CN114376609A - Nasal sound reflectometer, nasal airway measuring method, measuring device, and medium - Google Patents
Nasal sound reflectometer, nasal airway measuring method, measuring device, and medium Download PDFInfo
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Abstract
The invention discloses a nasal sound reflectometer, a nasal airway measuring method, measuring equipment and a medium, wherein the method comprises the following steps: after the upper computer detects the starting detection signal, the electric spark generating device is controlled to periodically discharge based on the FPGA controller; recording a sound signal generated after the electric spark generating device carries out periodic discharge based on a microphone sampling device arranged in the sound wave guide pipe; after the sound signals in the microphone sampling device are read and stored through the FPGA controller, the sound signals stored in the FPGA controller are sent to an upper computer for calculation, and a nasal airway measuring result is obtained. Through with the sound source by the extremely short electric spark of pulse replacement for the speaker, shortened the length of required sound wave pipe, and then avoid the problem that the nasal air flue measurement accuracy descends because of helical structure's sound wave pipe leads to, through handling the calculation to the sound signal of gathering many times in succession, further promote nasal air flue measurement's stability and measurement accuracy.
Description
Technical Field
The invention relates to the technical field of nasal sound reflectometers, in particular to a nasal sound reflectometer, a nasal airway measuring method, measuring equipment and a computer readable storage medium.
Background
The existing nasal sound reflectometer for measuring nasal airway usually uses a loudspeaker as a sound source, and after echo information is collected by a microphone, the condition inside the cavity to be measured is calculated according to the impulse response of the incident signal by adopting WA algorithm or other inverse scattering calculation algorithm.
However, in the prior art, when the impulse response of an incident signal is calculated, the incident pulse and an echo signal need to be effectively separated, and because a loudspeaker as a sound source can make the pulse time longer, a longer sound wave guide tube must be used to ensure the effective separation of the incident pulse and the echo signal, in the design of the sound wave guide tube of the existing nose sound reflectometer, the sound wave guide tube is usually made into a spiral structure to reduce the volume occupied in the nose sound reflectometer, but when the spiral sound wave guide tube is made of a hose, the inside condition of a cavity to be measured cannot be accurately measured by the nose sound reflectometer due to the fact that the inside diameter of the hose is easy to change, and when the rigid tube is used as the sound wave guide tube, the problems of complex manufacturing process and measurement accuracy reduction due to the fact that the cross section of the inside diameter of the hose is not uniform exist.
Therefore, the existing nasal sound reflectometer has the problems of lower precision and poorer measurement stability of the nasal airway measurement result during output due to the design problem of a longer acoustic wave guide tube spiral structure.
Disclosure of Invention
The invention mainly aims to provide a nasal sound reflectometer, a nasal airway measuring method, measuring equipment and a computer readable storage medium, and aims to solve the technical problem that the existing nasal sound reflectometer has the problem of low precision in the process of outputting a nasal airway measuring result due to the design problem of a long sound wave guide tube spiral structure.
In order to achieve the above object, the present invention provides a nasal sound reflectometer, comprising:
an upper computer;
the FPGA controller is in communication connection with the upper computer;
the electric spark generating device is in communication connection with the FPGA controller;
an acoustic waveguide connected to the spark generating device;
a microphone sampling device disposed in the sonic conduit;
and the FPGA controller is in communication connection with the microphone sampling device.
Optionally, the electric spark generating device includes a control terminal, a discharge electrode, a first coil, a second coil, a third coil, a fourth coil, a fifth coil, a first resistor, a second resistor, a third resistor, a fourth resistor, a fifth resistor, a first diode, a second diode, a third diode, a capacitor, a triode, and a battery;
the output end of the control end is connected with one end of the first resistor, the other end of the first resistor is connected with the gate electrode of the second diode, the negative electrode of the second diode is connected with the negative electrode of the battery, the positive electrode of the battery is connected with the emitting electrode of the triode, the base electrode of the triode is connected with one end of the third resistor, the other end of the third resistor is connected with one end of the second coil, the other end of the second coil is connected with one end of the second resistor, the other end of the second resistor is connected with the positive electrode of the second diode, one end of the first coil is connected with the connecting wire of the second coil and the second resistor, and the other end of the first coil is connected with the collector electrode of the triode;
one end of the third coil is connected with the third resistor, the other end of the third coil is connected with the anode of the first diode, the cathode of the first diode is connected with one end of the capacitor, and the other end of the capacitor is connected with one end of the fourth coil;
the fourth resistor and the fifth resistor are connected in series, the gate of the third diode is connected to the connection point of the fourth resistor and the fifth resistor, and the fourth resistor, the fifth resistor and the third diode are connected with the fourth coil and the third coil in parallel;
the fifth coil is opposite to the fourth coil, and the discharge electrode is connected to two ends of the fifth coil;
the control end is used for receiving a preset direct-current power supply sent by the FPGA controller;
and the discharge electrode is used for carrying out periodic discharge after the control end receives the preset direct-current power supply.
The invention also provides a nasal airway measuring method, which comprises the following steps:
after the upper computer detects a starting detection signal, the electric spark generating device is controlled to periodically discharge based on the FPGA controller;
recording a sound signal generated after the electric spark generating device carries out periodic discharge based on the microphone sampling device in the sound wave guide pipe;
after the sound signals in the microphone sampling device are read and stored through the FPGA controller, the first sound signals to be calculated stored in the FPGA controller are sent to the upper computer to be calculated, and the nasal airway measuring result is obtained.
Optionally, the step of controlling the electric spark generation device to perform periodic discharge by the FPGA controller includes:
and applying a preset direct current voltage on a control end of the electric spark generating device based on the FPGA controller, and controlling a discharge electrode of the electric spark generating device to perform periodic discharge.
