the following description is of the best mode presently contemplated for carrying out the invention . this description is not to be taken in a limiting sense , but is made merely for the purpose of describing the general principles of the invention . the scope of the invention should be determined with reference to the claims . a functional diagram of a typical implantable cochlear stimulation ( ics ) system is shown in fig1 . the ics includes a speech processor 10 that could be a wearable speech processor , or a behind - the - ear ( bte ) speech processor . a microphone 12 may be connected to the speech processor 10 by a first wire 14 , or may be attached to the speech processor 10 as in the case of a bte speech processor . the microphone 12 converts acoustic energy into an electrical signal for subsequent processing . the speech processor 10 contains a signal processor 16 that processes the electrical signal from the microphone 12 . the output signal of the signal processor 16 is carried by a second wire 18 to a headpiece 20 carried on the patient &# 39 ; s head . a first coil 22 transmits the control signal 23 from the headpiece 20 to the implantable electronics 24 , which implantable electronics 24 includes a second coil 26 for receiving the control signal . the implantable electronics 24 processes the control signal 23 to generate stimulation current for the electrode array 28 , which electrode array 28 is implanted in the patient &# 39 ; s cochlea . the architecture of an ics system may vary . the ics may include a wearable speech processor that is worn on the users belt and is connected to a microphone and headpiece by wiring , or a behind - the - ear ( bte ) speech processor resembling a typical hearing aid , that is worn behind the patient &# 39 ; s ear and retained by an earhook . another example is a fully implantable ics in which a speech processor 10 is integrated into the implantable electronics 26 . those skilled in the are will recognize that all of these variations require a microphone ( or more generally a transducer ), and a signal processor , to provide a stimulation level . all of these variations benefit from the present invention as described below . the human ear adjusts sound intensity with a logarithmic like scaling . thus , if a sound is 10 times stronger , it may only be perceived to be twice as loud . ics systems must perform a similar scaling , or mapping , if the patient is to perceive sounds with a natural intensity . additionally , such logarithmic scaling has the advantage of providing intelligible hearing for low level sounds , without overwhelming the patient when loud sounds are encountered . a functional flow for a single channel of prior - art amplitude mapping is shown in fig2 . in known systems , there may be from 4 to 30 such parallel channels operating in different frequency bands . the microphone 12 provides an electrical signals to a bandpass filters 32 . the bandpass filter 32 process the electrical signal 30 to generate a filtered signal 34 . the filtered signal 34 is then processed by a mapper 36 which outputs the mapped signal 38 . the mapper 36 maps the electrical signal 36 level measured by the microphone 12 into an electrical stimulation level to be provided to the electrode array 28 . in a preferred embodiment the mapper 36 is a log mapper , reflecting normal human hearing . those skilled in the art will recognize that other mapping may produce similar results and those other mappings are withing the scope of the present invention . the mapped signal 38 is processed by output processing 40 which outputs the stimulation signal 42 which is provided to the electrode array 28 . the log - mapper 36 operates on every signal processed by the amplitude mapping . a first embodiment of the present invention , depicted by one channel of an envelope based amplitude mapping applied to simultaneous analog stimulation ( sas ), is shown in fig3 . in practice , there are from 4 to 30 such parallel channels operating in different frequency bands . the processing up to and including the bandpass filter 32 is unchanged from known systems . the sample rate for the filtered signal 34 is between 10 khz and 25 khz and is preferably 13 khz or 17 khz . identical filtered signals 34 produced by the bandpass filter 32 are carried on two paths . the top paths in fig3 represents the heart of the envelope based amplitude mapping . an envelope detector 44 computes an envelop signal 46 from the filtered signal 34 . in a preferred embodiment the envelope detector 44 is a full wave rectifier followed by a lowpass filter with a cutoff of 100 hz . the particular envelope detector 44 that is best for a specific ics system depends on the details of processing that precedes the envelope detector 44 . various other implementations of envelope detectors will be apparent to those skilled in the art , and these variations are intended to fall within the scope of the present invention . the next step in the processing shown in fig3 is a decimator 48 . the decimator 48 creates a decimated signal 50 by reducing the sample rate by only passing every m th value of the envelope signal 46 . the sample rate of the decimated signal 50 may be between 50 hz and 1000 hz and is 800 hz in a preferred embodiment . the decimated sample rate in other embodiments of the invention may vary based on other parameters of ics the present invention is exercised in , and on the preferences of the patient . while the envelope detector and decimator are shown as separate processing steps , in a preferred implementation , the lowpass filter and decimator are combined into a single finite impulse response ( fir ) filter . continuing on in fig3 a log mapper 52 computes a mapped signal 54 from the decimated signal 50 by taking a compressive transformation of the decimated signal 50 . the preferred transformation is of the form f ′( x )= f ( x )/ x , where f ( x )= c 1 * log ( x )+ c 2 . the division by x is required due to the multiplying step described below . c 1 and c 2 are based on psycho - acoustical phenomena and are patient dependent . specifically , during a fitting process , measurements are made for each patient , and c 1 and c 2 are determined - for the individual patient based on those measurements . the mapped signal 54 may be viewed as a scaling factor related to the average level of the filtered signal 34 in the locality of the sample the scaling is applied to . a multiplier 56 , multiplies the mapped signal 54 times the original filtered signal 34 , to generate an envelope based amplitude mapping output signal 58 . the mapped signal 54 sample rate ( hereafter the second sample rate ) is lower than