JPS6133320B2 - - Google Patents
Info
- Publication number
- JPS6133320B2 JPS6133320B2 JP10067478A JP10067478A JPS6133320B2 JP S6133320 B2 JPS6133320 B2 JP S6133320B2 JP 10067478 A JP10067478 A JP 10067478A JP 10067478 A JP10067478 A JP 10067478A JP S6133320 B2 JPS6133320 B2 JP S6133320B2
- Authority
- JP
- Japan
- Prior art keywords
- output
- preamplifier
- hearing
- sound pressure
- control signal
- 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.)
- Expired
Links
- 230000035945 sensitivity Effects 0.000 claims description 16
- 238000009499 grossing Methods 0.000 claims description 2
- 230000007274 generation of a signal involved in cell-cell signaling Effects 0.000 claims 1
- 230000006835 compression Effects 0.000 description 20
- 238000007906 compression Methods 0.000 description 20
- 208000032041 Hearing impaired Diseases 0.000 description 13
- 230000006870 function Effects 0.000 description 10
- 206010011878 Deafness Diseases 0.000 description 6
- 231100000888 hearing loss Toxicity 0.000 description 6
- 230000010370 hearing loss Effects 0.000 description 6
- 208000016354 hearing loss disease Diseases 0.000 description 6
- 230000003321 amplification Effects 0.000 description 4
- 238000012937 correction Methods 0.000 description 4
- 238000003199 nucleic acid amplification method Methods 0.000 description 4
- 239000003990 capacitor Substances 0.000 description 3
- 206010011891 Deafness neurosensory Diseases 0.000 description 2
- 208000009966 Sensorineural Hearing Loss Diseases 0.000 description 2
- 230000002238 attenuated effect Effects 0.000 description 2
- 210000005069 ears Anatomy 0.000 description 2
- 231100000879 sensorineural hearing loss Toxicity 0.000 description 2
- 208000023573 sensorineural hearing loss disease Diseases 0.000 description 2
- 208000000781 Conductive Hearing Loss Diseases 0.000 description 1
- 206010010280 Conductive deafness Diseases 0.000 description 1
- 230000002411 adverse Effects 0.000 description 1
- 208000023563 conductive hearing loss disease Diseases 0.000 description 1
- 230000003247 decreasing effect Effects 0.000 description 1
- 238000000034 method Methods 0.000 description 1
- 230000035807 sensation Effects 0.000 description 1
- 230000005236 sound signal Effects 0.000 description 1
Classifications
-
- 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
- H04R25/35—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception using translation techniques
- H04R25/356—Amplitude, e.g. amplitude shift or compression
Landscapes
- Health & Medical Sciences (AREA)
- General Health & Medical Sciences (AREA)
- Neurosurgery (AREA)
- Otolaryngology (AREA)
- Physics & Mathematics (AREA)
- Engineering & Computer Science (AREA)
- Acoustics & Sound (AREA)
- Signal Processing (AREA)
Description
【発明の詳細な説明】
本発明は、聴力障害を補充する補聴器、特に音
圧圧縮機能付補聴器の改良に関するものである。DETAILED DESCRIPTION OF THE INVENTION The present invention relates to an improvement in a hearing aid for compensating for hearing loss, particularly a hearing aid with a sound pressure compression function.
本発明の目的は、補聴器を使用する難聴者が、
最も聴取し易に任意の音圧ダイナミツクレンジに
入力信号とほぼリニアに圧縮、増幅、再生可能な
補聴器を提供することにある。 The purpose of the present invention is to enable hearing-impaired people who use hearing aids to
The object of the present invention is to provide a hearing aid that can compress, amplify, and reproduce an input signal almost linearly to any sound pressure dynamic range in the most audible manner.
本発明の他の目的は、上記目的を果しながら、
再生信号をひずませないことにある。 Another object of the present invention is to achieve the above object while
The purpose is not to distort the reproduced signal.