Optionally, the step of reading and storing the sound signal in the microphone sampling device by the FPGA controller includes:
reading the sound signal in the microphone sampling device through the FPGA controller;
judging whether the read sound signal is a first sound signal to be calculated with an initial part;
if the read sound signal is a first sound signal to be calculated with an initial part, pulling down the voltage of the control end, and storing the first sound signal to be calculated;
and if the read sound signal is not the first sound signal to be calculated with the initial part, keeping the high voltage of the control end and rejecting the sound signal.
Optionally, the step of judging whether the read sound signal is a first sound signal to be calculated having a start portion includes:
judging whether the address of the sound signal belongs to a cyclic storage area in a memory database of the FPGA controller;
if the address of the sound signal belongs to a cyclic storage area in a memory database of the FPGA controller, the read sound signal is judged to be a first sound signal to be calculated with an initial part;
if the address of the sound signal does not belong to a cyclic storage area in a memory database of the FPGA controller, judging whether the sound signal triggers a preset storage condition;
and if the sound signal triggers a preset storage condition, judging that the read sound signal is a first sound signal to be calculated with an initial part.
Optionally, the step of sending the first sound signal to be calculated stored in the FPGA controller to the upper computer for calculation to obtain the nasal airway measurement result includes:
sending the first sound signal to be calculated to the upper computer through the FPGA controller;
after the first to-be-calculated sound signal is compressed and dimension-reduced by a PCA dimension-reduction space method, a first low-dimension to-be-calculated sound signal is obtained in a dimension-reduction space;
based on a preset proportion, eliminating abnormal signals deviating from the central position of the first low-dimensional sound signal to be calculated in the first low-dimensional sound signal to be calculated to obtain a second low-dimensional sound signal to be calculated;
taking the second low-dimensional sound signal to be calculated as an extraction sample, and extracting the sound signal to be calculated corresponding to the second low-dimensional sound signal to be calculated in the first sound signal to be calculated to obtain a second sound signal to be calculated;
splitting the second sound signal to be calculated based on a cross-correlation positioning method to obtain a first sound incident wave pulse signal, a first sound echo signal and a baseline signal;
removing the baseline signal in the first sound incident wave pulse signal and the first sound echo signal by a compensation method to obtain a second sound incident wave pulse signal and a second sound echo signal;
performing fast Fourier transform on the second sound incident wave pulse signal and the second sound echo signal based on a fast Fourier transform algorithm to obtain a third sound incident wave pulse signal and a third sound echo signal;
and performing impulse response h (t) value calculation based on the third sound incident wave pulse signal and the third sound echo signal to obtain h (t) value, averaging the h (t) value, and performing calculation based on WA algorithm to obtain the nasal airway measurement result.
Optionally, after the step of obtaining the nasal airway measurement, the method further comprises:
and displaying the nasal airway measurement result through a display end of the upper computer.
Furthermore, to achieve the above object, the present invention also provides a measuring apparatus comprising a nasal acoustic reflectometer, a memory, a processor and a computer program stored on the memory and executable on the processor, which when executed by the processor implements the steps of the above nasal airway measuring method.
Furthermore, to achieve the above object, the present invention also provides a computer-readable storage medium having stored thereon a computer program which, when being executed by a processor, carries out the steps of the above nasal airway measurement method.
The problem that the accuracy of an output nasal airway measurement result is low due to instability of incident pulse and echo information in a transmission process caused by the fact that a long acoustic waveguide tube with a spiral structure has to be used due to long pulse time is used as a sound source is solved, the problem that sound signals are lost in a sending process due to the fact that the serial port communication speed between the microphone and an upper computer is lower than the signal sampling rate is solved by storing the sound signals collected by the microphone, and the accuracy and the anti-interference capability of the calculation result are improved by performing calculation processing on the collected sound signals through a cross-correlation positioning method, a PCA dimension reduction space elimination algorithm and an impulse response ht average algorithm.
Drawings
Fig. 1 is a schematic terminal structure diagram of a hardware operating environment according to an embodiment of the present invention;
FIG. 2 is a schematic structural diagram of a nasal sound reflectometer for controlling an electric spark generating device by combining an FPGA controller and an upper computer;
FIG. 3 is a schematic diagram of a discharge control circuit of the spark generating device;
FIG. 4 is a schematic flow chart of an embodiment of a nasal airway measurement method of the present invention;
FIG. 5 is a detailed flowchart of step S30 in FIG. 4;
FIG. 6 is a detailed flowchart of step S30 in FIG. 4;
FIG. 7 is a schematic diagram of a sound signal captured by a microphone sampling device;
FIG. 8 is a schematic diagram of the divided areas of a 12-bit AD sampling chip of the FPGA controller;
fig. 9 is a diagram illustrating the distribution of the first low-dimensional sound signal to be calculated in the reduced-dimensional space.
The implementation, functional features and advantages of the objects of the present invention will be further explained with reference to the accompanying drawings.
Detailed Description
It should be understood that the specific embodiments described herein are merely illustrative of the invention and are not intended to limit the invention.
The main solution of the embodiment of the invention is as follows: through the design of combining FPGA controller and host computer control electric spark generating device to produce the electric spark, can reduce the pulse time of sound signal, because of the reduction of pulse time, and then can reduce the length of the sound wave pipe of using and occupy the volume of nasal sound reflectometer to avoid the problem that the precision nature of the unstable and the nasal airway measuring result of output of the sound signal of collection that leads to because of the long and crooked characteristic of sound wave pipe of using is low.
In the prior art, a loudspeaker is used as a sound source of the nasal sound reflectometer, but due to the fact that the pulse time of a sound signal generated by the loudspeaker is long, an adopted sound wave guide tube needs to have enough length to better separate an incident pulse from an echo signal, and in order to reduce the occupied volume of the long sound wave guide tube in the nasal sound reflectometer, the long sound wave guide tube is generally made into a spiral structure, but no matter a hose or a steel tube is used as the long sound wave guide tube of the spiral structure, the problems that the collected sound signal is unstable and the accuracy of an obtained nasal airway measurement result is low exist.
