JP6954986B2 - Hearing aid strength and phase correction - Google Patents
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- 230000013707 sensory perception of sound Effects 0.000 title claims description 121
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- 238000003780 insertion Methods 0.000 claims description 56
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- 230000006870 function Effects 0.000 claims description 50
- 238000012546 transfer Methods 0.000 claims description 48
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- 210000003454 tympanic membrane Anatomy 0.000 claims description 19
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- 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
- H04R25/50—Customised settings for obtaining desired overall acoustical characteristics
- H04R25/505—Customised settings for obtaining desired overall acoustical characteristics using digital signal processing
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- H—ELECTRICITY
- H04—ELECTRIC COMMUNICATION TECHNIQUE
- H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
- H04R1/00—Details of transducers, loudspeakers or microphones
- H04R1/10—Earpieces; Attachments therefor ; Earphones; Monophonic headphones
- H04R1/1016—Earpieces of the intra-aural type
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- H—ELECTRICITY
- H04—ELECTRIC COMMUNICATION TECHNIQUE
- H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
- H04R2460/00—Details of hearing devices, i.e. of ear- or headphones covered by H04R1/10 or H04R5/033 but not provided for in any of their subgroups, or of hearing aids covered by H04R25/00 but not provided for in any of its subgroups
- H04R2460/05—Electronic compensation of the occlusion effect
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- H—ELECTRICITY
- H04—ELECTRIC COMMUNICATION TECHNIQUE
- H04S—STEREOPHONIC SYSTEMS
- H04S2420/00—Techniques used stereophonic systems covered by H04S but not provided for in its groups
- H04S2420/01—Enhancing the perception of the sound image or of the spatial distribution using head related transfer functions [HRTF's] or equivalents thereof, e.g. interaural time difference [ITD] or interaural level difference [ILD]
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- General Health & Medical Sciences (AREA)
- Neurosurgery (AREA)
- Otolaryngology (AREA)
- Headphones And Earphones (AREA)
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Description
背景技術
本発明は、人が着用すると、その人の聴覚(hearing)能力を改善する補聴器(hearing device)に関する。しかし、補聴器は時には聴覚補助具(hearing aid)と呼ばれるが、このような名称は難聴者による本発明の使用を限定するものではない。同様に、本発明は非聴覚障害者による使用も可能である。
Background Techniques The present invention relates to a hearing device that, when worn by a person, improves the person's hearing ability. However, hearing aids are sometimes referred to as hearing aids, but such names do not limit the use of the present invention by the hearing impaired. Similarly, the present invention can also be used by non-hearing impaired persons.
更に詳しくは本発明は、補聴器の少なくとも一部が外耳道を閉塞し、望ましくない挿入効果を創生する補聴器に関する。本発明は特にオープンイヤー型補聴器に利用可能性を有するが、閉塞型補聴器と共同しても使用できる。 More specifically, the present invention relates to hearing aids in which at least a portion of the hearing aid obstructs the ear canal, creating an undesired insertion effect. The present invention has particular potential for open-ear hearing aids, but can also be used in collaboration with obstructive hearing aids.
補聴器の全体又は一部を耳に挿入すると、鼓膜に到達する音の強度 (magnitude)及び位相の両者を歪める。理想的には補聴器は、到達する音が補聴器及び外耳道を通過した後、歪まずに留まるように、これらの効果に対して補償することである。多くの補聴器は、強度効果に対しては補償するが、位相歪に対しては充分に対処することができない。その結果、ユーザーは到達音が自然ではなく、聴き取り経験に重要な方向の手掛かり(directional cues)がない等の不平不満を言うことが多い。これらの不平不満は、特に音楽家や音楽業界のプロの間に広がっている。これらの人達の耳は微妙な差を識別するために訓練されているが、聴覚の部分的欠損に対し補償するために、補聴器を必要とする。 Inserting all or part of the hearing aid into the ear distorts both the magnitude and phase of the sound reaching the eardrum. Ideally, the hearing aid compensates for these effects so that the incoming sound remains undistorted after passing through the hearing aid and the ear canal. Many hearing aids compensate for intensity effects, but cannot adequately deal with phase distortion. As a result, users often complain that the arrival sound is not natural and there are no directional cues in the listening experience. These complaints are widespread, especially among musicians and professionals in the music industry. The ears of these people are trained to identify subtle differences, but require hearing aids to compensate for partial hearing deficits.
