01285776 PDF BRITISH STANDARD BS EN 60118 2 1996 BS 6083 2 1996 Implementing Amendment No 1, not published separately IEC 118 2 1983 (including Amendments 1 1993 and 2 1997 to IEC 118 2 1983) Hearing[.]
BRITISH STANDARD Hearing aids — Part 2: Methods for measurement of electroacoustical characteristics of hearing aids with automatic gain control circuits The European Standard EN 60118-2:1995 with the inclusion of amendment A2:1997 has the status of a British Standard ICS 17.140.50 BS EN 60118-2:1996 BS 6083-2: 1996 Implementing Amendment No 1, not published separately IEC 118-2: 1983 (including Amendments 1:1993 and 2:1997 to IEC 118-2:1983) BS EN 60118-2:1996 Committees responsible for this British Standard The preparation of this British Standard was entrusted to Technical Committee EPL/29, Electroacoustics, upon which the following bodies were represented: British Association of Otolaryngologists British Hearing Aid Industry Association British Medical Association British Society of Audiology British Telecommunications plc Confederation of British Industry Department of Health Department of Trade and Industry (National Physical Laboratory) Health and Safety Executive Institute of Acoustics Institute of Sound and Vibration Research Institution of Electrical Engineers Medical Research Council Ministry of Defence Royal Aeronautical Society Royal National Institute for Deaf people Society of Environmental Engineers University of Exeter This British Standard, having been prepared under the direction of the Electrotechnical Sector Board, was published under the authority of the Standards Board and comes into effect on 15 September 1996 © BSI 06-1999 The following BSI references relate to the work on this standard: Committee reference EPL/29 Draft for comment 84/20636 DC ISBN 580 26160 Amendments issued since publication Amd No Date Comments 9753 January 1998 Indicated by a sideline in the margin BS EN 60118-2:1996 Contents Committees responsible National foreword Foreword Text of EN 60118-2 List of references © BSI 06-1999 Page Inside front cover ii Inside back cover i BS EN 60118-2:1996 National foreword This British Standard has been prepared by Technical Committee EPL/29 and is the English language version of EN 60118-2:1996 Hearing aids Part 2: Hearing aids with automatic gain control circuits, including amendment A2:1997 published by the European Committee for Electrotechnical Standardization (CENELEC) It is identical with IEC 118-2, second edition 1983, together with its Amendments 1:1993 and 2:1997, and supersedes BS 6083-2:1984, which is withdrawn From January 1997, all IEC publications have the number 60000 added to the old number For instance, IEC 27-1 has been renumbered as IEC 60027-1 For a period of time during the change over from one numbering system to the other, publications may contain identifiers from both systems Cross-references Publication referred to Corresponding British Standard EN 60118-0:1993 (IEC 118-0:1983) BS EN 60118 Hearing aids BS EN 60118-0:1993 Measurement of electroacoustical characteristics BS 6083 Hearing aids Part 1:1984 Method for measurement of characteristics of hearing aids with induction pick-up coil input Part 6:1985 Specification for characteristics of electrical input circuits for hearing aids BS 6397:1983 Specification for scales and sizes for plotting frequency characteristics and polar diagrams BS 6840 Sound system equipment Part 8:1988 Methods for specifying and measuring the characteristics of automatic gain control devices HD 450.1 S1:1984a (IEC 118-1:1983) HD 450.6 S1:1986 (IEC 118-6:1984) IEC 263:1982 IEC 268-8:1973 a Superseded by EN 60118-1:1995 (IEC 118-1:1995), for which the corresponding British Standard is BS EN 60118-1:1995 A British Standard does not purport to include all the necessary provisions of a contract Users of British Standards are responsible for their correct application Compliance with a British Standard does not of itself confer immunity from legal obligations Summary of pages This document comprises a front cover, an inside front cover, pages i and ii, the EN title page, pages to 18, an inside back cover and a back cover This standard has been updated (see copyright date) and may have had amendments incorporated This will be indicated in the amendment table on the inside front cover ii © BSI 06-1999 EUROPEAN STANDARD EN 60118-2 NORME EUROPÉENNE November 1995 EUROPÄISCHE NORM July 1997 + A2 UDC 534.773.2:621.395.92:621.395.665:620.1:621.317.6 Supersedes HD 450.2 S1:1984 Descriptors: Electromedical device, hearing aid, automatic gain control, definitions, measurement procedures English version Hearing aids Part 2: Hearing aids with automatic gain control circuits (includes amendment A2:1997) (IEC 118-2:1983 + A1:1993 + A2:1997) Appareils de correction auditive Partie 2: Appareils de correction auditive comportant des commandes automatiques de gain (inclut l’amendement A2:1997) (CEI 118-2:1983 + A1:1993 + A2:1997) Hörgeräte Teil 2: Hörgeräte mit automatischer Verstärkungsregelung (Enthält Änderung A2:1997) (IEC 118-2:1983 + A1:1993 + A2:1997) This European Standard was approved by CENELEC on 1994-03-08; amendment A2 was approved by CENELEC on 1997-07-01 CENELEC members are bound to comply with the CEN/CENELEC Internal Regulations which stipulate the conditions for giving this European Standard the status of a national standard without any alteration Up-to-date lists and bibliographical references concerning such national standards may be