Method for detecting a tympanic membrane sound signal, electronic device, and storage medium

Abstract

The application provides a tympanic membrane sound signal detection method, an electronic device and a storage medium. In the process of detecting the sound level at the tympanic membrane position in the ear, the tympanic membrane position sound signal is determined by detecting the real-time cavity sound signal and the real-time sound signal outside the hearing protector, and combining multiple acoustic impedances. Thus, the problem that the real-time sound signal at the tympanic membrane position cannot be determined after wearing a hearing protector in the prior art is solved.

Description

TECHNICAL FIELD

[0001] The present application relates to the technical field of sound pressure measurement, and in particular to a tympanic membrane sound signal detection method, an electronic device and a storage medium. BACKGROUND

[0002] Currently, the damage to human hearing in high-noise workplaces is usually protected by wearing hearing protectors. The quantification of protection is based on wearing hearing protectors with corresponding sound insulation according to the noise intensity in the field. Head-mounted hearing protectors are the most common type of hearing protection equipment.

[0003] In addition, the human external auditory canal has acoustic resonance, which makes the external ear transfer function have a higher gain at 2kHz-4kHz, which is also an important reason why humans are more sensitive to this frequency band. Human high-noise hearing damage usually starts from this frequency band and leads to hearing damage in the entire frequency band. In some frequency bands, the acoustic resonance caused by the external auditory canal will cause the sound level at the tympanic membrane position to increase by more than 10dB, and the A-weighting currently used only makes a 1.3dB correction at the highest frequency. It can be said that due to the lack of consideration of the sound transmission of the external auditory canal, the current protection methods and standards have a major flaw in protecting the human ear.

[0004] Currently, some research has been conducted on the transfer function of the external auditory canal, and the sound transmission function from the entrance of the auditory canal to the tympanic membrane position and its magnitude correction in an open environment have been obtained. However, when wearing a head-mounted hearing protector, the external auditory canal actually forms a coupled space with the internal cavity of the hearing protector. Testing inside the hearing protector will be affected by the coupled environment and will change with the change of the coupled environment. Therefore, the sound transmission function of the external auditory canal in an open environment cannot be directly used to correct the actual sound level received by the tympanic membrane after wearing a hearing protector. There is still a gap in this aspect of technology and device. SUMMARY

[0005] The present application provides a tympanic membrane sound signal detection method to solve the problem of not being able to determine the real-time sound signal at the tympanic membrane position after wearing a hearing protector in the prior art, and to achieve accurate measurement of the real-time sound signal at the tympanic membrane position.

[0006] The present application provides a tympanic membrane sound signal detection method, which comprises:

[0007] obtaining the first equivalent impedance (Zc) of the tympanic membrane at the ear canal opening, the first transfer impedance (Zq) between the ear canal opening and the sealed cavity formed by the hearing protector and the ear when the hearing protector is sealed and worn;

[0008] obtaining the sealed cavity equivalent impedance (Zm) and the radiation acoustic impedance (Zk) when the hearing protector is sealed and worn and the ear canal opening is closed;

[0009] When the user wears the hearing protector, continuously acquiring a real-time intracavity acoustic signal of a cavity formed between the hearing protector and the ear canal opening and a real-time external acoustic signal of the hearing protector;

[0010] When a difference between the real-time intracavity acoustic signal and a preset first sealed acoustic signal is greater than a preset value, determining a tympanic membrane position acoustic signal of the ear according to the first equivalent impedance (Zc), the first transfer impedance (Zq), the sealed cavity equivalent impedance (Zm), the radiation acoustic impedance (Zk), the real-time intracavity acoustic signal and the real-time external acoustic signal of the hearing protector.

[0011] According to the present application, a method for detecting a tympanic membrane acoustic signal is provided, and the step of determining a tympanic membrane position acoustic signal of the ear according to the first equivalent impedance (Zc), the first transfer impedance (Zq), the sealed cavity equivalent impedance (Zm), the radiation acoustic impedance (Zk), the real-time intracavity acoustic signal and the real-time external acoustic signal of the hearing protector comprises:

[0012] The real-time intracavity acoustic signal is denoted as P1, the real-time external acoustic signal of the hearing protector is denoted as P2, and the tympanic membrane position acoustic signal of the ear is denoted as P4;

[0013] P4=Ax+(1-C)P2+C(P1-x)

[0014] In the above formula, A is equal to B is equal to C is equal to D is equal to x is a quadratic equation effective solution; wherein Zc is the first equivalent impedance, Zq is the first transfer impedance, Zm is the sealed cavity equivalent impedance, and Zk is the radiation acoustic impedance.

[0015] According to the present application, a method for detecting a tympanic membrane acoustic signal is provided, and the step of acquiring the first equivalent impedance (Zc) of the tympanic membrane at the ear canal opening and the first transfer impedance (Zq) between the ear canal opening and a sealed cavity formed between the hearing protector and the ear when the hearing protector is sealed worn comprises:

[0016] Acquiring a first sealed acoustic signal (ps4) of the sealed cavity formed between the hearing protector and the ear, a first test acoustic signal (ps1) of the ear canal opening of the hearing protector and an acoustic impedance (Ze) at the tympanic membrane when the hearing protector is sealed worn;

[0017] Determining the first equivalent impedance (Zc) according to the acoustic impedance (Ze) at the tympanic membrane, and determining the ear canal opening acoustic impedance and the first transfer impedance (Zq) between the ear canal opening and the sealed cavity according to the first sealed acoustic signal and the first test acoustic signal (ps1).