米国特許第5325436号(Sigfrid Soli等)には補聴器の挿入効果に対して補償する一解決方法が提案され、耳内への補聴器の挿入効果に対して補償するデジタルフイルターを決定する方法が開示されている。この方法では、耳内の強度レスポンス及び位相レスポンスを、補聴器なしの場合及び補聴器を所定位置に挿入した場合の両者について測定し、次いで所要の等化(equalization)(EQ)を計算する。しかし、前記方法は計算する際、複雑で、EQを計算し、また殆どの場合、正当(valid)ではない位相要素について仮定を行っている。位相について行った仮定のため、位相レスポンスは無効になりやすい。この方法は全ての外部(outside)音を減衰させるため、外耳道を完全
に閉塞するように、耳覆い(ear pierce)を仮定(pre-suppose)している。また、補正については、両耳間の互いの聴覚(interaural)タイミング差を保持することを意図しているだけで、絶対タイミング差は意図していない。このため、補聴器には両耳用(binaural)器具を必要とする。
U.S. Pat. No. 5,325,436 (Sigflide Soli et al.) Proposes a solution that compensates for the effect of hearing aid insertion and discloses a method of determining a digital filter that compensates for the effect of hearing aid insertion into the ear. ing. In this way, the intensity response and phase response of the ear was measured for both the case of inserting the case without hearing and hearing aids in position and then calculates the required equalization (equalization) (EQ). However, the method is complex when calculating, calculates EQ, and in most cases makes assumptions about non-valid phase elements. Due to the assumptions made about phase, the phase response is likely to be invalid. Since this method attenuates all outside sounds, it pre-supposes an ear pierce to completely block the ear canal. Further, the correction is intended only to maintain the mutual interaural timing difference between both ears, and is not intended to be an absolute timing difference. For this reason, hearing aids require binaural devices.
本発明は、位相レスポンスについて仮定を必要とせず、片耳用(monaural)器具と共用でき、しかもオープンイヤー型挿入に適合する、補聴器の耳内への挿入効果を補正する装置及び方法を提供する。本発明は、補聴器を外耳道に存在させることにより、生じた位相歪や種々の異常を鼓膜において補正するのに特に有効である。本発明の装置及び方法は、自然音として認識され、しかも聴き取り経験の向上により方向の手掛かりを留める増幅音を鼓膜に供給できる。即ち、この装置は音響的に透明であると認識される。聴き取り経験の向上は、殆どのユーザーに実現されようが、特に微妙な音楽的差異を識別する音楽的能力を取り戻したいとする音楽業界のプロ達に実現されよう。 The present invention provides a device and method for correcting the effect of inserting a hearing aid into the ear, which does not require any assumptions about the phase response, can be shared with a monaural device, and is suitable for open-ear insertion. The present invention is particularly effective in correcting the phase distortion and various abnormalities caused by the presence of the hearing aid in the ear canal in the eardrum. The apparatus and method of the present invention can supply an amplified sound to the eardrum, which is recognized as a natural sound and which keeps a clue in the direction by improving the listening experience. That is, the device is perceived to be acoustically transparent. An improved listening experience will be realized for most users, but especially for professionals in the music industry who want to regain their musical ability to discern subtle musical differences.
発明の開示
本発明は、ユーザーが着用すると、補聴器の少なくとも一部は耳内に挿入される補聴器の強度(magnitude)歪及び位相歪を補正する方法及び装置に向けたものである。この方法は、ユーザーの耳内に存在する補聴器の挿入効果を決定する工程を含む。この挿入効果は、強度レスポンス及び位相レスポンスを有する複雑な挿入伝達関数(ITF)を特徴とし、鼓膜の所で決定される。ITFの強度・位相レスポンスの両者とも、鼓膜への伝達関数が、所定場所にない補聴器の伝達関数と釣り合った際に補正される。
Disclosure of the Invention The present invention is directed to methods and devices for correcting the magnitude and phase distortion of a hearing aid that, when worn by the user, at least part of the hearing aid is inserted into the ear. This method involves determining the effect of inserting a hearing aid present in the user's ear. This insertion effect is characterized by a complex insertion transfer function (ITF) with intensity and phase responses and is determined at the eardrum. Both the strength and phase response of the ITF are corrected when the transfer function to the eardrum is balanced with the transfer function of the hearing aid that is not in place.
挿入効果は、好ましくは複数の2次最小位相フイルターの少なくとも1つ,好適には複数で補正する。この2次最小位相フイルターは、無限(indefinite)インパルスレスポンス(IIR)フイルター、更に好ましくは4次(biquad)フイルターである。 The insertion effect is preferably corrected by at least one of a plurality of second-order minimum phase filters, preferably a plurality of second-order minimum phase filters. The second-order minimum phase filter is an indefinite impulse response (IIR) filter, more preferably a fourth-order (biquad) filter.
強度及び位相における挿入効果の補正は、大ざっぱで完全ではないが、複雑な頭部伝達関数(HRTF)(head-related transfer function):複雑な挿入伝達関数ITFの比を取り入れることにより決定できる。これらの複雑なHRTF及びITFは、補聴器があってもなくても人体解剖模型上での測定により決定できる。或いは補聴器のユーザー上での測定により決定できる。位相レスポンスについては、位相レスポンスが最小位相である場合だけ補正する。 The correction of the insertion effect in intensity and phase can be determined by incorporating the ratio of complex head-related transfer function (ITF): complex insertion transfer function ITF, although it is rough and not perfect. These complex HRTFs and ITFs can be determined by measurement on a human anatomical model with or without hearing aids. Alternatively, it can be determined by measurement on the user of the hearing aid. The phase response is corrected only when the phase response is the minimum phase.
補聴器の強度・位相レスポンスが既知ならば、ITFを補正するための等化(equalization)は、最小位相である伝達関数の全ての部分について計算できる。しかし、殆どの場合、非最小位相領域を処理する解析法がないため、非最小位相領域については計算できない。
If the strength and phase response of the hearing aid is known, the equalization to correct the ITF can be calculated for all parts of the transfer function, which is the minimum phase. However, in most cases, the non-minimum phase region cannot be calculated because there is no analysis method for processing the non-minimum phase region.