The invention provides a solution, only a loudspeaker as a sound source is replaced by an electric spark generating device, and the effect of reducing the length of the acoustic waveguide tube is achieved by utilizing the characteristic that the pulse time of a sound signal generated by the electric spark is shorter, so that a series of problems which are not beneficial to improving the stability and the testing precision of the nasal sound reflectometer and are generated by adopting a long acoustic waveguide tube with a spiral structure to collect and process the sound signal are avoided.
As shown in fig. 1, fig. 1 is a schematic terminal structure diagram of a hardware operating environment according to an embodiment of the present invention.
The nasal airway measuring device provided by the embodiment of the invention can be a PC (personal computer), a tablet personal computer, a portable computer and other movable terminal equipment with a display function.
As shown in fig. 1, the terminal may include: a processor 1001, such as a CPU, a network interface 1004, a user interface 1003, a memory 1005, a communication bus 1002. Wherein a communication bus 1002 is used to enable connective communication between these components. The user interface 1003 may include a Display screen (Display), an input unit such as a Keyboard (Keyboard), and the optional user interface 1003 may also include a standard wired interface, a wireless interface. The network interface 1004 may optionally include a standard wired interface, a wireless interface (e.g., WI-FI interface). The memory 1005 may be a high-speed RAM memory or a non-volatile memory (e.g., a magnetic disk memory). The memory 1005 may alternatively be a storage device separate from the processor 1001. The terminal is arranged on the nasal sound reflectometer.
Optionally, the nasal airway measurement device may further include a camera, RF (Radio Frequency) circuitry, sensors, audio circuitry, a WiFi module, and so forth. Such as light sensors, motion sensors, and other sensors. Specifically, the light sensor may include an ambient light sensor that may adjust the brightness of the display screen according to the brightness of ambient light, and a proximity sensor that may turn off the display screen and/or the backlight when the mobile terminal is moved to the ear. As one of the motion sensors, the gravity acceleration sensor can detect the magnitude of acceleration in each direction (generally, three axes), detect the magnitude and direction of gravity when the mobile terminal is stationary, and can be used for applications (such as horizontal and vertical screen switching, related games, magnetometer attitude calibration), vibration recognition related functions (such as pedometer and tapping) and the like for recognizing the attitude of the mobile terminal; of course, the mobile terminal may also be configured with other sensors such as a gyroscope, a barometer, a hygrometer, a thermometer, and an infrared sensor, which are not described herein again.
Those skilled in the art will appreciate that the nasal airway measurement device configuration shown in fig. 1 does not constitute a limitation of nasal airway measurement devices and may include more or fewer components than shown, or some components in combination, or a different arrangement of components.
As shown in fig. 1, a memory 1005, which is a kind of computer storage medium, may include therein an operating system, a network communication module, a user interface module, and a computer program.
In the terminal shown in fig. 1, the network interface 1004 is mainly used for connecting to a backend server and performing data communication with the backend server; the user interface 1003 is mainly used for connecting a client (user side) and performing data communication with the client; and the processor 1001 may be configured to invoke the computer program stored in the memory 1005 and perform the following operations:
after the upper computer detects a starting detection signal, the electric spark generating device is controlled to periodically discharge based on the FPGA controller;
recording a sound signal generated after the electric spark generating device carries out periodic discharge based on the microphone sampling device in the sound wave guide pipe;
after the sound signals in the microphone sampling device are read and stored through the FPGA controller, the first sound signals to be calculated stored in the FPGA controller are sent to the upper computer to be calculated, and the nasal airway measuring result is obtained.
Further, the processor 1001 may call the computer program stored in the memory 1005, and also perform the following operations:
the step of controlling the electric spark generation device to perform periodic discharge based on the FPGA controller comprises the following steps: and applying a preset direct current voltage on a control end of the electric spark generating device based on the FPGA controller, and controlling a discharge electrode of the electric spark generating device to perform periodic discharge.
Further, the processor 1001 may call the computer program stored in the memory 1005, and also perform the following operations:
the step of reading and storing the sound signal in the microphone sampling device by the FPGA controller comprises: reading the sound signal in the microphone sampling device through the FPGA controller;
judging whether the read sound signal is a first sound signal to be calculated with an initial part;
if the read sound signal is a first sound signal to be calculated with an initial part, pulling down the voltage of the control end, and storing the first sound signal to be calculated;
and if the read sound signal is not the first sound signal to be calculated with the initial part, keeping the high voltage of the control end and rejecting the sound signal.
Further, the processor 1001 may call the computer program stored in the memory 1005, and also perform the following operations:
the step of judging whether the read sound signal is a first sound signal to be calculated having a start portion includes: judging whether the address of the sound signal belongs to a cyclic storage area in a memory database of the FPGA controller;
if the address of the sound signal belongs to a cyclic storage area in a memory database of the FPGA controller, the read sound signal is judged to be a first sound signal to be calculated with an initial part;
if the address of the sound signal does not belong to a cyclic storage area in a memory database of the FPGA controller, judging whether the sound signal triggers a preset storage condition;
and if the sound signal triggers a preset storage condition, judging that the read sound signal is a first sound signal to be calculated with an initial part.