[0018] According to the method for detecting eardrum sound signal provided by the application, the step of determining the first equivalent impedance (Zc) according to the acoustic impedance (Ze) at the eardrum and determining the acoustic impedance at the ear canal opening and the first transfer impedance (Zq) between the ear canal opening and the sealed cavity according to the first sealed sound signal (ps4) and the first test sound signal (ps1) comprises:

[0019] The first equivalent impedance is denoted as Zc, and the acoustic impedance at the eardrum is denoted as Ze;

[0020]

[0021] ρ0 is the density in air, c0 is the sound speed in air, k is the wave number, S is the cross-sectional area of the ear canal, and l is the length of the ear canal;

[0022] The first sealed sound signal is denoted as ps4, the first test sound signal is denoted as ps1, and the first transfer impedance is denoted as Zq;

[0023] Zq=Zc(1-Ps1 / Ps4).

[0024] According to the method for detecting eardrum sound signal provided by the application, the step of obtaining the equivalent impedance (Zm) of the sealed cavity and the radiation acoustic impedance (Zk) when the hearing protector is sealed and the ear canal opening is closed comprises:

[0025] Obtaining the second sealed sound signal of the sealed cavity formed between the hearing protector and the ear canal opening when the hearing protector is sealed , the second test sound signal outside the hearing protector

[0026] Obtaining the third sealed sound signal of the sealed cavity formed between the hearing protector and the ear canal opening when the hearing protector is sealed and the ear canal opening is closed , the fourth test sound signal outside the hearing protector

[0027] According to the second sealed sound signal the second test sound signal the third sealed sound signal The first transfer impedance (Zq) and the first equivalent impedance (Zc) determine the equivalent impedance (Zm) of the sealed cavity and the radiation acoustic impedance (Zk).

[0028] According to the method for detecting eardrum sound signal provided by the application, the step of determining the first equivalent impedance (Zc) according to the acoustic impedance (Ze) at the eardrum and determining the acoustic impedance at the ear canal opening and the first transfer impedance (Zq) between the ear canal opening and the sealed cavity according to the first sealed sound signal (ps4) and the first test sound signal (ps1) comprises: the second test sound signal​ fourth test acoustic signal The steps of determining the sealed cavity equivalent impedance (Zm) and the radiated acoustic impedance (Zk) by the first transfer impedance (Zq) and the first equivalent impedance (Zc) include:

[0029]

[0030]

[0031] wherein, is a second sealed acoustic signal, is a second test acoustic signal, is a third sealed acoustic signal, is a fourth test acoustic signal, Zq is a first transfer impedance, Zc is a first equivalent impedance, Zm is a sealed cavity equivalent impedance, and Zk is a radiated acoustic impedance.

[0032] According to the method for detecting a tympanic membrane acoustic signal provided by the application, the acoustic signal at any position in the cavity of a hearing protector, the tympanic membrane of a human ear or the ear canal opening of a human ear is equal to the sum of the leakage acoustic signal and the transmission acoustic signal at the corresponding position.

[0033] According to the method for detecting a tympanic membrane acoustic signal provided by the application, after the step of determining the acoustic signal at the tympanic membrane position of the ear, the method further includes:

[0034] According to the method for detecting a tympanic membrane acoustic signal provided by the application, after the step of determining the acoustic signal at the tympanic membrane position of the ear, the method further includes: determining the actual acoustic exposure of the human ear;

[0035] wherein L PE is the actual acoustic exposure of the human ear, Pe(k) is the acoustic signal at the tympanic membrane position of the ear, P ref is the reference quantity of the acoustic signal at the tympanic membrane position of the ear.

[0036] The application also provides an electronic device, which comprises a memory, a processor and a computer program stored in the memory and executable on the processor, wherein the processor implements the steps of the method for detecting a tympanic membrane acoustic signal according to any one of the above embodiments when executing the program.

[0037] The application also provides a storage medium, which stores a computer program executable by a processor, wherein the processor implements the steps of the method for detecting a tympanic membrane acoustic signal according to any one of the above embodiments when executing the program.

[0038] The application provides a tympanic membrane sound signal detection method, an electronic device and a storage medium. The tympanic membrane sound signal detection method comprises the following steps: obtaining a first equivalent impedance (Zc) of a tympanic membrane at an ear canal opening when a hearing protector is worn in a sealed manner, and a first transfer impedance (Zq) between the ear canal opening and a sealed cavity formed by the hearing protector and an ear; obtaining a sealed cavity equivalent impedance (Zm) and a radiation acoustic impedance (Zk) when the hearing protector is worn in a sealed manner and the ear canal opening is closed; and continuously obtaining a real-time cavity sound signal of the cavity formed between the hearing protector and the ear canal opening and a real-time external sound signal of the hearing protector when a user wears the hearing protector. Therefore, when a difference between the real-time cavity sound signal and a preset first sealed sound signal is greater than a preset value, i.e., the cavity between the hearing protector and the human body is not sealed, the tympanic membrane position sound signal of the ear can be determined according to the first equivalent impedance (Zc), the first transfer impedance (Zq), the sealed cavity equivalent impedance (Zm), the radiation acoustic impedance (Zk), the real-time cavity sound signal and the real-time external sound signal of the hearing protector. Through the above process, the real-time cavity sound signal and the real-time external sound signal of the hearing protector can be measured in real time during the user wears the hearing protector, and the finally measured tympanic membrane position sound signal can be determined. Therefore, when the cavity between the hearing protector and the human body is not sealed, the change parameter can be accurately introduced to correct the tympanic membrane position sound signal, so that the real-time sound signal of the tympanic membrane position can be accurately measured. BRIEF DESCRIPTION OF DRAWINGS

