CN111905257B - EABR detection equipment and detection method - Google Patents
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- A61N1/00—Electrotherapy; Circuits therefor
- A61N1/18—Applying electric currents by contact electrodes
- A61N1/32—Applying electric currents by contact electrodes alternating or intermittent currents
- A61N1/36—Applying electric currents by contact electrodes alternating or intermittent currents for stimulation
- A61N1/36036—Applying electric currents by contact electrodes alternating or intermittent currents for stimulation of the outer, middle or inner ear
- A61N1/36038—Cochlear stimulation
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- A61N1/04—Electrodes
- A61N1/05—Electrodes for implantation or insertion into the body, e.g. heart electrode
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- A61N1/00—Electrotherapy; Circuits therefor
- A61N1/18—Applying electric currents by contact electrodes
- A61N1/32—Applying electric currents by contact electrodes alternating or intermittent currents
- A61N1/36—Applying electric currents by contact electrodes alternating or intermittent currents for stimulation
- A61N1/36036—Applying electric currents by contact electrodes alternating or intermittent currents for stimulation of the outer, middle or inner ear
- A61N1/36038—Cochlear stimulation
- A61N1/36039—Cochlear stimulation fitting procedures
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Abstract
The invention discloses an EABR detection device and a detection method, wherein an integrated working system which simultaneously comprises a stimulation unit and a processing unit is arranged, an electric stimulator is controlled by the stimulation unit to generate a stimulation signal, a stimulation module receives the stimulation signal to stimulate cochlear nerves, and the processing unit processes an electric activity signal of the cochlear nerves, which is received by a host computer and is generated by the stimulation signal, acquired by an electrode module, specifically generates a result curve and compares the result curve with a preset curve; the integrated working system can reduce the cost, and an independent working system does not need to be respectively arranged for the electric stimulator and the recorder, so that the cost is reduced; and the cochlear nerve function can be evaluated according to the comparison result of the result curve and the preset curve before the cochlear implant is implanted, the accuracy is high, the risk that the cochlear implant cannot act after an expensive cochlear implant device is implanted can be reduced, and the cost is reduced. The invention can be widely applied to the technical field of auditory function detection.
Description
Technical Field
The invention relates to the field of auditory detection, in particular to EABR detection equipment and a detection method.
Background
At present, clinically, for patients needing cochlear implant surgery implantation, especially for patients with malformation or badness of inner ear and Auditory nerve hypoplasia/badness and Auditory neuropathy, except for EABR (Electrically-assisted Audio nerve networks) technology before operation, no more direct method is available for evaluating cochlear nerve functional integrity, and if the cochlear nerve functional integrity cannot be evaluated, the Auditory function of the Auditory handicapped patients cannot be reconstructed even though the cochlear implant is implanted.
However, because the cochlear implant has a high value, if a high-value implant device is implanted before implantation on the premise that the cochlear nerve function condition cannot be known, once the EABR response cannot be recorded after implantation, the patient/patient family is bound to suffer from huge economic loss, and therefore, a technology or a device which can complete cochlear nerve function integrity evaluation without implanting the cochlear implant is urgently needed in clinic and industry.
Disclosure of Invention
In view of the above, in order to solve the above technical problems, an object of the present invention is to provide an EABR detection apparatus and a detection method.
The technical scheme adopted by the invention is as follows:
an EABR detection apparatus comprising:
an electrical stimulator for outputting a stimulation signal;
a stimulation module to receive the stimulation signal to stimulate a cochlear nerve;
the recorder comprises an electrode module and a host connected with the electrode module, and the host is used for receiving the electrical activity signals of the cochlear nerve generated by the stimulation signals acquired by the electrode module;
the working system is connected with the electric stimulator and the recorder and comprises a stimulation unit and a processing unit, the stimulation unit is used for controlling the electric stimulator to generate the stimulation signals, the processing unit is used for processing the electric activity signals, and the processing comprises the step of generating a result curve according to the electric activity signals and comparing the result curve with a preset curve.