obtained on application to the Central Secretariat or to any CENELEC member This European Standard exists in three official versions (English, French, German) A version in any other language made by translation under the responsibility of a CENELEC member into its own language and notified to the Central Secretariat has the same status as the official versions CENELEC members are the national electrotechnical committees of Austria, Belgium, Denmark, Finland, France, Germany, Greece, Iceland, Ireland, Italy, Luxembourg, Netherlands, Norway, Portugal, Spain, Sweden, Switzerland and United Kingdom CENELEC European Committee for Electrotechnical Standardization Comité Européen de Normalisation Electrotechnique Europäisches Komitee für Elektrotechnische Normung Central Secretariat: rue de Stassart 35, B-1050 Brussels ©1995 Copyright reserved to CENELEC members Ref No EN 60118-2:1995 + A2:1997 E EN 60118-2:1995 Foreword Foreword to amendment A2 The text of the International Standard IEC 118-2:1983, prepared by IEC TC 29, Electroacoustics, was approved by CENELEC as HD 450.2 S1 on 1984-09-11 This Harmonization Document was submitted to the formal vote for conversion into a European Standard and was approved by CENELEC as EN 60118-2 on 1994-03-08 The text of amendment 1:1993 to the International Standard IEC 118-2:1983 was submitted to the formal vote and was approved by CENELEC as amendment A1 to EN 60118-2 on 1994-03-08 without any modification Having first withheld the publication of EN 60118-2 and its A1, the Technical Board of CENELEC has allowed on 1995-09-20 the circulation of the definitive version of EN 60118-2 with incorporation of its amendment A1 The following dates were fixed: The text of document 29/350/FDIS, future amendment to IEC 60118-2:1983, prepared by IEC TC 29, Electroacoustics, was submitted to the IEC-CENELEC parallel vote and was approved by CENELEC as amendment A2 to EN 60118-2:1995 on 1997-07-01 The following dates were fixed: — latest date by which the EN has to be implemented at national level by publication of an identical national standard or by endorsement (dop) 1996-07-01 — latest date by which the national standards conflicting with the European Standard have to be withdrawn — latest date by which the amendment has to be implemented at national level by publication of an identical national standard or by endorsement (dop) 1998-04-01 — latest date by which the national standards conflicting with the amendment have to be withdrawn (dow) 1998-04-01 Annexes designated “normative” are part of the body of the standard Annexes designated “informative” are given for information only In this standard, Annex ZA is normative and Annex B and Annex C are informative Annex ZA has been added by CENELEC (dow) 1996-07-01 Annexes designated “normative” are part of the body of the standard In this standard, Annex ZA is normative Annex ZA has been added by CENELEC © BSI 06-1999 EN 60118-2:1995 Contents Foreword Scope Object Conditions Explanation of terms 4.1 Automatic gain control (AGC) 4.2 Steady-state input/output graph 4.3 Lower AGC limit or AGC threshold 4.4 Compression ratio (between specified input sound pressure level values) 4.5 Dynamic output characteristics 4.6 Attack time 4.7 Recovery time 4.8 AGC activated frequency response 4.9 Operating frequency range of the AGC 4.10 Overall root-mean-square sound pressure level (overall r.m.s SPL) 4.11 One-third-octave band level 4.12 Auto-spectrum (power spectrum) 4.13 Cross-spectrum (GAB) 4.14 Coherence 4.15 Synchronous analysis Steady-state input/output graph 5.1 Graph showing the relation between input sound pressure level and output sound pressure level 5.2 Methods of measurement Dynamic output characteristics 6.1 Characteristics to be measured 6.2 Methods of measurement Non-linear distortion 7.1 Transients 7.2 Harmonic distortion 7.3 Intermodulation distortion Effect on steady-state and dynamic performance with respect to variation in battery or supply voltage AGC activated frequency response of hearing aids with a single channel AGC circuit in operation using pure tone signals 10 Frequency response of hearing aids with AGC circuits in operation using steady-state broad-band input signals © BSI 06-1999 Page Page 5 5 5 5 6 6 6 6 6 Annex A (informative) Examples of measuring Annex B (informative) Smoothed data presentation Annex C (informative) Bibliography Annex ZA (normative) Normative references to international publications with their corresponding European publications Figure — Example of steady-state input/output graph Figure — Dynamic output characteristics of an AGC circuit Figure — Example of measuring system according to the comparison method employing two tracking bandpass filters Figure — Example of a measuring system employing digitally controlled input SPL and a band rejection filter Figure — Nominal values with upper and lower limits (± dB) for one-third-octave band levels of the noise input signal at the test point Table — Nominal values for the one-third-octave band levels of the noise input signal at the test point 14 16 16 17 12 13 14 15 15 11 7 7 7 7 8 blank EN 60118-2:1995 Scope Conditions 1.1 This standard applies to the hearing aids of any type with automatic gain control (AGC) circuits This standard gives uniform methods for specifying dynamic and static performance characteristics of hearing aids with AGC circuits together with the relevant methods of measurement for these characteristics This standard is confined to a