CN111631728B - Method and device for measuring bone conduction transfer function and storage medium - Google Patents
Method and device for measuring bone conduction transfer function and storage medium Download PDFInfo
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- A—HUMAN NECESSITIES
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Abstract
The invention discloses a method for measuring a bone conduction transfer function, which comprises the following steps: synthesizing sweep frequency sound, wherein the sweep frequency sound comprises a probe sound and a suppression sound; playing the sweep tone at mastoids on both sides of the user's head; acquiring a mixed signal in an ear canal and extracting an acoustic signal of a swept frequency stimulation frequency otoacoustic emission from the mixed signal; and calculating bone conduction transfer function data according to the probe sound and the sound signals emitted by the stimulation frequency otoacoustic. The invention provides a method and a device for measuring a bone conduction transfer function and a storage medium, which can quickly measure the BCTF data of both sides of the head of a user.
Description
Technical Field
The present invention relates to the technical field of earphones and hearing aid devices, and in particular, to a method and an apparatus for measuring a bone conduction transfer function, and a storage medium.
Background
When a user wears a device such as a binaural bone conduction earphone and a hearing aid, due to crosstalk influence of bone conduction sound, the isolation between ears is not high, and the existence of the cross crosstalk sound will destroy spatial information carried by binaural sound signals and influence sound source positioning capacity. Designing a personalized cross talk cancellation system requires obtaining the user's own Bone-Conduction Transfer Function (BCTF). At present, researches on BCTF at home and abroad are mainly focused on corpse heads and dry skull bones, so that the real head BCTF characteristics of living people cannot be reflected, most of the measured data are discrete frequency point data with limited quantity, and the measuring method is long in time consumption, so that the accuracy is not high and the detection efficiency is low.
Disclosure of Invention
In view of the above technical problems, the present invention provides a method, an apparatus and a storage medium for measuring a bone conduction transfer function, which can quickly measure the BCTF data of both sides of the head of a user. The technical scheme is as follows:
in a first aspect, an embodiment of the present invention provides a method for measuring a bone conduction transfer function, including:
synthesizing a sweep tone, wherein the sweep tone comprises a probe tone and a suppressor tone;
playing the sweep tone at papillae on both sides of the user's head;
acquiring a mixed signal in an ear canal and extracting an acoustic signal of a swept frequency stimulation frequency otoacoustic emission from the mixed signal;
and calculating bone conduction transfer function data according to the probe sound and the sound signals emitted by the stimulation frequency otoacoustic.
In a first possible implementation manner of the first aspect of the present invention, the playing the sweep tone at the papillae on both sides of the head of the user specifically includes:
playing the sweep frequency sound at the mastoid on one side of the head of a living person by two bone conduction vibrators in a three-interval paradigm; playing one of the stimulating sounds only by using the first bone conduction vibrator in a first period of time; in a second period of time, only using the second bone conduction vibrator to play another kind of stimulation sound; in a third period of time, the two bone conduction vibrators respectively play two stimulation sounds simultaneously; the stimulating sound is a probe sound or a suppressor sound.
In a second possible implementation manner of the first aspect of the present invention, the amplitude spectrum and the phase spectrum of the probe tone and the suppression tone are designed according to a three-interval normal form method, which specifically includes the following steps:
setting an amplitude spectrum with an unchanged amplitude value according to the sound pressure level of the bone conduction sound;
and performing integral calculation according to the linear change of the frequency of the sweep tone in the duration to obtain a phase spectrum.
In a third possible implementation manner of the first aspect of the present invention, extracting an acoustic signal emitted by otoacoustic at a frequency sweep stimulation frequency from the mixed signal, and further performing signal preprocessing, specifically:
acquiring four groups of data from ears of a user, wherein each group of data records a plurality of mixed signals and filters high and low frequency noise through a band-pass filter;
after filtering, extracting three sections of response signals contained in each group of mixed signals, and obtaining a residual signal through linear operation;
according to a threshold rejection criterion, eliminating residual signals containing impulse noise in each group of residual signals;
performing superposition average processing on the residual signals subjected to the elimination processing;
and outputting the preprocessed mixed sound signal containing the frequency sweep stimulation frequency otoacoustic emission.
