Method for creating an audiogram of a test person by means of a hearing instrument

Abstract

The invention relates to a method for creating an audiogram of a test person by means of a hearing instrument (1), wherein a sound signal (22) is received in the ear canal (4) of the test person, which is at least partially closed by the hearing instrument (1), by means of a first electroacoustic input transducer (10) of the hearing instrument (1) and a first input signal (24) is generated therefrom, wherein a test sound (32) is generated by means of an electroacoustic output transducer (18) of the hearing instrument (1) and is output into the ear canal (4) of the test person, which is at least partially closed by the hearing instrument (1), and wherein the hearing threshold of the test person at at least one test frequency is determined from the reaction of the test person to the test sound (32) and by means of the first input signal (24).

Description

TECHNICAL FIELD

[0001] The invention relates to a method for creating an audiogram of a test person by means of a hearing instrument, wherein a test sound is generated by an electroacoustic output transducer of the hearing instrument and is output into an ear canal of the test person, which is at least partially closed by the hearing instrument, and wherein a hearing threshold of the test person at at least one test frequency is determined from a reaction of the test person to the test sound. The invention also relates to a hearing instrument by means of which a hearing threshold of a test person at at least one test frequency can be determined. BACKGROUND

[0002] A hearing instrument generally comprises any device which is set up and designed to generate a corresponding output sound by means of an electroacoustic output transducer from an electrical output signal and to feed this output sound to the auditory organs of a user. As such an output transducer hereinafter a loudspeaker can be used, however also a thermoacoustic transducer or a bone conduction earpiece can be used, in particular. Herein, the hearing instrument can be designed on the one hand only for generating an output sound from audio data, i.e. for example in the form of a wireless, in particular earplug-shaped earpiece. In this case, the output sound is generated from audio data which can be given for example by music and which has been stored in advance or is also transmitted to the hearing instrument by means of a corresponding antenna (by streaming).

[0003] However, the hearing instrument can also exist as a hearing aid which is set up for correcting or at least partially compensating a hearing impairment of a user in such a way that environmental sounds are converted into a corresponding electrical input signal by means of at least one electroacoustic input transducer, which is processed in the hearing aid according to the acoustical requirements of the user and is amplified hereinafter in particular frequency band by frequency band, so that the processed input signal is fed to the auditory organs of the user as an output sound by means of an electroacoustic output transducer.

[0004] In particular for said correction of a hearing impairment of a user in the case of a hearing aid (in the "narrower sense"), a hearing diagram of the user is generally generated. For various test frequencies which preferably cover the entire acoustic spectrum of the human hearing sensation, the hearing diagram gives the respective hearing threshold of the user at the relevant frequency, so that the hearing ability of the user can be compared in particular with the hearing ability of a person with normal hearing in order to draw conclusions for the above-mentioned individualized signal processing in the hearing aid. However, in order to adapt the hearing instrument (in the "broader sense") to the user for improving the sound sensation, i.e. for example for a better acoustic performance in a specific frequency range, it can be advantageous to create a hearing diagram.

[0005] Here, the measurement of the hearing threshold at the individual test frequencies is usually carried out at an audiologist or a qualified acoustician, wherein a test probe with a sound generator is often introduced into the ear canal of the user. The individual test tones at the respective test frequencies are each generated with a continuously increasing or decreasing sound level, so that the user can give a recognition from when he hears the test tone at one test frequency or no longer hears it. The disadvantage here is that this measurement of the audiogram is carried out by or with the audiologist / acoustician. SUMMARY

[0006] The technical problem addressed by the present application is therefore to provide a method by means of which an audiogram of a wearer of a hearing instrument can be established in as simple but reliable a manner as possible and as independently of the circumstances as possible by means of the hearing instrument. The technical problem addressed by the present application is also to provide a hearing instrument which is set up to create an audiogram of a wearer as simply and reliably as possible.

[0007] According to the application, the first-mentioned technical problem is solved by a method for creating an audiogram of a test person by means of a hearing instrument, wherein a sound signal is received by a first electroacoustic input transducer of the hearing instrument in an ear canal of the test person which is at least partially closed by the hearing instrument and a first input signal is generated therefrom, wherein a test sound is generated by an electroacoustic output transducer of the hearing instrument and is output into the ear canal of the test person which is at least partially closed by the hearing instrument, and wherein a hearing threshold of the test person at at least one test frequency is determined from a reaction of the test person to the test sound and by means of the first input signal. Advantageous and partly inventive design proposals are the subject of the following description.