[0039] In order to more clearly illustrate the technical solutions in the application or prior art, the following will briefly introduce the drawings needed in the embodiments or prior art description. Obviously, the drawings in the following description are some embodiments of the application, and other drawings can be obtained by those skilled in the art without creative effort.

[0040] Figure 1 FIG. 1 is a flowchart of a tympanic membrane sound signal detection method provided by the application;

[0041] Figure 2 FIG. 2 is another flowchart of a tympanic membrane sound signal detection method provided by the application;

[0042] Figure 3 FIG. 3 is a third flowchart of a tympanic membrane sound signal detection method provided by the application;

[0043] Figure 4 FIG. 4 is a structural schematic diagram of an electronic device provided by the application;

[0044] Figure 5 FIG. 5 is a schematic diagram of a sound pressure measurement point of a hearing protector in the application;

[0045] Figure 6 FIG. 6 is a schematic diagram of an acoustic influence parameter in the application.

[0046] Figure 7 The structure diagram of the in-ear sound pressure measuring device in the application;

[0047] Figure 8 The equivalent circuit in the experimental test state in the application;

[0048] Figure 9 The equivalent circuit of the sound transmission of the hearing protector shell in the application;

[0049] Figure 10 The equivalent circuit of the leakage sound of the hearing protector in the application;

[0050] Figure 11 The circuit diagram of the in-ear sound pressure measuring device in the application.

[0051] Reference signs:

[0052] 11: second detection circuit; 12: control circuit; 13: wireless communication circuit;

[0053] 14: charging power supply circuit; 15: wearing part; 16: prompting circuit;

[0054] 17: first detection circuit; 1: inner side of the in-ear sound pressure measuring device; 2: inner side of the in-ear sound pressure measuring device;

[0055] 4: ear canal opening; 3: tympanic membrane; DETAILED DESCRIPTION

[0056] In order to make the objects, technical solutions and advantages of the application clearer, the technical solutions in the application will be clearly and completely described below in combination with the drawings in the application. Obviously, the described embodiments are some of the embodiments of the application, rather than all the embodiments. Based on the embodiments in the application, all other embodiments obtained by those skilled in the art without creative labor fall within the protection scope of the application.

[0057] The application will be described below in combination with Figures 1-3 The application provides a detection method of a tympanic membrane sound signal, which comprises the following steps:

[0058] 100, obtaining a first equivalent impedance (Zc) of a tympanic membrane at an ear canal opening and a first transfer impedance (Zq) between the ear canal opening and a sealed cavity formed by a hearing protector and an ear when the hearing protector is worn in a sealed manner;

[0059] The ideal state of the hearing protector sealing wearing is actually a state of use, in the actual application, the hearing protector may not be worn tightly, therefore, when the above test is performed, the most ideal state is to be measured in the laboratory by means of the artificial head and the artificial ear. The first equivalent impedance (Zc) of the eardrum at the ear canal opening and the first transfer impedance (Zq) between the ear canal opening and the sealed cavity formed by the hearing protector and the ear include the impedance from the hearing protector to the ear canal opening, by segmenting the impedance, the accuracy of the data measured in the laboratory can improve the accuracy of the subsequent calculation.

[0060] 200, when the hearing protector is sealed and worn and the ear canal opening is closed, the sealed cavity equivalent impedance (Zm) and the radiation acoustic impedance (Zk) are obtained;

[0061] When the above test is performed, the most ideal state is to be measured in the laboratory by means of the artificial head and the artificial ear, in particular, the acoustic load needs to be changed during the test, and the ear canal structure part is removed. In addition, in order to measure truly, the ear canal opening needs to be closed by means of a tool. Thus, the accuracy of the measured sealed cavity equivalent impedance (Zm) and the radiation acoustic impedance (Zk) can be ensured. At this time, by further subdividing the impedance, the accuracy of the subsequent calculation can be improved by the accuracy of the data measured in the laboratory.

[0062] 300, when the user wears the hearing protector, the real-time cavity sound signal of the cavity formed between the hearing protector and the ear canal opening and the real-time sound signal outside the hearing protector are continuously obtained;

[0063] At this time, for the actual hearing protector, after the user wears the hearing protector, due to individual differences or wearing problems, there is a certain degree of sound leakage, so that the real-time cavity sound signal and the first sealed sound signal of the sealed cavity measured in the laboratory exist certain differences, therefore, the continuous monitoring of the real-time cavity sound signal can ensure that the change of the real-time cavity sound signal caused by the sound leakage can be collected, and the accuracy of the subsequent calculation can be improved by measuring the real-time variable.