In a fourth possible implementation manner of the first aspect of the present invention, the linear operation is specifically:
X SFOAE (t)＝X P (t)+X S (t)-X SP (t) (1)
in the formula (1), x P (t)，x S (t)，x SP (t) respectively corresponding to three sections of response signals recorded by the probe microphone after being played in a three-interval paradigm; x SFOAE (t) is a residual signal.
In a fifth possible implementation manner of the first aspect of the present invention, the signal obtained by the preprocessing is filtered by using a dynamic tracking filter, where a transfer function of the dynamic tracking filter is as follows:
h (z) is a signal after filtering processing, and z is an input signal;
pole z 1 Radius r of 1 ＝1-πΔf/f s Zero point z 2 Radius r of 2 Is 1, Δ f is the filter bandwidth, f s The system sampling frequency; omega 1 Is the instantaneous angular frequency, omega, of the pole 1 ＝2πf 1 /f s ，ω 2 Is the instantaneous angular frequency of the zero point, omega 2 ＝2πf 2 /f s ；f 1 、f 2 Respectively corresponding to the frequency of the probe sound and the frequency of the inhibiting sound; the gain G is compensated to ensure that at f 1 Without attenuation.
In a sixth aspect of the present inventionIn an implementation manner, the frequency of the probe and the suppression tones as a function of time are respectively: f. of 1 (t) =9900t +100, and f 2 (t) =9900t +300; time t =1,2,3, \ 8230;, f s ，f s For the system sampling frequency, f s Take 44100Hz.
In a seventh possible implementation of the first aspect of the invention, the two bone conduction elements are fixed at the mastoid process on the right or left side of the user's head and the probe microphone is placed in the right or left ear canal to collect the signals.
In a second aspect, an embodiment of the present invention provides a device for measuring a bone conduction transfer function, including a processor, a memory, and a computer program stored in the memory and configured to be executed by the processor, where the processor implements the method for measuring a bone conduction transfer function as described above when executing the computer program.
In a third aspect, an embodiment of the present invention provides a storage medium for a method for measuring a bone conduction transfer function, where the storage medium is used to store one or more computer programs, and the one or more computer programs include program codes, and when the computer programs are run on a computer, the program codes are used to execute the method for measuring a bone conduction transfer function.
Compared with the prior art, the embodiment of the invention has the following beneficial effects:
the invention provides a measuring method, a device and a storage medium of a bone conduction transfer function, wherein sweep frequency tones which are synthesized by a computer and comprise a detection tone and a suppression tone are played at mastoids on two sides of the head of a living person, so that sweep frequency stimulation frequency otoacoustic emission is induced by utilizing the sweep frequency stimulation sound, mixed signals in an ear canal are collected, and acoustic signals emitted by the sweep frequency stimulation frequency otoacoustic emission are extracted from the mixed signals; and calculating bone conduction transfer function data according to the probe sound and the sound signals emitted by the otoacoustic at the stimulation frequency. In the technical scheme of the invention, the BCTF between the bone conduction vibrator and the inner ears at two sides of the living human is estimated according to the frequency sweep SFOAE signal generated by the induced living human cochlea, so that the bone conduction acoustic characteristic of the head of the living human is reflected more truly, and compared with the measurement data acquired from the dry skull and the dead head, the measurement data is more accurate and has practical significance. In addition, the BCTF is estimated by using the sound signals emitted by the sweep frequency stimulation frequency otoacoustic induced by the sweep frequency sound, so that the measurement efficiency is greatly improved compared with the frequency point-by-frequency point induction.
Drawings
FIG. 1 is a schematic diagram of a method for measuring a bone conduction transfer function according to an embodiment of the present invention;
FIG. 2 is a flow chart illustrating steps of a method for measuring a bone conduction transfer function according to an embodiment of the present invention;
fig. 3 is a constant amplitude spectrum of a frequency sweep signal of a measurement method of a bone conduction transfer function in an embodiment of the present invention;
FIG. 4 is a diagram illustrating a relationship between a group delay and a frequency of a frequency-swept signal according to a measurement method of a bone conduction transfer function in an embodiment of the present invention;
FIG. 5 is a phase spectrum of a swept frequency signal of a method for measuring a bone conduction transfer function according to an embodiment of the present invention;
FIG. 6 is a schematic diagram of a three-interval paradigm of a method for measuring a bone conduction transfer function according to an embodiment of the present invention;
FIG. 7 is a graph illustrating the two-tone suppression of a bone conduction transfer function measurement method according to an embodiment of the present invention;
FIG. 8 is a zero-pole diagram of a dynamic tracking filter of a method for measuring a bone conduction transfer function according to an embodiment of the present invention;
fig. 9 is a flow chart of a method for measuring a bone conduction transfer function according to an embodiment of the present invention to extract a clean SFOAE signal.
