VOICE PARAMETER EXTRACTOR USING ORAL AIRFLOW

Abstract: A pneumotachographic device which produces an output voiced speech waveform which is appropriately filtered to remove the formant frequencies and to produce a smoothed glottal waveform. From the pneumotachograph output waveform and smoothed glottal waveform are derived a peak value P, a minimum value L, glottal wave period T and average value M for the glottal waveform. The amplitude and wave centre value are calculated, and from these the open quotient Q is derived, which represents the ratio of the duration of the open portion B of the glottal wave cycle to the entire period T thereof.

Description: This invention relates to the quantitative measurement of the parameters of human speech, especially to those relating to the functioning of the human larynx. The invention is more specifically directed to an apparatus for processing oral or combined oral and nasal airflow waveforms to provide information concerning laryngeal flow. In voiced speech, vowel sounds are formed by a glottal source waveform on which are superimposed vocal tract resonances or formants. The glottis is the passageway between the vocal folds when they are open. The glottal waveform, which represents the flow of air through the larynx as the vocal folds open and close in a quasi-periodic manner, has in each cycle an "open" portion which represents the outrush of air when the glottis is open, and a relatively flat, "closed" portion which represents the cessation of airflow when the vocal folds are closed. The formants are resonances produced by the vocal tract _ that is, the throat, mouth, sinuses, and nasal passages _ that selectively amplify certain of the harmonics of the glottal waveform. In very efficient voices, the glottal waveform will exhibit a slow rise when the glottis is opening, and then a sharp drop when the glottis closes, with a flat section between the open portions where there is little or no airflow occurring. In most persons, the waveform is much rounder than the ideal, and the glottal waveform more approximates a truncated sine wave shape which would result in a weaker voice for a given expenditure of airflow. It is also true that in most persons the closed portion of the glottal wave is not absolutely flat, and where there is some problem in the vocal folds closing completely, there may be a significant amount of airflow even during the closed portion. This can sometimes be heard as a breathiness or huskiness of voice. An otherwise unexplained increase in airflow during the closed portion over the level normal for a given speaker could also mean that there is a polyp or other growth in the larynx on or near the vocal folds. Ideally, a health practitioner should be able to chart the voice parameters of a patient from week to week to show the progress of disease or of therapy. The need for standardized quantitative measures of the functioning of the larynx is one that has long been in search of a solution. At present, there are only two non-invasive methods available for clinical use to estimate or describe the vibratory pattern of the vocal folds, namely electroglottography and inverse-filtering of the airflow or pressure waveform at the mouth. Electroglottography basically measures the variation and degree of contact between vocal folds during that part of the glottal cycle in which the folds are in contact with each other. Changes in electrical resistance at the throat are measured by a device that contacts the patient's skin and indicates the change in resistance as the vocal folds meet and come into tighter contact. Unfortunately, this technique gives no absolute measure of the degree of contact of the vocal folds and no real information about the portion of the glottal cycle in which the vocal folds are out of contact, beyond the duration of that period. For clinical purposes, inverse-filtering airflow at the mouth rather than pressure is preferred because the airflow measurement results in a known zero level and permits ready calibration of airflow scale of the resulting glottal flow waveform. In the inverse-filtering technique, a wire-screen peripheral flow pneumotachograph mask, such as the Rothenberg mask, produces an oral volume velocity waveform adequate for inverse-filtering. An electronic circuit or equivalent computer algorithm permits inverse-filtering of the mask output. By "inverse-filtering", what is meant is that the major formants are removed from the oral waveform. Because the formant frequencies and bandwidths can change from one patient to another, depending not only on the internal geometry of the patient's vocal tract, but on the precise vowel being spoken, the adjustments of a manual formant inverse-filtering system must be carefully selected by a trained technician. Consequently, voice parameter analysis using this technique has been a rather arduous affair, conducted by only a few highly trained specialists. Although this technique has been used for many voice research laboratories and some research-oriented facilities, the need to adjust the inverse-filter