Further, the processor 1001 may call the computer program stored in the memory 1005, and also perform the following operations:
the sound signal that will be stored in the FPGA controller is sent to calculate in the host computer, and the step that obtains nose air flue measuring result includes: sending the first sound signal to be calculated to the upper computer through the FPGA controller;
after the first to-be-calculated sound signal is compressed and dimension-reduced by a PCA dimension-reduction space method, a first low-dimension to-be-calculated sound signal is obtained in a dimension-reduction space;
based on a preset proportion, eliminating abnormal signals deviating from the central position of the first low-dimensional sound signal to be calculated in the first low-dimensional sound signal to be calculated to obtain a second low-dimensional sound signal to be calculated;
taking the second low-dimensional sound signal to be calculated as an extraction sample, and extracting the sound signal to be calculated corresponding to the second low-dimensional sound signal to be calculated in the first sound signal to be calculated to obtain a second sound signal to be calculated;
splitting the second sound signal to be calculated based on a cross-correlation positioning method to obtain a first sound incident wave pulse signal, a first sound echo signal and a baseline signal;
removing the baseline signal in the first sound incident wave pulse signal and the first sound echo signal by a compensation method to obtain a second sound incident wave pulse signal and a second sound echo signal;
performing fast Fourier transform on the second sound incident wave pulse signal and the second sound echo signal based on a fast Fourier transform algorithm to obtain a third sound incident wave pulse signal and a third sound echo signal;
and performing impulse response h (t) value calculation based on the third sound incident wave pulse signal and the third sound echo signal to obtain h (t) value, averaging the h (t) value, and performing calculation based on WA algorithm to obtain the nasal airway measurement result.
Further, the processor 1001 may call the computer program stored in the memory 1005, and also perform the following operations:
and after the step of obtaining the nasal airway measurement result, displaying the nasal airway measurement result through a display end of the upper computer.
Referring to fig. 2, an embodiment of the present invention provides a nasal sound reflectometer, including:
an upper computer (namely a 1 label in the figure);
the FPGA controller (namely the number 2 in the figure) is in communication connection with the upper computer;
the electric spark generating device (namely a reference numeral 4 in the figure) is in communication connection with the FPGA controller;
an acoustic waveguide (7 in the figure) connected to the spark generating device;
a microphone sampling device (i.e., reference number 6 in the figures) disposed in the acoustic waveguide;
and the FPGA controller is in communication connection with the microphone sampling device.
In this embodiment, the communication connection between the upper computer, the FPGA controller, the electric spark generating device, and the acoustic waveguide is established through a signal line (i.e., 3 marks in the drawing), and when the electric spark generating device receives a preset current sent by the FPGA controller, the electric spark generating device controls the discharging electrode (i.e., 5 marks in the drawing) to perform a discharging operation.
Further, referring to fig. 3, the electric spark generating apparatus includes a control terminal, a discharge electrode, a first coil, a second coil, a third coil, a fourth coil, a fifth coil, a first resistor, a second resistor, a third resistor, a fourth resistor, a fifth resistor, a first diode, a second diode, a third diode, a capacitor, a triode, and a battery;
the output end of the control end is connected with one end of the first resistor, the other end of the first resistor is connected with the gate electrode of the second diode, the negative electrode of the second diode is connected with the negative electrode of the battery, the positive electrode of the battery is connected with the emitting electrode of the triode, the base electrode of the triode is connected with one end of the third resistor, the other end of the third resistor is connected with one end of the second coil, the other end of the second coil is connected with one end of the second resistor, the other end of the second resistor is connected with the positive electrode of the second diode, one end of the first coil is connected with the connecting wire of the second coil and the second resistor, and the other end of the first coil is connected with the collector electrode of the triode;
one end of the third coil is connected with the third resistor, the other end of the third coil is connected with the anode of the first diode, the cathode of the first diode is connected with one end of the capacitor, and the other end of the capacitor is connected with one end of the fourth coil;
the fourth resistor and the fifth resistor are connected in series, the gate of the third diode is connected to the connection point of the fourth resistor and the fifth resistor, and the fourth resistor, the fifth resistor and the third diode are connected with the fourth coil and the third coil in parallel;
the fifth coil is opposite to the fourth coil, and the discharge electrode is connected to two ends of the fifth coil;
the control terminal is configured to receive a preset dc power source sent by the FPGA controller, and enable a circuit (i.e., the circuit of fig. 3) of the electric spark generating apparatus to enter an operating state based on the preset dc power source
The discharge electrode is used for receiving the preset direct current power supply at the control end, then the current in the fourth coil L4 changes, the magnetic flux in the fifth coil L5 opposite to the fourth coil L4 also changes, induced current is generated to flow through the discharge electrode for discharging, and the preset direct current power supply is sent to the control end again after the FPGA controller records a complete sound signal, a sound incident wave pulse signal and a sound echo signal, so that the circuit of the electric spark generating device enters a discharging state again, and periodic discharging is formed.
In the present embodiment, the first coil L1, the second coil L2, and the third coil L3 are connected by a magnetic core, and the fourth coil and the fifth coil are connected by windings, but the present embodiment merely provides an implementation example, the connection manner between the coils is not limited to the present embodiment, and the specific connection manner can be changed according to the actual use scenario.
Referring to fig. 4, an embodiment of the present invention further provides a nasal airway measurement method, including:
step S10, after the upper computer detects a start detection signal, the FPGA controller controls the electric spark generating device to discharge periodically;
in the invention, the used upper Computer is a Personal Computer (PC), and the PC upper Computer, a Field Programmable Gate Array (FPGA) controller, an electric spark generating device, a microphone sampling device and an acoustic waveguide tube are connected and communicated by adopting signal lines, so that the transmission and sampling rate of the acoustic signal can be accelerated.
After a user inputs a detection signal for starting detection of the cavity to be measured on the PC upper computer, the detection signal is transmitted to the FPGA controller through the signal wire, and after the FPGA controller detects the detection signal, the FPGA controller still controls the electric spark generating device connected with the FPGA controller through the signal wire to control the electric spark generating device to perform periodic discharge.
The periodic discharge means that after the FPGA controller records a complete sound incident wave pulse signal and a sound echo signal once, the electric spark generating device is controlled to enter a new discharge process between the reception of the detection stopping signal, so that a new sound incident wave pulse signal and a new sound echo signal are generated.
Optionally, the step of controlling the electric spark generation device to perform periodic discharge based on the FPGA controller in step S10 includes:
step A, referring to FIG. 3, based on the FPGA controller, applying a preset direct current voltage to a control end of the electric spark generating device, and controlling a discharge electrode of the electric spark generating device to perform periodic discharge.