更に実用的には、所望の等化は反復法により決定される。最小位相現象で支配されたスペクトル領域を補正するため、補聴器には種々の最小位相フイルタリングを導入できる。位相を補正できない他の領域では強度レスポンスは補正できるかも知れない。この補正工程は、所望の位相補正が達成されるまで繰返し行う。
More practically, the desired equalization is determined by the iterative method. Various minimum phase filters can be introduced into the hearing aid to correct the spectral region dominated by the minimum phase phenomenon. Intensity response may be correctable in other areas where phase cannot be corrected. This correction step is repeated until the desired phase correction is achieved.
或いはITF強度・位相レスポンスを補正するための所望の等化は、音を言葉で言う際に(in describing sound)経験したユーザーにより主観的に決定できる。ユーザーは外耳道中、補聴器の存在下で聴取した音と不存在下で聴取した音の認識力(perception)とを比較する。ユーザーはこれら2つの条件間に認識された差異がないと指示した時、所
望の等化が達成される。
Alternatively, the desired equalization for correcting the ITF intensity / phase response can be subjectively determined by the user who has experienced in describing sound. During the ear canal, the user compares the perception of sound heard in the presence of a hearing aid with that heard in the absence of a hearing aid. The desired equalization is achieved when the user indicates that there is no perceived difference between these two conditions.
本発明の最良の実施形態による補聴器は、該補聴器で増幅された全ての周波数で約120度未満の位相に相当するように構成される。換言すれば補聴器の遅れ時間(latency)は、補聴器により生じた最高周波数期間の約1/3未満が好ましい。例えば補聴器が音を10kHzまで増幅すれば、好ましい待ち時間は30μs未満であろう。
A hearing aid according to the best embodiment of the present invention is configured to correspond to a phase of less than about 120 degrees at all frequencies amplified by the hearing aid. In other words hearing aid delay time (latency) is less than about 1/3 of the highest frequency term generated by the hearing aid is preferred. For example, if the hearing aid amplifies the sound to 10 kHz, the preferred latency would be less than 30 μs.
本発明を実施するための最良の形態
外耳道に補聴器が存在すると、鼓膜への伝達関数は変化する。この変化は、2つの要素(component)、即ち補聴器自体の活動的(active)レスポンスとその受動的効果とからなる。受動的効果が補償されると、補聴器は真に透明となり、ユーザーに対し全ての音レベルで自然の音を出す(sound natural)。
Best Mode for Practicing the Invention The presence of a hearing aid in the ear canal alters the transfer function to the eardrum. This change consists of two components: the active response of the hearing aid itself and its passive effects. When the passive effect is compensated, the hearing aid becomes truly transparent and sounds natural to the user at all sound levels.
オープン型補聴器では、外耳道に受信器(又は拡声器(loudspeaker))があっても入射音は完全には減衰しない。これは事実で、受信器(又は拡声
器)周辺(around)の直接路は所定場所に保持するゴム製挿入チップ内の複数の孔で設けられる(provided)からである。これらの器具は低周波数(500Hz未満)を殆ど減衰させない傾向があるが、これより高い周波数は、補聴器、イヤーチップ及びユーザーの外耳道の幾何形状に依存する可変的方法で減衰する。
In open hearing aids, the incident sound is not completely attenuated even if there is a receiver (or loudspeaker) in the ear canal. This is true because the direct path around the receiver (or loudspeaker) is provided by a plurality of holes in the rubber insertion chip that holds it in place. These devices tend to attenuate low frequencies (less than 500 Hz) very little, but higher frequencies are attenuated in a variable way that depends on the geometry of the hearing aid, eartips and the user's ear canal.
このような開放型補聴器はユーザーにとって2つの利点がある。第一は高周波難聴性(普通は殆どこの種類)のユーザーでは、補聴器は低周波音を全く増幅する必要がなく、使用したミニチュア拡声器上には物理的束縛又は圧迫がいっそう少なくなる。第二に閉塞(occlusion)効果がなく、外耳道の入口が閉塞された時は、ユーザー自身の音声の変化となる。 Such open hearing aids have two advantages for the user. First, for users with high-frequency deafness (usually almost this type), the hearing aid does not need to amplify the low-frequency sound at all, and there is less physical restraint or pressure on the miniature loudspeaker used. Secondly, when there is no occlusion effect and the entrance of the ear canal is blocked, the user's own voice changes.
閉鎖型(closed)補聴器では、入射音は全ての周波数で減衰し、一般的には無視できる。これは、閉鎖型補聴器で生じた音は鼓膜に到達する有意の音だけであることを意味する。しかし、挿入効果は強度及び位相に留まるので、前述と同じ方法で補正を必要とする。 In closed hearing aids, incident sound is attenuated at all frequencies and is generally negligible. This means that the only sound produced by a closed hearing aid is a significant sound that reaches the eardrum. However, since the insertion effect remains in strength and phase, it needs to be corrected in the same way as described above.
耳内モニターのような、マイクロホンを持たない補聴器では、現時点の入力信号は電気信号である。このような補聴器の挿入効果は、前記閉鎖型補聴器の場合と同じで、スピーカーから着用者の前に音が出される(played)場合から決定できる。 For hearing aids that do not have a microphone, such as an intraocular monitor, the current input signal is an electrical signal. The effect of inserting such a hearing aid is the same as that of the closed hearing aid, and can be determined from the case where the speaker emits sound in front of the wearer (played).
