Abstract:
The present invention is an apparatus for and method of remotely, automatically, and routinely conducting diagnostic testing on a programmable hearing aid to ensure that it is functioning as intended when optimized for an individual&#39;s needs and preferences. Because hearing aids deteriorate with time and buildup of earwax, individuals can be uncertain whether their hearing is worsening or the hearing aid is malfunctioning. The net effect is diminished hearing aid performance—and thus diminished quality of life. The present invention tests the hearing aid for proper function as frequently as daily.

Description:
CROSS REFERENCE TO RELATED APPLICATION  
       [0001]     This application claims the benefit of U.S. Provisional Application Nos. 60/579,220 filed Jun. 14, 2004 and 60/579,479 filed Jun. 14, 2004, assigned to the assignee of this application and incorporated by reference herein. 
     
    
     FIELD OF THE INVENTION  
       [0002]     The present invention relates to hearing aids, specifically to a method of and apparatus for automatically testing an individual&#39;s hearing aid in the individual&#39;s home as frequently as daily in order to determine whether the hearing aid needs to be cleaned or serviced.  
       BACKGROUND OF THE INVENTION  
       [0003]     About two million hearing aids are sold annually in the U.S., generating $2.6 billion in revenue. Although 28 million Americans are hearing impaired, only six million use hearing aids. Year after year, market penetration has increased little, making it apparent that factors other than user need have inhibited market penetration of hearing aids. Central among these factors is the product-centric (as opposed to patient-centric) approach that the hearing aid industry has taken to fitting hearing aids. Hearing aid manufacturers concentrate efforts almost solely on improving their devices, most notably with digital signal processing&#39;s (DSP), while other patient needs and preferences are virtually ignored. Resources have not gone to improving the consequently ponderous process which patients face in purchasing, using, and maintaining a hearing aid.  
         [0004]     The anatomy of the ear canal includes ceruminous glands that secrete a yellowish, wax-like substance called cerumen (earwax), which accumulates in the ear canal. Due to both the action of cilia located in the ear canal and the natural movements of the ear canal, the cerumen gradually migrates outward. When a hearing aid is inserted into the ear canal, it is susceptible to the effects of cerumen accumulation and migration. Cerumen often mixes with sloughed off skin and dirt, further impairing the performance of the hearing aid.  
         [0005]     Acoustic speakers in most modern hearing aids are particularly susceptible to performance problems and damage from cerumen accumulation; initially, cerumen blocks the speaker port, occluding the acoustic path, in turn preventing sound waves from reaching the tympanic membrane. Eventually, the cerumen can penetrate the receiver housing, damaging the sensitive mechanical and electrical components whose failure necessitates repair or replacement of the hearing aid. Not only is the cost in time and money significant, but also individuals are uncertain whether their hearing is worsening or the hearing aid is malfunctioning. The net effect is diminished hearing-aid performance—and thus a diminished quality of life.  
         [0006]     U.S. Pat. No. 6,349,790, entitled, “Self-cleaning cerumen guard for a hearing device,” assigned to Sonic Innovations and incorporated by reference herein, describes a thermally activated cleaning element on the distal end of a hearing aid adjacent to the speaker, which retracts when heated by the inner ear to body temperature, then extends when cooled to room temperature. Upon removal of the hearing aid from the ear, the self-cleaning cerumen guard automatically removes any debris that has accumulated in the speaker port.  
         [0007]     U.S. Pat. No. 5,401,920, entitled, “Cerumen filter for hearing aids,” and incorporated by reference herein, discloses a replaceable and disposable wax guard that is affixed over the sound port of an in-the-ear hearing aid by means of a pressure sensitive tape. The filter itself is porous to sounds but is receptive to cerumen. While providing some level of protection against cerumen damage to the internal components of the hearing device, this and other similar types of filters become quickly soiled, resulting in poor device performance due to a blocked speaker port. As such, the user must frequently replace the disposable filter. The small size of these devices often requires a high level of visual acuity and dexterity for such maintenance.  
         [0008]     U.S. Pat. No. 5,327,500, entitled “Cerumen barrier for custom in the ear type hearing instruments,” and incorporated by reference herein, discloses a cerumen barrier for a custom, in-the-ear hearing aid. The cerumen barrier consists of a small door covering the receiver port that can be manually rotated open to provide cleaning under the door and around the receiver port. While also providing some level of protection against cerumen to the internal components of the hearing aid, significant user intervention is relied on to clean the filter.  
