Abstract:
This document provides a hearing assistance device for playing processed sound inside a wearer&#39;s ear canal, the hearing assistance device comprising a first housing, signal processing electronics disposed at least partially within the first housing, a first microphone connected to the first housing, the first microphone adapted for reception of sound, a second microphone configured to receive sound from inside the wearer&#39;s ear canal when the hearing assistance device is worn and in use and microphone mixing electronics in communication with the signal processing electronics and in communication with the first microphone and the second microphone, the microphone mixing electronics adapted to combine low frequency information from the first microphone and high frequency information from the second microphone to produce a composite audio signal.

Description:
RELATED APPLICATIONS 
     This application is a continuation of and claims the benefit of priority under 35 U.S.C. §120 to U.S. patent application Ser. No. 13/341,555, filed Dec. 30, 2011, which application is a continuation of and claims the benefit of priority under 35 U.S.C. §120 to U.S. patent application Ser. No. 12/174,450, filed on Jul. 16, 2008, which issued on Jan. 31, 2012 as U.S. Pat. No. 8,107,654, which is a continuation-in-part of and claims the benefit of priority under 35 U.S.C. §120 to U.S. Ser. No. 12/124,774, filed on May 21, 2008, the benefit of priority of each of which is claimed hereby, and each of which are incorporated by reference herein in their entirety. 
    
    
     TECHNICAL FIELD 
     This document relates to hearing assistance devices and more particularly to hearing assistance devices providing enhanced spatial sound perception. 
     BACKGROUND 
     Behind-the-ear (BTE) designs are a popular form factor for hearing assistance devices, including hearing aids. BTE&#39;s allow placement of multiple microphones within the relatively large housing when compared to in-the-ear (ITE) and completely-in-the-canal (CIC) form factor housings. One drawback to BTE hearing assistance devices is that the microphone or microphones are positioned above the pinna of the user&#39;s ear. The pinna of the user&#39;s ear, as well as other portions of the user&#39;s body, including the head and torso, provide filtering of sound received by the user. Sound arriving at the user from one direction is filtered differently than sound arriving from another direction. BTE microphones lack the directional filtering effect of the user&#39;s pinna, especially with respect to high frequency sounds. Custom hearing aids, such as CIC devices, have microphones placed at or inside the entrance to the ear canal and therefore do capture the directional filtering effects of the pinna, but many people prefer to wear BTE&#39;s rather than these custom hearing aids because of comfort and other issues. CICs typically only have omni-directional microphones because the port spacing necessary to accommodate directional microphones is too small. Also, were a CIC to have a directional microphone, the reflections of sound from the pinna could interfere with the relationship of sound arriving at the two ports of the directional microphone. There is a need to be able to provide the directional benefit obtained from a BTE while also providing the natural pinna cues that affect sound quality and spatialization of sound. 
     SUMMARY 
     This document provides method and apparatus for providing users of hearing assistance devices, including hearing aids, with enhanced spatial sound perception. In one embodiment, a hearing assistance device for enhanced spatial perception includes a first housing adapted to be worn outside a user&#39;s ear canal, a first microphone mechanically coupled to the first housing, hearing assistance electronics coupled to the first microphone and a second microphone coupled to the hearing assistance electronics and adapted for wearing inside the user&#39;s ear canal, wherein the hearing assistance electronics are adapted to generate a mixed audio output signal including sound received using the first microphone and sound received using the second microphone. In one embodiment, a hearing assistance device is provided including hearing assistance electronics adapted to mix low frequency components of acoustic sounds received using the first microphone with high frequency components of sound received using the second microphone. In one embodiment, a hearing assistance device is provided including hearing assistance electronics adapted to extract spatial characteristics from sound received using the second microphone and generate a modified first signal, wherein the modified first signal includes sound received using the first microphone and enhanced components of the extracted spatial characteristics. One method embodiment includes receiving a first sound using a first microphone positioned outside a user&#39;s ear canal, receiving a second sound using a second microphone positioned inside the user&#39;s ear canal, mixing the first and second sound electronically to form an output signal and converting the output signal to emit a sound inside the user&#39;s ear canal using a receiver, wherein mixing the first and second sound electronically to form an output signal includes electronically mixing low frequency components of the first sound with high frequency components of the second sound. 
     This Summary is an overview of some of the teachings of the present application and is not intended to be an exclusive or exhaustive treatment of the present subject matter. Further details about the present subject matter are found in the detailed description and the appended claims. The scope of the present invention is defined by the appended claims and their equivalents. 