Further, the stimulation module includes a probe for placement in the round window niche or on the cochlear nerve surface and an electrode pad for placement beneath the occipital skin.
Further, the electrode module includes a recording electrode, a reference electrode, and a ground electrode.
Further, the recording electrode is used for being arranged in the middle of the top of the forehead, the reference electrode is used for being arranged on the mastoid process or the temporomandibular joint, and the terrestrial pole is used for being arranged on the heart of the eyebrow.
The invention also provides an EABR detection method, which is applied to the EABR detection equipment and comprises the following steps:
controlling the electrical stimulator to generate the stimulation signal through the stimulation unit and to be received by the stimulation module to stimulate cochlear nerves;
acquiring, by the electrode module, an electrical activity signal of a cochlear nerve generated via the stimulation signal;
receiving, by the host, the electrical activity signal;
and receiving and processing the electrical activity signal through the processing unit, wherein the processing comprises generating a result curve according to the electrical activity signal and comparing the result curve with a preset curve.
Further, the step of controlling the electrical stimulator to generate the stimulation signal through the stimulation unit includes the following steps:
setting stimulation parameters through the stimulation unit to control the electrical stimulator to generate the stimulation signals;
wherein the stimulation parameters include at least one of stimulation intensity, maximum current, change step size, stimulation type, stimulation polarity and stimulation channel, stimulation rate, stimulation shape, pulse width.
Further, the stimulation shape comprises click, the stimulation intensity comprises 1mA, the maximum current comprises 5mA, the varying step size comprises 0.1mA, the stimulation polarity comprises positive and negative, the stimulation type comprises single or dual, the stimulation type comprises continuous or alternating, the pulse width comprises 100 μ S, and the stimulation rate comprises 5-48 Hz.
Further, the step of receiving and processing the electrical activity signal by the processing unit includes the steps of:
performing analog-to-digital conversion on the electrical activity signal by the processing unit;
carrying out waveform processing according to the analog-to-digital conversion result to generate a result curve, wherein the waveform processing comprises filtering superposition;
and comparing the result curve with the preset curve.
Further, the step of performing analog-to-digital conversion on the electrical activity signal by the processing unit includes the steps of:
amplifying the electrical activity signal, and performing analog-to-digital conversion on the amplified result;
wherein the amplification process is controlled by amplification parameters of the processing unit, the amplification parameters comprising at least one of signal input range, frequency, trap, harmonic filtering, sampling rate and impedance measurement.
And further, comparing the result curve with the preset curve according to at least one of appearance of the waveform, amplitude of the waveform and time interval between the waveforms in the result curve to obtain a scoring result.
The invention has the beneficial effects that: the stimulation unit is used for controlling the electrical stimulator to generate the stimulation signal, the stimulation module is used for receiving the stimulation signal to stimulate the cochlear nerve, and the processing unit is used for processing the electrical activity signal of the cochlear nerve, which is received by the host and generated by the stimulation signal and acquired by the electrode module, of the cochlear nerve, specifically generating a result curve and comparing the result curve with a preset curve; the integrated working system can reduce the cost, and a set of independent working system does not need to be respectively arranged for the electric stimulator and the recorder, so that the cost is reduced; and the cochlear nerve function can be evaluated according to the comparison result of the result curve and the preset curve before the cochlear implant is implanted, the accuracy is high, the risk that the cochlear implant cannot act after an expensive cochlear implant device is implanted can be reduced, and the cost is reduced.
Drawings
FIG. 1 is a block diagram of the apparatus of the present invention;
FIG. 2 is a schematic view of the electrode module arrangement position;
FIG. 3 is a flow chart illustrating the steps of the detection method of the present invention;
FIG. 4 is a schematic diagram of a reference waveform during a detection process;
FIG. 5 is a first schematic view of an interface in a working system using the detection method of the present invention;
FIG. 6 is a second schematic view of an interface in a work system using the detection method of the present invention;
fig. 7 is a third schematic view of an interface in a working system obtained by the detection method of the present invention.
