EP1309225A1 - Procédé pour déterminer le seuil de couplage dans une prothèse auditive - Google Patents

Procédé pour déterminer le seuil de couplage dans une prothèse auditive Download PDF

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Publication number
EP1309225A1
EP1309225A1 EP02022088A EP02022088A EP1309225A1 EP 1309225 A1 EP1309225 A1 EP 1309225A1 EP 02022088 A EP02022088 A EP 02022088A EP 02022088 A EP02022088 A EP 02022088A EP 1309225 A1 EP1309225 A1 EP 1309225A1
Authority
EP
European Patent Office
Prior art keywords
hearing aid
gain
feedback threshold
feedback
krit
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Granted
Application number
EP02022088A
Other languages
German (de)
English (en)
Other versions
EP1309225B1 (fr
Inventor
Andreas Von Buol
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Sonova Holding AG
Original Assignee
Phonak AG
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by Phonak AG filed Critical Phonak AG
Priority to EP02022088.5A priority Critical patent/EP1309225B1/fr
Priority to DK02022088T priority patent/DK1309225T3/da
Publication of EP1309225A1 publication Critical patent/EP1309225A1/fr
Application granted granted Critical
Publication of EP1309225B1 publication Critical patent/EP1309225B1/fr
Anticipated expiration legal-status Critical
Expired - Lifetime legal-status Critical Current

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    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R25/00—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception
    • H04R25/45—Prevention of acoustic reaction, i.e. acoustic oscillatory feedback
    • H04R25/453—Prevention of acoustic reaction, i.e. acoustic oscillatory feedback electronically
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R25/00—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception
    • H04R25/30—Monitoring or testing of hearing aids, e.g. functioning, settings, battery power
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R25/00—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception
    • H04R25/50—Customised settings for obtaining desired overall acoustical characteristics
    • H04R25/502—Customised settings for obtaining desired overall acoustical characteristics using analog signal processing
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R25/00—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception
    • H04R25/70—Adaptation of deaf aid to hearing loss, e.g. initial electronic fitting

Definitions

  • the present invention relates to a method for Determining a feedback threshold in a hearing aid, an application of the method and a hearing aid.
  • Hearing aids are electronic devices that contain noises recorded in a microphone, in a Signal processing unit processed or amplified and via a loudspeaker, also known as a handset, in the ear canal of the hearing aid wearer are delivered.
  • the amplified or processed noises from the listener can in turn be picked up by the microphone, which repeats the process.
  • it is a closed circle, consisting of the hearing aid, its output signal and the Input signal.
  • the path of sound energy is not limited to acoustic energy, but includes possibly also a mechanical transmission from Output to the input, for example via the housing of the Hearing aid (so-called structure-borne noise).
  • the present invention is therefore the object based on specifying a procedure that meets the above does not have the disadvantages mentioned.
  • the gain in the forward path of a compressive system like there is a hearing aid for compensation represents a hearing loss when closed Circuit, i.e. in "closed-loop" mode, to which Damping settles in the reverse path.
  • FIG. 1 shows a block circuit diagram for a feedback system as is well known.
  • 100 is a processing unit with a Transfer function G and with 200 one Feedback unit with a transfer function K designated.
  • An input signal I becomes one of the two Inputs of an adder 10 applied, the single output of the processing unit 100 fed is.
  • a Output signal O produces that, in addition to the fact that it is guided to the outside via the feedback unit 200 is guided to the second input of the adder unit 10.
  • FIG. 2 shows a block circuit diagram of a hearing device 1, consisting of the processing unit 100 with the Transfer function G based on the representation according to FIG. 1.
  • Upstream of the processing unit 100 downstream are a microphone 20 or a loudspeaker 30, who also works as a listener in the hearing aid industry referred to as.
  • the output signal of the hearing aid 1 or of the receiver 30 is via a feedback unit 200 again, and in addition to the input signal I, the Microphone 20 supplied.
  • an adder 10 upstream which as Input signals both the input signal I and that Output signal of the feedback unit 200.
  • the feedback unit 200 with the transfer function K is the actual equivalent circuit for the input mentioned effects, which lead to signal feedback can.
  • Fig. 3 shows, in a schematic representation, a course for the reinforcement of a compressive system like the one in a hearing aid to compensate for hearing loss Commitment comes. While on the abscissa the level of the Input signal I using a logarithmic Scale and the unit decibel (dB) is plotted on the ordinate uses the gain V, also a logarithmic representation. The history the gain as a function of the input signal level a negative slope on what is just one of the properties of a compressive system.
  • the forward path is a compressive system, as can be seen in FIG. 3 for the gain curve as a function of the input signal level, and if the gain V A for an input signal I A is greater than an assumed, that is to say still unknown, feedback threshold, then it is regulated the gain in the forward path to the attenuation in the reverse path.
  • the feedback threshold V KRIT can be determined by measuring the gain in the forward path, since no feedback will just occur with this measured gain.
  • the gradient of the gain curve V is set to -1 in a first phase in order to ensure a rapid settling to the feedback threshold V KRIT .
  • a flatter slope - ie a slope which is smaller than -1 - is then selected for the gain profile , with the result that a higher accuracy is obtained for the feedback threshold V KRIT .
  • Another embodiment of the invention provides for dividing the hearing range of the human ear into frequency bands, in each of which a feedback threshold V KRIT is determined according to one of the methods described above.
  • the determination of feedback thresholds V KRIT in one or individual as well as in all frequency bands is conceivable.
  • the so-called characteristic frequency bands which are predetermined by the structure of the human ear, are used as frequency bands.
  • a gain curve V is shown in the forward path of a hearing aid 1, the same scaling as in FIG. 3 being used.
  • the gain curve V corresponds to that which is set after the determination of the feedback threshold V KRIT , it being possible to identify four areas I, II, III and IV.
  • the gain curve V in the hearing aid 1 is limited to the maximum gain V KRIT with the aid of a limiting unit present in the hearing aid, with which signal feedback can be avoided.