本発明のさらに他の目的は過大出力に対して耳
を保護するレスボンスの早い出力制限機能を兼ね
備えることにある。 Still another object of the present invention is to provide a quick-response output limiting function that protects the ears against excessive output.
感音性難聴者の場合、第１図に示すように、特
に微小入力音圧に対して通常者より感度が落ちる
が一定レベル以上の入力音圧に対しては通常者と
ほぼ同じ感度を得られるという特性を有してい
る。 As shown in Figure 1, in the case of a person with sensorineural hearing loss, the sensitivity is lower than that of a normal person, especially for small input sound pressures, but the sensitivity is almost the same as a normal person for input sound pressures above a certain level. It has the characteristic of being
したがつて、入力音圧のレベルに関係せず一定
の増幅度を持たせた補聴器を使用すると、聴き取
りにくい低レベルの入力音圧に対して適正な増幅
度にセツトするため、高レベルの入力音圧に対し
ては過大な増幅度になつてしまい、非常にうるさ
く感じる他、極端な場合耳に痛みを感じる等、か
えつて不都合な面が大きくなつてしまつた。これ
らの欠点を解消するため従来から、通称
“AGC”，“ARC”等の名称の各種音圧圧縮回路が
用いられてきている。従来の音圧圧縮回路は細部
は異なるにしても基本的な構成は同様であつて、
出力増幅器出力から、補聴器を構成する各増幅段
のいずれかの入力に帰還をかける方式をとつてい
る。なかんずく帰還量を定める部分に印加電圧に
対して非線型の抵抗特性を示すダイオード等を使
用している場合が多い。 Therefore, if you use a hearing aid that has a constant amplification level regardless of the level of input sound pressure, the amplification level will be set to an appropriate level for low-level input sound pressures that are difficult to hear. This results in an excessive amplification level relative to the input sound pressure, making it extremely noisy and, in extreme cases, causing pain to the ears, resulting in even more inconveniences. To overcome these drawbacks, various sound pressure compression circuits, commonly known as "AGC", "ARC", etc., have been used. Although the details of conventional sound pressure compression circuits differ, the basic configuration is the same.
A method is used in which feedback is applied from the output of the output amplifier to one of the inputs of each amplification stage that makes up the hearing aid. In particular, a diode or the like that exhibits nonlinear resistance characteristics with respect to applied voltage is often used in the part that determines the amount of feedback.
その代表的な例を第２図，第３図に従つて説明
する。その構成の概略は、第２図に示すようにマ
イクロホン１、前置増幅器２、ボリウム３、主増
幅器４、出力増幅器５及びイヤホン６であり、他
に音質調節回路等が含まれることもある。音圧圧
縮回路は通常前記出力増幅器５に含まれている。
その詳細を第３図に示す。 A typical example thereof will be explained with reference to FIGS. 2 and 3. As shown in FIG. 2, its general configuration includes a microphone 1, a preamplifier 2, a volumetric volume 3, a main amplifier 4, an output amplifier 5, and an earphone 6, and may also include a sound quality adjustment circuit and the like. A sound pressure compression circuit is usually included in the output amplifier 5.
The details are shown in FIG.
前記主増幅器４からの出力は、コンデンサ７、
ベース抵抗１０を通して、イヤホンを駆動するト
ランジスタ１２のベースに入力される。２ケの端
子１１はイヤホン端子である。以上の基本的な構
成に加えて、逆並列ダイオード１３，コンデンサ
８，分割トリマー９によつて前記トランジスタ１
２のコレクタ側からベース側へ帰還をかけて、増
幅器をコントロールし、音圧圧縮を行なつてい
る。 The output from the main amplifier 4 is connected to a capacitor 7,
It is input through a base resistor 10 to the base of a transistor 12 that drives the earphone. The two terminals 11 are earphone terminals. In addition to the above basic configuration, the transistor 1 is
Feedback is applied from the collector side of 2 to the base side to control the amplifier and compress the sound pressure.