[0064] 400, when the difference between the real-time cavity sound signal and the preset first sealed sound signal is greater than a preset value, the eardrum position sound signal of the ear is determined according to the first equivalent impedance (Zc), the first transfer impedance (Zq), the sealed cavity equivalent impedance (Zm), the radiation acoustic impedance (Zk), the real-time cavity sound signal and the real-time sound signal outside the hearing protector.

[0065] Through the above process, the eardrum sound signal detection method of the application can measure the real-time cavity sound signal and the real-time sound signal outside the hearing protector in real time during the process of wearing the hearing protector by the user, further determine the last measured eardrum position sound signal, so that when the cavity between the hearing protector and the human body is not sealed, the change parameter can be accurately introduced to correct the eardrum position sound signal, so that the real-time sound signal of the eardrum position can be accurately measured. In order to determine the protection ability of the hearing protector at this time in real time by the real-time sound signal of the eardrum position for the person skilled in the art.

[0066] In an embodiment, the step of determining the eardrum position sound signal of the ear according to the first equivalent impedance (Zc), the first transfer impedance (Zq), the sealed cavity equivalent impedance (Zm), the radiation acoustic impedance (Zk), the real-time cavity sound signal and the real-time sound signal outside the hearing protector comprises:

[0067] The real-time cavity sound signal is denoted as P1, the real-time sound signal outside the hearing protector is denoted as P2, and the eardrum position sound signal of the ear is denoted as P4;

[0068] P4=Ax+(1-C)P2+C(P1-x)

[0069] In the above formula, A is equal to B is equal to C is equal to D is equal to x is a quadratic equation effective solution; wherein Zc is the first equivalent impedance, Zq is the first transfer impedance, Zm is the sealed cavity equivalent impedance, and Zk is the radiation acoustic impedance.

[0070] In the above embodiment, by introducing the real-time real-time cavity sound signal and the real-time sound signal outside the hearing protector, the eardrum position sound signal of the ear is determined by the two variables and the impedance of multiple parts, the variable caused by the possible problems in the use process is introduced into the final confirmation process, so that the purpose of correcting the eardrum position sound signal is achieved, and the accuracy of the finally confirmed eardrum position sound signal is greatly improved. Moreover, through the above calculation process, a new detection and calculation model of the eardrum position sound signal is established, so that the real-time eardrum position sound signal after detection and calculation is more accurate.

[0071] In an embodiment, as shown in Figure 2 the step of obtaining the first equivalent impedance (Zc) of the eardrum at the ear canal opening and the first transfer impedance (Zq) between the ear canal opening and the sealed cavity formed by the hearing protector and the ear when the hearing protector is worn includes:

[0072] 101, obtaining a first sealed sound signal (ps4) of a sealed cavity formed between the hearing protector and the ear when the hearing protector is worn in a sealed manner, a first test sound signal (ps1) of an ear canal opening of the hearing protector, and an acoustic impedance (Ze) at the eardrum;

[0073] At this time, the hearing protector is worn in a sealed manner and is recorded as a first state. An equivalent circuit in an experimental test state at this time is shown in Figure 8 , wherein the first sealed sound signal (ps4) and the first test sound signal (ps1) can be measured by arranging a microphone at each of an inner side of the hearing protector and the ear canal opening, and the acoustic impedance (Ze) at the eardrum currently has a lot of published research data, which can be directly adopted in a normal case. Alternatively, the test data at this time can also be measured by an artificial simulation head and a simulation ear. Actual measurement points can be referred to Figure 5 and Figure 6 , wherein 1 is a microphone mounting position in the cavity, used to measure the first test sound signal (ps1), 2 is an external microphone mounting position, used to measure a second test sound signal (ps2) outside the hearing protector, 3 is a position of the eardrum of the human ear, and 4 is a position of the ear canal opening.

[0074] 102, determining the first equivalent impedance (Zc) according to the acoustic impedance (Ze) at the eardrum, and determining a first transfer impedance (Zq) between the ear canal opening and the sealed cavity according to the first sealed sound signal and the first test sound signal (ps1).

[0075] In the above embodiment, since the hearing protector is worn in a sealed manner, it can be ensured that the measured first test sound signal (ps1) and the first sealed sound signal (ps4) do not have other interference factors, so as to ensure the accuracy of the first equivalent impedance (Zc) and the first transfer impedance (Zq) obtained by measurement and calculation at this time.

[0076] In an embodiment, the step of determining the first equivalent impedance (Zc) according to the acoustic impedance (Ze) at the eardrum, and determining a first transfer impedance (Zq) between the ear canal opening and the sealed cavity according to the first sealed sound signal (ps4) and the first test sound signal (ps1) comprises:

[0077] The first equivalent impedance is recorded as Zc, and the acoustic impedance at the eardrum is recorded as Ze.

[0078]

[0079] ρ0 is the density in air, c0 is the sound speed in air, k is the wave number, S is the cross-sectional area of the ear canal, and l is the length of the ear canal.

[0080] The first sealed sound signal is denoted as ps4, the first test sound signal is denoted as ps1, and the first transfer impedance is denoted as Zq;

[0081] Zq = Zc (1 - Ps1 / Ps4).