[0008] According to the application, the second-mentioned technical problem is solved by a hearing instrument comprising a first electroacoustic input transducer which is set up to receive a sound signal in an ear canal of a test person if the test person wears the hearing instrument as prescribed and to generate a first input signal therefrom, an electroacoustic output transducer which is set up to generate a test sound and to output it into the ear canal of the test person if the test person wears the hearing instrument as prescribed, and a control device which is set up to record a reaction of the test person to the test sound and to determine a hearing threshold of the test person at at least one test frequency from the reaction of the test person to the test sound and by means of the first input signal.

[0009] The hearing system according to the application shares the advantages of the method according to the application. The advantages given for the method and its improvement proposals can be transferred analogously to the hearing system.

[0010] The control device preferably comprises at least one signal processor and a working memory addressable by the signal processor, which working memory is provided for carrying out the mentioned signal processing steps. Here, the hearing system can be given on the one hand by the hearing instrument or can also have an auxiliary device, such as a smartphone or tablet, which can be connected in data technology with the hearing instrument, wherein the control device in the latter case can be given by a control unit in the hearing instrument and / or a control unit on the auxiliary device.

[0011] Here, the electroacoustic input transducer especially comprises any transducer which is designed to generate an electrical audio signal from the ambient sound, so that the air movements and air pressure fluctuations caused by the ambient sound at the location of the transducer are reproduced by a corresponding oscillation of the electrical parameter, in particular of the voltage in the generated audio signal. In particular, the electroacoustic input transducer can be given by a microphone. Correspondingly, the electroacoustic output transducer comprises any transducer which is designed to generate an output sound from an electrical output signal, i.e. especially a loudspeaker (e.g. Balanced Metal Case Receiver), but for example also a thermoacoustic transducer.

[0012] The reception of the sound signal by the first electroacoustic input transducer of the hearing instrument in the ear canal of the test person which is at least partially closed by the hearing instrument especially comprises that the hearing instrument is worn on the ear by the test person in a manner corresponding to the regular use of the hearing instrument, and that the ear canal of the relevant ear is at least partially closed outwardly here at least by a part of the hearing instrument. In particular, here a part of the hearing instrument can be firmly pressed in the concha by pressure and / or a part projects into the ear canal and is firmly pressed there by pressure.

[0013] Here, the hearing instrument is preferably designed such that the first electroacoustic input transducer is oriented into the relevant ear canal in the case of a prescribed wearing of the hearing instrument on the ear. The sound signal received by the first electroacoustic input transducer is especially given by the sound which propagates between the eardrum and the hearing instrument, and can contain a high proportion of body sounds which cannot escape into the surroundings due to the partial closure of the ear canal by the hearing instrument (so-called occlusion effect). Thus, the first input signal especially contains a signal contribution of said body sounds.

[0014] The test sound preferably has a defined first signal contribution, i.e. a defined sound level, especially in the range of the first test frequencies, at least at one test frequency. In particular, this defined first signal contribution or defined sound level in the range of the first test frequencies is varied, i.e. continuously increased, for example, from a sound level that is completely inaudible for each person being tested, or continuously decreased, for example, from a sound level that is completely audible for each person being tested. Here, the hearing instrument is preferably designed such that the electroacoustic output transducer is directed into the associated ear canal with the hearing instrument worn as prescribed on the ear.

[0015] Here, the reaction of the person being tested to the test sound can be captured as a speech signal, especially via a second electroacoustic input transducer of the hearing instrument, which is directed into the free environment of the hearing instrument and is set up to generate a second input signal from the ambient sound of the hearing instrument. The second input signal can then be analyzed by the control device of the hearing instrument with respect to a speech command, which contains the reaction to the test sound, as appropriate. However, the reaction can also be captured by means of an auxiliary device, which is controlled by the person being tested as appropriate, for example by means of a corresponding app for capturing the reaction by means of a screen input of the person being tested. The reaction can also be captured as a movement of the person being tested by means of a correspondingly set up sensor of the hearing instrument, i.e. for example as a nod or shake of the head for signaling the hearing or non-hearing of the test sound, for example by means of a motion and / or acceleration sensor and / or gyroscope.