したがつてその動作は、出力が大きくなるにし
たがつて指数関数的に帰還量が大きくなり、第４
図に示す如く、入力波形１４に対して出力波形１
５が大きくひずんでしまうという重大な欠点を有
している。 Therefore, as the output increases, the amount of feedback increases exponentially, and the fourth
As shown in the figure, for input waveform 14, output waveform 1
5 has a serious drawback in that it is greatly distorted.
さらに第５図に示す如く、フラツトな入出力特
性１６に対して、前記分割トリマー９を操作して
音圧圧縮してゆくと、その特性は１７，１８の如
くなり、ある入力音圧レベル以上になると出力音
圧は、一定になつてしまうし、第６図に示す如
く、一定の音圧圧縮量にしておいて、前記ボリウ
ム３を操作して増幅度を変化させた場合、１９な
いし２０といつた入出力特性となり、出力音圧が
あるレベルでクリツプするような音圧圧縮特性を
示している。 Furthermore, as shown in FIG. 5, when the sound pressure is compressed by operating the split trimmer 9 for the flat input/output characteristic 16, the characteristic becomes 17, 18, and above a certain input sound pressure level. When the output sound pressure becomes constant, the output sound pressure becomes constant, and as shown in FIG. The input/output characteristics are as follows, and the sound pressure compression characteristics are such that the output sound pressure clips at a certain level.
このような音圧圧縮の特性であると、第１図に
示した難聴カープの補正にはならない。なぜなら
ば第７図に示す如く、もともとの難聴者の感度特
性２１を上記音圧圧縮機能付補聴器によつて感度
補正し、難聴者にとつて聴き易い音圧ダイナミツ
クレンジ２３に入れようとすると、補聴器によつ
て補正された難聴者の感度特性は２２の如くな
り、そうでなくてさえ狭い難聴者の最適可聴ダイ
ナミツク音圧レンジを、全く有効に使つていない
結果となつている。そのため実際に従来の補聴器
（音圧圧縮機能付）を使用している難聴者から
は、本来、色々なレベルを持つ話声、騒音など
が、ほとんど全て同じレベルでしかも可聴限界ギ
リギリの大きな音で聞こえてくる。その上非常に
ひずんでしやつて、音は大きくなるが、明瞭度が
かえつて下がつてしまうように感じる等大きな不
満となつて出されて来ている。 With such sound pressure compression characteristics, the hearing loss curve shown in FIG. 1 cannot be corrected. This is because, as shown in FIG. 7, when the sensitivity characteristic 21 of a hearing-impaired person is corrected using the above-mentioned hearing aid with sound pressure compression function, and the sound pressure dynamic range 23 is brought into a level that is easy for the hearing-impaired person to hear. The sensitivity characteristics of a hearing-impaired person corrected by a hearing aid are as shown in 22, which means that the optimal audible dynamic sound pressure range for a hearing-impaired person, which is otherwise narrow, is not used effectively at all. For this reason, hearing-impaired people who use conventional hearing aids (with sound pressure compression function) find that speech, noise, etc. that normally have various levels are almost all the same level, and are loud enough to be at the limit of hearing. I can hear it. In addition, the sound is extremely distorted and dull, and while the sound gets louder, the clarity has actually deteriorated, which has led to major complaints.
本発明は上記のような、ひずみが大きい、ダイ
ナミツクレンジを有効に使つていない等の従来の
音圧圧縮機能付補聴器を抜本的に改良しようとし
たものであつて、前置増幅器とボリウムとの間
に、入力信号によつて変化する制御信号を発生す
る制御信号発生部と前記制御信号によつて減衰特
性が変化するゲイン制御部とを備え、入力信号に
よつて補聴器の音響利得を変化させるようにした
ものである。 The present invention is an attempt to fundamentally improve the conventional hearing aids with sound pressure compression function, which have large distortion and do not effectively use dynamic range, as described above. A control signal generating section that generates a control signal that changes depending on the input signal and a gain control section that changes the attenuation characteristic depending on the control signal are provided between the hearing aid and the acoustic gain of the hearing aid according to the input signal. It was designed to change.