[0082] In the above process, s and l can adopt the average data disclosed, and p0c0 and k can also adopt the average data disclosed. There are currently many published research data of the acoustic impedance Ze at the eardrum, and these data can be directly adopted in general cases. Therefore, the first equivalent impedance (Zc) and the first transfer impedance (Zq) can be calculated by measuring only the first sealed sound signal and the first test sound signal. Through the above process, the difficulty of calculating the impedance can be reduced, the data preparation work in the early stage can be simplified, and the speed of developing the detection method of the eardrum sound signal can be improved. In addition, the constants involved in the calculation process have been tested by predecessors many times, and thus the deviation of subsequent calculation can be greatly reduced.

[0083] In an embodiment, as shown in Figure 3 the step of obtaining the sealed cavity equivalent impedance (Zm) and the radiation acoustic impedance (Zk) when the hearing protector is sealed and the ear canal opening is closed comprises:

[0084] 201. obtaining a second sealed sound signal of a sealed cavity formed between the hearing protector and the ear canal opening when the hearing protector is sealed a second test sound signal outside the hearing protector

[0085] 202. obtaining a third sealed sound signal of a sealed cavity formed between the hearing protector and the ear canal opening when the hearing protector is sealed and the ear canal opening is closed a fourth test sound signal outside the hearing protector

[0086] At this time, the hearing protector is sealed and is denoted as a first state, the second sealed sound signal and the second test sound signal can be measured by arranging a microphone at each of the position outside the hearing protector and the ear canal opening. The hearing protector is sealed and the ear canal opening is closed, which is denoted as a second state, wherein the third sealed sound signal and the fourth test sound signal can be measured by arranging a microphone at each of the position outside the hearing protector and the ear canal opening, or the test data at this time can also be measured by an artificial head and a simulated ear. It should be noted that at this time, the acoustic load is changed during the test, such as removing the ear canal structure. The actual measurement point can be referred to Figure 5 , wherein 1 is the microphone installation position in the cavity, which is used to measure the second sealed sound signal and the third sealed sound signal 2 is the external microphone mounting position for measuring the second test sound signal outside the hearing protector and the fourth test sound signal

[0087] At this time, the influence of the ear canal structure on the equivalent impedance (Zm) of the sealed cavity and the radiation acoustic impedance (Zk) can be excluded, and the accuracy of the measurement data can be improved.

[0088] 203, according to the second sealed sound signal the second test sound signal the third sealed sound signal the fourth test sound signal The first transfer impedance (Zq) and the first equivalent impedance (Zc) determine the equivalent impedance (Zm) of the sealed cavity and the radiation acoustic impedance (Zk).

[0089] The second sealed sound signal is measured by two states respectively the second test sound signal the third sealed sound signal the fourth test sound signal Ensure that there is no interference of other interference factors in each data measurement process, so as to improve the accuracy of the finally determined equivalent impedance (Zm) of the sealed cavity and the radiation acoustic impedance (Zk).

[0090] In an embodiment, with reference to Figure 6 , the step of determining the equivalent impedance (Zm) of the sealed cavity and the radiation acoustic impedance (Zk) according to the second sealed sound signal (ps11), the second test sound signal (ps22), the first transfer impedance (Zq) and the first equivalent impedance (Zc) includes:

[0091]

[0092]

[0093] wherein, is the second sealed sound signal, is the second test sound signal, is the third sealed sound signal, is the fourth test sound signal, Zq is the first transfer impedance, Zc is the first equivalent impedance, Zm is the equivalent impedance of the sealed cavity, and Zk is the radiation acoustic impedance.

[0094] It should be noted that the volume V in the ear cap cavity in the acoustic system is to provide a sound capacity CA, the role of the ear canal can be considered by using the acoustic transmission line theory, and the sound leakage part is equivalent to a short tube to be considered, which is represented by the acoustic mass MA. The above equivalent acoustic elements are uniformly represented in the form of complex impedance. The sound capacity in the cavity is represented by Zm, and the comprehensive impedance of the sound leakage is represented by Zx, which includes the sound mass and the sound radiation resistance of the leakage part, which is simply and uniformly represented as Zx.

[0095] The principle of the above formula is explained as follows:

[0096] Ze is used to represent the acoustic impedance at the eardrum, and the relationship between the sound pressure Pe and the volume velocity Ue is as follows: Pe=Ze*Ue. Pc, Uc and Zc are used to represent the sound pressure, volume velocity and ear canal acoustic impedance at the actual ear canal entrance respectively. Zc can be represented by the acoustic impedance at the eardrum according to the acoustic transmission line theory, and the sound pressure can be converted. It should be noted that the sound signal in the present application refers to the sound pressure.

[0097] Under actual working conditions, due to the existence of sound leakage when the operator wears the hearing protector, the protection effect of the hearing protector cannot reach the best, so the influence of sound leakage cannot be ignored. Zx is used to represent the sound impedance caused by sound leakage, which includes the sound mass caused by leakage, the sound resistance caused by friction attenuation and the radiation resistance. Considering the existence of sound leakage, the sound received in the cavity of the hearing protector is the sum of the leakage sound and the transmission sound of the hearing protector, and the sound signal P1 inside the hearing protector is P1t+P1x, and the sound signal P4 at the ear canal entrance is P4t+P4x. In actual implementation conditions, P1 and the sound signal P2 outside the hearing protector can be measured, the sound signal P3 at the eardrum can be obtained by combining the transmission matrix with the sound signal P4 at the ear canal entrance, and the value of P4 cannot be directly measured in actual wearing, so the value of P4 needs to be calculated. The transmission sound and the leakage sound are considered as follows.

