Patent Grant
8842862
This application claims priority of the German application No. 10 2005 008 318.8 DE filed Feb. 23, 2005, which is incorporated by reference herein in its entirety.
The present invention relates to a hearing aid device with a measuring device for measuring a feedback path and an operating facility for operating the hearing device by the hearing aid wearer.
Two previous approaches are known for adapting a hearing aid device to an individual feedback situation. With a first approach, the actual feedback path or its characteristics is not known and adaptation is an ongoing process, with the danger of artifacts being very high. According to the second approach, the actual feedback path is first measured by an adapting computer or a programming device. Basic values for the feedback reduction are produced from this measurement and only a minimal ongoing adaptation still needs to be carried out by the hearing device based on these basic values or this fine adaptation is dispensed with altogether. Since a special adapting computer is necessary for measuring the feedback path, the measurement is only carried out by an acoustician and never however by a hearing aid wearer themselves.
U.S. Pat. No. 4,783,818 discloses a method and a device for the adaptive filtering of acoustic feedback signals. In order to identify the acoustic feedback parameters, the configuration of the communication system is changed from a conventional operating mode into a parameter identification mode. In this case, the amplifier is conventionally separated from the microphone and the loudspeaker and is replaced by an identification circuit. Automatic toggling between the two modes takes place as a function of a threshold value. The disadvantage here is that under some circumstances the hearing device fails very frequently during normal hearing operation, namely whenever it switches to identification mode.
Publications EP 0 415 677 B1, EP 0 634 084 B1 and WO 94/09604 also disclose hearing aids with feedback suppression. In this case own noise sources are partially used.
Furthermore, a digital hearing aid is described in the patent application DE 41 28 172 C2, in which an acoustic sensor detects an otoacoustic response of the inner ear of the hearing aid wearer to the measuring tones emitted by an electroacoustic converter. With the aid of the relevant sensor voltage, a microcomputer carries out a comparison and a correction of the transmission function. The measuring and correction process is initiated for instance by activating a key connected to the microcomputer, said key having the function of a switch.
The article Bisgaard, Nikolai; Dyrlund, Ole; “DFS—ein neues digitales System zur Rückkopplungsunterdrückung in Hörgeräten”; (DFS a new digital system for feedback suppression in hearing devices) in Audiological Acoustics 5/91, pages 166, 168 and 173-177 discloses a digital system for feedback suppression in hearing devices. The feedback signal is defined here as a part of the output signal which is fed to the microphone. The feedback either takes place via a ventilation flute or a leakage between the ear canal piece and the auditory canal. If the attenuation on the path of the feedback signal is lower than the amplification of the hearing device, oscillation with a very high acoustic pressure occur in the system. The digital feedback suppression system constantly measures the frequency curve of the feedback path and generates a correction system which is superimposed with the input signal in order to suppress the feedback. This system nevertheless also includes the above-mentioned disadvantages of a constantly adapting system.
As illustrated in exemplary embodiment of
In accordance with the invention, provision is made for the hearing device 10 with a measuring device 12 for the purpose of measuring a feedback path in the hearing device 10 and an operating facility 14 for operation of the hearing device 10 by the wearer, with a measuring cycle for determining at least one characteristic of the feedback path being activated using the operating facility 14.
As further illustrated in the exemplary embodiment of
The operating facility 14 of the hearing device 10 is preferably realized as a remote control. An individual circuit mechanism can thus be omitted for the activation of the measuring phase.
As further illustrated in the exemplary embodiment of
As further illustrated in the exemplary embodiment of
In a special embodiment, the operating facility 14 comprises an acoustic receiver 26 so that the measuring cycle can be activated or influenced by a tone or a sequence of tones. The measuring cycle can thus be activated with the aid of a cell phone for instance, where the cell phone is emitting the corresponding key tones.
The present invention is now described in more detail with reference to the appended drawing which shows a flow diagram for the adjustment of a hearing aid device.
FIG. 1—a flow chart providing the details of the preferred embodiment; and
FIG. 2—a schematic diagram providing the details of an exemplary embodiment of the hearing device.
The exemplary embodiment illustrated in more detail below displays a preferred embodiment of the present invention.
A special control is implemented in a hearing device according to the invention, said control being activated by a predetermined operation of the hearing device for implementing a measuring process. The measured coefficients are written into a non-volatile memory in the hearing device. From this time, the feedback algorithm present in the hearing device remains initialized with the measured parameters even after switching off and a battery change. An effective feedback reduction is thus immediately provided. As the feedback algorithm must no longer be adapted, there are no adapting artifacts.
The advantage of the adjustment methods according to the invention is that complex algorithms such as a feedback compensator can be individually adjusted and initialized even with non-programmable devices (e.g. headsets) or with devices in which the adaptation is not carried out by an acoustician. Adjustment processes are thus more user-friendly.
In detail, the adjustment process is carried out according to the steps shown in the figure. Step S1 symbolically indicates that the hearing equipment or particularly the hearing device is ready to implement a measuring process. In a step S2, the user activates the adjustment process by an intentional operation. For this purpose, an operating instruction or other information provides the hearing aid wearer with the necessary details and explanations for the system. For example, a special key combination or a control element must be activated in a specific chronological sequence. This can be implemented both directly on the hearing device and on any available remote control. As already mentioned, a further alternative consists in providing a non-visible control element e.g. a reed relay or a RFID detector and starting the adjustment process of the hearing device via this device.