description of the different characteristics and the relevant methods of measurement It does not attempt to specify performance requirements 1.2 This standard includes devices which have compression and/or limiting properties with respect to the envelope of the input signal Devices which control the long-term average output level are also included a) AGC is employed to obtain compression, or the reduction of the dynamic range of the sound at the output, with the object of preserving the integrity of the input waveform b) AGC circuits instead of clipping devices are often used for limiting purposes A limiting effect occurs when the input/output characteristic flattens out at higher input levels Limiting action is mainly used as a means of preventing excessive output sound from the hearing aid from reaching the listener’s ear 1.3 This standard does not include: a) Expanders b) Clipping devices, which cut off the signal peaks above a certain level; such devices differ basically from AGC circuits, which, in a steady state, tend to preserve the waveform of the input signal 3.1 General conditions NOTE An AGC circuit with very short recovery time may cause considerable distortion, especially in the low-frequency range This should be given special attention Object 2.1 The purpose of this standard is to facilitate measurements of certain characteristics of hearing aids with AGC circuits that are not described elsewhere in IEC Publication 118-0: Hearing Aids, Part 0: Measurement of Electroacoustical Characteristics, and which are considered necessary for a physical description of the function of the automatic gain control 2.2 In general, the methods of measurement recommended are those which are considered to be the most directly related to the characteristics This does not exclude the use of other stated methods which will give equivalent results © BSI 06-1999 Reference is made to IEC Publication 268-8: Sound System Equipment, Part 8: Automatic Gain Control Devices Measurements other than those described herein and that are stated in IEC Publication 118-0 can be performed in accordance with that publication, but with AGC operating, provided the operating conditions are stated 3.2 Throughout this standard, all sound pressure levels are referred to 20 4Pa Explanation of terms 4.1 Automatic gain control (AGC) A means in a hearing aid by which the gain is automatically controlled as a function of the magnitude of the envelope of the input signal or other signal parameter NOTE Throughout this standard, reference is made to the use of acoustic inputs However, where appropriate, additional measurements may be made with an electromagnetically induced input 4.2 Steady-state input/output graph The graph illustrating the output sound pressure level as a function of the input sound pressure level for a specified frequency, both expressed in decibels on identical linear scales (Figure 1, page 12) 4.3 Lower AGC limit or AGC threshold The input sound pressure level which, when applied to the hearing aid, gives a reduction in the gain of ± 0.5 dB with respect to the gain in the linear mode (Figure 1) 4.4 Compression ratio (between specified input sound pressure level values) Under steady-state conditions, the ratio of an input sound pressure level difference to the corresponding output sound pressure level difference, both expressed in decibels (Figure 1) 4.5 Dynamic output characteristics The output sound pressure envelope shown as a function of time when an input sound signal of a predetermined frequency and level is modulated by a square envelope pulse with a predetermined pulse amplitude (Figure 2, page 13) EN 60118-2:1995 4.6 Attack time 4.11 One-third-octave band level The time interval between the moment when the input signal level is increased abruptly by a stated number of decibels and the moment when the output sound pressure level from the hearing aid with the AGC circuit stabilizes at the elevated steady-state level within ± dB (Figure 2, page 13) The level of that part of the signal contained within a band one-third-octave wide as defined in IEC 61260 4.6.1 Attack time for the normal dynamic range of speech The attack time, as defined in Sub-clause 4.6, when the initial input sound pressure level is 55 dB and the increase in input sound pressure level is 25 dB 4.12 Auto-spectrum (power spectrum) The power spectrum of either the input signal (GAA) to or the output signal (GBB) from a hearing aid in the frequency domain It is computed by multiplying the Fourier transform of the signal by the complex conjugate of the Fourier transform of the same signal 4.13 Cross-spectrum (GAB) The attack time, as defined in Sub-clause 4.6, when the initial input sound pressure level is 60 dB and the increase in input sound pressure level is 40 dB The degree to which the same signal frequencies are mutually present in the input and output of a hearing aid It is computed by multiplying the complex conjugate of the Fourier transform of the input signal to the hearing aid by the Fourier transform of the output signal from the hearing aid 4.7 Recovery time 4.14 Coherence The time interval between the moment when the stated input signal level is reduced abruptly to a level a stated number of decibels lower after the AGC amplifier has reached the steady-state output under elevated input signal conditions, and the moment when the output sound pressure level from the hearing aid stabilizes again at the lower steady-state level within ± dB (Figure 2) A