Fig. 3 is a discharge control circuit of the electric spark generating device as a sound source according to the present invention, wherein the FPGA controller applies a dc voltage of 3.3V to a control terminal of the discharge control circuit to enable the electric spark generating device to operate, and when a current in the coil L4 changes, a magnetic flux in the coil L5 changes, and an induced current flows through the discharge electrode to discharge the discharge electrode, so that the electric spark generating device generates a sound signal.
After the FPGA controller records the complete sound signal once, the FPGA controller applies the 3.3V direct-current voltage to the control end of the electric spark generating device again, so that the electric spark generating device discharges again, and the effect of periodic discharge is achieved.
Compared with the existing loudspeaker as a sound source, the electric spark generating device has shorter pulse time, can effectively shorten the length of the required sound wave guide tube, and the shortening of the length of the sound wave guide tube can avoid the condition of a spiral structure which is needed for reducing the occupied volume of the sound wave guide tube in the nasal sound reflectometer, and further avoid the problem of the reduction of the measuring precision of the nasal airway caused by the sound wave guide tube with the spiral structure.
Step S20, referring to fig. 7, recording a sound signal generated by the electric spark generating device after periodic discharge based on the microphone sampling device in the sound wave guide;
after the electric spark generating device discharges, the generated sound signal can be captured by the microphone sampling device with the sampling rate of 500kHz, and the characteristics of the sound signal captured by the microphone sampling device are shown in fig. 7.
It is noted that there are multiple sets of acoustic signals because the spark generating device is periodically discharged.
The acoustic waveguide tube is one of important factors influencing the measurement accuracy of the nasal airway, the more irregular the shape of the acoustic waveguide tube is, the more the influence on the output accuracy of the measurement of the nasal airway is, and the acoustic waveguide tube used by the invention can avoid the acoustic waveguide tube from being designed into the irregular shape of a spiral structure, so that the measurement accuracy of the nasal airway is improved to a certain extent.
And step S30, after the sound signals in the microphone sampling device are read and stored by the FPGA controller, the first sound signals to be calculated stored in the FPGA controller are sent to the upper computer for calculation, and the nasal airway measuring result is obtained.
After the FPGA controller reads and stores a plurality of groups of sound signals in the microphone sampling device through a signal wire, the stored sound signals are sent to a PC upper computer for processing and calculation.
The FPGA controller can also process and calculate the stored multiple groups of sound signals, but the processing and calculating capacity of the FPGA controller is slightly lower than that of the PC upper computer, so that the embodiment of the invention processes and calculates the stored multiple groups of sound signals in the PC upper computer, and can accelerate the processing and calculating speed of the multiple groups of sound signals.
It should be noted that the first to-be-calculated sound signal is a to-be-calculated sound signal before being sent to the upper computer for calculation processing.
Optionally, after the step of obtaining the nasal airway measurement result in step S30, the method further includes:
and step B, displaying the nasal airway measurement result through a display end of the upper computer.
After the PC host computer finishes processing and calculating the multiunit sound signal that FPGA controller stored, can obtain the condition that the nasal airway cross-sectional area of the cavity that awaits measuring changes along with nasal cavity axial distance, nasal airway measuring result promptly, the PC host computer will show this nasal airway measuring result on the display end, for example the display screen of PC host computer also can pass through voice broadcast for the user can be clear know the nasal airway measuring condition of the cavity that awaits measuring.
In the embodiment, the nasal sound reflectometer is controlled by combining the FPGA controller with the upper computer to control the electric spark generating device, the electric spark generating device is controlled to discharge for multiple times in a short time, the FPGA controller reads and stores for multiple times through the microphone sampling device, the calculation mode taking a plurality of groups of sound signals as the calculation basis can improve the accuracy of the output nasal airway measurement result, the pulse time of the sound signal is shortened by replacing the sound source in the existing nose sound reflection instrument with electric spark, the shortening of the pulse time can effectively shorten the required length of the acoustic waveguide, and the shortening of the length of the acoustic waveguide can avoid the condition of a spiral structure which is required for reducing the occupied volume of the acoustic waveguide in the nasal acoustic reflectometer, and then avoid the problem that the accuracy of measuring the nose air flue descends because of the sound wave pipe of helical structure.
Further, referring to fig. 5, an embodiment of the present invention provides a nasal airway measuring method, based on the embodiment shown in step S30, the step of reading and storing the sound signal in the microphone sampling device by the FPGA controller includes:
step S31, reading the sound signal in the microphone sampling device through the FPGA controller;
step S32, determining whether the read sound signal is a first sound signal to be calculated having an initial portion;
step S33, if the read sound signal is a first sound signal to be calculated having an initial portion, pulling down the voltage of the control terminal, and storing the first sound signal to be calculated;
in step S34, if the read sound signal is not the first sound signal to be calculated having the initial portion, the high voltage of the control terminal is maintained, and the sound signal is rejected.
After the electric spark generating device carries out periodic discharge, the generated sound signal is captured by the microphone sampling device, the captured sound signal is read by the FPGA controller through a signal line, the FPGA controller judges the read sound signal, because not all the read sound signals are sound signals with a complete initial period, whether the read sound signals have the complete initial sound signal or not is judged, whether the read sound signals are a group of complete initial periods or not is judged, if the read sound signals are a group of complete initial periods, the sound signals corresponding to the initial periods can be classified into the sound signals to be calculated, the voltage of a control end of the electric spark generating device is pulled down through the FPGA controller, the sound signals to be calculated are stored into a memory database of the FPGA controller, the later stage of being convenient for calculates based on effectual sound signal, promotes the accuracy of the nasal airway measuring result of output.
If the read sound signals are not a group of complete initial cycles, the FPGA controller keeps the high voltage of the control end of the electric spark generating device unchanged, and meanwhile, the sound signals read in the time period when the control end is the high voltage are discarded, so that the influence of the incomplete sound signals on the output nasal airway measuring result is avoided.