以下実施例に基づいて説明する。 The following description will be made based on examples.
第８図は本発明の実施例であつて、第９図はそ
の一部の具体的な回路例である。マイクロホン２
４に入力された信号は、前置増幅器２５で20dB
程度増幅され、ゲイン制御部２７においてゲイン
を減衰された後、ボリウム２８，主増幅器２９，
出力増幅器３０を通して、イヤホン３１に出力さ
れる。制御信号発生部２６は、前記前置増幅器２
５の出力を入力として、制御信号を前記ゲイン制
御部２７に出力している。 FIG. 8 shows an embodiment of the present invention, and FIG. 9 shows a specific example of a part of the circuit. Microphone 2
The signal input to 4 is 20dB at preamplifier 25.
After the gain is amplified and the gain is attenuated in the gain control section 27, the volume 28, the main amplifier 29,
The signal is output to the earphone 31 through the output amplifier 30. The control signal generating section 26 includes the preamplifier 2
5 is input, and a control signal is output to the gain control section 27.
前記制御信号発生部２６は、詳しくは、増幅部
と整流および平滑部から成り、制御信号の感度を
決めるトリマー３３とオフセツトを決めるトリマ
ー３４を接続する増幅器３５の出力は、ダイオー
ド３６によつて整流されるが、そのアタツクタイ
ム抵抗３７及びコンデンサ３８のRC時定数、リ
リースタイムは抵抗３９及び前記コンデンサ３８
のRC時定数によつて設定された値を有してい
る。通常アタツクタイムムは10msec、リリース
タイムは0.5〜１秒程度になるようセツトする。
このようにして形成した制御信号は、前記ゲイン
制御回路２７を構成するＮチヤンネルMOSFET
４１のゲートに入力される。前記FET４１のド
レインは抵抗４０に接続され、この接続部が出力
端子になついるので入力信号レベルが大きくなれ
ば、制御信号も大きくなり、前記FET４１がON
して前記抵抗４０との分圧比が小さくなり、音圧
圧縮がなされる。オフセツトを決める前記トリマ
ー３４によつて、前記FETのスレツシヨルドレ
ベルを補償すると共に、音圧圧縮開始の入力レベ
ルを決定することが出来るし、又感度を決める前
記トリマー３３によつて同一入力レベル変化に対
する音圧圧縮量を決定することが出来る。 Specifically, the control signal generating section 26 consists of an amplifying section, a rectifying section, and a smoothing section. However, the RC time constant and release time of the resistor 37 and capacitor 38 are equal to the resistor 39 and the capacitor 38.
has a value set by the RC time constant of Normally, the attack time is set to 10 msec, and the release time is set to about 0.5 to 1 second.
The control signal thus formed is applied to the N-channel MOSFET constituting the gain control circuit 27.
It is input to gate 41. The drain of the FET 41 is connected to the resistor 40, and this connection is connected to the output terminal, so as the input signal level increases, the control signal also increases, turning the FET 41 ON.
As a result, the voltage division ratio with respect to the resistor 40 becomes small, and sound pressure is compressed. The trimmer 34, which determines the offset, can compensate the threshold level of the FET and determine the input level at which sound pressure compression starts, and the trimmer 33, which determines the sensitivity, can compensate for the threshold level of the FET and determine the input level at which the sound pressure compression starts. It is possible to determine the amount of sound pressure compression for changes.