After the start of the adjustment process, the hearing device usefully emits a control signal (step S3), which indicates the start of the adjustment to the hearing aid wearer. This control signal can be a tone, but also an optical signal. In a subsequent step S4, the hearing device is put into the measuring state. In this state any specific device settings which may be required are made.
The measuring process is thus started according to step S5, and a measurement signal is emitted. For example, a defined noise is emitted via the earpiece. The returning part of the measurement noise is recorded by an input converter, e.g. a microphone, according to step S6 and is fed to an analysis unit.
In a step S7 a check is carried out as to whether the measurement was terminated successfully. In this case, a check is carried out as to whether a measurement time has expired and/or a fault parameter has fallen below a specific limit. After successful measurement, the measured parameters for the current program are permanently stored in a non-volatile memory in the hearing device according to step S8. The hearing device subsequently returns to the original operating state according to step S9. The feedback system now operates with the newly measured parameters. Hereupon the hearing device according to step S10 emits a control signal to the hearing device wearer about the successful measurement. This control signal can also be of an optical, acoustic or also a tactile nature. The feedback algorithm is now available with the up-dated pre-adjustments and can operate without artifacts, since additional adaptation is not necessary or only necessary to a very minimal extent.
If a renewed adjustment is subsequently necessary on the basis of changes to the position of the otoplastic or the hearing device, this can be easily implemented by repeating the above-mentioned sequence. In principal, the sequence can be repeated as often as necessary.
If the measurement is still not terminated after step S7, one or more abort criteria are monitored according to step S11. These include exceeding a time limit or the presence of a specific fault condition for example. If the abort criteria are not fulfilled, the measurement continues with step S5. If, in contrast, an abort criterion applies, the hearing device returns to the original operating status according to step S12, but no parameters are stored. This means that the feedback system operates again with the former parameters.
With the unsuccessful measurement too, a control signal or an optical, acoustic or tactile nature is also emitted according to step S13 and it is indicated to the user that the adjustment, i.e. the measurement of the feedback path has failed. The end of the complete measurement process is shown in the diagram by step S14.
The described method for adjusting a hearing aid device in terms of a feedback path can be used for any hearing devices but also for non-programmable headsets and the like. In each case, a statistical, currently optimized compensation of the feedback can be achieved by the adjustment. In many cases this removes the need for a dynamic compensation or the dynamic compensation can be undertaken within a very restricted framework.
| Number | Date | Country | Kind |
|---|---|---|---|
| 10 2005 008 318 | Feb 2005 | DE | national |
| Number | Name | Date | Kind |
|---|---|---|---|
| 4471171 | Köpke et al. | Sep 1984 | A |
| 4731850 | Levitt et al. | Mar 1988 | A |
| 4783818 | Graupe et al. | Nov 1988 | A |
| 4955729 | Marx | Sep 1990 | A |
| 5091952 | Williamson et al. | Feb 1992 | A |
| 5991417 | Topholm | Nov 1999 | A |
| 6035050 | Weinfurtner et al. | Mar 2000 | A |
| 6128392 | Leysieffer et al. | Oct 2000 | A |
| 6236731 | Brennan et al. | May 2001 | B1 |
| 6404895 | Weidner | Jun 2002 | B1 |
| 6606391 | Brennan et al. | Aug 2003 | B2 |
| 6842647 | Griffith et al. | Jan 2005 | B1 |
| 7463745 | Miller, III | Dec 2008 | B2 |
| 20010010513 | Rosenberg et al. | Aug 2001 | A1 |
| 20020015506 | Aceti et al. | Feb 2002 | A1 |
| 20020026091 | Leysieffer | Feb 2002 | A1 |
| 20020176594 | Hohmann et al. | Nov 2002 | A1 |
| 20040136557 | Kaulberg | Jul 2004 | A1 |
| 20050078842 | Vonlanthen et al. | Apr 2005 | A1 |
| Number | Date | Country |
|---|---|---|
| 3109049 | Jun 1989 | DE |
| 41 28 172 | Mar 1993 | DE |
| 19904538 | Jul 2000 | DE |
| 100 41 726 | May 2002 | DE |
| 10345173 | Jan 2005 | DE |
| 0 415 677 | Mar 1991 | EP |
| 0581261 | Feb 1994 | EP |
| 0 634 084 | Jan 1995 | EP |
| WO 9409604 | Apr 1994 | WO |
| Entry |
|---|
| Nikolai Bisgaard and Ole Dyrlund, “DFS—ein neues digitales System zur Rückkopplungsunterdrückung in Hörgeräten”, Audiologische Akustik May 1991, pp. 166, 168, 173-177. |
| Sandlin Robert E.; “Understanding Digitally Programmable Hearing Aids”; Allyn and Bacon A Division of Simon & Schuster Inc.; pp. 305-309; ISBN: 0-205-14845-X; 1993. |
| Number | Date | Country | |
|---|---|---|---|
| 20060188106 A1 | Aug 2006 | US |