Detailed Description
The technical solutions in the embodiments of the present invention will be clearly and completely described below with reference to the drawings in the embodiments of the present invention, and it is obvious that the described embodiments are only a part of the embodiments of the present invention, and not all of the embodiments. All other embodiments, which can be derived by a person skilled in the art from the embodiments given herein without making any creative effort, shall fall within the protection scope of the present invention.
Referring to fig. 1 and 2, an exemplary embodiment of a method for measuring a bone conduction transfer function according to the present invention includes the steps of:
synthesizing sweep frequency sound, wherein the sweep frequency sound comprises a probe sound and a suppression sound;
playing the sweep tone at papillae on both sides of the user's head;
preferably, the sweep frequency sound is played at the mastoid positions on two sides of the head of the living person in a three-interval paradigm through two bone conduction vibrators;
acquiring a mixed signal in an ear canal and extracting an acoustic signal of a swept frequency stimulation frequency otoacoustic emission from the mixed signal;
it is understood that the mixed signal is a swept SFOAE signal generated after the cochlea is stimulated by the sweep tone, and then is added with the ambient noise in the ear canal;
SFOAE signals, i.e. acoustic signals that stimulate frequency otoacoustic emissions that are the products of cochlear hair cell movement, i.e. modulation of the basement membrane by the outer capillaries, so that weak acoustic signals are amplified. This acoustic signal can only be detected if the middle ear is functioning properly.
And calculating bone conduction transfer function data according to the probe sound and the sound signals emitted by the otoacoustic at the stimulation frequency.
Preferably, the calculated bone conduction transfer function data is calibrated to eliminate the influence of the vibration characteristics of the bone conduction vibrator itself.
In the present embodiment, the frequency sweep tone is synthesized from a preset magnitude spectrum and phase spectrum.
Referring to fig. 3, 4 and 5, the synthesized frequency sweep tone is first a linear frequency sweep stimulus sound required for synthesis, the linear frequency sweep signal is constructed in the frequency domain, and the frequency domain signal is synthesized according to the amplitude spectrum and the phase spectrum; the phase spectrum is obtained from the integration of the group delay with respect to frequency, and the phase spectrum of the linear sweep tone is shown in FIG. 5. Finally, the frequency domain signal is subjected to inverse Fourier transform to obtain a swept time domain waveform, the frequency domain construction can have good frequency domain characteristics, and the relative amplitude of each frequency component can be conveniently controlled.
In a specific embodiment, the computer synthesizes required sweep frequency sound according to a designed amplitude spectrum and a designed phase spectrum, wherein the sweep frequency sound comprises a probe sound M1 and a suppression sound M2; playing at the mastoid on two sides of the head of a living person by two bone conduction vibrators in a three-interval paradigm method; picking up the mixed signal in the ear canal with a probe microphone; the picked mixed signals are transmitted back to the sound card through the microphone and then transmitted back to the computer through the sound card, and the sweep frequency SFOAE signals induced by the probe are extracted through preprocessing procedures such as removing stimulation artifacts, filtering and superposing average and the like on the measured multiple groups of data; after the SFOAE signal is obtained, deconvolution calculation is carried out on the SFOAE signal according to the detection sound M1 to obtain a bilateral bone conduction impulse response, and then bilateral BCTF is calculated through Fourier transform; finally, relevant physiological parameters of the user, such as sex, age, head size, head fat and weight, hearing health condition and the like are recorded and stored in the database together with the BCTF data.
Referring to fig. 6, in a preferred embodiment, the frequency sweeping tone is played at the mastoid on both sides of the head of the user, specifically:
playing the sweep frequency sound at the mastoid on one side of the head of a living person by two bone conduction vibrators in a three-interval paradigm; in a first period of time, only using the first bone conduction vibrator to play one of the stimulation sounds; in a second period of time, only using the second bone conduction vibrator to play another kind of stimulation sound; in a third period of time, the two bone conduction vibrators respectively play two stimulation sounds at the same time; the stimulating sound is a probe sound or a suppressor sound.