parameters for each subject, that is, to adjust the frequency and damping of the lowest two or three vocal tract resonances, has made this system impractical for general clinical use. To overcome this problem, there have been many proposals to develop a computer-based automated inverse-filtering algorithm. Although these may eventually be of value as presently proposed, such automated inverse-filtering schemes can produce gross errors if the program is in error. Unfortunately, such errors are most likely to occur for abnormal voices, and such voices are quite often those of the patients who could benefit most from voice analysis. Such voices typically are breathy or have a significant nasality. Both of these conditions are contrary to the assumptions on which the automated inverse-filtering schemes would be predicated. Sophisticated schemes for automated inverse-filtering which are sufficiently robust to handle a wide variety of voice conditions are not forthcoming. The most important values that should be produced by an ideal automatic voice parameter extracting technique would be the maximum or peak value, the mean value, and the minimum value of airflow through the larynx during a given glottal cycle, and an open quotient value, which would represent the ratio of the duration of the open portion of the glottal waveform to the entire glottal vibratory period. However, prior to this invention, there have been no suitable techniques developed for automatically extracting these parameters. Objects and Summary of the Invention Accordingly, it is an object of this invention to provide a device for producing a quantitative record of the efficiency of the human voice source and particularly of the quality of the glottal airflow waveform. It is a more specific object to provide automatic extraction, from oral or combined oral and nasal airflow, of the parameters that relate to the vocal fold vibratory pattern, and to produce those parameters in a form that is suitable for use by otolaryngologists, speech therapists, and other practitioners such as voice and singing coaches. It is another object of this invention to produce a record of the condition of an individual's vocal airflow parameters so that the progress of the condition of the individual's laryngeal voice source can be charted and understood. It is another object of this invention to provide a voice parameter extraction technique which is reliable and highly repeatable, and which is also rapid and simple to use. In accordance with an aspect of this invention, a technique for extracting the voice parameters can be used with oral or oral and nasal airflow that is produced during voiced speech. In this technique, the patient pronounces a vowel sound into a pneumotachograph which produces an output signal that represents the vowel's voiced speech waveform, and includes a measure of the mean airflow. The patient is asked to pronounce a vowel having a high first formant such as "ah" or "ae", the vowels in the words "pop" and "pap", respectively. Though any speech context can be used, a word such as "bop" or "pop" (or "bap" or "pap") is preferably chosen because an unvoiced bilabial stop ("p") adjoining the desired vowel sound allows the air pressure in the lungs to be readily measured in the mouth during the period of oral closure. This procedure is explained in Rothenberg, A New Inverse-Filtering Technique for Deriving the Glottal Airflow Waveform During Voicing, Journal of the Acoustical Society of America, Vol. 53, 1973, pages 1632-1654. A low-pass filtering operation is performed on the amplified and prefiltered pneumotachograph output signal to produce a smooth version of the glottal waveform in which the formants of the pronounced vowel are almost entirely suppressed. Then, from this waveform and the filtered output are derived the peak value P, the minimum value L, and the period T O of the glottal wave, as well as the average or mean airflow value M. The amplitude A of the glottal waveform is derived as the difference between the peak and minimum values, and the center value M of the glottal wave is derived as the difference between the mean airflow value M and the minimum value L. The open quotient Q O , which represents the ratio of the duration of the open portion B of the glottal wave cycle (in which the patient's vocal folds are not in contact) to the duration of the entire cycle T O , is derived from an approximation of the glottal wave to a truncated sine wave. The open quotient Q O can be derived from the following relationship: The values of P, L, and Q O can be provided on a display and/or printed out to produce a record of the voice parameters of the patient. Equipment for carrying out this technique can include a pneumotachograph instrument into which the patient pronounces the vowel, and a low-pass filter system for prefiltering that has an input coupled to the pneumotachograph instrument and which filters the output signal of the instrument to produce a waveform in which the formants of the pronounced vowels above the second are suppressed. Further signal