantar center of pressure of four foot types using sample entropy method. Med Biol Eng Comput. 2017;55:537–48. https://doi.org/10.1007/s1151701615327.
Mei Z, Zhao G, Ivanov K, Guo Y, Zhu Q, Zhou Y, et al. Sample entropy characteristics of movement for four foot types based on plantar centre of pressure during stance phase. BioMed Eng OnLine. 2013;12:101. https://doi.org/10.1186/1475925X12101.
Zhu H, Maalej N, Webster JG, Tompkins WJ. An umbilical dataacquisition system for measuring pressures between the foot and shoe. IEEE Trans Biomed Eng. 1990;37:908–11. https://doi.org/10.1109/10.58601.
Zhu HS, Wertsch JJ, Harris GF, Loftsgaarden JD, Price MB. Foot pressure distribution during walking and shuffling. Arch Phys Med Rehabil. 1991;72:390–7.
Lin YC, Lin YT. Human recognition based on plantar pressure patterns during gait. J Mech Med Biol. 2013;13:1350039. https://doi.org/10.1142/S0219519413500395.
Sazonov ES, Bumpus T, Zeigler S, Marocco S. Classification of Plantar Pressure and Heel Acceleration Patterns Using Neural Networks, 2005.
Chen M, Huang B, Yangsheng Xu. Intelligent shoes for abnormal gait detection. IEEE Int Conf Robot Autom. 2008;2008:2019–24. https://doi.org/10.1109/ROBOT.2008.4543503.
Robb J. InToeing and OutToeing Gait. In: Joseph B, Robb J, Loder RT, Torode I, editors. Paediatric Orthopaedic Diagnosis: Asking the Right Questions, Springer India; 2015, p. 207–20. https://doi.org/10.1007/9788132223924_21.
Thackeray C, Beeson P. Is intoeing gait a developmental stage? Foot. 1996;6:19–24. https://doi.org/10.1016/S09582592(96)900553.
Thackeray C, Beeson P. Intoeing gait in children. A review of the literature. The Foot. 1996;6:1–4. https://doi.org/10.1016/S09582592(96)900516.
Jacobs B. Toe walking, flat feet and bow legs, intoeing and outtoeing. Paediatr Child Health. 2010;20:221–4. https://doi.org/10.1016/j.paed.2010.03.001.
GarcíaRodríguez A, MartínJiménez F, CarneroVaro M, GómezGracia E, GómezAracena J, FernándezCrehuet J. Flexible flat feet in children: a real problem? Pediatrics. 1999;103: e84. https://doi.org/10.1542/peds.103.6.e84.
Pfeiffer M, Kotz R, Ledl T, Hauser G, Sluga M. Prevalence of flat foot in preschoolaged children. Pediatrics. 2006;118:634–9. https://doi.org/10.1542/peds.20052126.
Yh L, Jc L. Intoeing gait in children. Hong Kong Med J. 1999;5:360–6.
Wren TAL, Rethlefsen S, Kay RM. Prevalence of specific gait abnormalities in children with cerebral palsy: influence of cerebral palsy subtype, age, and previous surgery. J Pediatr Orthop. 2005;25:79–83. https://doi.org/10.1097/0000469420050100000018.
Rosenbaum D. Foot loading patterns can be changed by deliberately walking with intoeing or outtoeing gait modifications. Gait Posture. 2013;38:1067–9. https://doi.org/10.1016/j.gaitpost.2013.04.001.
S YL, H JL, X FQ. Survey on the occurrence of flatfoot among 1 001 children aged 3–12 years old in CangZhou city. Modern Preventive Medicine 2008.
Barton JG, Lees A. An application of neural networks for distinguishing gait patterns on the basis of hipknee joint angle diagrams. Gait Posture. 1997;5:28–33. https://doi.org/10.1016/S09666362(96)010703.
Detti AH, Jemei S, Morando S, Steiner NY. Classification Based Method Using Fast Fourier Transform (FFT) and Total Harmonic Distortion (THD) Dedicated to Proton Exchange Membrane Fuel Cell (PEMFC) Diagnosis. IEEE Vehicle Power and Propulsion Conference (VPPC). 2017;2017:1–6. https://doi.org/10.1109/VPPC.2017.8331040.