[0016] Here, the hearing threshold at least at one test frequency can be determined, especially by outputting the test sound with a variable, preferably continuously increasing or decreasing, sound level in the range of the first test frequencies to the ear canal of the person being tested in the manner described above and identifying by the reaction of the person being tested from when the test sound is heard (increasing) or from when the test sound is no longer heard (decreasing).

[0017] Here, the first input signal can be used on the one hand to determine the hearing threshold as follows, namely to determine a kind of "noise background" in the ear canal from the first input signal before the test sound is emitted and to take this noise background into account to determine the sound level at the at least one test frequency (the further important signal contribution at the test frequency comes from the test sound, the defined sound level of which is offset against the noise background of the final sound level at the test frequency). On the other hand, the defined first signal contribution of the test frequency in the test sound can also be adapted in accordance with the first input signal and in particular during the output of the test sound, for which purpose the first input signal can be filtered in particular with respect to the first signal contribution at the at least one test frequency. Furthermore, active occlusion suppression can be carried out in accordance with the first input signal. For this purpose, a correction signal for the occlusion suppression is generated from the first input signal, which correction signal is converted into a correction sound by means of an electroacoustic output transducer. Here, for the output, the correction signal can be superimposed on the signal set up for generating the test sound.

[0018] The audiogram is determined in accordance with and preferably directly from the hearing threshold thus determined for the at least one test frequency. The audiogram can now be created entirely in the manner described, in that a plurality of test frequencies are predefined and the respective test sound with the defined signal contribution is generated in succession at the respective test frequency and is output into the ear canal of the person being tested, and for each of the test frequencies the hearing threshold is determined from the respective reaction of the person being tested to the relevant test sound and from the first input signal. Preferably, the test frequencies here entirely cover the human hearing spectrum and furthermore an as advantageous as possible frequency resolution of the hearing spectrum is able to be achieved (i.e. for example a substantially constant number of test frequencies per arbitrarily chosen octave).

[0019] However, the hearing threshold determined as described for the at least one test frequency can also be used to replace the respective data in an already existing or predefined audiogram or as a supplement to such an audiogram.

[0020] Just for a hearing instrument, which is worn on the ear for a prescribed operation, so that the associated ear canal is largely closed here, the measurement of the hearing threshold by means of the hearing instrument through the closure of the ear canal is made difficult or even distorted due to the occlusion effect. The proposed method solves this problem by the fact that noise in the ear canal which does not belong to the test sound and in particular does not belong to the first signal contribution of the test sound at the at least one test frequency can be actively attenuated or its contribution to the total sound level in the ear canal can be taken into account in the range of the at least one test frequency. Thus, the hearing threshold can also be determined by means of the hearing instrument since the above-mentioned distortion is avoided. It is thereby possible to dispense with the person being tested having to consult an audiologist or a practicing acoustician in order to recreate the audiogram or only to adjust or correct the audiogram.

[0021] Preferably, the test sound has a defined first signal contribution at the at least one test frequency, wherein a second signal contribution of the sound signal in the ear canal is determined at the at least one test frequency from the first input signal, and wherein, for determining the hearing threshold of the at least one person being tested, at least the second signal contribution is taken into account. This can be achieved in particular in that the second signal contribution at the at least one test frequency captures all the sound in the ear canal, which consists of the defined first signal contribution of the test sound and a sound contribution which is largely caused by body sounds and, if necessary, also contains environmental sound which reaches the ear canal through the ear canal which is not completely closed by the hearing instrument as a rule. In the hearing instrument, only the first signal contribution is known a priori which is produced in the test sound by the hearing instrument itself, whereby the reaction to the sum of the test sound and the other mentioned contributions can lead to an incorrect, in particular low, hearing threshold if necessary. By taking into account the second signal contribution, this can be corrected by adjusting the first signal contribution accordingly.

[0022] However, the second signal contribution, in particular after filtering the first input signal with respect to the first signal contribution, can only have a contribution caused by body sounds and possibly environmental sound, so that in this case the first and the second signal contribution are used for determining the sound level in the ear canal (and accordingly for the correct hearing threshold).