number ranging from to showing to what degree the output from a hearing aid is correlated to the input Coherence for a random noise test signal is reduced by non-linearity and by system noise The coherence is calculated from the auto- and cross-spectrum averages as follows: 4.6.2 High level attack time 4.7.1 Recovery time for the normal dynamic range of speech The recovery time, as defined in Sub-clause 4.7, when the initial input sound pressure level is 80 dB and the decrease in input sound pressure level is 25 dB 4.7.2 High level recovery time The recovery time, as defined in Sub-clause 4.7, when the initial sound pressure level is 100 dB and the decrease in input sound pressure level is 40 dB 4.8 AGC activated frequency response The frequency response when the AGC circuit is activated by a specified AGC activating signal 4.9 Operating frequency range of the AGC For a specified input sound pressure level, the frequency range in which the AGC threshold is reached or exceeded 4.10 Overall root-mean-square sound pressure level (overall r.m.s SPL) The root-mean-square sound pressure level with measurement bandwidth equal to the frequency range covered by the one-third-octave frequency bands (see IEC 61260) from 200 Hz to 000 Hz Coherence = 4.15 Synchronous analysis Analysis which is synchronized with the period of the input signal, for example with the periodicity of pseudo-random noise Steady-state input/output graph 5.1 Graph showing the relation between input sound pressure level and output sound pressure level The graph shall have the input sound pressure level as abscissa and the output sound pressure level as ordinate, both expressed in decibels on linear scales having divisions of identical size NOTE In the input/output graph of an AGC device, different portions may be distinguished: — Below the lower AGC limit the slope is essentially 45° (linear amplifier mode) — Above this limit, the graph curves over in a portion having a decreasing slope, often followed by another portion having a nearly flat slope (AGC mode) — At very high input levels, a flat or sloping portion may be followed by a portion with a steeper slope, generally due to saturation of the AGC circuit © BSI 06-1999 EN 60118-2:1995 5.2 Methods of measurement The gain control is adjusted to its maximum setting Any adjustable gain control after the AGC-loop shall be adjusted in such a manner that overload of the hearing aid is avoided An input sound signal of frequency 600 Hz or 500 Hz when appropriate, is applied at the lowest possible level consistent with an adequate signal-to-noise ratio of preferably more than 10 dB The input sound pressure level is increased up to 100 dB in sufficiently small steps, and the corresponding output sound pressure level is measured after steady-state conditions have been reached The graph is plotted with the input sound pressure level as abscissa and the output level as ordinate, as described in Sub-clause 5.1 Where separate adjustable controls exist, such as AGC, gain or output controls, which will influence the shape and other characteristics of the steady-state input/output graph, it is recommended that input/output graphs be plotted, when useful, for various additional stated setting of such controls NOTE The output signal should be monitored on a device such as an oscilloscope, the time constants of which are considerably shorter than those being measured NOTE When very short response times are to be measured, the response time of the source shall be reported NOTE For half-wave rectifying AGC circuits, the attack time is dependent upon the polarity of the first half wave of the test signal after the onset of the modulating square wave envelope Depending upon the polarity, a shorter or longer attack time will occur This is best demonstrated in the case of an instantaneous rise in the amplitude occurring at a zero crossing of the test signal 6.2.2 Dynamic output characteristics for high level input At the maximum setting of the gain control an input signal of 600 Hz or 500 Hz when appropriate with a sound pressure level of 60 dB is applied Any adjustable gain control after the AGC loop shall be adjusted in such a manner that overload of the hearing aid is avoided This signal is modulated by a square envelope pulse raising the input level by 40 dB The pulse length shall be at least five times the attack time observed If more than a single pulse is applied, the interval between two pulses should be at least five times the longest recovery time being measured Dynamic output characteristics NOTE 6.1 Characteristics to be measured Non-linear distortion The purpose of this test is to determine the dynamic characteristics of the AGC circuit, particularly attack and recovery times It should be emphasized that all these characteristics will depend on test frequency as well as on such factors as signal level, control settings and battery voltage 7.1 Transients 6.2 Methods of measurement 6.2.1 Dynamic output characteristics for speech levels At the maximum setting of the gain control an input signal of 600 Hz or 500 Hz when appropriate with a sound pressure level of 55 dB is applied Any adjustable gain control after the AGC loop shall be adjusted in such a manner that overload of the hearing aid is avoided This signal is modulated by a square envelope pulse raising the input level by 25 dB The pulse length shall be at least five times longer than the attack time being measured If more than a single pulse is applied, the