Detailed Description
In order to make the technical solutions better understood by those skilled in the art, the technical solutions in the embodiments of the present application will be clearly and completely described below with reference to the drawings in the embodiments of the present application, and it is obvious that the described embodiments are only partial embodiments of the present application, but not all embodiments. All other embodiments, which can be derived by a person skilled in the art from the embodiments given herein without making any creative effort, shall fall within the protection scope of the present application.
The terms "first," "second," "third," and "fourth," etc. in the description and claims of this application and in the accompanying drawings are used for distinguishing between different objects and not for describing a particular order. Furthermore, the terms "include" and "have," as well as any variations thereof, are intended to cover non-exclusive inclusions. For example, the inclusion of a list of steps, processes, methods, etc. is not limited to only those steps recited, but may alternatively include additional steps not recited, or may alternatively include additional steps inherent to such processes, methods, articles, or devices.
Reference herein to "an embodiment" means that a particular feature, structure, or characteristic described in connection with the embodiment can be included in at least one embodiment of the application. The appearances of the phrase in various places in the specification are not necessarily all referring to the same embodiment, nor are separate or alternative embodiments mutually exclusive of other embodiments. It is explicitly and implicitly understood by one skilled in the art that the embodiments described herein can be combined with other embodiments.
As shown in fig. 1, the present embodiment provides an EABR detection apparatus, including an electrical stimulator, a stimulation module, a recorder, and an integrated working system. The electric stimulator is connected with the stimulation module and the working system, and the working system is connected with the recorder; optionally, the working system is a PC system, comprising a stimulation unit and a processing unit.
Optionally, the working system is connected with a USB hub through a USB cable, and the USB hub is connected with the recorder and the electric stimulator through the USB cable; the recorder is a Neuro-EP host, the electric stimulator is a Neuro-MEP electric stimulator, and the working system is provided with software matched with the functions of the recorder and the electric stimulator.
In this embodiment, the electrical stimulator is controlled by the stimulation unit, and outputs a corresponding stimulation signal to the stimulation module according to the control result. Optionally, the stimulation unit may control the stimulation signal output by the electrical stimulator through setting of stimulation parameters, where the stimulation parameters include, but are not limited to, at least one of stimulation intensity, maximum current, change step size, stimulation type, stimulation polarity and stimulation channel, stimulation rate, stimulation shape, and pulse width, in this embodiment, all kinds of adjustments of the stimulation parameters are included, in other embodiments, at least one kind of adjustment is included, and one or more kinds of others may be default values.
In this embodiment, a stimulation signal with a good effect is obtained through an experiment, and the corresponding stimulation parameters are set as: the stimulation shapes include click, the stimulation intensity includes 1mA, the maximum current includes 5mA, the step size of change includes 0.1mA, the stimulation polarity includes positive and negative, the stimulation types include single or dual (e.g., single for right or left ear and dual for both right and left ear, where the corresponding stimulation channel is also single or dual), the stimulation types include continuous or alternating, the pulse width includes 100 μ S, and the stimulation rate includes 5-48 Hz.
In this embodiment, the stimulation module includes a probe having a stimulation electrode as a positive electrode and an electrode pad having a stimulation electrode as a negative electrode. In this embodiment, the positive stimulation electrode on the probe can be placed in the round window niche or on the cochlear nerve surface; the stimulating electrode of the negative pole on the electrode plate can be arranged under the occipital skin, so that the cochlear nerve can be stimulated through the probe and the electrode plate to generate excitation.
As shown in fig. 2, in this embodiment, the recorder includes an electrode module and a host connected to the electrode module, the electrode module includes, but is not limited to, an electrode sheet, the electrode module includes a recording electrode as a positive electrode, a reference electrode as a negative electrode, and a ground electrode GND, the recording electrode is optionally configured to be disposed at a middle position a (hairline position) on the top of the forehead, the reference electrode is configured to be disposed at a mastoid process or a temporomandibular joint (for example, a side to be operated is disposed at a temporomandibular joint B below an earlobe, and a non-operated side is disposed at the mastoid process), and the ground electrode GND is configured to be disposed at an eyebrow position C. It will be appreciated that the position setting can be adjusted within a certain error range centered on the above-mentioned position.