processing circuitry has inputs coupled to the prefilter system to receive the waveform and to derive from this waveform the peak value P and minimum value L, of glottal waveform, and the glottal wave period T O , as well as the mean airflow value M. A calculating device is input with the values P, L, T O , and M to produce the values of the amplitude A and the wave center value M , of the glottal waveform and further, e.g., by means of a programmed lookup table or equivalent approximating equation, to find the open quotient Q O corresponding to the input values of A and M . The low-pass prefilter system can include a linear-phase l, p, f, (that is, constant delay) low-pass filter having an input coupled to receive the output signal of the pneumotachograph instrument. The input of a band-pass filter is coupled to the output of the low-pass prefilter which has a pass band that extends from about the lowest frequency F O to the highest F O expected from the glottal waveform of the pronounced vowel. This produces a filtered AC output. A zero-crossing detector measures the glottal period T O from the output of the band pass filter. An approximate inverse-filter circuit consisting of an antiresonance or simple notch filter is coupled to the output of the low-pass prefilter for reducing in the waveform the energy near formant frequency F₁ of the pronounced vowel. The output of this notch filter is coupled to the input of a second linear-phase low-pass filter, with a roll-off frequency below the first formant frequency but well above the expected range of voice fundamental F O (f -3dB at approximately 1/2 F₁). This low-pass filter removes almost all remaining formant energy and furnishes a smoothed version of the glottal waveform to another circuit designed to measure the minimum value, which is also furnished with the output of the zero-crossing detector, to derive the minimum value L of the glottal airflow waveform during each glottal period. A third low-pass filter is coupled to the output of the second low-pass filter and has a roll-off frequency below the frequency F O of the glottal waveform. This produces the value of the mean airflow M. The output of the prefilter is also coupled to the input of a peak detector circuit, as is the output of the zero-crossing detector which defines the glottal period. The output of the peak detector system is interpreted as the peak value P of the glottal waveform. Adders combine the peak value P and the minimum value L to produce the amplitude value A, and combine the mean airflow value M and the minimum value L to produce the wave center value M . In an alternative arrangement, a digitizer is input with the waveform from the output of the pneumotachographic instrument and produces a sequence of numerical sample values, with the low-pass filtering, bandpass and inverse-filtering being carried out by selectively combining the numerical sample values to produce a derivative sequence of values that represent the respective filtered waveforms. The peak value P, minimum value L, and mean airflow value M and the values of M and Q O computed from P, L and M can be derived directly from the digitized waveforms by a programmed microprocessor device that is input with the derivative sequences of numerical values. The apparatus of this invention bypasses the pitfalls inherent in the more conventional inverse-filtering, and provides a cost effective and robust means for obtaining those parameters relating to glottal airflow that have the greatest significance for clinical applications. The parameter values can be displayed or printed directly or can instead be used to reconstruct a stylized representation of the patient's glottal waveform. In this apparatus, the average lung pressure during the vowel can be estimated from the oral pressure during the neighboring unvoiced stop by means of a pressure sensor mounted on the pneumotachographic mask and coupled through the corner of the mouth into the oral cavity. Although this is not essential, lung pressure is often helpful in interpreting the significance of the glottal flow waveform. In its basic form, this apparatus uses the peak value P of the slightly smoothed oral flow waveform, the minimum value L derived from an oral flow waveform that is linear-phased low-pass filtered at approximately 1/2 F₁, where F₁ is the estimated frequency of the first formant for the vowel spoken, and the average or mean value M of the oral flow waveform. This apparatus differs from previous apparatus in that precise formant measurements are not required; rough aural monitoring of the vowel is sufficient. Nasality is permitted, provided that the sum of oral and nasal flow is used instead of oral flow alone where significant nasality is present. This technique is more robust than previous techniques, because there are no variable parameters that can cause gross errors if set incorrectly during the measurement procedure. The stylized waveform that can be reconstructed from the measured parameters permits easy intrasubject and intersubject comparisons. To simplify the process of