    
    
     
       BRIEF DESCRIPTION OF DRAWINGS 
         FIG. 1A  is a block diagram of a hearing assistance device according to one embodiment of the present subject matter. 
         FIG. 1B  illustrates a hearing assistance device according to one embodiment of the present subject matter. 
         FIG. 2  is a signal flow diagram of microphone mixing electronics of a hearing assistance device according to one embodiment of the present subject matter. 
         FIG. 3A  illustrates frequency responses of a low-pass filter and a high-pass filter of microphone mixing electronics according to one embodiment of the present subject matter. 
         FIG. 3B  illustrates examples of high and low pass filter frequency responses of microphone mixing electronics according to one embodiment of the present subject matter. 
         FIG. 4  is a signal flow diagram of microphone mixing electronics according to one embodiment of the present subject matter. 
         FIG. 5  is a flow diagram of microphone mixing electronics according to one embodiment of the present subject matter. 
     
    
    
     DETAILED DESCRIPTION 
     The following detailed description of the present invention refers to subject matter in the accompanying drawings which show, by way of illustration, specific aspects and embodiments in which the present subject matter may be practiced. These embodiments are described in sufficient detail to enable those skilled in the art to practice the present subject matter. References to “an”, “one”, or “various” embodiments in this disclosure are not necessarily to the same embodiment, and such references contemplate more than one embodiment. The following detailed description is, therefore, not to be taken in a limiting sense, and the scope is defined only by the appended claims, along with the full scope of legal equivalents to which such claims are entitled. 
     Behind-the-ear (BTE) designs are a popular form factor for hearing assistance devices, particularly with the development of thin-tube/open-canal designs. Some advantages of the BTE design include a relatively large amount of space for batteries and electronics and the ability to include a large directional or multiple omni-directional microphones within the BTE housing. 
     One disadvantage to the BTE design is that the microphone, or microphones, are positioned above the user&#39;s pinna and, therefore, the spatial effects of the pinna are not received by the BTE microphone(s). In general, sounds arriving at a person&#39;s ear experiences a head related transfer function (HRTF) that filters the sound differently depending on the direction, or angle, from which the sound arrived. A sound wave arriving from in front of a person is filtered differently than sound arriving from behind the person. This filtering is due in part to the person&#39;s head and torso and includes effects resulting from the shape and position of the pinna with respect to the direction of the sound wave. The pinna effects are most pronounced with sound waves of higher frequency, such as frequencies characterized by wavelengths of the same as or smaller than the physical dimensions of the head and pinna. Spectral notches that occur at high frequencies and vary with elevation or arrival angle no longer exist when using a BTE microphone positioned above the pinna. Such notches provide cues used to inform the listener at which elevation and/or angle a sound source is located. Without the filtering effects of the pinna, high frequency sounds received by the BTE microphone contain only subtle cues, if any, as to the direction of the sound source and result in confusion for the listener as to whether the sound source is in front, behind or to the side of the listener. 
     Loss of pinna and ear canal effects can also impair the externalization of sound where sound sources no longer sound as if spatially located a distance away from the listener. Externalization impairment can also result in the listener perceiving that sound sources are within the listeners head or are located mere inches from the listeners ear. 
     Therefore, sounds received by a CIC device microphone include more pronounced directional cues as to the direction and elevation of sound sources compared to a BTE device. However, current CIC housings limit the ability to use directional microphones. Directional microphones, as opposed to omni-directional microphones, assist users hearing certain sound sources by directionally attenuating unwanted sound sources outside the direction reception field of the microphone. Although omni-directional microphones used in CIC devices provide directional cues to the listener. 
     The following detailed description refers to reference characters M o  and M i . The reference characters are used in the drawings to assist the reader in understanding the origin of the signals as the reader proceeds through the detailed description. In general, M o  relates to a signal generated by a first microphone positioned outside of the ear and typically situated in a behind-the-ear portion of a hearing assistance device, such as a BTE hearing assistance device or Receiver-in-canal (RIC) hearing assistance device. M i  relates to a signal generated by a second microphone for receiving sound from a position proximal to the wearer&#39;s ear canal, such sound having pinna cues. It is understood that BTE&#39;s, RIC&#39;s and other types of hearing assistance devices may include multiple microphones outside of the ear, any of which may provide the M o  microphone signal alone or in combination. 