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  • Health & Medical Sciences (AREA)
  • General Health & Medical Sciences (AREA)
  • Otolaryngology (AREA)
  • Neurosurgery (AREA)
  • Physics & Mathematics (AREA)
  • Engineering & Computer Science (AREA)
  • Acoustics & Sound (AREA)
  • Signal Processing (AREA)
  • Circuit For Audible Band Transducer (AREA)
  • Measurement Of The Respiration, Hearing Ability, Form, And Blood Characteristics Of Living Organisms (AREA)
EP02022088.5A 2002-10-02 2002-10-02 Procédé pour déterminer le seuil de couplage dans une prothèse auditive Expired - Lifetime EP1309225B1 (fr)

Priority Applications (2)

Application Number Priority Date Filing Date Title
EP02022088.5A EP1309225B1 (fr) 2002-10-02 2002-10-02 Procédé pour déterminer le seuil de couplage dans une prothèse auditive
DK02022088T DK1309225T3 (en) 2002-10-02 2002-10-02 Method for determining the feedback threshold in a hearing aid

Applications Claiming Priority (1)

Application Number Priority Date Filing Date Title
EP02022088.5A EP1309225B1 (fr) 2002-10-02 2002-10-02 Procédé pour déterminer le seuil de couplage dans une prothèse auditive

Publications (2)

Publication Number Publication Date
EP1309225A1 true EP1309225A1 (fr) 2003-05-07
EP1309225B1 EP1309225B1 (fr) 2014-04-16

Family

ID=8185483

Family Applications (1)

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EP02022088.5A Expired - Lifetime EP1309225B1 (fr) 2002-10-02 2002-10-02 Procédé pour déterminer le seuil de couplage dans une prothèse auditive

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EP (1) EP1309225B1 (fr)
DK (1) DK1309225T3 (fr)

Cited By (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
EP1655993A1 (fr) * 2003-07-23 2006-05-10 Toa Corporation Dispositif de mesure de la marge de sifflement
WO2006136615A2 (fr) * 2006-08-03 2006-12-28 Phonak Ag Procede de reglage d'un instrument auditif
WO2008000843A2 (fr) * 2007-09-20 2008-01-03 Phonak Ag Procédé de détermination d'un seuil de réaction dans un dispositif d'écoute et dispositif d'écoute
WO2008000842A2 (fr) * 2007-09-20 2008-01-03 Phonak Ag Procédé de détermination d'un seuil de réaction dans un dispositif d'écoute et dispositif d'écoute

Citations (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5991417A (en) * 1995-05-02 1999-11-23 Topholm & Westerman Aps Process for controlling a programmable or program-controlled hearing aid for its in-situ fitting adjustment
US6134329A (en) * 1997-09-05 2000-10-17 House Ear Institute Method of measuring and preventing unstable feedback in hearing aids
US6404895B1 (en) * 1999-02-04 2002-06-11 Siemens Audiologische Technik Gmbh Method for feedback recognition in a hearing aid and a hearing aid operating according to the method

Patent Citations (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5991417A (en) * 1995-05-02 1999-11-23 Topholm & Westerman Aps Process for controlling a programmable or program-controlled hearing aid for its in-situ fitting adjustment
US6134329A (en) * 1997-09-05 2000-10-17 House Ear Institute Method of measuring and preventing unstable feedback in hearing aids
US6404895B1 (en) * 1999-02-04 2002-06-11 Siemens Audiologische Technik Gmbh Method for feedback recognition in a hearing aid and a hearing aid operating according to the method

Cited By (10)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
EP1655993A1 (fr) * 2003-07-23 2006-05-10 Toa Corporation Dispositif de mesure de la marge de sifflement
EP1655993A4 (fr) * 2003-07-23 2009-06-10 Toa Corp Dispositif de mesure de la marge de sifflement
US7596238B2 (en) 2003-07-23 2009-09-29 Toa Corporation Howling margin measuring device
WO2006136615A2 (fr) * 2006-08-03 2006-12-28 Phonak Ag Procede de reglage d'un instrument auditif
WO2006136615A3 (fr) * 2006-08-03 2007-08-02 Phonak Ag Procede de reglage d'un instrument auditif
WO2008000843A2 (fr) * 2007-09-20 2008-01-03 Phonak Ag Procédé de détermination d'un seuil de réaction dans un dispositif d'écoute et dispositif d'écoute
WO2008000842A2 (fr) * 2007-09-20 2008-01-03 Phonak Ag Procédé de détermination d'un seuil de réaction dans un dispositif d'écoute et dispositif d'écoute
WO2008000842A3 (fr) * 2007-09-20 2008-07-31 Phonak Ag Procédé de détermination d'un seuil de réaction dans un dispositif d'écoute et dispositif d'écoute
WO2008000843A3 (fr) * 2007-09-20 2008-07-31 Phonak Ag Procédé de détermination d'un seuil de réaction dans un dispositif d'écoute et dispositif d'écoute
US8582793B2 (en) 2007-09-20 2013-11-12 Phonak Ag Method for determining of feedback threshold in a hearing device and a hearing device

Also Published As

Publication number Publication date
EP1309225B1 (fr) 2014-04-16
DK1309225T3 (en) 2014-05-26

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