Güler NF, Koçer S. Classification of EMG Signals Using PCA and FFT. J Med Syst. 2005;29:241–50. https://doi.org/10.1007/s1091600551847.
Holzreiter SH, Köhle ME. Assessment of gait patterns using neural networks. J Biomech. 1993;26:645–51. https://doi.org/10.1016/00219290(93)90028D.
Prasad BVP, Parthasarathy V. Detection and classification of cardiovascular abnormalities using FFT based multiobjective genetic algorithm. Biotechnol Biotechnol Equip. 2018;32:183–93. https://doi.org/10.1080/13102818.2017.1389303.
Ramón MM, Atwood T, Barbin S, Christodoulou CG. Signal classification with an SVMFFT approach for feature extraction in cognitive radio. SBMO/IEEE MTTS Int Microw Optoelectr Conf. 2009;2009:286–9. https://doi.org/10.1109/IMOC.2009.5427579.
Steinwart I, Christmann A. Support Vector Machines. 1st ed. Incorporated: Springer Publishing Company; 2008.
Deisenroth MP, Faisal AA, Ong CS. Mathematics for Machine Learning. Cambridge: New York, NY; 2020.
Chen M, Huang B, Lee KK, Xu Y. An Intelligent ShoeIntegrated System for Plantar Pressure Measurement. 2006 IEEE International Conference on Robotics and Biomimetics, Kunming, China: IEEE; 2006, p. 416–21. https://doi.org/10.1109/ROBIO.2006.340213.
Platt JC. Fast training of support vector machines using sequential minimal optimization. Advances in Kernel Methods: Support Vector Learning 1999:185–208.
Urry S. Plantar pressuremeasurement sensors. Meas Sci Technol. 1999;10:R1632. https://doi.org/10.1088/09570233/10/1/017.
Sundaram S, Kellnhofer P, Li Y, Zhu JY, Torralba A, Matusik W. Learning the signatures of the human grasp using a scalable tactile glove. Nature. 2019;569:698–702. https://doi.org/10.1038/s415860191234z.
D’Alessio T. Measurement errors in the scanning of piezoresistive sensors arrays. Sens Actuators, A. 1999;72:71–6. https://doi.org/10.1016/S09244247(98)002040.
Speeter TH. A tactile sensing system for robotic manipulation. Int J Robot Res. 1990;9:25–36. https://doi.org/10.1177/027836499000900603.
Casiez G, Roussel N, Vogel D. 1€ Filter: A Simple Speedbased Lowpass Filter for Noisy Input in Interactive Systems, ACM; 2012, p. 2527. https://doi.org/10.1145/2207676.2208639.
Qihang W, Wenlian L, Zuyun F. A new system for foot pressure measurement and gait analysis. Chin J Biomed Eng. 2000;19(1):32–40.
Acknowledgements
We are very grateful to the children and parents who generously gave their time to assist with this research.
Funding
This research is supported by both National Natural Science Foundation of China (Grant No. 51805469) and Science and technology plan project of drug regulatory system of Zhejiang province (No. 2020016).
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LX, FW, and WY carried out the concept and design of the study and interpreted the data. LX performed the statistical analysis and signal processing. LX, JC, and WY participated in the acquisition of gait data. LX drafted the manuscript. JC, YC, WY, and CY provided critical revision of the manuscript for important intellectual content. FW, WY, and CY conceived of the study and obtained funding. CY provided administrative, technical, and material support for the study. CY supervised the study. All authors read and approved the final manuscript.
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The study was performed following the principles outlined in the Helsinki Declaration and it was approved by Clinical Research Ethics Committee. All procedures were carried out with the adequate understanding and written informed consent of each subject.
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The participants acknowledged their consent to publish the acquired data.
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The authors declare that they have no competing interests.
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Xu, L., Chen, J., Wang, F. et al. Machinelearningbased children’s pathological gait classification with lowcost gaitrecognition system. BioMed Eng OnLine 20, 62 (2021). https://doi.org/10.1186/s12938021008980
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DOI: https://doi.org/10.1186/s12938021008980
Keywords
 Pathological gait recognition
 Pressuresensor array
 Gait classification
 Feature extraction