       FIG. 1A  illustrates a block diagram of a hearing assistance device according to one embodiment of the present subject matter.  FIG. 1A  shows a hearing assistance device housing  115 , including a first microphone  101  and hearing assistance electronics  117 , a receiver (or speaker)  116  and a second microphone  102 . In various embodiments, the housing  115  is adapted to be worn behind or over the ear and the first microphone  101  is therefore worn above the pinna of a wearer&#39;s ear. In various embodiments, the receiver  116  is either mounted in the housing (e.g., as in a BTE design) or adapted to be worn in an ear canal of the user&#39;s ear (e.g., as in a receiver-in-canal design). In various embodiments, the second microphone  102  is adapted to receive sound from the entrance of the ear canal of the user&#39;s ear. In some embodiments, the second microphone  102  is adapted to be worn in the user&#39;s ear canal. In various embodiments, where the receiver is adapted to be worn in the user&#39;s ear canal, some designs include a second housing connected to the receiver, for example an ITE housing, a CIC housing, an earmold housing, or an ear bud. In various embodiments, a second microphone adapted to be worn in the user&#39;s ear canal, includes a second housing connected to the second microphone, for example an ITE housing, a CIC housing, an earmold housing, or an ear bud. In various embodiments, the second microphone  102  is housed in an outside-the-canal housing, for example a BTE housing, and includes a sound tube extending from the housing to inside the user&#39;s ear canal. 
     In the illustrated embodiment, the hearing assistance electronics  117  receive a signal (M o ) 105  from the first microphone  101 , and a signal (M i ) 108  from the second microphone  102 . An output signal  120  of the hearing assistance electronics is connected to the receiver  116 . The hearing assistance electronics  117  include microphone mixing electronics  103  and other processing electronics  118 . The other processing electronics  118  include an input coupled to an output  104  of the mixing circuit  103  and an output  120  coupled to the receiver  116 . In various embodiments, the other processing electronics  118  apply hearing assistance processing to an audio signal  104  received from the microphone mixing circuit  103  and transmits an audio signal to the receiver  116  for broadcast to the user&#39;s ear. General amplification, frequency band filtering, noise cancellation, feedback cancellation and output limiting are examples of functions the other processing electronics  118  may be adapted to perform in various embodiments. 
     In various embodiments, the microphone mixing circuit  103  combines spatial cue information received using the second microphone  102  and speech information of lower audible frequencies received using the first microphone  101  to generate a composite signal. In various embodiments, the hearing assistance electronics include analog or digital components to process the input signals. In various embodiments, the hearing assistance electronics includes a controller or a digital signal processor (DSP) for processing the input signals. In various embodiments, the first microphone  101  is a directional microphone and the second microphone  102  is an omni-directional microphone. 
       FIG. 1B  illustrates a hearing assistance device  100  according to one embodiment of the present subject matter. The illustrated device  100  includes a housing  135  adapted to be worn on, about or behind a user&#39;s ear and to enclose hearing assistance electronics, including microphone mixing electronics according to the teachings set forth herein. The device also includes a first microphone  131  integrated with the housing, an ear bud  120  for holding a second microphone  132  and a receiver  136 , or speaker, a cable assembly  121  for connecting the receiver  136  and second microphone  132  to the hearing assistance electronics. It is understood that optional means for stabilizing the position of the ear bud  120  in the user&#39;s ear may be included. It is understood that the cable assembly  121  provides a plurality of wires for electrically connecting the receiver  136  and the second microphone  132 . In one embodiment, four wires are used. In one embodiment, three wires are used. Other embodiments are possible without departing from the scope of the present subject matter. 
       FIG. 2  illustrates a signal flow diagram of microphone mixing electronics of a hearing assistance device according to one embodiment of the present subject matter. The mixer of  FIG. 2  shows a first microphone (M o ) signal  205  that is low-pass filtered through low-pass filter  207  and combined by summer  206  with a high-pass filtered second microphone (M i ) signal  208  from high pass filter  209 . The first microphone signal  205  is produced by a microphone external to a wearer&#39;s ear canal and the second microphone signal  208  is produced by a microphone receiving sound proximal with the ear canal of the user. The microphone mixing electronics  203  combine low frequency information received from the first microphone signal  205  and high frequency information received from the second microphone signal  208  to form a composite output signal  204 . In various embodiments, the high-pass filter  209  is a band-pass filter that passes the high frequency information used for spatial cues. 