         [0009]     With the exception of the &#39;790, the hearing aid devices from the prior art have a profound shortcoming of relying upon the hearing aid user to remember to periodically clear the cerumen that has accumulated on the device. Yet hearing aid users are no different from consumers of other products: all want convenience. Cleaning a hearing aid is one more thing to remember, so it is not done faithfully. This issue has become even more important as hearing aids have gotten smaller. Primarily to overcome the stigma of wearing a hearing aid, manufacturers have miniaturized hearing aids to the point that completely-in-canal (CIC) hearing aids reside out of sight deep in the ear canal, proximate to the tympanic membrane (eardrum). This placement provides the overriding benefits of improving frequency response, reducing distortion due to jaw extrusion, and improving overall sound fidelity; however, it worsens the problem of earwax buildup.  
         [0010]     When users are unsure of or unhappy with their hearing aid&#39;s performance, they must bear the inconvenience and cost of taking it to their audiologist for assessment and adjustment. There is currently no way for users to test and calibrate their hearing aids to manufacturers&#39; standards, ensuring optimal hearing aid performance, from the convenience of their homes. Moreover, no automatic tests, i.e., tests that do not require the hearing aid users&#39; manual intervention, exist today.  
         [0011]     U.S. Pat. No. 6,379,314, entitled, “Internet system for testing hearing,” assigned to Health Performance, Inc and incorporated by reference herein, relates to a computer system that is accessible to a community of users for self-administered hearing tests over the Internet, which is a significant improvement to conventional hearing testing that requires sophisticated equipment at dedicated hearing and health centers by experienced personnel. Such automatic audiometers are becoming widely accepted in hearing screening applications such as in schools and industrial clinics. This automated approach results in minimal operator involvement, faster testing, and improved accuracy.  
         [0012]     U.S. Pat. No. 4,284,847, entitled, “Audiometric testing, analyzing, and recording apparatus and method,” and incorporated by reference herein, discloses a microprocessor-based audiometry apparatus that includes tone-generation means at variable frequency and intensities, memory for software, and patient-data storage. The apparatus is capable of being networked with remote computers for data transfer. One of the main features of the &#39;847 patent is its ability to compare recent audiogram data with previously acquired ones, and then automatically compute such changes as hearing threshold shifts.  
         [0013]     U.S. Pat. No. 6,411,678, entitled, “Internet based remote diagnostic system,” assigned to General Electric Company and incorporated by reference herein, discloses a remote diagnostic communication system that uses a public or private remote access infrastructure to facilitate wide-area communications between the remote site and the diagnostic center and that requires only local telephone calls. The diagnostic center and one or more remote sites at which monitored equipment is located are coupled to a wide area network (WAN). When data are to be transferred from a remote site to the central diagnostic center, the remote site initiates a local telephone call to a point-of-presence (POP) server on the WAN backbone. This could be an Internet service provider (ISP) in the case of the Internet, or an intranet POP server in the case of a private network. Data is then transferred to a computer in the POP server or anywhere on the network, as long as it is outside the “firewall” electronically isolating the diagnostic center from unwanted communications. To complete the transfer, the diagnostic center transfers the data from the POP server to the diagnostic center via the public or private wide-area network (the Internet or an intranet). The data transfer can take place either on a scheduled basis, or when an alarm condition is detected at the remote site. The central diagnostic center can prompt the remote site to connect to the POP server via a wireless paging service or a direct-dial phone call.  
         [0014]     The &#39;314 demonstrates a means for conducting automatic hearing tests over the Internet while the &#39;687 patent discloses remote diagnostic testing of electronic equipment over the Internet, either on demand or as scheduled. The prior art, however, does not combine these means in a manner that provides a remote diagnostic hearing aid test, much less an automated one, that doesn&#39;t rely on the faithful and concerted efforts of patients.  
       SUMMARY OF THE INVENTION  
       [0015]     It is therefore an object of the present invention to simplify the process of diagnostic testing and maintaining hearing aids, so that the hearing aid testing can be done in a more convenient location for the user, such as the user&#39;s home.  
         [0016]     It is another object of the present invention to provide automatic, convenient, at-home remote diagnostic testing of a hearing aid that can be performed as frequently as daily and that can signal hearing aid status updates, such as improper functioning or the need for service.  
