圖1.7 ：塊圖的信號處理中的ACE的計劃.
通道,在那里（ ）第一是在一個過濾器的輸出通道,（ ） 29日是希爾伯特
變換（ ）規(guī)科技.的Hilbert信封大小的解析信號
（ ） （ ） （ ） 2 （ ） 2日在圣 圣圣[市,1948 ] .在實踐中,希爾伯特變換
往往結合帶通濾波使用復雜的過濾器,其真正的和
虛部是正交,如在一個變換.
對數(shù)變換用于地圖相對寬動態(tài)范圍的
衍生信封信號（在該命令的30分貝,但一些處理器允許多達80
分貝）到窄動態(tài)范圍電誘發(fā)聽（按2
到15分貝,根據(jù)主題和刺激的條件） .的動態(tài)范圍
所界定的不同的T -級到C級.T型水平對應
最小電流是一個需要引起聽覺的
特別是病人和特別通道.這架C -級別相對應的級別
電流的要求,爭取一個相對舒適的響亮,但仍
聽覺.的第二個作用是消除壓縮的區(qū)別
在響度增長之間的聲學和電聽證會聽證.聲學
響度是聽覺功能的壓縮強度,而在電動聽證
響度增長十分迅速（指數(shù)）的增加電流強度[增
和Shannon ,1994 ] .
壓縮通道輸出是用來調節(jié)列車雙相脈沖.那個
調制脈沖列車適用于通過射頻傳輸連結
相應的電極在耳蝸.脈沖列車來自低頻
渠道是針對心尖電極植入,并產生脈沖列車
從高頻率頻道是針對基底電極植入.
一個主要特點獨聯(lián)體戰(zhàn)略[威爾遜等人.,1991 ] ,以及有關的戰(zhàn)略,是
沒有各種豆類的渠道重疊的時間,但他們
交錯.這消除了一個主要組成部分之間的互動渠道
否則會產生通過矢量求和的電氣領域,從
不同的（同時刺激）電極.這種互動將預期
減少渠道的顯著相關的線索.
英語翻譯
英語翻譯
Figure 1.7:Block-Diagram of signal processing in ACE scheme.
channel,where ( ) r s t is the filter output in one channel,( ) i s t is the Hilbert
transform of ( ) r s t .The Hilbert envelope is the magnitude of the analytic signal
( ) ( ) ( )2 ( )2 r i Atst s t s t [Ville,1948].In practice,the Hilbert transform is
often combined with the band-pass filtering using complex filters whose real and
imaginary parts are in quadrature,such as in a FFT.
A logarithmic transformation is used to map the relatively wide dynamic range of
derived envelope signals (in the order of 30 dB,but some processors allow up to 80
dB) onto the narrow dynamic range of electrically evoked hearing (in the order of 2
to 15 dB,depending on the subject and stimulus conditions).The dynamic range is
defined by the difference from the T-level to the C-level.The T-level corresponds to
the minimal electrical current that is required to elicit an auditory sensation in the
particular patient and for the particular channel.The C-level corresponds to the level
of the electrical current required to elicit a relatively loud but still comfortable
auditory sensation.A second function of the compression is to remove the difference
in loudness growth between acoustic hearing and electric hearing.In acoustic
hearing loudness is a compressive function of intensity,while in an electric hearing
loudness grows very rapidly (exponentially) with increasing current intensity [Zeng
and Shannon,1994].
The compressed channel outputs are used to modulate trains of biphasic pulses.The
modulated pulse trains are applied through the RF transmission link to the
corresponding electrodes in the cochlea.Pulse trains derived from low-frequency
channels are directed to apical electrodes in the implant,and pulse trains derived
from high-frequency channels are directed to basal electrodes in the implant.
A key feature of the CIS strategy [Wilson et al.,1991],and related strategies,is that
none of the various pulses on the channels overlap in time,but that they are
interleaved.This eliminates a major component of interaction among channels that
otherwise would be produced through vector summation of the electrical fields from
different (simultaneously stimulated) electrodes.Such interaction would be expected
to reduce the salience of channel-related cues.
Figure 1.7:Block-Diagram of signal processing in ACE scheme.
channel,where ( ) r s t is the filter output in one channel,( ) i s t is the Hilbert
transform of ( ) r s t .The Hilbert envelope is the magnitude of the analytic signal
( ) ( ) ( )2 ( )2 r i Atst s t s t [Ville,1948].In practice,the Hilbert transform is
often combined with the band-pass filtering using complex filters whose real and
imaginary parts are in quadrature,such as in a FFT.
A logarithmic transformation is used to map the relatively wide dynamic range of
derived envelope signals (in the order of 30 dB,but some processors allow up to 80
dB) onto the narrow dynamic range of electrically evoked hearing (in the order of 2
to 15 dB,depending on the subject and stimulus conditions).The dynamic range is
defined by the difference from the T-level to the C-level.The T-level corresponds to
the minimal electrical current that is required to elicit an auditory sensation in the
particular patient and for the particular channel.The C-level corresponds to the level
of the electrical current required to elicit a relatively loud but still comfortable
auditory sensation.A second function of the compression is to remove the difference
in loudness growth between acoustic hearing and electric hearing.In acoustic
hearing loudness is a compressive function of intensity,while in an electric hearing
loudness grows very rapidly (exponentially) with increasing current intensity [Zeng
and Shannon,1994].
The compressed channel outputs are used to modulate trains of biphasic pulses.The
modulated pulse trains are applied through the RF transmission link to the
corresponding electrodes in the cochlea.Pulse trains derived from low-frequency
channels are directed to apical electrodes in the implant,and pulse trains derived
from high-frequency channels are directed to basal electrodes in the implant.
A key feature of the CIS strategy [Wilson et al.,1991],and related strategies,is that
none of the various pulses on the channels overlap in time,but that they are
interleaved.This eliminates a major component of interaction among channels that
otherwise would be produced through vector summation of the electrical fields from
different (simultaneously stimulated) electrodes.Such interaction would be expected
to reduce the salience of channel-related cues.
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