In this embodiment, the host may receive the electrical activity signals of the cochlear nerve generated via the stimulation signals collected from the surface of the skin of the subject by the electrode module and transmit them into the working system for processing.
In this embodiment, the processing unit of the working system is configured to process the received electrical activity signal, and the processing includes, but is not limited to:
1) amplifying the electrical activity signal, and performing analog-to-digital conversion on the amplified electrical activity signal to generate a waveform;
optionally, amplifying the electrical activity signal is performed by an amplifier in the working system, and the amplification parameter of the amplifier may be adjusted by the processing unit to control the result of the amplification process. Optionally, the amplification parameter includes at least one of a signal input range, a frequency, a trap, a harmonic filter, a sampling rate, and an impedance measurement, and this embodiment includes all the amplification parameters described above, and in other embodiments, one or more amplification parameters may be included, and the others may be fixed to default values. Wherein in this embodiment the signal input range comprises 500 μ V, the frequency comprises a high frequency comprising 100Hz and a low frequency comprising 2000Hz, the trap comprises a switch for a trap, a type of trap, a switch for (higher) harmonic filtering, the sampling rate comprises 160000Hz, and the impedance measurement comprises 5k Ω.
In this embodiment, the digital signal is converted into a curve by a fourier technique after analog-to-digital conversion is completed to obtain a waveform.
2) Processing the waveform to generate a result curve;
alternatively, the processing of the waveform may include waveform averaging, waveform (filtering) superposition, and the like, wherein the number of waveform superpositions may be adjusted by the processing unit;
3) comparing the result curve with a preset curve to obtain a scoring result;
optionally, the preset curve may be a curve obtained by a previous test when the cochlear nerve is normal, or a curve in a certain pathological state.
As shown in fig. 3, the present invention further provides a detection method applied to the EABR detection apparatus, including the following steps:
the stimulation unit controls the electrical stimulator to generate stimulation signals, and the stimulation signals are received by the stimulation module to stimulate cochlear nerves;
acquiring, by an electrode module, an electrical activity signal of a cochlear nerve generated via a stimulation signal;
receiving, by a host, an electrical activity signal;
and receiving and processing the electrical activity signal through the processing unit, wherein the processing comprises generating a result curve according to the electrical activity signal and comparing the result curve with a preset curve.
As a further optional embodiment, the step of controlling the electrical stimulator to generate the stimulation signal by the stimulation unit includes the following steps:
setting stimulation parameters through a stimulation unit to control an electrical stimulator to generate stimulation signals;
wherein the stimulation parameters include at least one of stimulation intensity, maximum current, change step size, stimulation type, stimulation polarity and stimulation channel, stimulation rate, stimulation shape, pulse width.
Specifically, in practical use, the stimulation may be started by 2mA until the reference waveform of fig. 4 is obtained, and then the intensity may be reduced by performing filtering and superimposing (for example, 300 times), and the intensity may be reduced by 0.5mA or (0.1mA step by step) until the detection is finished without reaction. In fig. 4, there are multiple reference curves, each having multiple reference waveforms, and 02, 03, and 05 represent the 2 nd, 3 rd, and 5 th reference curves in the detection process.
Further as an alternative embodiment, the stimulation shape comprises click, the stimulation intensity comprises 1mA, the maximum current comprises 5mA, the varying step size comprises 0.1mA, the stimulation polarity comprises positive and negative, the stimulation type comprises single or dual, the stimulation type comprises continuous or alternating, the pulse width comprises 100 μ S, and the stimulation rate comprises 5-48 Hz.
