Amyotrophic lateral sclerosis (ALS) is a neurodegenerative disease with an irregular and asymmetric progression, characterized by a progressive loss of both upper and lower motor neurons that leads to muscular atrophy, paralysis, and death, mainly from respiratory failure. The life expectancy of patients with ALS is between 3 and 5 years from the onset of symptoms. ALS produces muscular weakness and difficulties of mobility, communication, feeding, and breathing, making the patient heavily dependent on caregivers and relatives and generating significant social costs. Currently, there is no cure for ALS, but early detection can slow the disease progression [1].

The disease is referred to as spinal ALS when the first symptoms appear in the arms and legs (limb or spinal onset; 80% of cases) and bulbar ALS when it begins in cranial nerve nuclei (bulbar onset; 20% of cases). Patients with the latter form tend to have a shorter life span because of the critical nature of the bulbar muscle function that is responsible for speech and swallowing. However, 80% of all patients with ALS experience dysarthria, or unclear, difficult articulation of speech [2]. On average, speech remains adequate for approximately 18 months after the first bulbar symptoms appear [3]. These symptoms usually become noticeable at the beginning of the disease in bulbar ALS or in later stages of spinal ALS. Early identification of bulbar involvement in people with ALS is critical for improving diagnosis and prognosis and may be the key to effectively slowing progression of the disease. However, there are no standardized diagnostic procedures for assessing bulbar dysfunction in ALS.

Speech impairment may begin up to 3 years prior to diagnosis of ALS [3], and as ALS progresses over time there is significant deterioration in speech [4]. Individuals with ALS with severe dysarthria present specific speech production characteristics [5-7]. However, it is possible to detect early, often imperceptible, changes in speech and voice through objective measurements, as suggested in previous works [8-11]. The authors concluded that phonatory features may be well suited to early ALS detection.

Previous speech production studies have revealed significant differences in specific acoustic parameters in patients with ALS. Carpenter et al [7] studied the articulatory subsystem of individuals with ALS and found different involvement of articulators—that is, the tongue function was more involved than the jaw function. In a recent study, Shellikeri et al [5] found that the maximum speed of tongue movements and their duration were only significantly different at an advanced stage of bulbar ALS compared with the healthy control group. Connaghan et al [12] used a smartphone app to identify and track speech decline. Lee et al [6] obtained acoustic patterns for vowels in relation to the severity of the dysarthria in patients with ALS.

Other works have demonstrated the efficiency of features obtained from the phonatory subsystem for detecting early deterioration in ALS [8-11,13-15]. Studies have shown significant differences between jitter, shimmer, and the harmonics-to-noise ratio (HNR) in patients with ALS [8,10,11]. More specifically, Silbergleit et al [8] obtained these features from a steady portion of sustained vowels that provided information regarding changes in the vocal signal that are believed to reflect physiologic changes of the vocal folds. Alternative approaches used formant trajectories to classify the ALS condition [13], correlating formants with articulatory patterns [14], fractal jitter [15], Mel Frequency Cepstral Coefficients (MFCCs) [16], or combined acoustic and motion-related features [9] at the expense of introducing more invasive measurements to obtain data. Besides, the findings revealed significant differences in motion-related features only at an advanced stage of bulbar ALS.

Other related studies, such as one by Frid et al [17], used speech formants and their ratios to diagnose neurological disorders. Teixeira et al [18] and Mekyska et al [19] suggested jitter, shimmer, and HNR as good parameters to be used in intelligent diagnosis systems for dysphonia pathologies.

Garcia-Gancedo et al [20] demonstrated the feasibility of a novel digital platform for remote data collection of digital speech characteristics, among other parameters, from patients with ALS.

In the literature, classification models are widely used to test the performance of acoustic parameters in the analysis of pathological voices. Norel et al [21] identified acoustic speech features in naturalistic contexts and machine learning models developed for recognizing the presence and severity of ALS using a variety of frequency, spectral, and voice quality features. Wang et al [9] explored the classification of the ALS condition using the same features with support vector machine (SVM) and neuronal network (NN) classifiers. Rong et al [22] used SVMs with two feature selection techniques (decision tree and gradient boosting) to predict the intelligible speaking rate from speech acoustic and articulatory samples.