         [0017]     The present invention is an at-home hearing aid tester apparatus and method of operating the tester, which can be performed as frequently as daily. An individual places the hearing aid in a small countertop device at regular intervals, such as at the end of each day; the device can test the audio frequency range for which the hearing aid is designed and for which the device is soundproof. The device tests the hearing aid for proper function by pinging it with a series of audio waves, after which the device signals the individual as appropriate of such status as improper function, service required, etc. Additionally, the apparatus may be connected via Internet or other network connectivity to a central computer that remotely further diagnoses the hearing aid. The device may also issue a series of corrective tones (if the hearing aid is programmable) to provide some degree of servicing, for instance, adding amplification in response to the hearing aid&#39;s normal degradation over time. This networking capability also enables continuous updating of an individual&#39;s file on the central computer, for reference and analysis by audiologists and other stakeholders for ways to continually improve the individual&#39;s hearing.  
         [0018]     Thus, the present invention provides for a portable hearing aid testing apparatus comprising:  
         [0019]     a resealable housing defining a cavity for receiving a hearing aid, wherein the cavity includes a microphone and has a configuration for securing the hearing aid in a position where a speaker of the hearing aid is opposite of the microphone;  
         [0020]     communications interface means for coupling to a data signal connection means of the hearing aid; and  
         [0021]     a controller coupled to the communications interface means, the microphone and an indicia output means (e.g., indicator light), wherein the controller is operable for testing the operation of the hearing aid.  
         [0022]     In a further preferred embodiment, the testing of operation of the hearing aid by the controller comprises:  
         [0023]     transmitting testing data from the controller (e.g., directly to the hearing aid or to a speaker within the cavity) to cause the hearing aid to generate sound output;  
         [0024]     receiving the hearing aid sound output at the microphone and forwarding sound data signals representative of the sound output to the controller;  
         [0025]     evaluating the sound signals to determine whether frequencies and amplitudes of the sound signals correspond to respective expected frequencies and amplitudes associated with the testing data; and  
         [0026]     generating a selected indicia (e.g., pass, fail, clean hearing aid) for output at the indicia output means based on the evaluation.  
         [0027]     In a further preferred embodiment, the apparatus includes a communications network interface coupled to the controller and for receiving hearing aid testing and programming data from and transmitting user hearing aid profile data to a remote hearing health database, wherein the controller includes a memory for storing the hearing aid programming data and the hearing aid testing data received at the network interface.  
         [0028]     In still another preferred embodiment, the hearing aid is programmable based on receipt of a corrective sound signal and the controller, based on the hearing aid programming data received from the health database, causes the speaker to generate the corrective sound signal. 
     
    
     BRIEF DESCRIPTION OF THE DRAWINGS  
       [0029]     Other objects and advantages of the present invention will be apparent from the following detailed description of the presently preferred embodiments, which description should be considered in conjunction with the accompanying drawings in which like references indicate similar elements and in which:  
         [0030]      FIG. 1A  is a block diagram illustrating the basic operation of a hearing aid that is programmable by a serial interface.  
         [0031]      FIG. 1B  is a block diagram illustrating a serial interface for programming a hearing aid.  
         [0032]      FIG. 2  is a device for in-home, routine, automatic diagnostic testing of a hearing aid.  
         [0033]      FIG. 3  is a method of conducting a routine automatic diagnostic test using the apparatus of the present invention with tones and other test data generated by the tester.  
         [0034]      FIG. 4  is a method of conducting a routine automatic diagnostic test using the apparatus of the present invention with tones and other test data generated by the hearing aid.  
         [0035]      FIG. 5  is a block diagram of the interface between an in-home, routine, diagnostic tester and a hearing aid. 
     
    
     DETAILED DESCRIPTION OF THE INVENTION  
       [0000]     Description of the Prior Art  
         [0036]      FIG. 1A  is a block diagram illustrating the components of a basic hearing aid  100 , and basic operation of a programmable hearing aid, which is programmable by a serial interface in order to be optimized for an individual patient&#39;s hearing needs and preferences.  
         [0037]     Hearing aid  100  consists of the following conventional components: a microphone  101 , a pre-amplifier (pre-amp)  102 , an analog-to-digital converter (ADC)  180 , a digital signal processor (DSP)  103 , a digital-to-analog converter (DAC)  190 , an amplifier  104 , an output speaker  105 , a data table memory  130 , an address and data bus  121 , a memory  107 , a controller  106 , an address and data bus  120 , an address and data bus  110 , a plurality of input/output devices (I/O)  108 , a programming connection  150 , a socket connector  151 , and a computer  152 .  