voice parameter extraction, this technique utilizes a number of special features of the voice waveform and of vocal tract acoustics during an open vowel (such as "ah" or "ae"). During the most open phase of the glottal cycle, there is little acoustic energy at the vocal tract resonances in the oral flow waveform. Thus, the positive peak of the oral wave does not differ much from the positive peak of the glottal wave, and can be used as an estimate for it. This occurs because there is little formant energy added by the glottal source near the positive peak of the flow waveform, since the motion of the vocal folds is relatively smooth and uninterrupted. Also, the strong oscillations that can be generated at the lower formants during the closed phase are quickly damped when the glottis opens and absorbs some of the energy. To aid in the damping process, added dissipation of the formant energy can be obtained increasing the flow resistance of the pneumotachograph mask. Sound absorbing materials can also be added at the mouth to improve accuracy by further increasing the formant damping, if the resultant change in voice quality is acceptable. As long as F O is less than about 1/3 of F₁, the minimum value of the glottal waveform is well represented by the minimum value of the low-pass filtered output of the approximate inverse-filter. If vocal folds are oscillating in an abducted state, the glottal airflow and oral airflow are both relatively sinusoidal at the fundamental frequency F O , so that a low-pass filter with a cutoff significantly above F O will retain the gross features of the entire waveform and therefore have both maximum and minimum values that approximate those of the glottal waveform. If, on the other, hand, the vocal folds are less abducted, the glottal flow waveform will tend to have a relatively flat portion near the minimum value, as part of the vocal folds come into contact and the glottal area consequently changes less during the period of contact. During this flatter portion, the output of the low-pass filter will have time to approach the value of the minimum level of glottal flow. Thus, the minimum value of the waveform taken from the output of a linear-phase low-pass filter set at about 1/2 F₁ will be very close to the actual minimum of the glottal waveform. To improve accuracy of this approximation, an anti-resonance can be added that is set at approximately the frequency and damping of the first formant F₁. This will allow the low-pass filter to be set somewhat higher in frequency and yet adequately reject the first formant acoustic oscillations, thus extending the range of the frequencies over which this technique is usable. For the purpose of visualizing the underlying vocal fold motions from the measured parameter values, the glottal waveform can be represented by a sinusoid that is truncated at its negative side, and offset from the level of zero flow by a value representing the air "leakage" during the most-closed glottal phase. This waveform would be constructed so as to conform to the glottal parameters measured by the system. An additional feature representing the asymmetry of the glottal flow pulse can be added, but since this asymmetry is caused mostly by vocal tract acoustics, and not by vocal fold motion, it is of less clinical interest. Therefore this can be omitted in most cases. This underlying model for the glottal flow pulse permits computation of the clinically important feature of the glottal duty cycle or open quotient Q O from the negative and positive extremes and the average value. The glottal pulse asymmetry can be estimated from the phase relationship between the fundamental component F O and the lower harmonics, at 2F O , 3F O etc., which for a symmetrical pulse would be in such a phase relationship as to all reach their maximum value simultaneously at one instant in every cycle. Alternatively, the pulse asymmetry can be computed from a moment calculation, as the third central moment is zero for any symmetrical waveform. This estimate can be used, as desired, to correct the computation of open quotient Q O , and may be included in the reconstructed representation of the glottal pulse. An estimate of the vocal fold vibratory period T O , or its reciprocal F O , is required for determining the maximum and minimum of the glottal waveform, and for computing the mean value M. This estimate can be obtained by filtering the oral waveform through a linear-phase (i.e. constant delay) band-pass filter whose pass band lies between the lowest expected fundamental frequency F O and a point between the first formant frequency F₁ and the highest expected fundamental frequency F OH . The glottal period T O can be assumed to be the interval between negative-going zero crossings of the resulting waveform, corrected for the delay introduced by the filter. However, any other similarly robust measure of the glottal period may be used, provided that it employs a cycle-by-cycle determination. The signal from an electroglottograph (EGG) may be useful for this purpose, if a strong EGG signal is