本発明方法を、まずオープンイヤー型補聴器の場合について説明する。この方法では、補聴器の挿入効果について(for)等化を決定するのに必要な測定に音響的人体解剖模型が使用される。この等化には効果的な補正が必要とされている。人体解剖模型を用いる代りの方法、即ち、人体解剖模型を使わないが、生身の人(live person)に依存する方法は後述する。前述の他の2つの例、即ち、閉塞型補聴器及び耳内モニターの例は事実上同一で、前述と同じ補正方法を用いるので、補正可能である。
First, the method of the present invention will be described in the case of an open-ear hearing aid. In this method, an acoustic human anatomical model is used for the measurements necessary to determine the (for) equalization of the hearing aid insertion effect. Effective correction is required for this equalization. An alternative method using a human anatomy model, that is, a method that does not use a human anatomy model but depends on a live person, will be described later. The other two examples described above, namely the obstructive hearing aid and the intraoural monitor, are substantially the same and can be corrected because they use the same correction method as described above.
音響的人体解剖模型は、平均的な人間の頭部をまねる(emulate)ように設計され、目盛付き(calibrate)人工耳内にマイクロホンを含有する。このように埋設されたマイクロホンにより、人体模型の鼓膜の位置で音圧を容易に測定することができる。これらの測定値(measurements)は複雑な伝達関数を決定するのに使用できる。これらの複雑な伝達関数は、補聴器が所定の場所にあってもなくても、音がどのようにして耳内を通って鼓膜に達するかを表示する。補聴器なしでは耳は閉塞されず、複雑な伝達関数は、通常、頭部伝達関数(HRTF)と呼ばれる。所定場所にあり電源が切られている補聴器では、耳は閉塞され、複雑な伝達関数は挿入伝達関数(ITF)と呼ぶことができる。挿入効果はHRTFとITFとの差であり、時には挿入ロスと呼ばれる。挿入ロスは、これと関連する強度減衰のためであるが、強度レスポンスを変化させる共鳴又はフイルターのいずれも同様に位相を必然的に変化させるので、位相も影響を受ける。
The acoustic human anatomy model is designed to emulate the average human head and contains a microphone in the calibrate cochlear implant. With the microphone embedded in this way, the sound pressure can be easily measured at the position of the eardrum of the human model. These measurements can be used to determine complex transfer functions. These complex transfer functions display how sound passes through the ear and reaches the eardrum, whether or not the hearing aid is in place. Without hearing aids, the ear is not obstructed and the complex transfer function is commonly referred to as the head related transfer function (HRTF). The hearing aid that have Yes Power is turned off in a predetermined location, the ear is closed, complex transfer function may be referred to as insertion transfer function (ITF). The insertion effect is the difference between the HRTF and the ITF, sometimes referred to as insertion loss. Insertion loss is due to the associated intensity attenuation, but the phase is also affected because either the resonance or the filter that changes the intensity response inevitably changes the phase as well.
HRTFとITF間の強度及び位相の差は、透明な認識力用に補正しなければならない。外耳道及び補聴器の挿入効果は静的且つ受動的である。したがって、それらの共鳴は最小位相として説明できる。最小位相システムは幾つかの有用な特性を有する。即ち、該システムの効果はスペクトル的に局在化される。;該システムは安定な逆関係を有する。;また所定の強度レスポンスに対し、最小位相レスポンスは独特のものである。 Intensity and phase differences between HRTFs and ITFs must be corrected for transparent cognitive ability. The ear canal and hearing aid insertion effects are static and passive. Therefore, their resonance can be explained as the minimum phase. The minimum phase system has some useful properties. That is, the effect of the system is spectrally localized. The system has a stable inverse relationship. Also, for a given intensity response, the minimum phase response is unique.
これら全ての特性は、補聴器の処理に補足的な2次最小位相フイルターを追加することにより、挿入効果が除去できることを意味する。フイルターを追加する際、強度レスポンス及び位相レスポンスの両方を補正できる。もし、非最小位相フイルターを使用すれば、強度レスポンス又は位相レスポンスのいずれかを補正できるが、同時に両者を補正することはできない。挿入効果に対して補償する伝達関数は、補助(aided)伝達関数(ATF)と呼ばれ、補聴器なしのHRTFと同一である。 All these characteristics mean that the insertion effect can be eliminated by adding a complementary secondary minimum phase filter to the hearing aid processing. When adding a filter, both intensity response and phase response can be corrected. If a non-minimum phase filter is used, either the intensity response or the phase response can be corrected, but not both at the same time. The transfer function that compensates for the insertion effect is called the aided transfer function (ATF) and is identical to an HRTF without a hearing aid.