[0023] Advantageously, a correction signal for active occlusion suppression is generated from the first input signal, wherein a correction sound is generated from the correction signal for compensating the body sound in the ear canal sound signal by means of an electroacoustic output transducer of the hearing instrument and is output into the ear canal (closed at least partially by the hearing instrument) of the test person. The active occlusion suppression determines the noise in the largely closed ear canal, which is based on the body sound, and then generates a compensation sound in the ear canal, which compensates the body sound as far as possible. Here, the signal contribution in the ear canal, which is based on the body sound, can be determined from the first input signal, which is for this purpose preferably purified from the defined first signal contribution caused by the test sound by means of a corresponding filtering. For the remaining signal contribution thus determined, a corresponding, preferably anti-phase, correction signal is now generated for compensation, which is converted into a correction sound by means of the electroacoustic output transducer of the hearing instrument, which is output into the ear canal.

[0024] The compensation of the body sound due to the occlusion effect thus described, which is preferably carried out broadband, here reduces the sound level in the ear canal, thereby allowing the test person to concentrate better on the test sound and in particular on its first signal contribution at the test frequency on the one hand and enabling a prevention of masking effects due to sound events away from the test frequency, which become significant precisely at the low sound level of the test sound as it almost inevitably occurs for determining the hearing threshold. A possible additional compensation of the noise caused by the environmental sound can here further positively influence the determination of the hearing threshold.

[0025] Here, advantageously, the correction sound is generated and output as a broadband sound signal, wherein, as a second signal contribution, the remaining noise signal not purified by the active occlusion suppression is determined from the first input signal. This second signal contribution is in particular taken into account for generating the test sound in such a way that, in correspondence to the second signal contribution, the first signal contribution of the test sound is set at the test frequency in order to achieve the desired sound level in the ear canal in the range of the test frequency.

[0026] Advantageously, the ambient sound of the hearing instrument is received by a second electroacoustic input transducer of the hearing instrument and a second input signal is generated therefrom, wherein, in addition to the outputting of the test sound, an active noise cancelling ("Active Noise Cancelling", ANC) is performed by the electroacoustic output transducer of the hearing instrument in accordance with the second input signal. The ANC determines the noise in the ambient sound and then generates a compensation sound in the ear canal which compensates for the noise reaching the ear canal from the surroundings as far as possible. In the case of a hearing instrument given as a hearing aid, the hearing instrument already has at least one electroacoustic input transducer for receiving the ambient sound for normal operation. However, the hearing instrument generally has such an input transducer for receiving the ambient sound without specific hearing defect correction in order to be able to receive, for example, speech commands of the user or for a telephone function. Here, the correction signal generated for the ANC can be superimposed on the signal set for generating the test sound for the output. By means of the ANC, the person being tested is exposed to less ambient noise in determining the hearing threshold, so that here too the distortion and masking effect is further prevented.

[0027] Here, advantageously, the active noise cancelling is concentrated on a frequency range around the at least one test frequency. In general, the ANC has a specific operating region in which the noise is particularly effectively suppressed. Here, a narrowband frequency range of, for example, 50 Hz or 100 Hz or 250 Hz around the test frequency can be better optimized with regard to complete noise suppression, whereas a broadband ANC can achieve a greater reduction in the overall noise energy, although there can be greater residual noise in the vicinity of the test frequency which is not eliminated by the ANC. Therefore, for the purpose of as complete a noise suppression as possible, here the bandwidth of the ANC is reduced at the test frequency and preferably in its immediate surroundings. The ANC provides the best results in the case of a strong, predictable signal which has a high-pitched component and thus a clear positioning in the frequency spectrum. For determining the hearing threshold, this means that the ANC is preferably applied when a strong, tonal noise signal occurs in the surroundings of the person being tested which is in the range of the test frequency.

[0028] It proves advantageous here that the active noise cancelling is concentrated on a frequency range around the at least one test frequency and that the active occlusion cancelling is carried out broadband by means of the correction signal. In contrast to the ANC, the compensation signal of the active occlusion cancelling is preferably generated in a feedback loop, whereby further possibilities arise in the compensation of the noise. Since the occlusion effect generally occurs with a greater spectral width, it can be advantageous that the compensation by means of the correction sound is not limited to a specific frequency range. In particular, the correction signals of the ANC and the active occlusion cancelling can here be superimposed on the signal set for generating the test sound for the output.

[0029] In an advantageous design variant, the hearing instrument is designed as a hearing aid and further comprises a second electroacoustic input transducer which is arranged for receiving ambient sound of the hearing aid and generating a second input signal therefrom, wherein the control device is further arranged for generating an output signal from the second input signal and feeding the output signal to the electroacoustic output transducer for conversion into the output sound signal. In particular for a hearing aid, it is advantageous that a hearing map is created by the user without an audiological care.