Specifically, two kinds of sweep tones, namely a probe tone M1 and a suppression tone M2, are respectively played in three equal time intervals T, specifically, in the first interval T, only the bone conduction vibrator a plays the stimulation sound M1; in the second section T, only the bone conduction vibrator B plays the stimulation sound M2; in a third segment T, transducers a and B play simultaneously stimulating sounds M1 and M2, respectively, where T takes 1 second.
In a preferred embodiment, the amplitude and phase spectra of the probe and the suppressor are designed according to a three-interval paradigm as follows:
setting an amplitude spectrum with an unchanged amplitude value according to the sound pressure level of the bone conduction sound; the sound pressure level of the bone conduction sound is calibrated through sound level equalization of the air conduction sound and the bone conduction sound;
and carrying out integral calculation according to the linear change of the frequency sweeping tone along with time in the duration to obtain a phase spectrum.
Specifically, the amplitude spectrum of the sweep frequency probe M1 calibrates the sound pressure level of the bone conduction sound to 60dB SPL according to the air conduction sound and the sound level balance of the bone conduction sound, calibrates the input voltage amplitude of the bone conduction sound by taking the air conduction 1kHz pure sound of the 60dB SPL perceived by the subject as a reference, and integrates the frequency to obtain the phase spectrum of the M1, wherein the frequency is linearly increased from 100Hz to 10000Hz within 1 second time interval; the amplitude of the amplitude spectrum of the sweep frequency probe M2 calibrates the sound pressure level of the bone conduction sound to 80dB SPL according to the sound level balance of the air conduction sound and the bone conduction sound, and the specific steps are as above, the frequency-time relation is that the frequency is linearly increased from 300Hz to 10200Hz within the time interval of 1 second, and the phase spectrum of the M2 is obtained by integrating the frequency and the time. The sampling rates are all 44.1kHz, and the quantization bit number is 24bits.
In a preferred embodiment, extracting the acoustic signal of the otoacoustic emission at the frequency of the sweep stimulus from the mixed signal, further needs to perform signal preprocessing, specifically:
acquiring four groups of data from ears of a user, wherein each group of data records a plurality of mixed signals and filters high and low frequency noise through a band-pass filter;
the four sets of data are data measured according to different measurement orders for each user's ears, with each set (each side) measured 10 times in this embodiment; the binaural measurement order is:
RR, the two bone conduction vibrators are worn on the right mastoid, and the probe microphone is placed in the right auditory canal;
RL, two bone conduction vibrators are worn on the right mastoid, and a probe microphone is placed in the left auditory canal;
LR, two bone conduction vibrators are worn on the left mastoid, and a probe microphone is placed in the right auditory canal;
two bone conduction vibrators are worn on the left mastoid, and a probe microphone is placed in the left auditory canal.
R is the right side and L is the left side.
After filtering, extracting three sections of response signals contained in each group of mixed signals, and obtaining a residual signal through linear operation;
the linear operation is specifically as follows:
X SFOAE (t)＝X P (t)+X S (t)-X SP (t) (1)
in the formula (1), x P (t),x S (t),x SP (t) respectively corresponding to three sections of response signals recorded by the probe microphone after being played in a three-interval paradigm; x SFOAE Is a residual signal. Due to the principle of dual-tone suppression and the linearity of the stimulus and the nonlinearity of the swept frequency SFOAE, the linear operation of equation (1) can basically eliminate the stimulus artifact and the swept frequency SFOAE signal E2 induced by the sweep frequency suppression tone M2, and the residual (residual) signal x SFOAE In (t), only the sweep frequency SFOAE signal E1 induced by the sweep frequency probe M1 and a small amount of residual noise remain.
According to a threshold rejection criterion, eliminating residual signals containing impulse noise in each group of residual signals;
performing superposition average processing on the signals subjected to the rejection processing;
and outputting the preprocessed mixed sound signal containing the frequency sweep stimulation frequency otoacoustic emission.