[0098] The equivalent circuit of the hearing protector shell transmission sound is shown in Figure 9 , compared with Figure 8 The load caused by the leakage channel is added to the load part, and the sound leakage channel and the sound load of the ear canal are in parallel. In the above parameters, P1t, P4t, Zx are unknown parameters, and there are two voltage division nodes in the above circuit at the positions of P1t and P4t, so two equations can be established.

[0099]

[0100] The equivalent circuit of the hearing protector leakage sound is shown in Figure 10 , P1x, P4x, Zx are unknown parameters, and there are two voltage division nodes in the above circuit at the positions of P1x and P4x, so two equations can be established.

[0101]

[0102] Furthermore, by combining the equation P1=P1t+P1x, where P1 is a measurable value, there are a total of 5 equations and 5 unknown parameters. By solving this set of equations, P4t and P4x can be obtained. Based on P4=P4t+P4x, the sound pressure at the ear canal opening can be calculated, and thus the sound pressure at the tympanic membrane can be obtained.

[0103] Through the above process, the leakage sound of the sound signal at each location is taken into account, thereby further ensuring the accuracy of the final sound signal (sound pressure) of the tympanic membrane.

[0104] In one embodiment, the acoustic signal at any location within the cavity of the hearing protector, the tympanic membrane of the ear, or the opening of the ear canal is equal to the sum of the leakage acoustic signal and the transmitted acoustic signal at the corresponding location.

[0105] In one embodiment, the step of determining the position of the eardrum acoustic signal further includes:

[0106] in accordance with Determine the actual acoustic exposure of the human ear;

[0107] Where L PE Pe(k) represents the actual acoustic exposure of the human ear, and Pe(k) represents the acoustic signal indicating the position of the eardrum. ref This is the reference value for the acoustic signal indicating the position of the eardrum. That is, Pe(k) = P4.

[0108] Through the above process, the sound signal is converted into acoustic exposure, which allows users to intuitively understand the actual leakage situation and adjust the wearing status of the hearing protector in real time.

[0109] Figure 4 An example is a schematic diagram of the physical structure of an electronic device, such as... Figure 4 As shown, the electronic device may include a processor 810, a communication interface 820, a memory 830, and a communication bus 840, wherein the processor 810, the communication interface 820, and the memory 830 communicate with each other through the communication bus 840. The processor 810 can call logical instructions in the memory 830 to execute a method for detecting tympanic membrane acoustic signals, the method including: detecting tympanic membrane acoustic signals.

[0110] Moreover, the logic instructions in the memory 830 described above can be implemented in the form of software functional units and sold or used as independent products, and can be stored in a computer readable storage medium. Based on such understanding, the technical solutions of the present application essentially or the parts that make contributions to the prior art or parts of the technical solutions can be embodied in the form of a software product. The computer software product is stored in a storage medium, and includes a number of instructions for causing a computer device (which can be a personal computer, a server, or a network device, etc.) to execute all or part of the steps of the methods described in the various embodiments of the present application. The aforementioned storage medium includes: a U disk, a mobile hard disk, a read-only memory (ROM, Read-Only Memory), a random access memory (RAM, Random Access Memory), a magnetic disk or an optical disk, and various media that can store program codes.

[0111] In another aspect, the present application also provides a computer program product, which comprises a computer program stored in a storage medium, and the computer program comprises program instructions, and when the program instructions are executed by a computer, the computer can execute the tympanic membrane sound signal detection method provided by the above-mentioned methods, and the method comprises: tympanic membrane sound signal detection.

[0112] In another aspect, the present application also provides a storage medium, which stores a computer program, and when the computer program is executed by a processor, the computer program realizes the tympanic membrane sound signal detection method provided by the above-mentioned methods, and the method comprises: tympanic membrane sound signal detection.

[0113] The device embodiments described above are only schematic, wherein the units described as separate components can or can not be physically separate, and the components displayed as units can or can not be physical units, that is, they can be located in one place, or can be distributed on multiple network units. Part or all of the circuits can be selected according to actual needs to achieve the purpose of the present embodiment. Those skilled in the art can understand and implement without creative labor.

[0114] From the above description of the embodiments, those skilled in the art can clearly understand that the embodiments can be realized by means of software and the necessary general hardware platforms, and of course can also be realized by hardware. Based on such understanding, the technical solutions described above essentially or the parts that make contributions to the prior art can be embodied in the form of a software product. The computer software product can be stored in a computer readable storage medium, such as a ROM / RAM, a magnetic disk, an optical disk, etc., and includes a number of instructions for causing a computer device (which can be a personal computer, a server, or a network device, etc.) to execute the methods described in the various embodiments or some parts of the embodiments.

[0115] The ear sound pressure measuring device provided by the present application is described below, and the ear sound pressure measuring device described below can be referred to in correspondence with the detection method of the tympanic membrane sound signal described above.

[0116] The ear sound pressure measuring device provided by the present application is described below, and the ear sound pressure measuring device described below can be referred to in correspondence with the detection method of the tympanic membrane sound signal described above. Figure 7 Figure 11 The ear sound pressure measuring device provided by the present application is described below, and the ear sound pressure measuring device described below can be referred to in correspondence with the detection method of the tympanic membrane sound signal described above.