the filtered signal 34 sample rate ( hereafter the first sample rate .) if the first sample rate is not substantially higher than the second sample rate , for example , the first sample rate is less than sixteen times the second sample rate , the mapped signal 54 may be used directly by the multiplier 56 . if the first sample rate is substantially higher than the second sample rate , for example , the first sample rate is more than sixteen times the second sample rate , the mapped signal 54 may be linearqy interpolated to the first sample rate . the envelope based amplitude mapping described above for sas amplitude mapping may also be applied to continuous interleaved sampler ( cis ) amplitude mapping . a flow chart for a cis amplitude mapping incorporating the present invention is shown in fig4 . the microphone 12 and bandpass filter 32 are the same as in fig2 and 3 . the filtered signal 34 is processed by a second envelope detector 60 to produce a second envelope signal 62 , and the envelope signal 62 is processed by a second decimator 64 , to generate a second decimated signal 66 . a preferred envelope detector 60 comprises a full wave rectifier and a low pass filter . the lowpass filter has a cut off frequency of about 800 hz to 2000 hz , preferably 800 hz . while the envelope detector and decimator are shown as separate processing steps , in a preferred implementation , the lowpass filter and decimator are combined into a single finite impulse response ( fir ) filter . continuing with fig4 the decimated signal 66 is processed by a third envelope detector 68 to obtain a third envelope signal 70 , and the envelope signal 70 is processed by a third decimator 72 to obtain a third decimated signal 74 . a preferred envelope detector 70 comprises a full wave rectifier and a low pass filter . the lowpass filter has a cut off frequency of about 40 hz to 100 hz , preferably 40 hz . while the envelope detector and decimator are shown as separate processing steps , in a preferred implementation , the lowpass filter and decimator are combined into a single finite impulse response ( fir ) filter . the decimated signal 74 is processed by the log mapper 52 to generate a second mapped signal 78 . the mapped signal 78 and the decimated signal 66 are provided to the multiplier 80 , resulting in the second output signal 82 , which output signal 82 is provided to a pulse generator . one output signal 82 is provided for each pulse in cis processing . the decimated signal 66 is at a higher data rate than the mapped signal 78 . in a preferred embodiment , the mapped signal 78 is interpolated to the data rate of the decimated signal 66 in the multiplier 80 . a third embodiment comprising a second application of the present invention to cis amplitude mapping is shown in fig5 . the microphone 12 and bandpass filter 32 are the same as in fig2 , and 4 . the filtered signal 34 is processed by two parallel paths in the second cis embodiment . a fourth envelope detector 84 to produce a fourth envelope signal 86 , and the envelope signal 86 is processed by a fourth decimator 88 , to generate a fourth decimated signal 90 . a preferred envelope detector 84 comprises a half wave rectifier and a low pass filter . the lowpass filter has a cut off frequency of about 800 hz to 2000 hz , preferably 800 hz . while the envelope detector and decimator are shown as separate processing steps , in a preferred implementation , the lowpass filter and decimator are combined into a single finite impulse response ( fir ) filter . continuing with fig5 the filtered signal 34 is processed by a fifth envelope detector 92 to obtain a fifth envelope signal 94 , and the envelope signal 94 is processed by a fifth decimator 96 to obtain a fifth decimated signal 98 . a preferred envelope detector 92 comprises a full wave rectifier and a low pass filter . the lowpass filter has a cut off frequency of about 40 hz to 100 hz , preferably 40 hz . while the envelope detector and decimator are shown as separate processing steps , in a preferred implementation , the lowpass filter and decimator are combined into a single finite impulse response ( fir ) filter . the decimated signal 98 is processed by the log mapper 52 to generate a fifth mapped signal 102 . the mapped signal 102 and the decimated signal 90 are provided to the multiplier 80 , resulting in a third output signal 102 , which output signal 102 is provided to a pulse generator . one output signal 102 is provided for each pulse in cis processing . the decimated signal 90 is at a higher data rate than the mapped signal 102 . in a preferred embodiment , the mapped signal 102 is interpolated to the data rate of the decimated signal 90 in the multiplier 80 . the log mapping function is used to compress the stimulation current in a manner similar to the natural compression of the human ear . those skilled in the art will recognize that other compressive mapping functions produce similar results , and fall within the scope of the present invention . similarly , the embodiment described above includes a family of parallel band pass filters , but the use of a fast fourier transformation ( fft ) would produce similar results and is within the scope of the invention . thus an envelope amplitude mapping for cochlear stimulation has been presented to both reduced computational requirements , and improves performance . in applications requiring miniature devices , such reductions in computational requirements meet the important goal of extending battery life . further , the improved performance provides more accurate hearing and thus represents a step forward in restoring natural sounding hearing to the deaf . while the invention herein disclosed has been described by means of specific embodiments and applications thereof , numerous modifications and variations could be made thereto by those skilled in the art without departing from the scope of the invention set forth in the claims .
an envelope based amplitude mapping achieves the signal compression required to provide a natural sound level without the high processor loading or waveform alteration . in a preferred embodiment , the output of a family of parallel bandpass filters is processed by an envelope detector , followed by decimation . the resulting reduced data rate envelope is log mapped to produce a scaling factor for the original high data rate bandpass filter output sequence . the resulting scaled signal determines the current level for stimulation of the cochlea for each frequency band , which stimulation achieves a log mapping of the sound amplitude effect similar to natural hearing , while reducing processor load , and preserving waveform shape .