Referring to fig. 7, 8 and 9, the signal preprocessing process is as follows:
and after the probe microphone collects the mixed signal, preprocessing the mixed signal. The mixed signal is filtered by a band-pass filter with the cut-off frequency of 300 to 10kHz to filter high-frequency and low-frequency noise. Three sections of response signals recorded by the microphone are respectively x P (t)，x S (t) and x SP (t)。x P (t) contains, in addition to M1 and its induced SFOAE signal E1, background noise, and similarly, x S (t) contains M2 and its induced SFOAE signal E2 and background noise. In the third section, due to the cochlear diphone suppression mechanism, the probe M1-induced SFOAE signal E1 is almost completely suppressed by M2, while the M2-induced SFOAE signal E1 is almost completely suppressedThe signal E2 remains largely unchanged, i.e. x SP The (t) mainly includes M1, M2 and M2 induced SFOAE signals E2 and background noise. And the SFOAE signal induced by the linear stimulation sound is nonlinear, for x P (t)，x S (t) and x SP (t) performing the following linear operation on the three sections of response signals:
X SFOAE (t)＝X P (t)+X S (t)-X SP (t) (1)
a signal x can be obtained SFOAE (t) the main component of which is the probe M1 induced SFOAE signal E1, while the other stimulus artifacts M1, M2 and M2 induced SFOAE are substantially eliminated.
Since 10 measurements were made on each side, there will be some x SFOAE (t) impulse noise due to the sound emitted by the subject's body movement or chewing, rejecting measurement signals containing large impulse noise based on a threshold rejection principle, and then averaging the remaining signals.
Preferably, the signal obtained after the preprocessing is subjected to dynamic tracking filtering, where the dynamic tracking filter is used to extract an SFOAE signal E1 induced by the sweep frequency probe M1 in the signal, and specifically:
when the stimulus signal is a swept frequency signal, the signal frequencies all become functions with respect to time, respectively denoted as f 1 (t)，f 2 (t) of (d). First of all, according to the frequency f of the probe M1 1 (t) and delay estimating the frequency of the induced SFOAE signal E1, taking the frequency as the central frequency of the dynamic pole of the tracking filter, and simultaneously placing the dynamic zero at the frequency f corresponding to the suppression sound M2 2 On (t), the two frequencies are denoted in the following by f 1 ，f 2 The transfer function of the dynamic tracking filter is shown as follows:
wherein
Pole z 1 Radius r of 1 ＝1-πΔf/f s Zero point z 2 Radius r of 2 Is 1, Δ f is the filter bandwidth, f s The system sampling frequency; omega 1 Is the instantaneous angular frequency, omega, of the pole 1 ＝2πf 1 /f s ，ω 2 Is the instantaneous angular frequency of the zero point, omega 2 ＝2πf 2 /f s ；f 1 、f 2 Respectively corresponding to the frequency of the probe sound and the frequency of the inhibiting sound; the gain G is compensated to ensure that at f 1 Coefficient introduced without attenuation:
the frequency of the two frequency sweeps as a function of time is: f. of 1 (t)＝9900t+100，f 2 (t)＝9900t+300(t＝1,2,3,…,f s ) And Δ f is 75Hz, f s Take 44100Hz.
Although the frequency of the induced sweep frequency SFOAE signal is almost completely coincided with the frequency of the sweep frequency stimulating sound, the setup of the center frequency of the zero point and the pole of the tracking filter must consider the influence of the delay to accurately extract the sweep frequency SFOAE signal because the SFOAE signal has a certain delay from induction to recording. The delay comprises two parts of system delay and group delay of SFOAE generated by a basement membrane, the system delay is calculated according to a cross-correlation method, the group delay of the SFOAE is obtained by a power law fitting model of SFOAE delay and frequency researched by the predecessor, and the function relationship is as follows:
τ(f)＝10.4f -0.4 (4)
the present invention also provides an embodiment in which prior to the start of the measurement, cerumen removal is performed on subject 1 (female, 24 years old) with normal hearing and no history of outer or middle ear, and then a two-sided BCTF measurement experiment is started by sitting in a sound isolation booth as shown in fig. 1. The measurement equipment is connected as shown in fig. 1, two bone conduction vibrators A and B are fixed at the mastoid of a subject 1 by an elastic bandage, and a probe microphone with a sound insulation sponge plug connected at the tail part is placed in the ear canal of the subject 1, and the distance between the probe head and the ear canal mouth is about 2cm. The measurement sequence, namely the wearing positions of the bone conduction vibrator and the probe microphone are as follows:
RR, wearing two bone conduction vibrators on the right mastoid, and placing a probe microphone in the auditory canal of the right side;
RL, two bone conduction vibrators are worn on the right mastoid, and a probe microphone is placed in the left auditory canal;
LR, two bone conduction vibrators are worn on the left mastoid, and the probe microphone is placed in the right auditory canal;
two bone conduction vibrators are worn on the left mastoid, and a probe microphone is placed in the left auditory canal.