interval between two pulses shall be at least five times the longest recovery time being measured NOTE This test may be carried out at various control settings as stated in Sub-clause 5.2 NOTE If lower gain control settings are applied, the method of obtaining these settings shall be clearly specified NOTE The loudspeaker employed for the measurement of dynamic output characteristics as in Clause must be sufficiently free of transient distortion so that test results are not appreciably affected © BSI 06-1999 See Notes to of Sub-clause 6.2.1 The signal may be distorted during the attack time and recovery time by transients as well as by unwanted low-frequency modulation caused by instabilities The effect of these phenomena on the listener is not sufficiently understood to allow a recommendation for measuring transient distortions to be made 7.2 Harmonic distortion 7.2.1 Characteristics to be specified The purpose of this test is to determine the harmonic distortion as a function of the input sound pressure level after steady-state conditions have been reached 7.2.2 Methods of measurement Harmonic distorsion is measured in accordance with the test procedure described in IEC Publication 118-0 NOTE This test may be carried out at various control settings as mentioned under Sub-clause 5.2 7.3 Intermodulation distortion Intermodulation distortion is measured in accordance with the test procedure, described in IEC Publication 118-0 EN 60118-2:1995 Effect on steady-state and dynamic performance with respect to variation in battery or supply voltage In accordance with IEC Publication 118-0, Sub-clause 7.8, it is recommended that the change in the following performance parameters be tested with respect to variation in battery or supply voltage: steady-state input/output graphs as mentioned in Clause 5, dynamic-output characteristics, attack and recovery times as mentioned under Clause 6, and non-linear distortion as mentioned in Clause AGC activated frequency response of hearing aids with a single channel AGC circuit in operation using pure tone signals 9.1 Introduction 9.1.1 Measurement below the AGC threshold It is important to know the frequency response of hearing aids when the automatic gain control is active Measurements carried out in accordance with 7.4 of IEC 118-0 can be employed, provided that the input signal levels at all measuring frequencies are below the AGC thresholds 9.1.2 Measurement above the AGC threshold When measurements are taken above the AGC threshold with moderately slow scanning speeds and the attack and decay times in current use, they can be considered at any frequency as steady-state measurements From the set of comprehensive frequency response curves obtained using this method of measurement, a steady-state input/output graph can be constructed for any frequency 9.2 General conditions Throughout this standard all sound pressure levels specified refer to 20 4Pa When appropriate, sound pressure level will be abbreviated SPL NOTE Throughout the standard, reference is made to the use of acoustic input However, when appropriate, additional measurements may be made with electromagnetic or electric inputs in accordance with IEC 118-1 and IEC 118-6 Test results obtained by the substitution method (see 4.2 of IEC 118-0) shall be considered basic 9.3 Test equipment The test equipment shall comply with clause of IEC 118-0 Figure and Figure give schematic illustrations of the measuring equipment A tracking bandpass filter, centred at a centre frequency fc, shall be inserted in the measuring system The dB bandwidth shall not be greater than 10 % of the centre frequency, and the 20 dB bandwidth shall not be greater than 20 % of the centre frequency For frequencies higher that fc or less than fc/4,fc being the centre frequency, the attenuation shall be greater than 40 dB For frequencies higher than fc or lower than fc/8, the attenuation shall be equal to or greater than 60 dB NOTE In certain cases it may be necessary to use a filter with an attenuation higher than 40 dB or 60 dB, respectively, in order not to increase the frequency range relative to the activating frequency where no reliable results can be obtained When automatic swept frequency recording using a compressor system to maintain a constant input sound pressure level is employed, a second tracking bandpass filter complying with the specifications given above shall be inserted in the feed-back loop NOTE When synchronizing the tracking bandpass filter to the swept frequency, consideration should be given to the influence of the transmission time from the sound source to test point, the bandwidth of the filter and the scanning speed Alternatively, a band rejecting filter tuned to the AGC activating signal frequency and having an attenuation equal to or greater than 50 dB at the centre frequency (fc) may be employed For frequencies greater than 1,05 fc or less than fc/1,05, the attenuation shall be less than dB 9.4 Test conditions The AGC control should be set for maximum AGC effect (i.e lowest AGC threshold) Otherwise the test conditions shall comply with the specifications stated in clause of IEC 118-0, as applicable, The settings shall be stated 9.5 Measurement Data should be quoted for that part of the frequency range between 200 Hz and 000 Hz over which the output of the hearing aid falls by at least 10 dB when the signal sources are switched off 9.5.1 Determination of the operating range of the AGC Test procedure a) Adjust the gain