Suhas et al [16] implemented SVMs and deep neuronal networks (DNNs) for automatic classification by using MFCCs. An et al [23] used convolutional neuronal networks (CNNs) to compare the intelligible speech produced by patients with ALS to that of healthy individuals. Gutz et al [24] merged SVM and feature filtering techniques (SelectKBest). In addition, Vashkevich et al [25] used linear discriminant analysis (LDA) to verify the suitability of the sustain vowel phonation test for automatic detection of patients with ALS.

Among feature extraction techniques, principal component analysis (PCA) [26] shows good performance in a wide range of domains [27,28]. Although PCA is an unsupervised technique, it can efficiently complement a supervised classifier in order to achieve the objective of the system. In fact, any classifier can be used in conjunction with PCA because it does not make any kind of assumption about the subsequent classification model.

Based on previous works, our paper suggests that the acoustic parameters obtained through automated signal analysis from a steady portion of sustained vowels may be used efficiently as predictors for the early detection of bulbar involvement in patients with ALS. For that purpose, the main objectives (and contributions) of this research were (1) to design a methodology for diagnosing bulbar involvement efficiently through the acoustic parameters of uttered vowels in Spanish; and (2) to demonstrate that the performance of the automated diagnosis of bulbar involvement is superior to human diagnosis.

To fulfill these objectives, 45 Spanish patients with ALS and 18 control subjects took part in the study. They were recruited by a neurologist, and the five Spanish vowel segments were elicited from each participant. The study focused on the extraction of features from the phonatory subsystem—jitter, shimmer, HNR, and pitch—from the utterance of each Spanish vowel.

Once the features were obtained, we used various classification algorithms to perform predictions based on supervised classification. In addition to traditional SVMs [9,16,21,22,24], NNs [9,16,23], and LDA [25], we used logistic regression (LR), which is one of the most frequently used models for classification purposes [29,30]; random forest (RF) [31], which is an ensemble method in machine learning that involves the construction of multiple tree predictors that are classic predictive analytic algorithms [22]; and naïve Bayes (NaB), which is still a relevant topic [32] and is based on applying Bayes’ theorem.

Prior to feeding the models, PCA was applied to the features obtained due to the good performance observed of this technique in a wide range of domains.

The study was approved by the Research Ethics Committee for Biomedical Research Projects (CEIm) at the Bellvitge University Hospital in Barcelona, Spain. A total of 45 participants with ALS (26 males and 19 females) aged from 37 to 84 (mean 57.8, SD 11.8) years and 18 control subjects (9 males and 9 females) aged from 21 to 68 (mean 45.2, SD 12.2) years took part in this transversal study. All participants with ALS were diagnosed by a neurologist.

Bulbar involvement was diagnosed by following subjective clinical approaches [33], and the neurologist made the diagnosis of whether a patient with ALS had bulbar involvement. Of the 45 participants with ALS, 5 reported bulbar onset and 40 reported spinal onset, but at the time of the study 14 of them presented bulbar symptoms.

To summarize, of the 63 participants in the study, 14 were diagnosed with ALS with bulbar involvement (3 males and 11 females; aged from 38 to 84 years, mean 56.8 years, SD 12.3 years); 31 were diagnosed with ALS but did not display this dysfunction (23 males and 8 females, aged from 37 to 81 years, mean 58.3 years, SD 11.7 years); and 18 were control subjects (9 males and 9 females; aged from 21 to 68 years, mean 45.2 years, SD 12.2 years).

The severity of ALS and its bulbar presentation also varied among participants, as assessed by the ALS Functional Rating Scale-Revised (ALSFRS-R). The ALSFRS-R score (0-48) was obtained from 12 survey questions that assess the degree of functional impairment, with the score of each question ranging from 4 (least impaired) to 0 (most impaired). The scores of the 45 participants in this study ranged from 6 to 46 (mean 31.3, SD 8.6; 3 patients’ scores were reported as not available). Within the subgroups, the scores of patients diagnosed with bulbar involvement ranged from 6 to 46 (mean 23.1, SD 9.8), and the scores of participants with ALS who did not present this dysfunction ranged from 17 to 46 (mean 30.2, SD 8.0; 3 patients’ scores reported as not available).

The main clinical records of the participants with ALS are summarized in Multimedia Appendix 1.