例えば、上記実施例を用いて、第１０図に示す
ような難聴特性４２を有する難聴者が本発明によ
る音圧圧縮機能付補聴器を使用する場合を考えて
みたい。この難聴者の場合、通常の会議室の暗騒
音レベルの60dB以上で考えると、60dBで−20dB
感度がダウンしており、それが90dBではほぼ通
常者と同様の感度に回復するような特性を有して
いる。 For example, using the above-mentioned embodiment, let us consider a case where a hearing-impaired person having a hearing loss characteristic 42 as shown in FIG. 10 uses a hearing aid with a sound pressure compression function according to the present invention. In the case of this hearing-impaired person, considering the background noise level of 60 dB or more in a normal conference room, 60 dB is -20 dB.
The sensitivity is down, but at 90dB, it has the characteristic that it recovers to almost the same sensitivity as a normal person.
そこでまず、基本的な補聴器の音響利得を
20dB持たせ、かつ前記トリマー３３，３４を調
節することによつて第１１図のような減衰特性４
３を前記ゲイン制御部２７に持たせることが出来
る。最終的に飽和する減衰率は、前記抵抗４０と
前記FET４１のサイイズ，特性，使用電圧等に
も影響されるので、注意を要する。さて補聴器ト
ータルで考えてみると、第１２図に示すような入
出力時４４を有する本発明による音圧圧縮機能付
補聴器を使用した前記の難聴者は、第１３図のよ
うな補正された聴感度４６を持つことになる。４
５はもともとの聴感度である。 First, let's look at the acoustic gain of basic hearing aids.
By giving 20 dB and adjusting the trimmers 33 and 34, the attenuation characteristic 4 as shown in FIG.
3 can be provided in the gain control section 27. The attenuation rate that finally saturates is affected by the size, characteristics, operating voltage, etc. of the resistor 40 and the FET 41, so care must be taken. Now, considering the hearing aid as a whole, the above-mentioned hearing-impaired person who uses the hearing aid with sound pressure compression function according to the present invention having the input/output time 44 as shown in FIG. It has a sensitivity of 46. 4
5 is the original hearing sensitivity.
したがつて、本発明によれば、もつとも通常者
の聴感に近いような補正が、好みのダイナミツク
レンジで、好みの深さで可能であるので、軽，中
症者，重症者ともに難聴者の難聴特性にあわせた
最適可聴レベルで、音の大小とも自然に近い形で
聴取出来るため快適な聴取が可能となつた。ま
た、負帰還をかけていず、しかも0.5〜１秒のリ
リースタイムを持つているので、瞬間的には、減
衰比は入力音声信号のピークレベルの主に小さく
なる方向への変動には無関係となるほで、第１４
図に示す如く、入力信号波形４７は、相似的に出
力信号波形４８となるため、殆んどひずみを生じ
ないので、明瞭度が低下しない。加えて、前記ゲ
イン制御部２７を出来る丈前へ持つて来ているた
め信号がクリツプしてしまつた後減衰されること
が少ないことも、ひずみを広い範囲にわたつて発
生させないためには必要なことである。さらに
は、アタツクタイムを10msec程度に取れるた
め、実用上充分なレスボンスを持つ出力制限機能
もあわせ持つている。 Therefore, according to the present invention, it is possible to make corrections that are close to the hearing sensation of a normal person at the desired dynamic range and desired depth, so that it is suitable for people with mild, moderate, and severe hearing loss. The optimal audible level is tailored to the hearing loss characteristics of the user, allowing for comfortable listening as both loud and small sounds can be heard in a way that is close to natural. In addition, since negative feedback is not applied and the release time is 0.5 to 1 second, the attenuation ratio is momentarily unrelated to changes in the peak level of the input audio signal, mainly in the direction of decreasing. Naruhode, 14th
As shown in the figure, since the input signal waveform 47 becomes the output signal waveform 48 in a similar manner, almost no distortion occurs, so that the clarity does not deteriorate. In addition, since the gain control section 27 is placed as far forward as possible, the signal is less likely to be attenuated after clipping, which is necessary in order to prevent distortion from occurring over a wide range. That's true. Furthermore, since the attack time can be set to about 10 msec, it also has an output limiting function with a practically sufficient response.