ATFは、鼓膜での直接音(ITFで表す)と増幅音とを集計したもの(combination)である。適切に作動させる該集計(summation)用(for)には、位相遅れが補聴器で増幅された全周波数において120度未満の位相に相当するように、前記複数の音間の時間遅れを最小化しなければならない。したがって、マイクロホンを補聴器の受信器に近接するように移動させたり、補聴器を設計することにより、位相遅れを調整することができる。これらの変化は、設計に不可欠な結果となる。これに対し、ATF用の補償フイルターは、補聴器がデジタルであれば、例えばデジタル信号処理チップを再プログラミングすることにより変化できる。(本発明はデジタル実施形態に限定されない。) ATF is a combination of direct sound (expressed by ITF) and amplified sound on the eardrum. For the summation (for) to operate properly, the time delay between the plurality of sounds must be minimized so that the phase delay corresponds to a phase of less than 120 degrees at all frequencies amplified by the hearing aid. Must be. Therefore, the phase lag can be adjusted by moving the microphone closer to the receiver of the hearing aid or by designing the hearing aid. These changes have essential design consequences. On the other hand, the compensation filter for ATF can be changed if the hearing aid is digital, for example, by reprogramming the digital signal processing chip. (The present invention is not limited to digital embodiments.)
本発明方法を人間の耳に利用するには、耳内レスポンスをプローブマイクロホンで測定する。プローブマイクロホンは外耳道中に配置され、音響的人体解剖模型のような模型によりHRTF,ITF,及びATFを正確に測定する。 To apply the method of the present invention to the human ear, the intraoural response is measured with a probe microphone. The probe microphone is placed in the ear canal and accurately measures HRTFs, ITFs, and ATFs with a model such as an acoustic human anatomy model.
代替の人間への適用法は、主観的音路(subjective path)を取り入れることである。被験者(the subject)が難なく聞けるようなレベルにある原(source)材料を用いて、被験者は、補聴器(HRTF)なしでの原材料認識がATFと釣り合うかどうか尋ねられるであろう。HRTFとATF間の正確なスペクトル差に関して詳細な手引きを提供できる被験者(a subject)によって、人はこれらの測定法と同じフイルターを見出すであろう。このアプローチは音楽家や録音技術者のような熟練した聴取者に最も良く機能する。 An alternative human application is to incorporate a subjective path. Using a source material that is at a level that the subject can easily hear, the subject will be asked if raw material recognition without a hearing aid (HRTF) is commensurate with ATF. With a subject who can provide detailed guidance on the exact spectral differences between HRTFs and ATFs, one will find the same filters as these measurements. This approach works best for experienced listeners such as musicians and recording engineers.
図1は、マイクロホン13,処理器15及びスピーカー17からなるオープンイヤー型補聴器(12)の一例を概略的に示す。ここで符号10で示した入射音は2つの音路A及びB経由で鼓膜11に到達する。直接路Aは、耳覆い(earpiece)(図示せず)周辺(around)を通る音路で、挿入伝達関数(ITF)を特徴とする。増幅路Bは、マイクロホン13,処理器15(補正の等化を提供する。)及びスピーカー17を経由する。矢印Pで示した認識音はこれら2つの音路を経由して鼓膜に到達する音の集計(summation)である。
FIG. 1 schematically shows an example of an open-ear hearing aid (12) including a
オープンイヤー型補聴器から生じる挿入効果の一例を図2に示す。図2は音響的人体解剖模型から得られた伝達関数測定値(measurements)を示す。挿入効果はHRTFとITFとの差である。上図のグラフで示されるように、強度は500Hz以上から異なり(“挿入ロス”)、また下図のグラフで示されるように、位相は500Hz超で異なる。 FIG. 2 shows an example of the insertion effect generated by the open-ear hearing aid. FIG. 2 shows transfer function measurements obtained from an acoustic human anatomy model. The insertion effect is the difference between the HRTF and the ITF. As shown in the graph above, the intensities differ from above 500 Hz (“insertion loss”), and as shown in the graph below, the phases differ above 500 Hz.
図3には、挿入効果は2次(2nd order)最小位相フイルターを用いて補正されることが示されている。ATFとHRTFとの差が、強度及び位相において、1〜8kHzの範囲に亘ってかなり減少していることに注目すべきである。950Hzでの小さい凹み(dig)は、最小位相の共鳴ではない。 3, the insertion effect is shown to be corrected by using a secondary (2 nd order) minimum phase filter. It should be noted that the difference between ATF and HRTF is significantly reduced over the range of 1-8 kHz in intensity and phase. The small dig at 950 Hz is not the smallest phase resonance.
この考え方を図4A及び4Bに最小位相フイルターの例で数学的に示す。安定な逆関係(inverse)を有するいかなる因果律の(causual)フイルターにとっても一般に事実である。この実施形態では補聴器(ITF)により減衰した直接音は、鈴形の減衰用フイルター(“減衰”)としてモデル化される。このフイルターは中心周波数で最小であり、中心周波数から離れて単一に近づく。その(that)2次最小位相フイルターは、数学的に下記4次(biquadratic)方程式で示される。
式中、sはラプラス(Laplace)変数、Wは角度周波数(=2πF、但しFは中心周波数)、Qは品質因子、Gは利得で、この場合、利得は1より大に限定される。このフイルターの伝達関数を図4Aに断続線で示した。
This idea is mathematically shown in FIGS. 4A and 4B with an example of a minimum phase filter. This is generally true for any causual filter that has a stable inverse. In this embodiment, the direct sound attenuated by the hearing aid (ITF) is modeled as a bell-shaped attenuation filter (“attenuated”). This filter is the smallest at the center frequency and approaches a single one away from the center frequency. The (that) second-order minimum phase filter is mathematically represented by the following fourth-order (biquadratic) equation.