The Spanish phonological system includes five vowel segments—a, e, i, o, and u. These were obtained and analyzed from each patient with ALS and each control participant, all of whom were Spanish speakers.

Sustained samples of the Spanish vowels a, e, i, o, and u were elicited under medium vocal loudness conditions for 3-4 s. The recordings were made in a regular hospital room using a USB GXT 252 Emita Streaming Microphone (Trust International BV) connected to a laptop. The speech signals were recorded at a sampling rate of 44.100 Hz and 32-bit quantization using Audicity, an open-source application [34].

Each individual phonation was cut out and anonymously labeled. The boundaries of the speech segments were determined with an oscillogram and a spectrogram using the Praat manual [35] and were audibly checked. The starting point of the boundaries was established as the onset of the periodic energy in the waveform observed in the oscillogram and checked by the apparition of the formants in the spectrogram. The end point was established as the end of the periodic oscillation when a marked decrease in amplitude in the periodic energy was observed. It was also identified by the disappearance of the waveform in the oscillogram and the formants in the spectrogram.

Acoustic analysis was done by taking into account the following features: jitter, shimmer, HNR, and pitch. Once the phonations of each participant had been segmented, the parameters were obtained from each vowel through the standard methods used in Praat [35]; they are explained in detail in this section and consist of a short-term spectral analysis and an autocorrelation method for periodicity detection.

Jitter and shimmer are acoustic characteristics of voice signals. Jitter is defined as the periodic variation from cycle to cycle of the fundamental period, and shimmer is defined as the fluctuation of the waveform amplitudes of consecutive cycles. Patients with lack of control of the vibration of the vocal folds tend to have higher values of jitter. A reduction of glottal resistance causes a variation in the magnitude of the glottal period correlated with breathiness and noise emission, causing an increase in shimmer [18].

To compute jitter parameters, some optional parameters in Praat were established. Period floor and period ceiling, defined as the minimum and maximum durations of the cycles of the waveform that were considered for the analysis, were set at 0.002 s and 0.025 s, respectively. The maximum period factor—the largest possible difference between two consecutive cycles—was set at 1.3. This means that if the period factor—the ratio of the duration of two consecutive cycles—was greater than 1.3, this pair of cycles was not considered in the computation of jitter.

The methods used to determine shimmer were almost identical to those used to determine jitter, the main difference being that jitter considers periods and shimmer takes into account the maximum peak amplitude of the signal.

Once the previous parameters had been established, jitter and shimmer were obtained by the formulas shown below [35].

Jitter(absolute) is the cycle-to-cycle variation of the fundamental period (ie, the average absolute difference between consecutive periods):

The PCA technique [37], a ranking feature extraction approach, was implemented in R [38] using the Stats package [38]. PCA was used to decompose the original data set into principal components (PCs) to obtain another data set whose data were linearly independent and therefore uncorrelated. It was performed by means of singular value decomposition (SVD) [39].

Prior to applying PCA, given that the mean age of control subjects was approximately 12 years younger than patients with ALS, we removed the age effects by using the data from the control subjects and applying the correction to all the participants as in the study by Norel et al [21]. We fitted the features extracted for healthy people and their age linearly. Then, the “normal aging” of each single feature of each participant was obtained by multiplying the age of the participants by the slope parameter obtained from the linear fit. Finally, the computed “normal aging” was removed from the features. Afterward, a standardized data set was obtained by subtracting the mean and centering the age-adjusted features at 0.

Then, by applying SVD to the standardized data set, a decomposition was obtained: , where X is the matrix of the standardized data set, U is a unitary matrix and S is the diagonal matrix of singular values s_i. PCs are given by US, and V contains the directions in this space that capture the maximal variance of the features of the matrix X. The number of PCs obtained was the same as the original number of features, and the total variance of all of the PCs was equal to the total variance among all of the features. Therefore, all of the information contained in the original data was preserved.

From the PCA, a biplot chart was obtained for a visual appraisal of the data [40]. The biplot chart allowed us to visualize the data set structure, identify the data variability and clustering participants, and display the variances and correlations of the analyzed features. Then, the first eight PCs that explained almost 100% of the variance were selected to fit the classification models.