available. However, the glottal period T O can be calculated from the oral airflow waveform. The system employing the principles described hereinabove can be used to find the value of the open quotient Q O from the values of the wave center value M , and the amplitude A (which is the peak P minus the minimum L). The implicit function relating the open quotient Q O to the values of M and A, under the assumption of a truncated symmetrical sinusoid, would observe the following relationship: The apparatus of this invention can comprise standard linear or analog type filters and circuits, or, more preferably, can comprise digital filtering and other algorithms on a microcomputer that has analog/digital capabilities added by means of a data acquisition board. To increase formant damping, the pneumotachograph mask could have an airflow resistance about twice the value that is normally used, that is, about one cm H₂O-second per liter. The results of the analysis of a patient's voice can be presented both as a tabulation of the glottal waveform parameters, and as a reconstructed waveform having the shape of a sinusoid clipped at the bottom at the measured open quotient Q O , and having a peak-to-peak amplitude and offset from zero flow corresponding to the measured values of A and L respectively. Glottal pulse asymmetry can be inserted, if desired, but as it does not relate to the functioning of the vocal folds, asymmetry may not be necessary for most clinical applications. Aperiodicity in the glottal flow waveform may be represented by measuring and portraying a sequence of successive glottal cycles. Moreover, a second channel can be used to record the intraoral pressure of the neighboring bilabial stops, as sampled, for example, through a tube at the corner of the mouth, to permit the estimation tracheal pressure. The data can be recorded directly in a computer in digital form or on a multi-channel FM instrumentation-type tape recorder and then played back into the computer for analysis. The above and other objects, features and advantages of this invention will be more fully understood from the ensuing description of a preferred embodiment, which should be considered in connection with the accompanying drawing. Brief Description of the Drawing Fig. 1 is a schematic circuit drawing of a first embodiment of this invention. Fig. 2 is a chart for explaining the operation of the embodiment of Fig. 1. Fig. 3 is a schematic block diagram of a second embodiment of this invention. Figs. 4A-4D are waveform charts for explaining the operation of the embodiment of Fig. 3. Detailed Description of Preferred Embodiments With reference to the drawing, and initially to Fig. 1 thereof, the apparatus of this invention employs a pneumotachographic mask 11, which is a device that detects the velocity of airflow of a human subject's speech. Here the mask 11 is a circumferentially vented pneumotachograph mask of the type often referred to as the Rothenberg mask, and as described in Rothenberg, M., A New Inverse-Filtering Technique For Deriving The Glottal Airflow Waveform During Voicing , Journal of the Acoustical Society of America, Vol. 53, 1973, pages 1632-1645. The mask 11 covers the subject's nose and mouth, and can accommodate both oral and nasal airflow. The shape of the mask is not critical, but generally conforms to the shape of the face with a compressible seal fitting against the patient's face. A number of peripheral openings on mask surfaces closest to the mouth are covered with fine mesh either of wire or other material stiff enough not to vibrate at the voice frequencies, so that the airflow moves out through these holes. The handle shown in Fig. 1 or some other contrivance allows the mask to be kept in an airtight seal with the face during the speech act. Facial hair interfering with such a seal may have to be coated with some form of grease such as petroleum jelly for an accurate recording. In an alternative arrangement that permits accurate measurements when natural speech is not required, a mask may be fit to the lips of the open mouth, and the nares closed to keep all airflow through the mouth. The mask includes a transducing device for measuring the pressure differential between the inside of the mask and immediately outside of the mask, preferably a Glottal Enterprises model MTW differential pressure transducer, which is a Microswitch type 164 transducer modified to extend the frequency response. The mask requires M a uniform frequency response from zero Hz (DC) to at least about three times F O . The transducer output is provided through an amplifier and linear-phase low-pass filter 13 with a roll off above the range of expected values for F₁ to a filter 15 whose transfer function extends from below the lowest fundamental glottal wave frequency F OL (i.e., about 50 Hz) to just above the highest expected glottal frequency F OH (i.e., about 400 Hz). This filter 15 produces an AC wave and supplies the same to a zero crossing detector 16 which provides a measure of the glottal period T O . The output of the amplifier and filter 13 is also fed to a