In the equation, s is the Laplace variable, W is the angular frequency (= 2πF, where F is the center frequency), Q is the quality factor, and G is the gain. In this case, the gain is limited to greater than 1. The transfer function of this filter is shown intermittently in FIG. 4A.
補聴器のレスポンス“boost(ブースト)”は、利得を有するバンドパスフイルターとしてモデル化される。このフイルターは中心周波数で最大の強度を有し、縁端部ではゼロに近づく。
これらフイルターの鼓膜での集計伝達関数はATFに相当する。下記式3及び式4で示す複数のパラメーター
を有するブーストが単一強度及びゼロ位相レスポンスa(図4B参照)となる所定の固定減衰フイルターを解析的に示すことができる。図4A及び4Bのフイルターのパラメーターは、このような関係に従って選択した。このようなシステムは完全に透明である。
The aggregate transfer function of these filters in the eardrum corresponds to ATF. Multiple parameters represented by the following
It is possible to analytically show a predetermined fixed damping filter in which the boost having a single intensity and zero phase response a (see FIG. 4B). The filter parameters of FIGS. 4A and 4B were selected according to this relationship. Such a system is completely transparent.
この実施形態は並列に集合させた複数のフイルターに相当することに注目すべきである。2つのフイルターを直列に配置した場合は、一方のフイルターは他方のフイルターの出力に作用し、更に単純な条件下、即ち、複数のフイルターが互いに逆関係である場合は単一に集計することが多い。以上概説した数学的見解は、特定の例であり、他の多くのフイルターの組合わせ、2つの鈴形フイルター(2つの4次フイルター)、高パスフイルター及び低パスフイルター等に対して維持することができる。 It should be noted that this embodiment corresponds to a plurality of filters assembled in parallel. When two filters are placed in series, one filter acts on the output of the other filter, and under simpler conditions, i.e., if multiple filters are inversely related to each other, they can be aggregated in a single unit. many. The mathematical view outlined above is a specific example and should be maintained for many other combinations of filters, such as two bell-shaped filters (two quaternary filters), high pass filters and low pass filters. Can be done.
以上の例では、直接音と増幅音間に時間遅れがないと推定した。したがって、ピークの周波数では位相シフトはなく、周囲の周波数では位相シフトは無視できるので、これらの音は、鼓膜において合算される。このような条件は、補聴器に遅れ時間がなく、マイクロホンと補聴器間の距離(又は伝播時間)が殆どない場合に適合する。
In the above example, it is estimated that there is no time delay between the direct sound and the amplified sound. Therefore, since there is no phase shift at the peak frequency and the phase shift is negligible at the surrounding frequencies, these sounds are added up in the eardrum. Such conditions are suitable when the hearing aid has no delay time and there is little distance (or propagation time) between the microphone and the hearing aid.
増幅音が充分に遅れるならば、直接音に対し位相を180度ほど(by)シフトさせる周波数が存在する。鼓膜において集計されると、これらの音は互いに集計音に対して破壊的に作用し、集計音を消去する。所定周波数での増幅音:直接音の相対強度は、前記消去が完全である(同等の強度)か、部分的である(同等ではない強度)かどうかを決定する。 If the amplified sound is delayed sufficiently, there is a frequency that shifts the phase by about 180 degrees with respect to the direct sound. When aggregated in the eardrum, these sounds act destructively on each other and eliminate the aggregated sound. Amplified sound at a predetermined frequency: The relative intensity of the direct sound determines whether the erasure is complete (equivalent intensity) or partial (non-equivalent intensity).
殆どの補聴器には少なくとも1.5msの遅れ時間(latency)があり、それより長くなければ、重要な消去が行えるし、ITFの適切な補償を防止する。このような例は、パンドパスフイルターに純粋な遅れ(delay)を加えることによりモデル化される。図5A及び5Bに示すように、遅れは線状の位相レスポンスを有する。1.5msの遅れに対しては、次の2つの顕著な効果がある。1)中心周波数での強度レスポンスは増幅音単独未満である。2)中心周波数周辺には広範の梳き性(combining)がある。この梳き性フイルタリング(comb filtering)は、−10dB未満の利得を有し、また入力信号を顕著に歪める数個のノッチを有する。
Most hearing aids have at least 1.5ms delay time (latency), if not longer than, to perform important erase, preventing proper compensation of ITF. Such an example is modeled by adding a pure delay to the Pandopath filter. As shown in FIGS. 5A and 5B, the lag has a linear phase response. There are two significant effects on the 1.5 ms delay: 1) The intensity response at the center frequency is less than the amplified sound alone. 2) There is a wide range of combining around the center frequency. This comb filtering has a gain of less than -10 dB and has several notches that significantly distort the input signal.
マイクロホンの遅れは、マイクロホンと受信機間の距離を短縮することにより、低減できる。処理回路構成(処理回路構成は必ずしも必要ではないが、恐らくデジタル処理器である。)中に遅れを加えるか、或いは受信器から更に離れてマイクロホンを移動することにより、マイクロホンの遅れは増大できる。 The microphone delay can be reduced by reducing the distance between the microphone and the receiver. The microphone delay can be increased by adding a delay in the processing circuit configuration (the processing circuit configuration is not necessary, but probably a digital processor), or by moving the microphone further away from the receiver.