In this example, experimental data obtained from only the RR side and the LR side are shown.
When the measurement is started, a subject presses a play key on a computer, the computer can play three sections of linear sweep frequencies with the length of 3 seconds on two channels as a stimulation signal according to a three-interval paradigm method, the sweep frequency signal outputs a sweep frequency signal to a bone conduction vibrator through a sound card headset interfaces, a transducer is driven to sound, an acoustic probe placed in an external auditory canal is used for picking up an SFOAE signal which is induced by a cochlea at the moment, the picked-up signal is transmitted back to the computer through the sound card to be stored, and each side experiment is repeatedly measured for ten times to reduce random errors. Then deconvolution is carried out by utilizing the stimulation signal and the picked SFOAE signal to obtain the total impulse response, and then the BCTF is obtained by calibrating and eliminating the transmission characteristic of the bone conduction vibrator.
The amplitude of the second half part of the time domain waveform is small because the vibration force level curve of the used bone conduction vibrator is uneven, so that the influence of the transmission characteristic of the bone conduction vibrator needs to be removed by later calibration, and in addition, the amplitude of an RR side (the same side) is larger than that of an LR side (the different side) because the stimulation sound component collected by the same side is larger. Compared with the time domain waveform, more noise still exists on each frequency band on the frequency domain, especially more than 2 kHz.
After the signals are subjected to dynamic tracking filtering, the overall amplitude of the signals is found to be smaller than that of the signals without filtering by an order of magnitude, because stimulation artifact components with larger amplitude are filtered, meanwhile, the amplitude of the front small half part of the RR side is smaller than that of the LR side, the possible reason is that the transcranial transmission of the subject 1 is higher, in addition, the edges of the whole time domain waveform are found to be smooth, no edge burrs exist in the amplified part, and random noise is filtered.
According to the extracted SFOAE signal and the sweep frequency stimulus sound, the total impulse response c at two sides can be obtained by deconvolution RR And c LR The impulse response is centered on the first 15ms. Fourier transform is carried out on the impulse response to obtain a total transfer function C within the range of 400-10 kHz RR And C LR The amplitude is gradually reduced along with the increase of the frequency, the difference of the high-frequency amplitude and the low-frequency amplitude is about 20-30 dB, meanwhile, an anti-resonance phenomenon exists before 3kHz, in addition, the superposition phenomenon of transfer function curves at two sides caused by rigid body vibration of the skull under the low frequency does not occur at the first 500Hz, and the possible reason is that the influence of skin tissues of the head of a living person and the influence caused by the difference of the measurement positions and the coupling degree at two sides can exist because the head of the living person is measured instead of the dry skull in the embodiment. To C RR And C LR Carrying out calibration processing to eliminate the transmission characteristic of the bone conduction vibrator and obtain BCTF data H at two sides RR And H LR Compared with the transfer function before calibration, the overall reduction after calibration is about 20-30 dB, but the high-frequency part is improved by about 20dB relative to the low frequency part, and the overall trend is not changed greatly. Finally, the physiological parameters of the subject 1, such as sex, age, head size and hearing health, are recorded and stored in a database.
The results of this example show that a bilateral bone conduction transfer function measurement method using swept tone induced stimulation frequency otoacoustic emissions is feasible. The method has the advantages of short measurement time, small calculated amount and easy analysis.
The invention provides an exemplary embodiment, a device for measuring a bone conduction transfer function, comprising a processor, a memory and a computer program stored in the memory and configured to be executed by the processor, wherein the processor implements the method for measuring the bone conduction transfer function as described above when executing the computer program.