As a further optional implementation, the step of receiving and processing the electrical activity signal by the processing unit includes the following steps:
performing analog-to-digital conversion on the electrical activity signal by a processing unit;
performing waveform processing according to the analog-to-digital conversion result to generate a result curve, wherein the waveform processing comprises filtering superposition;
and comparing the result curve with a preset curve.
As a further alternative, the step of performing analog-to-digital conversion on the electrical activity signal by the processing unit includes the following steps:
amplifying the electrical activity signal, and performing analog-to-digital conversion on the amplified result;
wherein the amplification process is controlled by amplification parameters of the processing unit, the amplification parameters comprising at least one of signal input range, frequency, trap, harmonic filtering, sampling rate and impedance measurement.
Further as an optional implementation manner, the scoring result is obtained by comparing at least one of the appearance of the waveform, the amplitude of the waveform and the time interval between the waveforms in the result curve with a preset curve.
It will be appreciated that the result curves are one or more, for example there may be multiple result curves at different stimulation currents or frequencies, optionally automatically selecting the curve that exhibits the most waveform among the several result curves when the result curves are analysed.
Specifically, the result curve is analyzed, 1), the analysis comprises detecting the occurrence of the waveform (such as I wave, II wave, III wave, IV wave and V wave) in the curve, and calculating and displaying corresponding parameters according to the result curve, such as the amplitudes (amplitudes) of the I wave, II wave, III wave, IV wave and V wave; and then comparing the signal with a preset curve (for example, a curve chart obtained by testing in advance when the cochlear nerve is normal) to judge whether the signal is a real reaction signal, thereby obtaining a scoring result to judge whether the result curve is normal or abnormal. For example, different scores may be set, such as different scores for the occurrence of I-wave than for the non-occurrence of I-wave, and the same applies to II-wave, III-wave, IV-wave, and V-wave. Optionally, the amplitude of the waveform in the result curve may be compared with a first preset amplitude in a preset curve, and different thresholds may be set, for example, when an I-wave occurs and an absolute value of a difference between the amplitude of the I-wave and the first preset amplitude of the I-wave in the preset curve is smaller than the first threshold to give a score, and when the absolute value is larger than the first threshold to give another score, the same applies to the ii-wave, the iii-wave, the iv-wave, and the v-wave, a first scoring result is finally obtained, so as to accurately and effectively evaluate the integrity of the cochlear nerve function of the test subject.
Specifically, the result curve is analyzed, and 2) the analysis comprises detecting the occurrence of the waveform (such as I wave, II wave, III wave, IV wave, V wave) in the curve, and calculating and displaying corresponding parameters according to the result curve, such as the amplitudes (amplitudes) of the I wave, II wave, III wave, IV wave, V wave; then comparing with a preset curve (for example, a curve in a certain pathological state) to judge whether the curve is a real response signal, thereby obtaining a scoring result to judge whether the result curve is normal or abnormal. For example, different scores may be set, such as different scores for the occurrence of I-wave than for the non-occurrence of I-wave, and the same applies to II-wave, III-wave, IV-wave, and V-wave. Optionally, the amplitude of the waveform in the result curve may be compared with a second preset amplitude in a preset curve (e.g., a curve in a certain pathological state), and different thresholds may be set, for example, when an I wave appears and an absolute value of a difference between the amplitude of the I wave and the second preset amplitude of the I wave in the preset curve is smaller than the second threshold and gives a score, and when the absolute value is greater than the second threshold, another score is given, and the second, iii, iv and v waves are the same, a second scoring result is finally obtained, so as to accurately and effectively evaluate the cochlear nerve functional integrity of the test subject.
Optionally, the scoring result may be further obtained by detecting a time interval between the waveforms and comparing the time interval with a preset time interval in a preset result curve. For example, a corresponding threshold is set, when the absolute value of the difference between the time interval and the preset time interval is smaller than a third threshold, a score is obtained, another score is obtained when the absolute value is larger than the third threshold, and then all scores are added to obtain a third scoring result. It will be appreciated that if the time interval is different from the predetermined time interval, for example, the extension means that the intermediate pathway may be diseased or abnormal.