以上から本発明によれば、特に感音性難聴者に
好適な自然に近い聴感補正が任意に出来、しかも
そのことによつて従来生じていた明瞭度に悪影響
を及ぼすひずみを殆んど生じさせることがない
上、出力制御機能を兼ね備えた、音圧圧縮機能付
補聴器を提供出来る。 From the foregoing, according to the present invention, it is possible to arbitrarily perform auditory correction that is close to natural and is particularly suitable for persons with sensorineural hearing loss, and it also eliminates most of the distortions that adversely affect intelligibility that conventionally occur. In addition, it is possible to provide a hearing aid with a sound pressure compression function that also has an output control function.
第１図は、伝音性難聴者の聴感度特性、第２図
は従来の補聴器の構成例、第３図は、第２図中、
特に音圧圧縮回路を含む出力増幅器の詳細な回路
例、第４図は従来の音圧圧縮回路の入出力波形特
性、第５図は、従来の音圧圧縮回路付補聴器のゲ
イン特性、第６図は、第５図において、圧縮度一
定、ボリウムを変化させた場合の特性、第７図
は、従来の音圧圧縮回路付補聴器を使用して得ら
れた難聴者の補正聴感度特性、第８図は本発明に
よる補聴器の構成の一実施例、第９図は、第８図
中の一部ブロツクの詳細な回路例、第１０図は、
本発明の実施例において例示した特定の難聴者の
難聴度、第１１図は、本発明の実施例によつて得
られた減衰特性、第１２図は、本発明の実施例の
音響利得を示す入出力特性、第１３図は、本発明
の実施例によつて補正された難聴者の聴感度特
性、第１４図は、本発明の実施例における、入出
力波形特性をそれぞれ示す。
１３……逆並列ダイオード、２２……従来の補
聴器で補正後の聴感度、２４……マイク、２５…
…前置増幅器、２６……制御信号発生部、２７…
…ゲイン制御部、２８……ボリウム、２９……主
増幅器、３０……出力増幅器、３１……イヤホ
ン、３３……感度調節用トリマ、３４……オフセ
ツト調節用トリマ、４１……Ｎチヤンネル
MOSFET、４６……本発明の実施例によつて得
られた補正後の難聴者の聴感度。
Figure 1 shows the hearing sensitivity characteristics of a person with conductive hearing loss, Figure 2 shows an example of the configuration of a conventional hearing aid, and Figure 3 shows the characteristics in Figure 2.
In particular, a detailed circuit example of an output amplifier including a sound pressure compression circuit, Fig. 4 shows input/output waveform characteristics of a conventional sound pressure compression circuit, Fig. 5 shows gain characteristics of a conventional hearing aid with a sound pressure compression circuit, and Fig. Figure 5 shows the characteristics when the compression level is constant and the volume is varied. Figure 7 shows the corrected hearing sensitivity characteristics for a hearing-impaired person obtained using a conventional hearing aid with a sound pressure compression circuit. Figure 8 shows an example of the configuration of a hearing aid according to the present invention, Figure 9 shows a detailed circuit example of some blocks in Figure 8, and Figure 10 shows the following:
The degree of hearing loss of a specific hearing-impaired person illustrated in the embodiment of the present invention, FIG. 11 shows the attenuation characteristic obtained by the embodiment of the present invention, and FIG. 12 shows the acoustic gain of the embodiment of the present invention. Input/output characteristics. FIG. 13 shows the hearing sensitivity characteristics of a hearing-impaired person corrected by the embodiment of the present invention, and FIG. 14 shows the input/output waveform characteristics in the embodiment of the present invention. 13... Anti-parallel diode, 22... Hearing sensitivity after correction with conventional hearing aid, 24... Microphone, 25...
...Preamplifier, 26... Control signal generator, 27...