control to full on and set other controls in accordance with 9.4 of this standard b) Apply a sinusoidal input signal and vary its frequency, keeping the input SPL constant at 50 dB, 60 dB, 70 dB, 80 dB and 90 dB or until the AGC threshold has been exceeded c) Plot the output SPL versus frequency at a constant input SPL for each of the input sound pressure levels © BSI 06-1999 EN 60118-2:1995 d) From these curves, determine the approximate frequency range over which the AGC is operating and determine the approximate value of the AGC threshold in this frequency range See 4.3 of this standard e) A precise determination of the AGC operation can be made with the use of input/output curves at specific frequencies 9.5.2 Measurement of the AGC activated frequency response Test procedure a) Adjust controls as stated in 9.4 b) Apply a sinusoidal input signal and adjust its frequency to a value within the frequency range determined in 9.5.1 d) or e) and state it NOTE To avoid problems arising from higher harmonics, the frequency of the activating signal should preferably be chosen at the higher end of this frequency range c) Adjust the level of this signal to 10 dB above the approximate AGC threshold as determined in 9.5.1 d) or e) d) Apply a second sinusoidal input signal keeping its level constant at 20 dB below the level of the activating signal Vary the frequency over the range 200 Hz to 000 Hz and measure the output SPL using a tracking bandpass filter or a band rejection filter tuned to the frequency of the activating signal e) Plot the output SPL versus frequency NOTE Since no valid results can be gained in the vicinity of the frequency of the activating signal, it is recommended that the plotting of the frequency response be interrupted in an appropriate frequency range (e.g ± 20 %) relative to the activating frequency 9.6 Frequency response recording chart All curves showing variation of a parameter with frequency shall be plotted on a grid with a linear decibel ordinate scale and a logarithmic frequency abscissa scale with the length for a 10 : frequency ratio on the abscissa equal to the length of 50 dB on the ordinate, in accordance with IEC 263 © BSI 06-1999 10 Frequency response of hearing aids with AGC circuits in operation using steady-state broad-band input signals 10.1 General The frequency response of electroacoustic systems, including hearing aids, has traditionally been obtained using a swept pure tone input signal whose level is held constant while the output of the system is measured over the frequency range of interest However, other methods have evolved for obtaining frequency responses of electronic systems as a result of the recent proliferation of digital spectrum analysers that utilise steady-state broad-band noise as one of their test signals A time-stationary, steady-state broad-band noise which is more typical of the complex input signals that hearing aids are required to process in non-laboratory real-world environments, may be a more suitable test signal for depicting performance, particularly for those hearing aids with level-dependent gain circuitry For those hearing aids that not have automatic gain control (AGC) or other forms of adaptive signal processing circuitry, or for hearing aids having such circuitry but tested with input levels below their activation point, the same frequency response should result, whether a swept pure tone or broad-band noise is used, as long as the hearing aid is operating linearly, and the signal-to-noise ratio is adequate The method used shall be stated IEC 60118-0 describes methods of measurements for the evaluation of the electroacoustical characteristics of hearing aids employing swept pure tone signals When testing hearing aids with AGC or other non-linear circuits in action, the response at a given frequency will depend on the way the measuring signal activates the non-linear element at the same frequency In IEC 60118-2, Amendment 1, a method of measurement to characterize AGC hearing aids is described This method uses an AGC-activating pure tone signal with a fixed frequency, and a swept pure tone signal with a 20 dB lower level for obtaining the frequency response Using this method, the effect of the non-linear element is controlled by the AGC-activating signal alone, and is not influenced by the measuring signal This clause describes a method for the measurement of hearing aid frequency response using a steady-state broad-band input signal and employing single or dual-channel spectrum analysis to measure the frequency response EN 60118-2:1995 The spectral characteristics of the specified test signal have been chosen to be in conformance with the American standard ANSI S3.42 [1]1) This specification has been used for many years to test hearing aids, and has been shown to represent a reasonable compromise, ensuring sufficient signal-to-noise ratio in the high frequency area, and also to some extent representing the spectral characteristics of speech Using this method, the non-linear element will respond to the broad-band signal, with contributions from many frequencies, and not from an individual frequency component as when using the methods in IEC 60118-0 or IEC 60118-2, Amendment Care should be exercised interpreting measurements made with the steady-state noise signal, because hearing aids whose frequency response is changed by the dynamic characteristics of the input signal cannot be fully characterized by this almost time-invariant signal An