Alternatively, referring to fig. 8, the step of determining whether the read sound signal is the first sound signal to be calculated having the initial portion in step S32 includes:
step S35, judging whether the address of the sound signal belongs to a circular storage area in a memory database of the FPGA controller;
step S36, if the address of the sound signal belongs to the circular storage area in the memory database of the FPGA controller, the read sound signal is judged to be the first sound signal to be calculated with the initial part;
step S37, if the address of the sound signal does not belong to the circular storage area in the memory database of the FPGA controller, judging whether the sound signal triggers a preset storage condition;
in step S38, if the sound signal triggers a preset storage condition, it is determined that the read sound signal is the first sound signal to be calculated having an initial portion.
As can be seen from fig. 8, the present invention divides a 12-bit AD (Analog-to-Digital) sampling chip of an FPGA controller into two parts, a small part is a circular storage area for determining whether a read sound signal is a first to-be-calculated sound signal having an initial portion, and a large part is a storage area for storing the first to-be-calculated sound signal having the initial portion, and the sound signal stored in the storage area is to be sent to a PC upper computer for processing and calculation.
After the FPGA controller detects a new start detection signal, the FPGA controller initializes the previously stored sound signal, and avoids the influence of the data of the previous cavity on the output result of the new cavity.
After the FPGA controller detects that the microphone sampling device captures a sound signal, reading the captured sound signal, writing the read sound signal into a cyclic storage area, judging whether an address to which the read sound signal belongs in the cyclic storage area, classifying the sound signal into a first sound signal to be calculated if the address to which the read sound signal belongs in the cyclic storage area, and storing the first sound signal to be calculated in the storage area.
If the read address of the sound signal does not belong to the cyclic storage area, the method and the device can improve the accuracy of the output nasal airway measurement result in order to avoid omission of the sound signal, carry out secondary judgment on the sound signal not belonging to the cyclic storage area, and judge whether the storage condition is triggered.
The storage condition is that whether the read sound signal has an obvious beginning section of a sound signal section or not, that is, whether a complete electromagnetic pulse signal exists in a section of the sound signal is obviously read or not, if the complete sound signal begins to have the beginning section, the storage condition is judged to be triggered, and the sound signal is classified as a first sound signal to be calculated and stored in a storage area.
And transmitting the signals stored in the storage area and the circulating storage area to a PC upper computer for waiting processing until the storage is finished.
If the sound signal with the unsatisfied judgment condition exists after the two times of judgment, the address is reset to zero, and the sound signal is covered by another group of sound signals, so that the judgment operation of the newly read sound signal is prevented from being influenced.
It should be noted that when the FPGA controller detects that the memory in the storage area is full, the FPGA controller does not need to judge and store the subsequently read sound signals, directly stops the reading operation of the microphone sampling device, and sends the multiple groups of sound signals in the storage area to the PC upper computer through the signal line for the next operation.
In this embodiment, carry out the secondary through the multiunit sound signal to reading and judge, can avoid unusual measuring signal to the influence of measuring result, effectively promote systematic judgement operation to promote the accuracy of the nasal airway measuring result of output.
Further, referring to fig. 6, an embodiment of the present invention provides a nasal airway measuring method, where based on the step of sending the first to-be-calculated sound signal stored in the FPGA controller to the host computer for calculation in step S30, the method further includes:
step S39, sending the first sound signal to be calculated to the upper computer through the FPGA controller;
step S40, obtaining a first low-dimensional sound signal to be calculated in a dimensionality reduction space after carrying out compression dimensionality reduction on the first sound signal to be calculated by a PCA dimensionality reduction space method;
step S41, based on a preset proportion, eliminating abnormal signals deviating from the center position of the first low-dimensional to-be-calculated sound signals in the first low-dimensional to-be-calculated sound signals to obtain second low-dimensional to-be-calculated sound signals;
step S42, referring to fig. 9, taking the second low-dimensional to-be-calculated sound signal as an extraction sample, and extracting a to-be-calculated sound signal corresponding to the second low-dimensional to-be-calculated sound signal from the first to-be-calculated sound signal to obtain a second to-be-calculated sound signal;
aiming at the problems of the existing nose sound reflectometer, the invention provides that during processing and calculation, a plurality of groups of continuously acquired sound signals are adopted for data analysis, a PCA dimension reduction space method is used for carrying out compression dimension reduction on a first to-be-calculated sound signal, the first to-be-calculated sound signal which is positioned in the dimension reduction space after compression dimension reduction is obtained, as shown in figure 9, 10 groups of low-dimensional to-be-calculated sound signals with the number of 0-9 are obtained after compression dimension reduction, the preset proportion in the embodiment is 30%, therefore, 3 groups of low-dimensional to-be-calculated signals which are farthest from the central position (namely star-shaped signals in the figure) are classified into abnormal signals and eliminated, and the rest low-dimensional to-be-calculated sound signals after elimination are second low-dimensional to-be-calculated sound signals.
The second low-dimensional sound signal to be calculated is used as a comparison group, and the corresponding sound signal to be calculated is extracted from the first sound signal to be calculated according to the second low-dimensional sound signal to be calculated, for example, as shown in fig. 9, and the second low-dimensional sound signal to be calculated is 0, 1, 5, 6, 7, 8 and 9, so that 0, 1, 5, 6, 7, 8 and 9 in the first sound signal to be calculated are correspondingly extracted as the second sound signal to be calculated, thereby ensuring the stability of the output nasal airway measurement result.
Step S43, splitting the second sound signal to be calculated based on a cross-correlation positioning method to obtain a first sound incident wave pulse signal, a first sound echo signal and a baseline signal;
step S44, removing the baseline signal from the first sound incident wave pulse signal and the first sound echo signal by a compensation method to obtain a second sound incident wave pulse signal and a second sound echo signal;
when an existing nasal sound reflectometer processes and calculates a sound signal, the WA algorithm is usually directly used for processing and calculating according to a sound incident wave pulse signal, but the read sound signal is usually susceptible to external factors, so that a nasal airway measurement result output by the WA algorithm is deviated from an actual value.
