Abstract: A compression method for a hearing aid used by a hearing-impaired person is provided. The hearing aid comprises n frequency channels, each characterized by a linear gain and lower compression thresholds. The method determines compression parameters for each channel, including compression ratios, upper compression thresholds, and corresponding gains. For each channel, the upper compression threshold is set to the hearing-impaired person's annoyance threshold, adjusted by a parameter to convert from dB HL to dB SPL. The gain at the upper compression threshold is set to 0 dB. The compression ratio for each channel is calculated based on the linear gain, lower compression threshold, and annoyance threshold. The method allows for personalized compression settings tailored to the individual's hearing characteristics and comfort levels.

Abstract: Application of a hearing aid alters the distribution of sound pressure at the tympanic membrane in the ear. Measurements of sound pressure of a free ear and with a hearing aid are performed to evaluate the alteration produced and the in situ frequency response of the hearing aid itself. The following steps are performed: calculating the REUG; calculating a magnitude; calculating one of two components and designing of the filter for the compensation for such component; calculating the REAG; calculating one of two components. The sum of two components is the Insertion Gain; designing the compensating filter of the POST component of the Insertion Gain; testing and verifying, on the subject wearing the hearing aid, the compensating filter of REIG, and possible refinement procedure to correct the compensation of the Insertion Gain obtained in the previous step; tuning the hearing aid for deafness taking into account the compensating filter.

Abstract: The application of a hearing aid alters the distribution of sound pressure at the tympanic membrane in the ear. Measurements of sound pressure of a free ear and with a hearing aid are performed in order to evaluate the alteration produced and the in situ frequency response of the hearing aid itself. The following steps are performed: (A) calculating the REUG (Real Ear Unaided Gain), that is, a comparison between a sound pressure measurement performed with a microphone positioned in the ear near the tympanic membrane and a sound pressure measurement performed with a reference microphone positioned on the face outside the ear; (B) calculating a magnitude (the so-called ALMIC), i.e.