[0030] Advantageously, the control device is further arranged for performing an active noise suppression by means of the electroacoustic output transducer from the second input signal in addition to outputting the test sound. BRIEF DESCRIPTION OF DRAWINGS

[0031] Embodiments of the application are explained in detail below with reference to the drawings. In this drawing:

[0032] Figure 1 A hearing instrument is schematically shown in a sectional view, which hearing instrument encloses an ear canal and by means of which a hearing threshold of a user can be determined. DETAILED DESCRIPTION

[0033] In Figure 1 A hearing instrument 1 is schematically and not to scale shown in a sectional view, which hearing instrument is currently designed as a hearing aid 2. The hearing aid 2 is introduced into an ear canal 4 and is fixed in its position here by pressure on the skin on the ear canal 4. Thereby, the ear canal 4 is largely enclosed with respect to the surrounding environment 6, so that a small portion of ambient sound 8 reaches into the ear canal 4 after passing the hearing aid 2 (by not completely enclosing the ear canal 4 due to the earplug of the hearing aid 2 not precisely lying in the ear canal 4) and through the thin skin portion at the entrance of the ear canal 4.

[0034] The hearing aid 2 has a first electroacoustic input transducer 10 and a second electroacoustic input transducer 12, which are given here as first or second microphones 14, 16, and an electroacoustic output transducer 18, which is given as a loudspeaker 20. Here, the first microphone 14 and the loudspeaker 20 are directed into the ear canal 4 in the case of a prescribed wearing of the hearing aid 2, the second microphone 16 is directed to the free environment 6 of the hearing aid 2.

[0035] The first microphone is arranged for receiving a sound signal 22 in the ear canal 4 and generating a first input signal 24 therefrom, which is fed to a control device 26. The second microphone 16 is configured to generate a second input signal 28 from the ambient sound 8, which is likewise fed to the control device 28. In particular, the hearing aid 2 can also have a further electroacoustic input transducer (not shown) directed towards the free environment 6, which is arranged for generating a further input signal from the ambient sound 8.

[0036] In normal operation of the hearing aid 2, in the control device 26 the second input signal (and if necessary the further input signals mentioned) is processed and in particular amplified band-specifically and an output signal 30 is thereby generated, which is fed to the loudspeaker 20. To this end, the control device 26 can in particular have a signal processor (not shown) and a working memory addressable by the signal processor. The loudspeaker 20 generates an output sound signal (not shown) from the output signal 30. In order to generate the output signal 30, the hearing loss of the user of the hearing aid 2 is taken into account here by the control device 26 in that band-specific amplification is carried out in particular in accordance with the user's audiometric requirements in order to compensate for his hearing loss. To this end, a hearing diagram is required in the hearing aid 2 as information for these audiometric requirements.

[0037] Usually, such a hearing diagram, which gives the user's hearing threshold for individual frequencies, is generated at an audiologist or acoustician, whom the user visits for this purpose.

[0038] However, the hearing aid 2 is set up by some features described below in such a way that a hearing diagram can also be created with the aid of the hearing aid 2 or that an already existing (and preferably stored in the non-volatile memory of the hearing aid 2, in particular also for use in ongoing operation) hearing diagram can be updated for some frequencies.

[0039] In order to be able to determine the user's hearing threshold with the aid of the hearing aid 2 (and thus to be able to use it for a hearing diagram), the hearing aid 2 is advantageously designed for suppressing disturbing noise, which can make the measurement of the hearing threshold difficult ("non-conclusive result") or can also distort it (false result), and which usually does not occur to a noteworthy extent in the environment set up specifically for such a measurement at an audiologist or acoustician.

[0040] The test sound 32 is output by the electroacoustic output transducer 18, which is generated by a corresponding contribution in the output signal 30 converted by the electroacoustic output transducer 18. Here, the test sound 32 has a defined first signal contribution 34 in the range of test frequencies for which the hearing threshold is to be determined. The test sound 32 with the first signal contribution 34 is here transmitted through the ear canal 4 to the user's eardrum 35 and is perceived by the user in accordance with the sound level of the first signal contribution 34. In order to measure the hearing threshold at the test frequency, the first signal contribution 34 is here changed (i.e. continuously increased, for example, from an inaudible starting value, or continuously decreased from an audibly good starting value), so that the user can signal a change in his perception (the test sound becomes audible or becomes inaudible).