example is hearing aids that have adaptive AGC time constants based on the temporal pattern of the input signal This clause is basically in keeping with ANSI S3.42 [1] with regard to the test signal and the frequency response measuring procedures Important exceptions are the reference test gain control position, which in this international standard is defined in accordance with IEC 60118-0, Amendment 1, and the use of the IEC 60711 ear simulator The coherence function in connection with dual-channel measurements is used to validate the frequency response measurements 10.3 Test conditions 10.2 Test enclosure The amplitude of the one-third-octave band levels of the noise input signal measured at the test point shall meet the nominal values indicated in Table with a tolerance of ± dB Above kHz and below 200 Hz, the one-third-octave band levels shall not increase above the upper tolerance limit at those frequencies These nominal values with upper and lower tolerance limits are shown in Figure The test enclosure shall fulfil the requirements specified in IEC 60118-0 The residual noise at the test point shall give a signal-to-noise ratio in each one-third-octave band equal to or greater than 10 dB, with a noise input signal as specified in 10.3.1.2 with an overall r.m.s level of 50 dB 1) All sound pressure levels are referred to 20 µPa and abbreviated SPL Reference is made to IEC 60118-0 and IEC 60711 The comparison method (see 4.3 of IEC 60118-0) shall be applied when using cross-spectrum measurements, and the substitution method (see 4.2 of IEC 60118-0) when using auto-spectrum and swept filter measurements 10.3.1 Noise input signal 10.3.1.1 Noise type and peak levels Random noise or pseudo-random noise shall be used as input signals The type of noise and its period shall be stated The noise signal shall have a normal probability distribution that is truncated so that the maximum peak signal level is 12 dB ± dB above the r.m.s signal level The noise shall be continuous, that is its level should be constant for a sufficiently long time before each analysis period to allow any adaptive signal processing elements of the hearing aid to stabilize NOTE Many adaptive hearing aids use fast-acting detectors to develop their signal-processing control signals The amount of signal processing action, which often regulates the amount of gain the hearing aid provides (e.g AGC aids), therefore may be dependent on the probability distribution of the input signal Because of the relatively large peak levels of the broad-band noise input signal, as compared to that for the pure tones traditionally used for testing hearing aids, it is expected that there may be more variability in the measurements with broad band noise inputs having varying peak levels than with pure tone input signals NOTE Pseudo-random noise having the same period as the analysis time record is an acceptable input signal However, the results may differ from those obtained with random noise in some cases 10.3.1.2 Spectrum of noise input signal Figures in square brackets indicate the references listed in Annex C 10 © BSI 06-1999 EN 60118-2:1995 800 – 10,5 000 – 10,5 250 – 10,5 600 – 11,0 000 – 11,5 Dual-channel analysis using the cross-spectrum method is preferred Single-channel analysis that uses the auto-spectrum method will give almost equivalent results if: a) the sound field has been equalized in accordance with 10.3.1.2; b) the hearing aid under test is operating in a steady-state mode; c) the signal-to-noise ratio is sufficient (see 10.2) Otherwise, results from the two methods may differ The frequency range of analysis shall include the range covered by the one-third-octaves from 200 Hz to 000 Hz The test method (auto-spectrum or cross-spectrum with FFT (Fast Fourier Transform), digital filter or swept tracking filter), averaging time, analysis bandwidth, and total frequency range of analysis shall be stated 500 – 12,5 10.5 Measurements of frequency responses 150 – 13,0 000 – 14,0 10.5.1 Comprehensive frequency responses and basic frequency response (acoustic gain) 000 – 15,0 300 – 16,0 000 – 17,0 Table — Nominal values for the one-third-octave band levels of the noise input signal at the test point One-third-octave centre frequency Nominal value Hz dB 200 – 17,0 250 – 14,5 315 – 13,0 400 – 12,0 500 – 11,0 630 – 10,5 NOTE level The levels are expressed relative to the overall r.m.s NOTE The nominal mid and high frequency shaping of the noise signal is equivalent to that of a single-pole low-pass Butterworth filter (e.g., single resistor-capacitor filter section) having a cut-off frequency at 900 Hz The dB per octave slope shall continue to at least kHz The nominal low frequency shaping is equivalent to a two-pole high-pass Butterworth filter with a cut-off frequency at 200 Hz The filter characteristic for the combination of these two filters can be calculated from the formula: NOTE The input spectrum level is subtracted out in the measurement and calculation of the frequency response Control of the input spectrum is required, since the AGC may be frequency dependent 10.4 Test equipment Either single- or dual-channel spectrum analysis equipment may be used An analyzer that sweeps a tracking filter across the frequency range is also acceptable For any type of analyzer, the filter bandwidth shall be equal to or less than one-third-octave of the centre frequency The effective filter analysis bandwidth and smoothing, including windowing, shall be stated © BSI 