     In various embodiments, the cutoff frequency of the low-pass filter f cL  is approximately the same as the cutoff frequency of the high-pass filter f cH . In various embodiments, the cutoff frequency of the low-pass filter f cL  higher than the cutoff frequency of the high-pass filter f cH .  FIG. 3A  illustrates frequency responses of the low-pass filter and the high-pass filter where the cutoff frequency of the low pass filter, f cL  is approximately equal to the cutoff frequency of the high-pass filter f cH . The values of the cutoff frequencies are adjustable for specific purposes. In some embodiments, a cutoff frequency of about 3 KHz is used. In some embodiments a cutoff frequency of approximately 5 KHz is used. In various embodiments, the cutoff frequencies are programmable. The present system is not limited to these frequencies, and other cutoff frequencies are possible without departing from the scope of the present subject matter. 
       FIG. 3B  illustrates high and low pass filter frequency responses of the microphone mixing electronics according to one embodiment of the present subject matter where the low-pass filter cutoff frequency is higher than the high-pass filter cutoff frequency. In various embodiments, the cutoff frequencies are programmable. In various embodiments, the values for the cutoff frequencies are between approximately 1 KHz and approximately 6 KHz. Other ranges possible without departing from the scope of the present subject matter. In various embodiments, the cutoff frequencies are programmable. In various embodiments, the value of the high-pass filter cutoff frequency is limited to be less than the value of the low-pass filter cutoff frequency. 
     In various embodiments, a hearing assistance device according to the present subject matter can be programmed to select between one or more cutoff frequencies for the low and high-pass filters. For example, the cutoff frequencies may be selected to enhance speech. The cutoff frequencies may be selected to enhance spatial perception. 
     A user in a crowded room trying to talk one on one with another person may select a higher cut-off frequency. Selecting a higher cut-off frequency emphasizes the external microphone over the ear canal microphone. In general, information contributing to intelligibility resides in the low-frequency part of the spectrum of speech. Emphasizing the low frequencies helps the user better understand target speech. In some embodiments, low frequencies are emphasized with the use of directional filtering of the external microphone. In contrast, lowering the cutoff frequency emphasizes the ear-canal microphone and thereby spatial cues conveyed by high frequencies. As a result, the user gets a better sense of where multiple sound sources are located around them and thereby facilitates, for example, the ability to switch between listening to different people in a crowded room. 
       FIG. 4  illustrates a signal flow diagram of microphone mixing electronics according to one embodiment of the present subject matter.  FIG. 4  shows a composite output signal  404  produced by a feature generator module  411  using a low-pass filtered first microphone (M o ) signal  405  and an output from a notch feature detector  412  based on the second microphone signal  408 . The composite output signal  404  of the microphone mixing electronics  403  includes low frequency components of the first microphone signal  405  and spatial cue information derived from the notch feature detection of the second microphone signal  408 . 
     The composite output signal  404  also includes features derived and created from the second microphone signal  408 . In general, the second microphone signal  408  includes significant spatial cues resulting from sound received in the ear canal. The spatial cues result from the filtering effects of the user&#39;s head and torso, including the pinna and ear canal. The notch feature detector  412  quantifies the spatial features of the second microphone signal  408  and passes the data to the feature generator  411 . In various embodiments, the notch feature detector  412  uses parametric spectral modeling to identify spatial features in the second microphone signal  408 . The feature generator  411  modifies the filtered first microphone signal with data received from the notch feature detector  412  and indicative of the spatial cues detected from the second microphone signal  408 . In various embodiments, the feature generator adds frequency data to create tones indicative of spatial cues detected in the second microphone signal. The frequency of the tones depends on the spatial features detected in the second microphone signal. In some embodiments, noise is added to the filtered first microphone signal using the feature generator  411 . The bandwidth of the noise depends on the spatial features detected in the second microphone signal  408 . In various embodiments, the feature generator  411  adds one or more notches in the spectrum of the filtered first microphone signal. The frequency of the notches depends on the spatial features detected in the second microphone signal  408 . In some situations, the feature generator  411  generates artificial spatial cue at frequencies different than the spatial cues, or spatial features, detected in the second microphone signal  408 , to accommodate hearing impairment of the user. In various embodiments, artificial spatial cues are created in the composite output signal at lower frequencies then the frequencies of cues detected in the second microphone signal  408  to accommodate hearing impairment of the user. It is understood that the described embodiments of the microphone mixing electronics may be implemented using a combination of analog devices and digital devices, including one or more microprocessors or a digital signal processor (DSP). 
       FIG. 5  illustrates a flow diagram of microphone mixing electronics according to one embodiment of the present subject matter. The microphone mixing electronics  503  include a low pass filter  510  applied to a first microphone (M o ) signal  505  from a microphone receiving sound from outside a user&#39;s ear canal, a high-pass filter  514  applied to a second microphone (M i ) signal  508  from a microphone receiving sound from inside a user&#39;s ear canal, a processing junction  506  combining the output of the low pass filter  510  and the high pass filter  514  to form a composite signal  520 , a notch feature detector  512  for detecting spatial cues detected in the second microphone signal  508 , and a feature generator  511  for modifying the composite signal  520  with information from the notch feature detector  512  to generate spatial features indicative of spatial cues detected in the second microphone signal  508 . 