Optionally, when obtaining the scoring result, the first scoring result, the second scoring result, or the third scoring result may be obtained through the above manner, and it may be understood that corresponding weights may be set for different scoring results, and at least two of the first scoring result, the second scoring result, and the third scoring result are used for performing weighting calculation to obtain a final scoring result. The evaluation result can be used as a reference for a tester to refer to, so that the judgment efficiency of the tester is improved.
As shown in fig. 5, a first result curve of sensorineural hearing loss (SNHL, typical) measured by the method of the present invention is a schematic diagram in the interface of software in the working system, and there are several result curves, where N is the number, and 0, 02, 03, 04, 05 represents the 1 st, 2 nd, 3 rd, 4 th and 5 th result curves in the test; the latency refers to the time required for the stimulation signal to be transmitted to a specific sensing organ on a corresponding auditory conduction channel to induce a response signal after the stimulation signal is emitted, and the unit is ms, namely the numerical value in the table of the schematic diagram in the interface of the software, which shows that the time used for measurement by the device is short and the efficiency is high, for example, the latency of the II wave in the 02 curve is 2.09ms, which represents that the conduction time of the signal transmitted to the II wave from the cochlear nucleus is 2.09ms after the stimulation signal is emitted, and II-III refers to the time required between the II wave and the III wave, and other similar reasons. Wherein optionally in this embodiment the waves I are auditory nerve action potentials, the waves II originate in the cochlear nucleus, the waves III originate from the suprapontine nucleus olivocorticoids and the rhombohedral, the waves IV and V represent the lateral thalamic and hypothalamic nuclei, respectively, and in other embodiments the waves VI and VII may be included as well, the gonadal and auditory radiation action potential waveforms, respectively; thus, the I and II waves actually represent the peripheral wave groups of the auditory afferent pathways, with each subsequent wave representing the hub action potential. The first 5 waveforms, i-v, are most stable, while the amplitude (amplitude) refers to the level of excitatory potential produced by the nerves after the corresponding auditory organ has experienced a stimulus. The right hand content represents stimulation intensity, pulse width, and stimulation rate, respectively.
As shown in FIG. 6, in a second result curve of Auditory Neuropathy (AN) measured by the method of the present invention, the same reference numerals 02, 05, 07, 08 represent the results of the 2 nd, 5 th, 7 th and 8 th tests.
As shown in FIG. 7, 0, 03, 010, 011, 014 represents the 1 st, 3 rd, 10 th and 11 th result curves in this test, which is the third result curve of the stenosis of the internal auditory canal measured by the method of the present invention.
It is understood that the reason why the types of the waveforms in each example are different is that the waveforms recorded by different physiological structures in each example are different, so that different responses can be recorded due to the structural differences of different auditory conduction paths, and the physiological states and characteristics (high sensitivity) of different auditory organs can be accurately evaluated.
According to the detection device and the detection method, the detection device and the detection applicability of the detection device are wide, the detection device can be applied to different detection objects, the detection efficiency is high, the stimulation parameters and the data processing can be adjusted according to different requirements, and the detection device is more humanized.
The contents in the above device embodiments are all applicable to the method embodiments, the functions specifically implemented by the method embodiments are the same as those in the above device embodiments, and the beneficial effects achieved by the method embodiments are also the same as those achieved by the above device embodiments.
The present invention also provides an apparatus comprising:
at least one processor;
at least one memory for storing at least one program;
when the at least one program is executed by the at least one processor, the at least one processor is enabled to implement the detection method.
The contents in the above method embodiments are all applicable to the present apparatus embodiment, the functions specifically implemented by the present apparatus embodiment are the same as those in the above method embodiments, and the advantageous effects achieved by the present apparatus embodiment are also the same as those achieved by the above method embodiments.