The present invention provides an exemplary embodiment, a storage medium of a method of measuring a bone conduction transfer function for storing one or more computer programs, the one or more computer programs comprising program code for performing the above method of measuring a bone conduction transfer function when the computer program runs on a computer.
The computer readable media of the embodiments of the present application may be computer readable signal media or computer readable storage media or any combination of the two. More specific examples (a non-exhaustive list) of the computer readable storage medium would include the following: an electrical connection (electronic device) having one or more wires, a portable computer diskette (magnetic device), a Random Access Memory (RAM), a read-only memory (ROM), an erasable programmable read-only memory (EPROM or flash memory), an optical fiber device, and a portable read-only memory (CDROM). Additionally, the computer-readable storage medium could even be paper or another suitable medium upon which the program is printed, as the program can be electronically captured, via for instance optical scanning of the paper or other medium, then compiled, interpreted or otherwise processed in a suitable manner if necessary, and then stored in a computer memory.
It should be understood that portions of the present application may be implemented in hardware, software, firmware, or a combination thereof. In the above embodiments, the various steps or methods may be implemented in software or firmware stored in memory and executed by a suitable instruction execution system. For example, if implemented in hardware, as in another embodiment, any one or combination of the following technologies, which are well known in the art, may be used: a discrete logic circuit having a logic gate circuit for implementing a logic function on a data signal, an application specific integrated circuit having an appropriate combinational logic gate circuit, a Programmable Gate Array (PGA), a Field Programmable Gate Array (FPGA), or the like.
It will be understood by those skilled in the art that all or part of the steps carried out in the method for implementing the above embodiment may be implemented by hardware that is related to instructions of a program, and the program may be stored in a computer readable storage medium, and when executed, the program includes one or a combination of the steps of the method embodiment.
In addition, functional units in the embodiments of the present application may be integrated into one processing module, or each unit may exist alone physically, or two or more units are integrated into one module. The integrated module can be realized in a hardware mode, and can also be realized in a software functional module mode.
The invention provides a measuring method, a device and a storage medium of a bone conduction transfer function, wherein sweep frequency sounds which are synthesized by a computer and comprise a detection sound and a suppression sound are played at mastoids on two sides of the head of a living person, so that sweep frequency stimulation frequency otoacoustic emission is induced by utilizing the sweep frequency stimulation sound, mixed signals in an ear canal are collected, and acoustic signals emitted by the sweep frequency stimulation frequency otoacoustic emission are extracted from the mixed signals; and calculating bone conduction transfer function data according to the probe sound and the sound signals emitted by the stimulation frequency otoacoustic. In the technical scheme of the invention, the BCTF between the bone conduction vibrator and the inner ears at two sides of the living human is estimated according to the frequency sweep SFOAE signal generated by the induced living human cochlea, so that the bone conduction acoustic characteristic of the head of the living human is reflected more truly, and compared with the measurement data acquired from the dry skull and the dead head, the measurement data is more accurate and has practical significance. In addition, the BCTF is estimated by using the sound signals emitted by the sweep frequency otoacoustic stimulation frequency induced by the sweep frequency tone, so that the measurement efficiency is greatly improved compared with a frequency point-by-frequency point induction method.
While the foregoing is directed to the preferred embodiment of the present invention, it will be understood by those skilled in the art that various changes and modifications may be made without departing from the spirit and scope of the invention.