図6のブロックダイアグラムは、本発明に従って補聴器の挿入効果を補正する前述の基本工程を示す。第一工程として、外耳道への補聴器の挿入効果を決定しなければならない(ブロック102)。挿入効果は,前述のように、外耳道中に存在する補聴器と外耳道中で移動させた補聴器の両者について測定することにより達成できる。(前述のように、挿入効果は着用者による入力から、主観的に達成できる。)いったん、補聴器の外耳道への挿入効果が決定されたならば、引続き、強度及び位相両者の補正が可能である(ブロック103)。 The block diagram of FIG. 6 shows the aforementioned basic steps of correcting the insertion effect of a hearing aid according to the present invention. As a first step, the effect of inserting the hearing aid into the ear canal must be determined (block 102). The insertion effect can be achieved by measuring both the hearing aid present in the ear canal and the hearing aid moved in the ear canal, as described above. (As described above, the insertion effect can be subjectively achieved from the input by the wearer.) Once the effect of inserting the hearing aid into the ear canal is determined, both strength and phase can be continuously corrected. (Block 103).
図7は音響的人体解剖模型(acoustic manikin)を用いてこの補正を決定する際のこれらの工程を詳細に示す。音響的人体解剖模型は、鼓膜の所で平均周波数のレスポンスにシミュレートするように設計されて、耳外側(outside ear)の背後に埋設されたマイクロホンを供給する(provide)(ブロック104)。外耳道が閉塞されないように、人体解剖模型の耳から移動した補聴器で頭部伝達関数(HRTF)を測定する(ブロック105)。次に、補聴器を人体解剖模型の外耳道内に配置する(ブロック106)ことにより、電源が切られている(turned off)補聴器で複雑な挿入伝達関数(ITF)を測定することができる(ブロック107)。こうして測定されたHRTF及びITFにより、外耳道への補聴器の挿入効果に対して補正するのに必要な等化を決定することができる(ブロック108)。前述のように、補正に対する等化は、HRTF測定値:ITF測定値の比となる。この補正は補聴器に適用することができる(ブロック109)。次に、得られた補助(aided)伝達関数(ATF)を測定し、HRTFと比較することができる。
FIG. 7 details these steps in determining this correction using an acoustic manikin. The acoustic human anatomy model is designed to simulate an average frequency response at the eardrum and provides a microphone embedded behind the outside ear (block 104). Head-related transfer functions (HRTFs) are measured with a hearing aid that is moved from the ear of a human anatomical model so that the ear canal is not obstructed (block 105). Then, hearing aid by placing the ear canal of the human anatomy model (block 106), it can be measured power is off the (Turned off) complex insertion transfer function hearing aid (ITF) (Block 107 ). The HRTFs and ITFs thus measured can determine the equalization required to compensate for the effect of hearing aid insertion into the ear canal (block 108). As mentioned above, the equalization to the correction is the ratio of HRTF measurement value: ITF measurement value. This correction can be applied to hearing aids (block 109). The resulting aided transfer function (ATF) can then be measured and compared to the HRTF.
音響的人体解剖模型により挿入効果を補正するため、図7に示した複数の工程は、生身の人間を用いても採用することができる。この場合、測定は鼓膜上のプローブマイクロホンで行われる。 Since the insertion effect is corrected by the acoustic human anatomy model, the plurality of steps shown in FIG. 7 can also be adopted by using a living human being. In this case, the measurement is made with a probe microphone on the eardrum.
補正をきれいに調和させて(to fine tune)最適ATFに到達させるため、前記複数の工程は繰返し行えることが理解される。 It is understood that the plurality of steps can be repeated in order to reach the optimum ATF by fine tune the correction.
以上、本発明を明細書中でかなり詳細に説明したが、本発明は特許請求の範囲で必要とされる他は、このような詳細な説明に限定されるものではないことは理解されよう。 Although the present invention has been described in considerable detail in the present specification, it will be understood that the present invention is not limited to such detailed description except that it is required within the scope of claims.
Claims (27)
前記補聴器が耳内にあり電源が切られている時、補聴器の挿入効果を決定する工程であって、該挿入効果は、強度レスポンス及び位相レスポンスを持った複雑な挿入伝達関数(ITF)で特定される工程と、
前記挿入伝達関数(ITF)の強度レスポンス及び位相レスポンスの両者を補正することにより、前記挿入効果に対し補正する工程であって、前記位相レスポンスが最小位相である場合、位相レスポンスだけ補正される該工程と、
を含む前記方法。 When a user wears a hearing aid, at least part of the hearing aid is a method of correcting the intensity distortion and phase distortion of the hearing aid that is inserted into the ear .
When the hearing aid is that uncut is Ri power ear near, comprising the steps of determining the insertion effect of the hearing aid, the insert effect is a complex insertion transfer function having an intensity response and phase response (ITF) and as the factory to be specific,
In the step of correcting the insertion effect by correcting both the intensity response and the phase response of the insertion transfer function (ITF), when the phase response is the minimum phase, only the phase response is corrected. Process and
The method comprising.