peak value circuit 14 which calculates the maximum or peak value P within each estimated glottal period from detector 16. The output of the amplifier and filter 13 is further fed through an approximate inverse-filter 17, which is a notch filter consisting of a single antiresonant circuit tuned to the approximate expected frequency and damping of the first formant F₁. The output of this filter 17 is supplied to a linear-phase low-pass filter 18 which has a - 3dB roll off frequency F c at about half the frequency of the first formant F₁. An eight-pole Bessel filter or equivalent would be appropriate for this filter. The signal appearing at the output of the filter 18 will be a smoothed representation of the glottal waveform, and will have a negative extreme either at zero or substantially offset above zero as appears in Fig. 2. This output signal and the glottal period from the circuit 16 are fed to a calculating circuit 19 which determines the minimum value of the output signal within the glottal period, which value represents an estimate of the airflow at the point of maximum closure of the vocal folds, a value sometimes referred to as glottal airflow leakage. A difference circuit 20 receives the peak value P from the circuit 14 and also receives the minimum value from the circuit 19, and produces an amplitude value A which corresponds the difference between the peak and minimum values. The output signal from the linear-phase filter 18 is also fed to a low-pass filter whose cutoff frequency is substantially below the fundamental glottal frequency F O , i.e., with a time constant greater than the glottal period T O . This produces generally a DC value corresponding to the mean or average airflow value M. The value M from the filter 21 and the minimum value L from the circuit 19 are supplied to a difference circuit 22 which produces an output signal that corresponds to the wave center value M , which is the difference between the mean airflow M and the minimum value. Finally, the amplitude value A and the glottal wave center value M are fed to an open quotient detecting circuit 23, which provides the value of the glottal duty cycle or open quotient Q O . This open quotient Q O is simply the duration of the open portion of the glottal wave B (representing the period when the vocal folds are not in contact) to the entire glottal period T O . Appropriate relationships of these values P, L, M, M , A, T O , B, and C are all shown on the waveform chart of Fig. 2. In the circuit 23, the open quotient Q O can be determined as a function of the wave center value M and the wave amplitude A, according to the relationship: This relationship arises from the truncated sinusoidal wave approximation. Rather than having an intricate circuit to solve for Q O as a function of M and A directly, it is adequate to provide the values of Q O from a programed look-up table as a function of the ratio M /A. An alternative arrangement is shown in Fig. 3. Here, a circumferentially-vented pneumotachograph mask 31 has a differential pressure transducer 32 connected to a suitable amplifier 33 which amplifies signals in the voice frequency range down to direct current and a linear-phase low-pass prefilter which removes energy substantially above F₁. The output of this amplifier and prefilter 33 is supplied to a speech digitizer circuit 34, which can include a data acquisition board within a personal computer or a similar digital processing device. The digitizer 34, which has an associated clock pulse generator 35, digitizes the input as a series of sample values, and these are stored in a waveform storage device 36, which can be a random access memory of suitable capacity. The digitized values as stored in the storage device 36 are manipulated in a suitably programed processor 37, which automatically produces the values T O , P, L, M, A, M , and Q O . The airflow through the subject's glottis or larynx, which airflow has the general form as shown in Fig. 4A, is modified by the vocal tract resonant and formant frequencies to produce a rather complex voice airflow which after some smoothing or low-pass filtering appears as the signal generally shown in Fig. 4B. The digitizer 34 produces corresponding digital values which appear at the output thereof as quantitized numerical estimates of the sample values (vertical bars) shown in Fig. 4C. These are stored in respective memory locations in the waveform storage device 36. The processor 37 can perform various filtering techniques using appropriate algorithms, such as taking a weighted moving average over a selected time period which may correspond to the glottal period T O , to produce a smoothed approximation of the glottal waveform, as generally shown in Fig. 4D. The digitized waveform values in 4C and 4D can be measured directly to obtain the values P, L, and T O . An average of the stored digitized signal values over any given glottal period T O will produce a mean or average flow value M. The amplitude A, the center value M , and the open quotient Q O can be derived from the above, as with the first embodiment.