... Gain control section, 28 ... Volume, 29 ... Main amplifier, 30 ... Output amplifier, 31 ... Earphone, 33 ... Trimmer for sensitivity adjustment, 34 ... Trimmer for offset adjustment, 41 ... N channel
MOSFET, 46...Hearing sensitivity of a hearing-impaired person after correction obtained by the embodiment of the present invention.
Claims (1)
幅器、出力増幅器およびイヤホンを有する補聴器
において、前記前置増幅器とボリウムとの間に前
記前置増幅器の出力ゲインを減衰させるゲイン制
御部および前記ゲイン制御部の減衰特性を前記前
置増幅器の出力に応じて制御する制御信号発生部
を備え、前記ゲイン制御部は、一方の端子が前記
前置増幅器の出力端子に接続され、他方の端子が
前記ボリウムの入力端子に接続されている抵抗お
よびドレインが前記抵抗の他方の端子に接続さ
れ、ゲートが前記制御信号発生部の出力端子に接
続されているＮチヤンネルMOSFETからなり、
前記制御信号発生部は、制御信号の感度を調節す
るトリマーをオフセツトを調節するトリマーとを
備えた前記前置増幅器の出力信号を増幅する増幅
器、前記増幅器の出力を整流するダイオードおよ
び前記前置増幅器の出力信号に応じて出力する制
御信号のアタツク時間およびリリース時間を設定
する平滑回路からなることを特徴とする補聴器。1. A hearing aid having a microphone, a preamplifier, a volume, a main amplifier, an output amplifier, and an earphone, which includes a gain control section that attenuates the output gain of the preamplifier between the preamplifier and the volume, and a gain control section that attenuates the output gain of the preamplifier. The gain control section includes a control signal generation section that controls attenuation characteristics according to the output of the preamplifier, one terminal of which is connected to the output terminal of the preamplifier, and the other terminal connected to the input of the volume control section. consisting of a resistor connected to a terminal and an N-channel MOSFET whose drain is connected to the other terminal of the resistor and whose gate is connected to the output terminal of the control signal generator,
The control signal generating section includes an amplifier that amplifies the output signal of the preamplifier, which includes a trimmer that adjusts the sensitivity of the control signal and a trimmer that adjusts the offset, a diode that rectifies the output of the amplifier, and the preamplifier. A hearing aid comprising a smoothing circuit that sets the attack time and release time of a control signal to be output according to the output signal of the hearing aid.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP10067478A JPS5527742A (en) | 1978-08-18 | 1978-08-18 | Hearing aid |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP10067478A JPS5527742A (en) | 1978-08-18 | 1978-08-18 | Hearing aid |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| JPS5527742A JPS5527742A (en) | 1980-02-28 |
| JPS6133320B2 true JPS6133320B2 (en) | 1986-08-01 |
Family
ID=14280299
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| JP10067478A Granted JPS5527742A (en) | 1978-08-18 | 1978-08-18 | Hearing aid |
Country Status (1)
| Country | Link |
|---|---|
| JP (1) | JPS5527742A (en) |
Cited By (1)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JPS62140631U (en) * | 1986-02-28 | 1987-09-04 |
Families Citing this family (3)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JPH0632558B2 (en) * | 1984-04-14 | 1994-04-27 | リオン株式会社 | hearing aid |
| JPS61187499A (en) * | 1985-02-14 | 1986-08-21 | Kenjiro Owada | Hearing aid having circumferential noise suppressing function |
| US4750207A (en) * | 1986-03-31 | 1988-06-07 | Siemens Hearing Instruments, Inc. | Hearing aid noise suppression system |
-
1978
- 1978-08-18 JP JP10067478A patent/JPS5527742A/en active Granted
Cited By (1)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JPS62140631U (en) * | 1986-02-28 | 1987-09-04 |
Also Published As
| Publication number | Publication date |
|---|---|
| JPS5527742A (en) | 1980-02-28 |
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