Therefore, in combination with the above calculation steps, before the impulse response calculation is performed on the sound incident wave pulse signal, the second sound signal to be calculated needs to be subjected to the splitting of the sound incident wave pulse signal and the sound echo signal, because the waveforms of the sound incident wave pulse signals are basically consistent, the invention takes the prerecorded artificial incident wave sound signal as a reference before implementation, selects the position where the maximum value appears as the actually measured initial sound incident wave pulse signal, and because the distance between the sound wave guide and the microphone sampling device is fixed, therefore, the sampling point between the initial positions of the sound incident wave pulse signal and the sound echo signal is fixed, and the initial position of the sound echo signal can be determined as long as the initial position of the sound incident wave pulse signal is determined, so that the separation of the sound incident wave pulse signal and the sound echo signal is realized.
The formula of the cross-correlation positioning method of the sound incident wave pulse signal and the sound echo signal is as follows:
the first sound incident wave pulse signal and the first sound echo signal are sound signals separated by a cross-correlation positioning method.
It should be noted that, the first sound incident wave pulse signal and the first sound echo signal cause a loss of the sound echo signal due to a gap between the sound wave guide tube and the cavity to be measured, so when the situation that the first sound incident wave pulse signal and the first sound echo signal have a signal loss is detected, the first sound echo signal is input into the compensation module to perform sound signal compensation and baseline signal extraction, and the second sound incident wave pulse signal and the second sound echo signal output after compensation can enter the next processing calculation.
Step S45, performing fast fourier transform on the second sound incident wave pulse signal and the second sound echo signal based on a fast fourier transform algorithm to obtain a third sound incident wave pulse signal and a third sound echo signal;
step S46, calculating an impulse response h (t) value based on the third sound incident wave pulse signal and the third sound echo signal to obtain an h (t) value, averaging the h (t) value, and calculating based on a WA algorithm to obtain the nasal airway measurement result.
Performing Fourier transform on the second sound incident wave pulse signal and the second sound echo signal based on a fast Fourier transform algorithm to obtain a third sound incident wave pulse signal and a third sound echo signal which are subjected to Fourier transform, and calculating impulse response h (t) based on the third sound incident wave pulse signal and the third sound echo signal which are subjected to Fourier transform
The impulse response h (t) has the formula:
wherein, in the above formula
And
respectively representing a third acoustic incident wave pulse signal and a third acoustic echo signal, the sign representing the calculated deconjugated complex number,
representative digital filter
Of a quantity of
The number of which is determined by the window size of the fast fourier transform,
is a parameter, the size of which determines the degree of smoothing of the calculated h (t),
the larger the value, the smoother h (t) becomes, and generally, the value is about 0.1. While the digital filter
The calculation formula of (a) is as follows:
after the h (t) value is obtained by calculation, the h (t) value needs to be averaged to obtain the average impulse response of the test result of the group
And finally, calculating by using a WA algorithm to obtain the condition that the cross-sectional area of the nasal airway of the cavity to be measured changes along with the axial distance of the nasal cavity, namely the measurement result of the nasal airway.
In the embodiment, the cross-correlation positioning method, the PCA dimension reduction space elimination method, the fast Fourier transform algorithm and the WA algorithm are carried out on the multiple groups of sound signals stored in the storage area of the FPGA controller in the PC upper computer, so that the problems of low test precision and poor anti-interference capability caused by only adopting the WA algorithm in the existing algorithm are solved, and the stability and the test precision of the nasal sound reflectometer are improved.
Furthermore, an embodiment of the present invention further provides a measurement apparatus, which includes a nasal acoustic reflectometer, a memory, a processor, and a computer program stored on the memory and executable on the processor, and when executed by the processor, the computer program implements the steps of the nasal airway measurement method described above.
Furthermore, the present invention also proposes a computer-readable storage medium having stored thereon a computer program which, when being executed by a processor, carries out the steps of the above-mentioned nasal airway measurement method.
It should be noted that, in this document, the terms "comprises," "comprising," or any other variation thereof, are intended to cover a non-exclusive inclusion, such that a process, method, article, or system that comprises a list of elements does not include only those elements but may include other elements not expressly listed or inherent to such process, method, article, or system. Without further limitation, an element defined by the phrase "comprising an … …" does not exclude the presence of other like elements in a process, method, article, or system that comprises the element.
The above-mentioned serial numbers of the embodiments of the present invention are merely for description and do not represent the merits of the embodiments.
Through the above description of the embodiments, those skilled in the art will clearly understand that the method of the above embodiments can be implemented by software plus a necessary general hardware platform, and certainly can also be implemented by hardware, but in many cases, the former is a better implementation manner. Based on such understanding, the technical solution of the present invention may be embodied in the form of a software product, which is stored in a storage medium (e.g., ROM/RAM, magnetic disk, optical disk) as described above and includes instructions for enabling a terminal device (e.g., a mobile phone, a computer, a server, an air conditioner, or a network device) to execute the method according to the embodiments of the present invention.
The above description is only a preferred embodiment of the present invention, and not intended to limit the scope of the present invention, and all modifications of equivalent structures and equivalent processes, which are made by using the contents of the present specification and the accompanying drawings, or directly or indirectly applied to other related technical fields, are included in the scope of the present invention.
Claims (10)
1. A nasal sound reflectometer, wherein the nasal sound reflectometer comprises:
an upper computer;
the FPGA controller is in communication connection with the upper computer;
the electric spark generating device is in communication connection with the FPGA controller;
an acoustic waveguide connected to the spark generating device;
a microphone sampling device disposed in the sonic conduit;
and the FPGA controller is in communication connection with the microphone sampling device.