The participants in this study belonged to three different groups: the control group (n=18), patients with ALS with bulbar involvement (n=14), and patients with ALS without bulbar involvement (n=31). Each participant was properly labeled as control (C) if the subject was a control participant, ALS with bulbar (B) if the subject was a participant with ALS diagnosed with bulbar involvement, or ALS without bulbar (NB) if the subject was a participant with ALS without bulbar involvement. In addition, the ALS (A) label was added to every participant with ALS, with or without bulbar involvement.

Supervised models were built to obtain predictions by comparing the four labeled groups between them. Textbox 2 summarizes the procedure used to create proper classification models.

Several supervised classification models were implemented in R [38] to measure the classification performance. The classification models were fitted with the first eight PCs that explained almost 100% of the data variability. Finally, 10-fold cross-validation was implemented in R using the caret package [41] to draw suitable conclusions. The upsampling technique with replacement was applied to the training data by making the group distributions equal to deal with the unbalanced data set, which could bias the classification models [42].

The first classifier employed was SVM, which is a powerful, kernel-based classification paradigm. SVM was implemented using the e1071 [43]. We used a C-support vector classification [44] and a linear kernel that was optimized through the tune function, assigning values of 0.0001, 0.0005, 0.001, 0.01, 0.1, and 1 to the C parameter, which controls the trade-off between a low training error and a low testing error. A C parameter value of 1 gave the best performance, and thus this was the SVM model chosen.

Next, a classical NN trained with the back propagation technique with an adaptive learning rate was implemented using the RSNNS package [45]. After running several trials to decide the NN architecture, a single hidden layer with three neurons was implemented because it showed the best performance. The activation function (transfer function) used was the hyperbolic tangent sigmoid function.

LDA was implemented using the MASS package [46]. It estimated the mean and variance in the training set and computed the covariance matrix to capture the covariance between the groups to make predictions by estimating the probability that the test set belonged to each of the groups.

LR was implemented by using the Gaussian generalized linear model applying the Stats package [38] for binomial distributions. A logit link function was used to model the probability of “success.” The purpose of the logit link was to take a linear combination of the covariate values and convert those values into a probability scale.

Standard NaB based on applying Bayes’ theorem was implemented using the e1071 package [43].

Finally, the RF classifier was implemented using the randomForest package [47] with a forest of 500 decision tree predictors. The optimal mtry—a parameter that indicated the number of PCs that were randomly distributed at each decision tree—was optimized for each classification problem by using the train function included in the caret package [41]. Each decision tree performed the classification independently and RF computed each tree predictor classification as one “vote.” The majority of the votes computed by all of the tree predictors decided the overall RF prediction.

The code of these implementations is freely available online [48].

There are several metrics to evaluate classification algorithms [49]. The analysis of such metrics and their significance must be interpreted correctly to evaluate these algorithms.

There are four possible results in the classification task. If the sample is positive and it is classified as positive, it is counted as a true positive (TP), and when it is classified as negative, it is considered a false negative (FN). If the sample is negative and it is classified as negative or positive, it is considered a true negative (TN) or false positive (FP), respectively. Based on that, three performance metrics, presented below, were used to evaluate the performance of the classification models.

A total of 15 features were obtained in this study. These features were jitter(absolute), jitter(relative), jitter(rap), jitter(ppq5), shimmer(relative), shimmer(dB), shimmer(apq3), shimmer(apq5), shimmer(apq11), pitch(mean), pitch(SD), pitch(min), pitch(max), HNR(mean), and HNR(SD).

Figure 1 shows the box plot of the features obtained from the control (C) group, patients with ALS with bulbar involvement (B), and patients with ALS without bulbar involvement (NB). The means in the B group were higher than those in the C and NB groups. The means in the NB group were located in the middle of the means of the C and B groups. On the contrary, the B group obtained the lowest values for the mean HNR(mean) and HNR(SD). Differences in the standard deviation between the three groups were also observed. In general, features obtained from the B group presented the highest standard deviations.

PCA was performed using the data set that contained the 15 features extracted from all of the participants. Figure 2 shows the associated PCA biplot chart. The two axes represent the first (Dim1) and second (Dim2) PCs. The biplot uses the diagonalization method to give a graphical display of its dimensional approximation [51,52]. The interpretation of the biplot involves observing the lengths and directions of the vectors of the features, the data variability, and the clusterization of the participants.