[0041] This can be achieved, for example, by means of a corresponding speech input through the second electroacoustic input transducer 12, wherein the second input signal 28 is analyzed with respect to such speech input during the output of the test sound 32. It is likewise possible to use a user input by means of a smartphone, tablet computer (both not shown) or the like, which is connected to the hearing aid 2, preferably wirelessly, wherein an application program for input and also for selecting test frequencies, etc. can be used, in particular.

[0042] In order to make the measurement of the hearing threshold difficult or distorted by external disturbing noise 36 in the ambient sound 8, which propagates into the ear canal 4 (and thus further to the eardrum 35 of the user) by means of the schematically shown sound path 38, the external disturbing noise 36 is compensated by means of ANC in such a way that a compensation signal (not shown) is generated in the control device 26 from the second input signal 28 generated by the second electroacoustic input transducer 12, which picks up the ambient sound 8 and thus the external disturbing noise 36, and which is input into the output signal 30. Here, the compensation signal is generated in terms of phase and amplitude in such a way that the relevant signal contribution in the output sound signal generated by the loudspeaker 20 completely compensates the portion of the external disturbing noise 36 that propagates into the ear canal 4 via the sound path 38 as completely as possible.

[0043] Furthermore, a second signal contribution 40 in the sound signal 22 in the ear canal 4 at the test frequency of the test sound 32 is determined by means of the first electroacoustic input transducer 10. This is done with the aim of suppressing the body sound 42 that enters the ear canal 4 by means of active occlusion suppression. The share of the body sound 4 in the sound signal 22 can be picked up by means of the first input signal 24 generated by the first electroacoustic input transducer 10, so that a correction signal (not shown) can be generated from the picked-up body sound 42, which is input into the output signal 30. The output sound signal generated by the electroacoustic output transducer 18 accordingly then contains a correction sound, which completely compensates the body sound 42 as completely as possible. Here, the picking up of the body sound 42 can preferably be carried out separately in time from the output of the test sound 32, so that the body sound 42 to be compensated for can be determined, for example, shortly before such output, and the corresponding compensation by means of the correction sound during the output of the test sound. The output sound signal generated by the electroacoustic output transducer 18 can thus pick up the test sound 32 as well as the contribution of the active occlusion suppression for compensating the body sound 42 in the sound signal 22 in the ear canal 4 and the contribution of the ANC for compensating the external disturbing noise 36 in the ambient sound 8.

[0044] Alternatively, the body sound 42 can also occur during the output of the test sound 32 (not shown). In this case, the second signal contribution 40 of the sound signal 22 in the ear canal 4 also comprises a first signal contribution 34 of the test sound 32 at the test frequency. The second signal contribution 40 can then be used to adjust the first signal contribution 34 in the test sound 32 such that, in the range of the test frequency, the desired sound level impinges on the eardrum 35 as a sum signal composed of the body sound 42 and the first signal contribution 34, respectively. The second signal contribution 40 is thus used here to directly correct the first signal contribution 34 in the test sound 32.

[0045] Although the application has been illustrated and described in detail by preferred embodiments, the application is not restricted to the disclosed examples and can be modified in other ways without departing from the scope of the application.