     The composite signal  520  of the microphone mixing electronics include low frequency components of the first microphone signal  505  and high frequency components of the second microphone signal  508 . The low frequency components of the composite signal  520  are derived from applying the low pass filter  510  to the first microphone signal  505 . In general, low frequency sound received from a microphone external to a user&#39;s ear or near the external opening of the user&#39;s ear canal, includes most components of perceptible speech but lacks some important spatial cues. The low pass filter  510  preserves the speech content of the first microphone signal  505  in the composite signal  520 . The second microphone signal  508  includes significant spatial cues, or spatial features, as a result of filtering of the signal by the user&#39;s head and torso. The high pass filter  514  preserves spatial features of the second microphone signal  508  in higher acoustic frequencies, including frequencies above about 1 kHz. The processing junction  506  generates a composite signal  520  using the output signal data from the low-pass  510  and high-pass  514  filters. 
     In the illustrated embodiment, the composite output signal  504  of the microphone mixing electronics  503  includes additional features derived and created from the second microphone signal  508 . From above, the second microphone signal  508  includes significant spatial cues resulting from sound received in the user&#39;s ear canal. The notch feature detector  512  quantifies the spatial features of the second microphone signal  508  and passes the data to the feature generator  511 . In various embodiments, the notch feature detector  512  uses parametric spectral modeling to identify spatial features in the second microphone signal  508 . The feature generator  511  modifies the composite signal  520  with data received from the notch feature detector and indicative of the spatial cues detected from the second microphone signal  508 . In various embodiments, the feature generator  511  adds frequency data to create tones indicative of spatial cues detected in the second microphone signal  508 . The frequency of the tones depends on the spatial features detected in the second microphone signal. In some embodiments, noise is added to the composite signal  520  using the feature generator  511 . The bandwidth of the noise depends on the spatial features detected in the second microphone signal  508 . In various embodiments, the feature generator  511  modifies the spectrum of the composite signal  520  with one or more notches. The frequency of the notches depends on the spatial features detected in the second. signal  508 . In some situations, the feature generator  511  generates artificial spatial cue at frequencies different than the spatial cues, or spatial features, detected in the second microphone signal  508 , to accommodate hearing impairment of the user. In various embodiments, artificial spatial cues are created in the composite output signal at lower frequencies then the frequencies of cues detected in the second microphone signal  408  to accommodate hearing impairment of the user. It is understood that the described embodiments of the microphone mixing electronics may be implemented using a combination of analog devices and digital devices, including one or more microprocessors or a digital signal processor (DSP). 
     In various embodiments, the feature generator  511  includes a filter. The output composite signal  504  includes signal components generated by applying the filter to the first microphone signal  505 . One or more coefficients of the filter are determined from the second microphone signal  508  using parametric spectrum modeling. In various embodiments, the coefficients operate through the filter to modify the first microphone signal with high frequency notches to emphasize higher frequency spatial components in the composite output signal  504 . 
     In various embodiments, the feature generator  511  includes one or more notch filters. In some embodiments, the frequency range of the one or more notch filters overlap. In various embodiments, one or more notch frequencies for the notch filters is selected from a range bounded by and including about 6 kHz at the low end to approximately 10 kHz at the high end. Other ranges possible without departing from the scope of the present subject matter. The notch filters modify the first microphone signal with high frequency notches to emphasize higher frequency spatial components in the composite output signal  504 . 
     The present subject matter includes hearing assistance devices, including but not limited to, cochlear implant type hearing devices, hearing aids, such as behind-the-ear (BTE), and Receiver-in-the-ear (RIC) hearing aids. It is understood that behind-the-ear type hearing aids may include devices that reside substantially behind the ear or over the ear. Such devices may include hearing aids with receivers associated with the electronics portion of the behind-the-ear device, or hearing aids of the type having receivers in the ear canal of the user. It is understood that other hearing assistance devices not expressly stated herein may fall within the scope of the present subject matter. 
     This application is intended to cover adaptations or variations of the present subject matter. It is to be understood that the above description is intended to be illustrative, and not restrictive. The scope of the present subject matter should be determined with reference to the appended claims, along with the full scope of legal equivalents to which such claims are entitled.