It can be observed that a considerable proportion of variance (70.1%) of the shimmer, jitter, pitch, and HNR was explained. The relative angle between any two vector features represents their pairwise correlation. The closer the vectors are to each other (<90°), the higher their correlation. When vectors are perpendicular (angles of 90° or 270°), the variables have a small or null correlation. Angles approaching 0° or 180° (collinear vectors) indicate a correlation of 1 or –1, respectively. Thus, in this case, shimmer and jitter show a strong positive correlation. Another important observation reflected in Figure 2 is the spatial proximity of the groups in relation both to each other and to the set of features. The projection of the B group onto the vector for shimmer and jitter falls to the left of the vector features. This means that subjects labelled as the B group had higher average values for those features than the average values of the other groups. Conversely, the projection of the C group onto those variables falls on the opposite side. In addition, the C and B groups are more distant from each other when projected onto shimmer and jitter. This indicates that shimmer and jitter features are the most important features for the classification of participants in the B and C groups.

The projection of subjects in the NB group requires special attention. Although the projection of these subjects has a spatial proximity with respect to the C group, their variability is higher, overflowing the gray circle corresponding to the B group.

This indicates that some features, especially shimmer and jitter, of some subjects in the NB group have similar projections to the features of the B group.

To fit the models, as explained in detail in the next section, the first eight PCs were selected in order to reduce the dimensionality but preserve almost 100% of the variability as shown in Figure 3.

The first eight PCs were selected. Then, each classification model was applied to these PCs. Consequently, better results were obtained than when applying the classification models alone. The results of the classification methods alone are not shown because of their limited contribution to the analysis.

Tables 1 and 2 show the classification performance (accuracy, sensitivity, and specificity metrics) of the supervised models tested for the four cases with the classification threshold set at 50% and 95%, respectively.

In the case of the C group versus the B group, with the classification threshold set at 50%, the results indicated that all classifiers had a good classification performance. SVM obtained the best accuracy (95.8%). The tests of significance, which are reported in Multimedia Appendix 2, revealed statistically significant differences between SVM and the other models, with the exception of LDA, which obtained an accuracy (94.3%) that closely approximated that of the SVM model. NN also showed really good results (accuracy 94.8%).

Similar behavior was obtained in the C group versus the NB group and the C group versus all patients with ALS. In these cases, NN was the best model (92.5% for C vs NB and 92.2% for C versus ALS). Meanwhile, generally poor performance was obtained in the B group versus the NB group compared with the other cases. Although RF showed the best accuracy (75.5%), the performance of specificity and especially sensitivity dropped dramatically in comparison with the previous cases. In general, the model performance dropped with a 95% threshold. In the C group versus the B group, the accuracy of the classification models (Table 2) was worse than when the classification threshold was set at 50%. LR shows the best accuracy (92.8%). LDA, SVM, and NaB obtained accuracies of 88.1%, 86.3%, and 82.3%, respectively. RF did not seem to be a good model for this threshold, with an accuracy of 58.3%.

Lower results were obtained in the C group versus the NB group and the C group versus the group with ALS. NN showed the best performance, with accuracies of 84.8% and 86.8%, respectively.

With the 95% threshold, the performance of sensitivity dropped in all cases, especially for the B group versus the NB group, where LR obtained the best performance with an accuracy of 74.1% but a sensitivity of 16.7%.

This study was guided by 2 objectives: (1) to design a methodology for diagnosing bulbar involvement efficiently through the acoustic parameters of uttered vowels in Spanish, and (2) to demonstrate the superior performance of automated diagnosis of bulbar involvement compared with human diagnosis. This was based on the accurate acoustic analysis of the five Spanish vowel segments, which were elicited from all participants. A total of 15 acoustic features were extracted: jitter(absolute), jitter(relative), jitter(rap), jitter(ppq5), shimmer(relative), shimmer(dB), shimmer(apq3), shimmer(apq5), shimmer(apq11), pitch(mean), pitch(SD), pitch(min), pitch(max), HNR(mean), and HNR(SD). Then, the PCs of these features were obtained to fit the most common supervised classification models in clinical diagnosis: SVM, NN, LDA, LR, NaB, and RF. Finally, the performance of the models was compared.