[0046] List of reference signs

[0047] 1 hearing instrument

[0048] 2 hearing aid

[0049] 4 ear canal

[0050] 6 free field

[0051] 8 environmental sound

[0052] 10 first electroacoustic input transducer

[0053] 12 second electroacoustic input transducer

[0054] 14 first microphone

[0055] 16 second microphone

[0056] 18 electroacoustic output transducer

[0057] 20 loudspeaker

[0058] 22 sound signal

[0059] 24 first input signal

[0060] 26 control device

[0061] 28 second input signal

[0062] 30 output signal

[0063] 32 test sound

[0064] 34 first signal contribution

[0065] 35 eardrum

[0066] 36 external interference noise

[0067] 38 sound path

[0068] 40 second signal contribution

[0069] 42 body sound

Claims

1. An audiological instrument (1) for creating an audiogram of a test subject, wherein, The hearing instrument is designed as a hearing aid, which is configured to correct or at least partially compensate for a user’s hearing loss, wherein the hearing instrument (1) includes a first electroacoustic input converter (10), an electroacoustic output converter (18), a second electroacoustic input converter (12), and a control device (26). The first electroacoustic input converter (10) of the hearing instrument (1) receives sound signals (22) in the ear canal (4) of the test subject, which is at least partially closed by the hearing instrument (1), and thereby generates a first input signal (24). The test sound (32) is generated by the electroacoustic output converter (18) of the hearing instrument (1) and output to the ear canal (4) of the test subject, which is at least partially closed by the hearing instrument (1). The control device (26) records the test subject's response to the test sound (32), and determines the test subject's hearing threshold at at least one test frequency based on the test subject's response to the test sound (32) and with the aid of the first input signal (24). The control device (26) also generates a correction signal for active occlusion suppression based on the first input signal (24), and wherein the electroacoustic output converter (18) of the hearing instrument (1) generates a correction sound based on the correction signal for compensating for body sounds (42) in the sound signal (22) of the ear canal (4) and outputs the correction sound to the ear canal (4) of the test subject, which is at least partially closed by the hearing instrument (1).

2. The hearing instrument according to claim 1, in, The test sound (32) has a defined first signal contribution (34) at at least one test frequency. Specifically, based on the first input signal (24), a second signal contribution (40) of the sound signal (22) in the ear canal (4) is determined at at least one test frequency, and In order to determine the hearing threshold in the case of at least one test subject, the contribution of the second signal is taken into account at least (40).

3. The hearing instrument according to claim 2, in, The corrected sound is generated and output as a broadband audio signal, and Among them, the remaining noise signal that has not been purified by the active blocking suppression is determined as the second signal contribution (40) based on the first input signal (24).

4. The hearing instrument according to claim 1, in, The second electroacoustic input converter (12) of the hearing instrument (1) receives the ambient sound (8) of the hearing instrument (1) and thereby generates a second input signal (28). In addition to the output of the test sound (32), active noise suppression is performed by the electroacoustic output converter (18) of the hearing instrument (1) based on the second input signal (28).

5. The hearing instrument according to claim 4, in, The active noise suppression focuses on a frequency range around at least one test frequency.

6. The hearing instrument according to claim 3, in, The second electroacoustic input converter (12) of the hearing instrument (1) receives the ambient sound (8) of the hearing instrument (1) and thereby generates a second input signal (28). In addition to the output of the test sound (32), active noise suppression is performed by the electroacoustic output converter (18) of the hearing instrument (1) based on the second input signal (28). The active noise suppression is focused on a frequency range around at least one test frequency, and The active blocking suppression is performed broadband by the correction signal.

7. A hearing system having a hearing instrument (1), wherein, The hearing instrument (1) is designed as a hearing aid (2), the hearing aid being configured to correct or at least partially compensate for a user's hearing impairment, wherein the hearing instrument (1) comprises: - A first electroacoustic input converter (10) is configured to receive a sound signal (22) in the ear canal (4) of the test subject when the test subject wears the hearing instrument (1) as prescribed, and thereby generate a first input signal (24). - An electroacoustic output converter (18), configured to generate a test sound (32) and output the test sound to the ear canal (4) of the test subject while the hearing instrument (1) is worn as prescribed, and The hearing system includes a control device (26) configured to record the subject's response to the test sound (32), and to determine the subject's hearing threshold at at least one test frequency based on the subject's response to the test sound (32) and with the aid of the first input signal (24). The control device is further configured to generate a correction signal for active occlusion suppression based on the first input signal (24), and, by means of the electroacoustic output converter (18), generate a correction sound based on the correction signal for compensating for body sounds (42) in the sound signal (22) of the ear canal (4) and output the correction sound to the ear canal (4) of the test subject, which is at least partially closed by the hearing instrument (1).

8. The hearing system according to claim 7, wherein, The hearing aid (1) also includes a second electroacoustic input converter (12) configured to receive ambient sound (8) of the hearing aid (2) and thereby generate a second input signal (28). The control device (26) is further configured to generate an output signal based on the second input signal (28) and feed the output signal to the electroacoustic output converter (18) to convert it into an output sound signal.

9. The hearing system according to claim 8, in, The control device (26) is also configured to perform active noise suppression based on the second input signal (28) by means of the electroacoustic output converter (18), in addition to the output of the test sound (32).

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