2. The nasal acoustic reflectometer as in claim 1 wherein the spark generating means comprises a control terminal, a discharge electrode, a first coil, a second coil, a third coil, a fourth coil, a fifth coil, a first resistor, a second resistor, a third resistor, a fourth resistor, a fifth resistor, a first diode, a second diode, a third diode, a capacitor, a triode, and a battery;
the output end of the control end is connected with one end of the first resistor, the other end of the first resistor is connected with the gate electrode of the second diode, the negative electrode of the second diode is connected with the negative electrode of the battery, the positive electrode of the battery is connected with the emitting electrode of the triode, the base electrode of the triode is connected with one end of the third resistor, the other end of the third resistor is connected with one end of the second coil, the other end of the second coil is connected with one end of the second resistor, the other end of the second resistor is connected with the positive electrode of the second diode, one end of the first coil is connected with the connecting wire of the second coil and the second resistor, and the other end of the first coil is connected with the collector electrode of the triode;
one end of the third coil is connected with the third resistor, the other end of the third coil is connected with the anode of the first diode, the cathode of the first diode is connected with one end of the capacitor, and the other end of the capacitor is connected with one end of the fourth coil;
the fourth resistor and the fifth resistor are connected in series, the gate of the third diode is connected to the connection point of the fourth resistor and the fifth resistor, and the fourth resistor, the fifth resistor and the third diode are connected with the fourth coil and the third coil in parallel;
the fifth coil is opposite to the fourth coil, and the discharge electrode is connected to two ends of the fifth coil;
the control end is used for receiving a preset direct-current power supply sent by the FPGA controller;
and the discharge electrode is used for carrying out periodic discharge after the control end receives the preset direct-current power supply.
3. A nasal airway measurement method, characterized in that the nasal airway measurement is applied to the nasal acoustic reflectometer of any one of claims 1 to 2, the nasal airway measurement method comprising the steps of:
after the upper computer detects a starting detection signal, the electric spark generating device is controlled to periodically discharge based on the FPGA controller;
recording a sound signal generated after the electric spark generating device carries out periodic discharge based on the microphone sampling device in the sound wave guide pipe;
after the sound signals in the microphone sampling device are read and stored through the FPGA controller, the first sound signals to be calculated stored in the FPGA controller are sent to the upper computer to be calculated, and the nasal airway measuring result is obtained.
4. The nasal airway measurement method of claim 3, wherein the step of controlling the electrical spark generating device to periodically discharge based on the FPGA controller comprises:
and applying a preset direct current voltage on a control end of the electric spark generating device based on the FPGA controller, and controlling a discharge electrode of the electric spark generating device to perform periodic discharge.
5. The nasal airway measurement method of claim 4, wherein the step of reading and storing the sound signals in the microphone sampling device by the FPGA controller comprises:
reading the sound signal in the microphone sampling device through the FPGA controller;
judging whether the read sound signal is a first sound signal to be calculated with an initial part;
if the read sound signal is a first sound signal to be calculated with an initial part, pulling down the voltage of the control end, and storing the first sound signal to be calculated;
and if the read sound signal is not the first sound signal to be calculated with the initial part, keeping the high voltage of the control end and rejecting the sound signal.
6. The nasal airway measurement method according to claim 5, wherein the step of judging whether the read sound signal is a first sound signal to be calculated having an initial portion includes:
judging whether the address of the sound signal belongs to a cyclic storage area in a memory database of the FPGA controller;
if the address of the sound signal belongs to a cyclic storage area in a memory database of the FPGA controller, the read sound signal is judged to be a first sound signal to be calculated with an initial part;
if the address of the sound signal does not belong to a cyclic storage area in a memory database of the FPGA controller, judging whether the sound signal triggers a preset storage condition;
and if the sound signal triggers a preset storage condition, judging that the read sound signal is a first sound signal to be calculated with an initial part.
7. The nasal airway measurement method according to claim 5, wherein the step of sending the first sound signal to be calculated stored in the FPGA controller to the upper computer for calculation to obtain the nasal airway measurement result comprises:
sending the first sound signal to be calculated to the upper computer through the FPGA controller;
after the first to-be-calculated sound signal is compressed and dimension-reduced by a PCA dimension-reduction space method, a first low-dimension to-be-calculated sound signal is obtained in a dimension-reduction space;
based on a preset proportion, eliminating abnormal signals deviating from the central position of the first low-dimensional sound signal to be calculated in the first low-dimensional sound signal to be calculated to obtain a second low-dimensional sound signal to be calculated;
taking the second low-dimensional sound signal to be calculated as an extraction sample, and extracting the sound signal to be calculated corresponding to the second low-dimensional sound signal to be calculated in the first sound signal to be calculated to obtain a second sound signal to be calculated;
splitting the second sound signal to be calculated based on a cross-correlation positioning method to obtain a first sound incident wave pulse signal, a first sound echo signal and a baseline signal;
removing the baseline signal in the first sound incident wave pulse signal and the first sound echo signal by a compensation method to obtain a second sound incident wave pulse signal and a second sound echo signal;
performing fast Fourier transform on the second sound incident wave pulse signal and the second sound echo signal based on a fast Fourier transform algorithm to obtain a third sound incident wave pulse signal and a third sound echo signal;
and performing impulse response h (t) value calculation based on the third sound incident wave pulse signal and the third sound echo signal to obtain h (t) value, averaging the h (t) value, and performing calculation based on WA algorithm to obtain the nasal airway measurement result.
8. The nasal airway measurement method of claim 7, wherein the step of obtaining a nasal airway measurement is further followed by:
and displaying the nasal airway measurement result through a display end of the upper computer.
9. A measurement device, characterized in that the measurement device comprises a nasal acoustic reflectometer according to any of claims 1 to 2, a memory, a processor and a computer program stored on the memory and executable on the processor, which when executing the computer program implements the steps of the nasal airway measurement method according to any of claims 3-8.
10. A computer-readable storage medium, characterized in that a computer program is stored thereon, which computer program, when being executed by a processor, carries out the steps of the nasal airway measurement method according to any one of claims 3-8.
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