該補聴器が耳内にあり電源が入れられている時の補聴器の遅れ時間が該補聴器で増幅された最高周波数の周期の約1/3未満となるように補聴器を構成する工程と、
複雑なITFの強度レスポンスに対して補正する工程と、
位相レスポンスが最小位相である場合はいつでも複雑な挿入伝達関数(ITF)の位相レスポンスに対して補正する工程と、
を含む前記方法。 A complex insertion transmission function (ITF) that, when worn by the user, is at least partially inserted into the ear and has a strong and phase response when the hearing aid is in the ear and turned off. ) Is a method of correcting intensity distortion and phase distortion in the hearing aid, which produces the insertion effect specified by .
The process of configuring the hearing aid so that the delay time of the hearing aid when it is in the ear and turned on is less than about 1/3 of the period of the highest frequency amplified by the hearing aid.
The process of correcting the complex ITF intensity response and
Whenever the phase response is the minimum phase, the process of correcting for the complex insertion transfer function (ITF) phase response and
The method comprising.
マイクロホンと、
耳に挿入可能のスピーカーであって、補聴器を着用した時のマイクロホンとスピーカー間の距離は、補聴器の待ち時間が補聴器で増幅された最大波長期間の約1/3未満となるように選択される該スピーカーと、
マイクロホンとスピーカー間に設けた処理器と、
を備え、補聴器の少なくともスピーカーは補聴器を耳に挿入した時、強度レスポンス及び位相レスポンスを有する複雑な挿入伝達関数(ITF)を特徴とする挿入効果を創生し、前記処理器は挿入伝達関数(ITF)の強度レスポンス及び位相レスポンスの両者、但し位相レスポンスは最小位相である場合のみ、を補正することにより、挿入効果に対して補正するように構成された補聴器。 A hearing aid that, when worn by the user, is at least partially inserted into the ear and produces amplified sound in one or more selected frequency bands .
And a microphone,
Ear-insertable speakers, the distance between the microphone and the speaker when wearing the hearing aid is selected so that the hearing aid wait time is less than about one-third of the maximum wavelength period amplified by the hearing aid. and the speaker,
The processor installed between the microphone and the speaker ,
The provided, at least when the speaker of the hearing aid is inserted in the ear hearing aid, an insertion effect, wherein a complex insertion transfer function (ITF) having an intensity response and phase response without wounds, said processor is inserted transfer function ( intensity response and the phase response both ITF), provided that only if the phase response is minimum phase, by correcting the, configured hearing aids to compensate for the insertion effect.
The hearing aid according to claim 25, wherein the minimum phase secondary filter is a quaternary filter.
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GB9026906D0 (en) * | 1990-12-11 | 1991-01-30 | B & W Loudspeakers | Compensating filters |
US5325436A (en) * | 1993-06-30 | 1994-06-28 | House Ear Institute | Method of signal processing for maintaining directional hearing with hearing aids |
US5825894A (en) * | 1994-08-17 | 1998-10-20 | Decibel Instruments, Inc. | Spatialization for hearing evaluation |
AU4676199A (en) * | 1998-06-29 | 2000-01-17 | Resound Corporation | High quality open-canal sound transduction device and method |
DE10318191A1 (en) * | 2003-04-22 | 2004-07-29 | Siemens Audiologische Technik Gmbh | Producing and using transfer function for electroacoustic device such as hearing aid, by generating transfer function from weighted base functions and storing |
JP4643651B2 (en) * | 2004-10-19 | 2011-03-02 | ヴェーデクス・アクティーセルスカプ | Adaptive microphone matching system and method in hearing aids |
DK1750483T3 (en) * | 2005-08-02 | 2011-02-21 | Gn Resound As | Hearing aid with wind noise suppression |
EP2177046B2 (en) * | 2007-08-14 | 2020-05-27 | Insound Medical, Inc | Combined microphone and receiver assembly for extended wear canal hearing devices |
DE102008024490B4 (en) * | 2008-05-21 | 2011-09-22 | Siemens Medical Instruments Pte. Ltd. | Filter bank system for hearing aids |
US8355517B1 (en) * | 2009-09-30 | 2013-01-15 | Intricon Corporation | Hearing aid circuit with feedback transition adjustment |
US8588441B2 (en) * | 2010-01-29 | 2013-11-19 | Phonak Ag | Method for adaptively matching microphones of a hearing system as well as a hearing system |
CN104205878B (en) * | 2012-03-23 | 2017-04-19 | 杜比实验室特许公司 | Method and system for head-related transfer function generation by linear mixing of head-related transfer functions |
US9082389B2 (en) * | 2012-03-30 | 2015-07-14 | Apple Inc. | Pre-shaping series filter for active noise cancellation adaptive filter |
ES2728724T3 (en) * | 2012-08-15 | 2019-10-28 | Meyer Sound Laboratories Incorporated | Hearing aid with level and frequency dependent gain |
US9426589B2 (en) * | 2013-07-04 | 2016-08-23 | Gn Resound A/S | Determination of individual HRTFs |
EP3138301B1 (en) * | 2014-04-28 | 2019-11-20 | Linear SRL | Method and apparatus for preserving the spectral cues of an audio signal altered by the physical presence of a digital hearing aid and tuning thereafter |
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