Claims (9)
1. An EABR detection apparatus, comprising:
an electrical stimulator for outputting a stimulation signal;
a stimulation module to receive the stimulation signal to stimulate a cochlear nerve;
the recorder comprises an electrode module and a host connected with the electrode module, and the host is used for receiving the electrical activity signals of the cochlear nerve generated by the stimulation signals acquired by the electrode module;
the working system is connected with the electric stimulator and the recorder and comprises a stimulation unit and a processing unit, the stimulation unit is used for controlling the electric stimulator to generate the stimulation signals, the processing unit is used for processing the electric activity signals, and the processing comprises generating a result curve according to the electric activity signals and comparing the result curve with a preset curve; comparing the result curve with the preset curve according to at least one of appearance of the waveform, amplitude of the waveform and time interval between the waveforms in the result curve to obtain a scoring result; different weights are set for different scoring results, and weighting calculation is carried out by utilizing at least two scoring results to obtain a final scoring result.
2. The EABR detection apparatus of claim 1, wherein: the stimulation module comprises a probe and an electrode plate, the probe is used for being arranged on the surface of the round window niche or the cochlear nerve, and the electrode plate is used for being arranged under the skin of the occipital part.
3. The EABR detection apparatus of claim 1, wherein: the electrode module includes a recording electrode, a reference electrode, and a ground electrode.
4. The EABR detection apparatus of claim 3, wherein: the recording electrode is used for being arranged in the middle of the top of the forehead, the reference electrode is used for being arranged on the mastoid process or the temporomandibular joint, and the terrestrial pole is used for being arranged on the eyebrow center.
5. An EABR detection method applied to the EABR detection device of claim 1, comprising the steps of:
controlling the electrical stimulator to generate the stimulation signal through the stimulation unit and to be received by the stimulation module to stimulate cochlear nerves;
acquiring, by the electrode module, an electrical activity signal of a cochlear nerve generated via the stimulation signal;
receiving, by the host, the electrical activity signal;
receiving and processing the electrical activity signal through the processing unit, wherein the processing comprises generating a result curve according to the electrical activity signal and comparing the result curve with a preset curve; comparing the result curve with the preset curve according to at least one of appearance of the waveform, amplitude of the waveform and time interval between the waveforms in the result curve to obtain a scoring result; different weights are set for different scoring results, and weighting calculation is carried out by utilizing at least two scoring results to obtain a final scoring result.
6. The EABR detecting method according to claim 5, wherein: the step of controlling the electrical stimulator to generate the stimulation signal through the stimulation unit comprises the following steps:
setting stimulation parameters through the stimulation unit to control the electrical stimulator to generate the stimulation signals;
wherein the stimulation parameters include at least one of stimulation intensity, maximum current, change step size, stimulation type, stimulation polarity and stimulation channel, stimulation rate, stimulation shape, pulse width.
7. The EABR detection method of claim 6, wherein:
the stimulation shape comprises click, the stimulation intensity comprises 1mA, the maximum current comprises 5mA, the varying step size comprises 0.1mA, the stimulation polarity comprises positive and negative, the stimulation type comprises single or dual, the stimulation type comprises continuous or alternating, the pulse width comprises 100 μ S, and the stimulation rate comprises 5-48 Hz.
8. The EABR detecting method according to claim 5, wherein: the step of receiving and processing the electrical activity signal by the processing unit comprises the following steps:
performing analog-to-digital conversion on the electrical activity signal by the processing unit;
carrying out waveform processing according to the analog-to-digital conversion result to generate a result curve, wherein the waveform processing comprises filtering superposition;
and comparing the result curve with the preset curve.
9. The EABR detecting method according to claim 8, wherein: the step of performing analog-to-digital conversion on the electrical activity signal by the processing unit includes the steps of:
amplifying the electrical activity signal, and performing analog-to-digital conversion on the amplified result;
wherein the amplification process is controlled by amplification parameters of the processing unit, the amplification parameters comprising at least one of signal input range, frequency, trap, harmonic filtering, sampling rate and impedance measurement.
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