The study demonstrated the feasibility of automatic detection of bulbar involvement in patients with ALS through acoustic features obtained from vowel utterance. It also confirms that speech impairment is one of the most important aspects for diagnosing bulbar involvement, as was suggested by Pattee et al [33]. Furthermore, bulbar involvement can be detected using automatic tools before it becomes perceptible to human hearing.

Voice features extracted from the B group compared with those features extracted from the C group showed the best performance of the classification model for determining bulbar involvement in patients with ALS.

Accuracy for the C group versus the B group revealed values of 95.8% for SVM with the classification threshold established at 50%. However, on increasing the threshold to 95%, the accuracy values for SVM dropped (86.3%) and LR showed the best performance (accuracy 92.8%). NN also showed a good accuracy at 92.6%. This implies that NN and LR are more robust for finding accuracy.

For that case, the results obtained reinforce the idea that it is possible to diagnose bulbar involvement in patients with ALS using supervised models and objective measures. The SVM and LR models provided the best performance for the 50% and 95% thresholds, respectively.

Great uncertainty was found in the analysis regarding bulbar involvement in the NB group. The accuracy values of the C group versus the NB group and the C group versus the group with ALS with the classification threshold at 50% were 92.5% and 92.2%, respectively, for NN. That reveals that the features extracted from the NB group differed significantly from those of the C group. Lower performance should be expected because participants labeled as the C group and NB group should have similar voice performance. This may indicate that some of the participants in the NB group probably had bulbar involvement but were not correctly diagnosed because the perturbance in their voices could not be appreciated by the human ear. Alternatively, it could be simply that a classification threshold of 50% was too optimistic. With a 95% classification threshold, lower results were obtained in the C group versus the NB group and in the C group versus patients with ALS. NN showed the best performance with accuracies of 84.8% and 86.8%, respectively, for the two cases.

The performance between the B group and C group showed better results than between the NB group and C group. Despite this, the unexpectedly high performance of the models for the C group versus the NB group still suggests that some participants in the NB group could have had bulbar involvement. Changing the classification threshold to 95% worsened the results, especially for sensitivity, although this still remained significant.

The case of the B group versus the NB group revealed that the classification models did not distinguish B group and NB group participants as well as they did with the other groups. The accuracy with the 50% threshold showed the highest performance for RF (75.5%), but the models showed difficulties in identifying positive cases. That may be due to the small difference in the variation of the data among participants in the B and NB groups. The same occurred for the 95% threshold: LR obtained the highest accuracy (74.1%) but a sensitivity of only 16.7%. These values remain far from those in the case of the C group versus the B group. These results also reinforce the idea that participants in the NB group were misdiagnosed.

The good model performance obtained in comparing the C and NB groups supports these findings and underscores the importance of using objective measures for assessing bulbar involvement. This corroborated the results obtained in the data exploration and PCA, which were presented in the Results section.

The projection of the NB group in the PCA biplot chart requires special attention. Although the projection of these subjects has a spatial proximity with regard to the C group, their variability is higher, overflowing the circle corresponding to the B group. This indicates that some features, especially shimmer and jitter, of some patients in the NB group have similar projections to those in the B group. This may reveal that these patients in the NB group could have bulbar involvement but were not yet correctly diagnosed because the perturbance in their voices could still not be appreciated by human hearing.

Figure 1 also indicates that the means of the features of the patients in the NB group were between the means of the features of the C and B groups, thus corroborating these assumptions.

This study has some limitations. First, using machine learning on small sample sizes makes it difficult to fully evaluate the significance of the findings. The sample size of this study was heavily influenced by the fact that ALS is a rare disease. At the time of the study, 14 of the patients with ALS presented bulbar symptoms. The relatively small size of this group was because ALS is a very heterogeneous disease and not all patients with ALS present the same symptomatology. Additionally, the control subjects were approximately 12 years younger than the patients with ALS. Vocal quality changes with age, and comparing younger control subjects’ vocalic sounds with those of older participants with ALS might introduce additional variations. Although upsampling techniques were used in this study to correct the bias and age adjustments have been applied to correct the vocal quality changes due to the age difference, it would be necessary in future studies to increase the number of participants, especially of patients with ALS with bulbar involvement and control participants of older ages, to draw definitive conclusions.