Claims: 1. Apparatus for extracting voice parameters from oral or combined oral and nasal air flow produced during voiced speech, in which a patient pronounces a voiced vowel into a pneumotachographic instrument that produces an output signal representing the vowel voiced-speech waveform including a signal component that represents the means air flow (M), CHARACTERIZED IN THAT a low pass filter (13) has an input coupled to said pneumotachographic instrument (11, 12) and filters said airflow signal to produce a prefiltered waveform in which frequencies higher than the first formant frequency (F₁) of the pronounced vowel are suppressed; a signal processing circuit (15, 16, 17, 18) has inputs to receive the prefiltered waveform and which derives from the prefiltered waveform its peak value P, minimum value L, glottal wave period T O , and mean airflow value M for a glottal waveform; a first calculating circuit (19, 20, 21, 22) supplied from said signal processing circuit (15, 16, 17, 18) with said values P, L, T O , and M for outputting an amplitude A of the glottal waveform based on the relationship A = P - L; and outputting a wave center value M based on the relationship M = M - L; a second calculating circuit (23) which outputs an open quotient Q O based on the relationship Q O = B/T O where B is the open portion of the glottal wave period in which the patient's glottis is open and T O is the duration of an entire glottal wave period, wherein the open quotient is output as a value that is based on a function of the amplitude A and wave center value M ; and a processing circuit (37) producing a record of the values T O , P, L, and Q O , of the patient. 2. The apparatus of claim 1 further characterized in that said low-pass filter includes a low-pass filter (13) having an input coupled to receive the output signal of the pneumotachographic instrument (11) and an output, a band-pass filter (15) coupled to the output of said low-pass filter having a pass band that extends from the lowest frequency F OL to the highest frequency F OH expected for the fundamental frequency of the glottal wave of said pronounced vowel, and producing an output signal, and a zero-crossing detector (16) which measures the period T O of the glottal waveform from the output signal of said band-pass filter. 3. The apparatus of claim 2 further characterized in that the input of a peak detector circuit (14) is coupled to the output of the said prefilter circuit and said zero crossing detector (16) to derive the peak glottal airflow (P) from the peak value of the prefilter output within the glottal period obtained from the zero crossing detector (16). 4. The apparatus of claim 2 further characterized in that said low-pass filter includes an approximate inverse-filter circuit (17) coupled to the output of said low-pass filter means and for reducing the energy at and near the first formant frequency F₁ of said vowel, followed by a second low-pass filter (18) of roll-off frequency below the lowest expected first formant frequency but well above the highest expected fundamental frequency F OH and said calculating circuit includes a minimum-value calculator (19) coupled to the output of said second low-pass filter and to said zero-crossing detector (16) to derive the minimum value L of the glottal airflow. 5. The apparatus of claim 3 further characterized in that said low pass filter includes a third low-pass filter (21) and having a roll-off frequency below the expected frequency F O of the glottal waveform for producing the value M of mean glottal airflow. 6. The apparatus of claim 5 further characterized in that said first calculating means includes a subtraction circuit (20) for combining the peak value P and minimum value L of said logic circuit (22) for combining the mean glottal airflow value M and the glottal waveform minimum value L to produce the wave center value M . 7. The apparatus of claim 1, further characterized in that said low-pass filter includes a digitizer (34) for digitizing the output of said pneumotachographic instrument (31) as a sequence of numerical samples values, and a circuit (36, 37) selectively combines the numerical sample values to produce a derivative sequence of values representing the glottal waveform, from which can be measured the values of T O , P, L, and M.

Inventors: ROTHENBERG, MARTIN
Applicants: SYRACUSE UNIVERSITY
Application year: 1988
Main classification: A61B5
IPC codes: G10L11, G10L15, A61B5