[0117] The inner side of the ear cover is attached to the wearer to form a cavity between the wearer and the ear cover. The first detection circuit 17 detects the real-time sound signal outside the ear cover. The second detection circuit 11 detects the real-time cavity sound signal inside the ear cover. The control circuit 12 determines the tympanic membrane position sound signal according to the real-time sound signal and the real-time cavity sound signal. The control signal realizes the purpose of the present application according to the detection method of the tympanic membrane sound signal as described above.

[0118] In the above scheme, the real-time sound signal and the real-time cavity sound signal are collected, and the sound signal that may be affected by sound leakage is collected. The collected sound signal is calculated according to the following formula:

[0119]

[0120]

[0121] wherein, is the second sealed sound signal, is the second test sound signal, is the third sealed sound signal, is the fourth, Zq is the first transfer impedance, Zc is the first equivalent impedance, Zm is the sealed cavity equivalent impedance, and Zk is the radiation sound impedance.

[0122] The above process can ensure the accuracy of the measured sealed cavity equivalent impedance (Zm) and the radiation sound impedance (Zk). At this time, by further subdividing the impedance measurement, the accuracy of the subsequent calculation can be ensured by the precision of the data measured in the laboratory.

[0123] ​It should be noted that the first detection circuit 17 and the second detection circuit 11 can be implemented by a standard microphone. The control circuit 12 can be a commonly used control chip.

[0124] In an embodiment, the in-ear sound pressure measuring device further comprises a wearing part 15, which is rotatably connected with the ear cover body, and is used to form a cavity with the human ear when the user wears it.

[0125] At this time, the rotatable connection can be selected from the existing rotatable connection scheme.

[0126] In an embodiment, the wearing part 15 is fixed by one or more of various ways such as adhesion, magnetic attraction, spring elastic force fixation, etc.

[0127] Through the above-mentioned various ways, the user can select according to the needs, which is convenient for the user to use.

[0128] In an embodiment, as shown in Figure 11 The in-ear sound pressure measuring device further comprises a wireless communication circuit 13, and the control circuit 12 further comprises a communication end, and the communication end of the wireless communication circuit 13 is electrically connected with the communication end of the control circuit 12.

[0129] The wireless communication circuit 13 can be selected from a communication chip and a communication circuit, which will not be described here.

[0130] In an embodiment, the in-ear sound pressure measuring device further comprises a charging power supply circuit 14, which comprises a power input end and a power output end; the power input end of the charging power supply circuit 14 is connected with a power supply, and the power output end of the charging power supply circuit 14 provides working power for each circuit of the in-ear sound pressure measuring device.

[0131] The charging power supply circuit 14 can also be selected from various existing power supply circuits and power supply chips.

[0132] In an embodiment, the charging power supply circuit 14 comprises a charging power supply circuit 14, a charging battery and a charging interface, the charging power supply circuit 14 is connected with the charging battery and the charging interface respectively, the charging interface is the power input end of the charging power supply circuit 14, and the output end of the charging power supply circuit 14 is the power output end of the charging power supply circuit 14.

[0133] The charging battery can be a storage battery, which can ensure the power supply of the in-ear sound pressure measuring device, so that the in-ear sound pressure measuring device can be used for a long time when it is used in an outdoor environment.

[0134] In an embodiment, when the charging interface is a data charging interface, the control circuit 12 further comprises a data end, and the data end of the control circuit 12 is electrically connected with the charging interface.

[0135] In an embodiment, the in-ear sound pressure measuring device further comprises a prompting circuit 16, a control end of the prompting circuit 16 being connected with a control end of the control circuit 12.

[0136] The prompting circuit 16 prompts according to the prompting signal output by the control circuit 12. It should be noted that the prompting information is provided when the human ear noise acceptance approaches the risk threshold. In a non-networking case, the prompting circuit 16 can adopt a micro loudspeaker, and the prompting circuit 16 can also adopt a vibrator or an optical signal generator to prompt. In a networking case, the prompting information can be sent to the control end.

[0137] The application will be described below in combination with Figure 7 An ear protector according to the application comprises two in-ear sound pressure measuring devices as above, which are respectively a left in-ear sound pressure measuring device and a right in-ear sound pressure measuring device.

[0138] The left in-ear sound pressure measuring device covers the left ear, and the inner side of the left in-ear sound pressure measuring device forms a cavity with the wearer when being attached to the wearer. The right in-ear sound pressure measuring device covers the right ear, and the inner side of the right in-ear sound pressure measuring device forms a cavity with the wearer when being attached to the wearer. The two in-ear sound pressure measuring devices constitute an ear protector.

[0139] Finally, it should be noted that: the above embodiments are only used to illustrate the technical solutions of the present application, but not to limit it; although the present application has been described in detail with reference to the foregoing embodiments, those skilled in the art should understand that: it can still modify the technical solutions recorded in the foregoing embodiments, or make equivalent replacement to part of the technical features; and these modifications or replacements do not make the essence of the corresponding technical solutions deviate from the spirit and scope of the technical solutions of the embodiments of the present application.