Second, the variability inherent in establishing the boundaries of the speech segments on spectrograms manually makes replicability challenging. Speakers will differ in their production, and even the same speaker in the same context will not produce two completely identical utterances. In this study, the recorded speech was processed manually in the uniform approach detailed in the Methods section. Automatic instruments have been developed, but unfortunately these methods are not yet accurate enough and require manual correction.

The PCA biplot charts indicated that shimmer and jitter were the most important features for group separation in the 2-PC model for ALS classification; however, they also revealed pitch and HNR parameters as good variables for this purpose. These results are consistent with those of Vashkevich et al [25], who demonstrated significant differences in jitter and shimmer in patients with ALS. They are also consistent with Mekyska et al [19] and Teixeira et al [18], who mentioned pitch, jitter, shimmer, and HNR values as the most popular features describing pathological voices. Finally, Silbergleit et al [8] suggested that the shimmer, jitter, and HNR parameters are sensitive indicators of early laryngeal deterioration in ALS.

Concerning the classification models, Norel et al [21] recently implemented SVM classifiers to recognize the presence of speech impairment in patients with ALS. They identified acoustic speech features in naturalistic contexts, achieving 79% accuracy (sensitivity 78%, specificity 76%) for classification of males and 83% accuracy (sensitivity 86%, specificity 78%) for classification of females. The data used did not originate from a clinical trial or contrived study nor was it collected under laboratory conditions. Wang et al [9] implemented SVM and NN using acoustic features and adding articulatory motion information (from tongue and lips). When only acoustic data were used to fit the SVM, the overall accuracy was slightly higher than the level of chance (50%). Adding articulatory motion information further increased the accuracy to 80.9%. The results using NN were more promising, with accuracies of 91.7% being obtained using only acoustic features and increasing to 96.5% with the addition of both lip and tongue data. Adding motion measures increased the classifier accuracy significantly at the expense of including more invasive measurements to obtain the data. We investigated the means of optimizing accuracy in detecting ALS bulbar involvement by only analyzing the voices of patients. An et al [23] implemented CNNs to classify the intelligible speech produced by patients with ALS and healthy individuals. The experimental results indicated a sensitivity of 76.9% and a specificity of 92.3%. Vashkevich et al [25] performed LDA with an accuracy of 90.7% and Suhas et al [16] used DNNs based on MFCCs with an accuracy of 92.2% for automatic detection of patients with ALS.

Starting with the most widely used features suggested in the literature, the classification models used in this paper to detect bulbar involvement automatically (C group versus B group) performed better than the ones used by other authors, specifically the ones obtained using NN (Wang et al [9]) and DNNs based on MCCFs (Suhas et al [16]). We obtained the best-ever performance metrics. This suggests that decomposing the original data set of features into PCs to obtain another data set whose data (ie, PCs) were linearly independent and therefore uncorrelated improves the performance of the models.

This paper suggests that machine learning may be an appropriate tool to help in the diagnosis of ALS by multidisciplinary clinical teams. In particular, it could help in the diagnosis of bulbar involvement. This work demonstrates that an accurate analysis of the features extracted from an acoustic analysis of the vowels elicited from patients with ALS may be used for early detection of bulbar involvement. This could be done automatically using supervised classification models. Better performance was achieved by applying PCA previously to the obtained features. It is important to note that when classifying participants with ALS with bulbar involvement and control subjects, the SVM with a 50% classification threshold exceeded the performance obtained by other authors, specifically Wang et al [9] and Suhas et al [16].

Furthermore, bulbar involvement can be detected using automatic tools before it becomes perceptible to human hearing. The results point to the importance of obtaining objective measures to allow an early and more accurate diagnosis, given that humans may often misdiagnose this deficiency. This directly addresses a recent statement released by the Northeast ALS Consortium’s bulbar subcommittee regarding the need for objective-based approaches [53].

Future work is directed toward the identification of incorrectly undiagnosed bulbar-involvement in patients with ALS. A time-frequency representation will be used to detect possible deviations in the voice performance of patients in the time-frequency domain. The voice distributions of patients with ALS diagnosed with bulbar involvement and patients with ALS without that diagnosis will be compared in order to detect pattern differences between these two groups. That could provide indications to distinguish undiagnosed participants with ALS who could be misdiagnosed. Also, an improvement in the voice database by increasing the sample size is envisaged.