06-1999 Adjust the hearing aid gain control to the reference test gain control position and set other controls to required positions Produce a family of frequency response curves (acoustic gain) using one of the methods described in 10.5.1.1, 10.5.1.2 or 10.5.1.3, and by adjusting the overall r.m.s noise input SPL in 10 dB steps to cover the desired range above and below 60 dB.The preferred input levels are 50 dB, 60 dB, 70 dB, 80 dB and 90 dB Ensure that the hearing aid is operating in a steady-state mode for each input level If possible, overlay all of the curves on one chart, with each curve labelled with the corresponding input level Additional input levels may be used All input levels shall be stated The basic frequency response is the response obtained with an overall input r.m.s SPL of 60 dB NOTE If random noise is used as the test signal, the number of averaged spectra necessary to obtain a desired measuring accuracy can be determined using the methods described in, for example, chapter 11 of [2] 10.5.1.1 Cross-spectrum method The input and output data are determined simultaneously in a complex format when using this method Calculate the frequency response by dividing the magnitude of the cross-spectrum average, GAB, by the input auto-spectrum average, GAA The result of the calculation for each frequency shall be converted to decibels by taking the log to the base ten and multiplying it by 20 The coherence function may be used to validate the frequency response If referred to, it should be plotted as a function of frequency 11 EN 60118-2:1995 NOTE If the coherence = 1, the hearing aid under test is prefectly linear and noise free If the coherence = 0, there is no linear relationship at all between the input to the hearing aid and the output from the hearing aid A low value of coherence can be caused by noise and non-linearities including system time variations If, for example, the coherence function falls below 0,5 at a given frequency, the contribution from noise and non-linearities is higher than the linear signal from the hearing aid at that frequency 10.5.1.2 Auto-spectrum method Measure or determine the input to the hearing aid as a function of frequency and store the results Measure the output of the hearing aid as a function of frequency and store the results Calculate the transfer function by dividing the auto-spectrum of the output signal from the hearing aids, GBB, by the auto-spectrum of the input signal to the hearing aid, GAA, and convert the result into decibels by taking the log to the base ten of the result and multiplying it by 10 If random noise is used as the test signal, then averaged auto-spectra shall be used For the auto-spectrum method, it is not necessary to measure the input and output signals simultaneously 10.5.1.3 Swept filter method Calculate the frequency response by dividing the output magnitude by the input magnitude at each frequency Convert the magnitude ratio to decibels at each frequency 10.6 Frequency response recording chart The frequency response curves shall be displayed on a grid having a linear decibel ordinate scale and a logarithmic frequency abscissa scale, with the length of one decade on the abscissa scale equal to the length of 50 dB on the ordinate scale, in accordance with IEC 60263 The control settings or programming parameters used shall be stated for each measurement Figure — Example of steady-state input/output graph 12 © BSI 06-1999 EN 60118-2:1995 Figure — Dynamic output characteristics of an AGC circuit © BSI 06-1999 13 EN 60118-2:1995 Annex A (informative) Examples of measuring systems Figure — Example of measuring system according to the comparison method employing two tracking bandpass filters 14 © BSI 06-1999 EN 60118-2:1995 Figure — Example of a measuring system employing digitally controlled input SPL and a band rejection filter Figure — Nominal values with upper and lower limits (± dB) for one-third-octave band levels of the noise input signal at the test point © BSI 06-1999 15 EN 60118-2:1995 Annex B (informative) Smoothed data presentation Annex C (informative) Bibliography Presenting the frequency response as computed using the FFT analysis can lead to a large amount of point-to-point fluctuation in the plotted curve Smoothing algorithms may be applied to the raw data values Selection of an appropriate smoothing algorithm depends on the application For example, if the functioning of the hearing aid close to the onset of acoustic feedback oscillation is of interest, little or no smoothing may be indicated to preserve the exact nature of the peaks in the frequency response Among the several possible methods for smoothing the frequency responses are the point or point running average method With this method, data at a number of sequentially higher and lower test frequencies are averaged with the data value at the test frequency [1] ANSI S3.42:1992, Testing hearing aids with a broad-band noise signal [2] Bendat, J S and Piersol, A G (1980): Engineering Applications of Correlation and- Spectral Analysis, Wiley & Sons, New York [3] Dyrlund, O (1989): “Characterisation of Non-Linear Distortion in Hearing Aids Using Coherence Analysis”, Scandinavian Audiology 18: 143–148 [4] Dyrlund, O (1992): “Coherence Measurements in Hearing Instruments Using Different Broad-Band Signals”, Scandinavian Audiology 21: 73–78 [5] Prokais, J and Manolakis, D (1988): Introduction to Digital Signal Processing, Macmillan Publishing Company, New York 16 © BSI 06-1999