Claims

1. A method of detecting a tympanic sound signal, characterized by The detection method of the eardrum sound signal comprises: obtaining a first equivalent impedance of the eardrum at the ear canal opening when the hearing protector is worn in a sealed manner, a first transfer impedance between the ear canal opening and a sealed cavity formed by the hearing protector and the ear; obtaining an equivalent impedance of the sealed cavity and a radiation acoustic impedance when the hearing protector is worn in a sealed manner and the ear canal opening is closed; continuously obtaining a real-time cavity sound signal of the cavity formed between the hearing protector and the ear canal opening and a real-time external sound signal of the hearing protector when the user wears the hearing protector; when a difference between the real-time cavity sound signal and a preset first sealed sound signal is greater than a preset value, determining an eardrum position sound signal of the ear according to the first equivalent impedance, the first transfer impedance, the equivalent impedance of the sealed cavity, the radiation acoustic impedance, the real-time cavity sound signal and the real-time external sound signal of the hearing protector; the step of determining the eardrum position sound signal of the ear according to the first equivalent impedance, the first transfer impedance, the equivalent impedance of the sealed cavity, the radiation acoustic impedance, the real-time cavity sound signal and the real-time external sound signal of the hearing protector comprises: the real-time cavity sound signal is recorded as P1, the real-time external sound signal of the hearing protector is recorded as P2, and the eardrum position sound signal of the ear is recorded as P4; ； In the above formula, A is equal to , B is equal to , C is equal to , D is equal to , is a valid solution of the quadratic equation ; wherein Zc is the first equivalent impedance, Zq is the first transfer impedance, Zm is the sealed cavity equivalent impedance, and Zk is the radiation acoustic impedance. the step of obtaining the first equivalent impedance of the eardrum at the ear canal opening when the hearing protector is worn in a sealed manner and the first transfer impedance between the ear canal opening and the sealed cavity formed by the hearing protector and the ear comprises: obtaining a first sealed sound signal of the sealed cavity formed between the hearing protector and the ear, a first test sound signal of the hearing protector and an acoustic impedance at the eardrum when the hearing protector is worn in a sealed manner; determining the first equivalent impedance according to the acoustic impedance at the eardrum, and determining an ear canal opening acoustic impedance and a first transfer impedance between the ear canal opening and the sealed cavity according to the first sealed sound signal and the first test sound signal; the step of obtaining the equivalent impedance of the sealed cavity and the radiation acoustic impedance when the hearing protector is worn in a sealed manner and the ear canal opening is closed comprises: obtaining a second sealed sound signal of the sealed cavity formed between the hearing protector and the ear canal opening and a second test sound signal outside the hearing protector when the hearing protector is worn in a sealed manner; obtaining a third sealed sound signal of the sealed cavity formed between the hearing protector and the ear canal opening and a fourth test sound signal outside the hearing protector when the hearing protector is worn in a sealed manner and the ear canal opening is closed; determining the equivalent impedance of the sealed cavity and the radiation acoustic impedance according to the second sealed sound signal, the second test sound signal, the third sealed sound signal, the fourth test sound signal, the first transfer impedance and the first equivalent impedance.

2. The method of claim 1, wherein the step of determining the first equivalent impedance according to the acoustic impedance at the eardrum and determining the ear canal opening acoustic impedance and the first transfer impedance between the ear canal opening and the sealed cavity according to the first sealed sound signal and the first test sound signal comprises: the first equivalent impedance is recorded as Zc, and the acoustic impedance at the eardrum is recorded as Ze; ； is the density in air, is the speed of sound in air, k is the wave number, S is the ear canal cross-sectional area, and l is the ear canal length; the first sealed sound signal is recorded as ps4, the first test sound signal is recorded as ps1, and the first transfer impedance is recorded as Zq; 。 3. The method of claim 1, wherein The step of determining the sealed cavity equivalent impedance and the radiated acoustic impedance according to the second sealed acoustic signal, the second test acoustic signal, a third sealed acoustic signal, a fourth test acoustic signal, a first transfer impedance and a first equivalent impedance comprises: ； wherein is a second sealed sound signal, is a second test sound signal, is a third sealed sound signal, is a fourth test sound signal, Zq is a first transfer impedance, Zc is a first equivalent impedance, Zm is a sealed cavity equivalent impedance, and Zk is a radiation acoustic impedance.

4. The method of claim 1-3, wherein The acoustic signal at any of the locations of the cavity of the hearing protector, the tympanic membrane of the human ear or the ear canal opening of the human ear is equal to the sum of the leakage acoustic signal and the transmission acoustic signal at the corresponding location.

5. The method of claim 1-3, wherein The step of determining the acoustic signal at the location of the tympanic membrane of the ear further comprises: In accordance with determining the actual acoustic exposure of the human ear; wherein is the actual acoustic exposure to the human ear, Pe(k) is the ear drum location sound signal of the ear, P ref is the reference quantity of the ear drum location sound signal of the ear.

6. An electronic device comprising a memory, a processor, and a computer program stored on the memory and executable on the processor, characterized in that, The processor implements the steps of the method of detecting the acoustic signal at the location of the tympanic membrane when executing the program.

7. A storage medium having stored thereon a computer program, characterized in that The computer program implements the steps of the method of detecting the acoustic signal at the location of the tympanic membrane when executed by the processor.

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