Claims (8)
1. A method for measuring a bone conduction transfer function, comprising the steps of:
synthesizing sweep frequency sound, wherein the sweep frequency sound comprises a probe sound and a suppression sound;
playing the sweep tone at papillae on both sides of the user's head;
the method comprises the following steps of collecting mixed signals in the auditory canal, and preprocessing the mixed signals, specifically: acquiring four groups of data from ears of a user, wherein each group of data records a plurality of mixed signals and filters high and low frequency noise through a band-pass filter;
after filtering, extracting three sections of response signals contained in each group of mixed signals, and obtaining a residual signal through linear operation;
according to a threshold rejection criterion, eliminating residual signals containing impulse noise in each group of residual signals;
performing superposition average processing on the residual signals subjected to the elimination processing;
outputting the preprocessed mixed signal containing the sweep frequency stimulation frequency otoacoustic emission, filtering the mixed signal by using a dynamic tracking filter, and extracting the acoustic signal of the sweep frequency stimulation frequency otoacoustic emission from the mixed signal, wherein the specific steps are as follows:
obtaining a first frequency of an acoustic signal induced by the probe according to the frequency and the delay of the probe, taking the first frequency as a central frequency of a dynamic pole of the dynamic tracking filter, and placing a dynamic zero of the dynamic tracking filter on a frequency corresponding to the suppression tone;
the transfer function of the dynamic tracking filter is shown as follows:
h (z) is a signal after filtering processing, and z is an input signal;
pole z 1 Radius r of 1 ＝1-πΔf/f s Zero point z 2 Radius r of 2 Is 1, Δ f is the filter bandwidth, f s The system sampling frequency; omega 1 Is the instantaneous angular frequency, omega, of the pole 1 ＝2πf 1 /f s ，ω 2 Is the instantaneous angular frequency of the zero point, omega 2 ＝2πf 2 /f s ；f 1 、f 2 Respectively corresponding to the frequency of the probe sound and the frequency of the inhibiting sound; the gain G is compensated to ensure that at f 1 The coefficients introduced without attenuation are processed,
the delay comprises a system delay and a group delay, wherein the system delay is calculated by adopting a cross-correlation method, the group delay is obtained by performing power law fitting on the delay and the frequency of an acoustic signal, and the group delay function is as follows:
τ(f)＝10.4f -0.4
wherein f is the frequency of the acoustic signal;
according to the sound signal emitted by the probe sound and the otoacoustic stimulation with the stimulation frequency, bone conduction transfer function data are calculated, and the method specifically comprises the following steps:
deconvoluting according to the sound signals emitted by the detection sound and the otoacoustic with the stimulation frequency to obtain total impulse responses at two sides;
carrying out Fourier transform on the total impulse responses at the two sides to obtain total transfer functions at the two sides;
and calibrating the total transfer functions on the two sides to obtain bone conduction transfer function data on the two sides.
2. The method for measuring bone conduction transfer function according to claim 1, wherein the sweeping tone is played at the mastoid on both sides of the head of the user, specifically:
playing the sweep frequency sound at the mastoid on one side of the head of a living person by two bone conduction vibrators in a three-interval paradigm; playing one of the stimulating sounds only by using the first bone conduction vibrator in a first period of time; in a second period of time, only using the second bone conduction vibrator to play another kind of stimulation sound; in a third period of time, the two bone conduction vibrators respectively play two stimulation sounds simultaneously; the stimulating sound is a probe sound or a suppression sound.
3. The method for measuring a bone conduction transfer function according to claim 1, wherein the amplitude spectrum and the phase spectrum of the probe tone and the suppressor tone are designed according to a three-interval normal form method as follows:
setting an amplitude spectrum with an unchanged amplitude value according to the sound pressure level of the bone conduction sound;
and performing integral calculation according to the linear change of the frequency of the sweep tone in the duration to obtain a phase spectrum.
4. The method for measuring a bone conduction transfer function according to claim 1, wherein the linear operation is specifically:
X SFOAE (t)＝X P (t)+X S (t)-X SP (t) (1)
in the formula (1), x P (t)，x S (t)，x SP (t) corresponding to three sections of response signals recorded by the probe microphone after being played in a three-interval paradigm respectively; x SFOAE (t) is a residual signal.
5. The method for measuring a bone conduction transfer function according to claim 1, wherein the frequencies of the probe and the suppressor are respectively as a function of time: f. of 1 (t) =9900t +100, and f 2 (t) =9900t +300; time t =1,2,3, \8230;, f s ，f s For the system sampling frequency, f s Take 44100Hz.
6. The method of measuring a bone conduction transfer function of claim 2, wherein the two bone conduction transducers are fixed at mastoids on the right or left side of the user's head, and a probe microphone is placed in the right or left ear canal to collect signals.
7. An apparatus for measuring a bone conduction transfer function, comprising a processor, a memory, and a computer program stored in the memory and configured to be executed by the processor, the processor implementing the method of measuring a bone conduction transfer function according to any one of claims 1 to 6 when executing the computer program.
8. A storage medium for a method of measuring a bone conduction transfer function, the storage medium storing one or more computer programs, the one or more computer programs comprising program code for performing the method of measuring a bone conduction transfer function of any one of claims 1 to 6 when the computer program runs on a computer.
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