         [0038]     With hearing aid  100  in a user&#39;s ear, sound is collected as an analog signal in microphone  101 . This signal is amplified using pre-amp  102 , is converted from analog to digital in ADC  180 , and then is processed by DSP  103  to meet the individual&#39;s unique requirements. The signal from DSP  103  is then converted from digital to analog using DAC  190 . This analog signal is then amplified using amplifier  104  for transmission to output speaker  105 . Microphone  101  and output speaker  105  have adjustable variable settings to control the input/output volume of sound to hearing aid  100 .  
         [0039]     A means of programming DSP  103  in order to optimize basic hearing aid  100  for an individual is described in U.S. Pat. No. 6,201,875, entitled, “Hearing aid fitting system,” assigned to Sonic Innovations, Inc. Programming DSP  103  requires that an individual&#39;s specific hearing compensation requirements data, like amplitude versus frequency, be loaded from data table memory  130  via address and data bus  121  to memory  107  (such as an EEPROM). Controller  106  then accesses memory  107  via address and data bus  120  to load the hearing compensation requirements data onto DSP  103  via address and data bus  110 . I/O  108 , such as on/off, volume, and squelch, connected to controller  106  provide individuals with a degree of external control of hearing aid  100 .  
         [0040]     Computer  152  is an external circuit that can be used to program basic hearing aid  100  via socket connector  151 , which allows for external communication, and programming connection  150 , which allows for a serial or parallel input. U.S. Pat. No. 6,319,020, entitled, “Programming connector for hearing devices,” assigned to Sonic Innovations, Inc., further describes the connections of a programmable hearing aid device. Building a serial interface for programming a hearing aid is also described in U.S. Pat. No. 6,240,193, entitled, “Two-line variable word length serial interface,” assigned to Sonic Innovations, Inc., and is briefly described below in  FIG. 2 .  
         [0041]     In operation, controller  106  gets programmed data from data table memory  130  and loads it into memory  107 . The programmed data is then used by DSP  103  when signals go through microphone  101  and pre-amp  102  to ADC  180 . After DSP  103  operates on the input signal, DSP  103  outputs the modified and processed signal to DAC  190  and then to amplifier  104  to output speaker  105  of hearing aid  100 . Controller  106  uses address and data buses  110 ,  120  and  121  to move data from DSP  103  as needed. Controller  106  also provides connection to I/O  108  on/off, volume, or squelch external adjusters. In addition, controller  106  connects to programming connection  150 , in which socket connector  151  allows communication with an external circuit, such as computer  152 , allowing a user to program or direct controller  106 .  
         [0042]      FIG. 1B  illustrates a prior art serial interface for programming a hearing aid, as described in U.S. Pat. No. 6,240,193, “Two-line variable word length serial interface,” assigned to Sonic Innovations, Inc.  FIG. 1B  is a block diagram of a digital programmable hearing aid  10  (e.g., basic hearing aid  100  of  FIG. 1A ). including the serial interface. In the serial interface circuit, an SDA pin  12  and an SCLK pin  14  are depicted, while the pins for power and ground are omitted for simplicity&#39;s sake. SDA pin  12  is connected to the input of an input buffer  16 , and to the output of an output buffer  18 . Input buffer  16  is connected to a gain register  20 , an ADC register  22 , a register file input buffer register  24 , a volume control register  26 , an EEPROM input buffer register  28 , a DSP output register  30 , a temporary trim register  32 , a command register  34 , and a control register  36 . Control register  36  includes a latch (not shown). Output buffer  18  is connected to ADC register  22 , a register file output buffer register  38 , an EEPROM output buffer register  40 , and DSP output register  30 .  
         [0043]     SCLK pin  14  is connected to command register  34 , control register  36 , a first two-input multiplexer  42 , and a second two-input multiplexer  44 . An internal oscillator  46  is connected to a second input of first two-input multiplexer  42  and also provides a clock to an ADC  48  (i.e., ADC  180  of  FIG. 1A ). During normal operation of hearing aid  10 , the input of ADC  48  is connected to the electrical input to hearing aid  10 . The output of ADC  48  is connected to ADC register  22 . The output of first two-input multiplexer  42  is connected to the input of a divide-by-four circuit  50 . The output of divide-by-four circuit  50  is connected to the second input of second two-input multiplexer  44 . The output of second two-input multiplexer  44  provides a clock to a DSP  52  (i.e., DSP  103  of  FIG. 1A ).  
         [0044]     The output of register file input buffer register  24  is connected to a register file  54 , and the output of register file  54  is connected to the input of register file output buffer register  38 . The output of DSP output register  30  is connected to a DAC  56  (i.e., DAC  190  of  FIG. 1A ). The output of EEPROM input buffer register  28  is connected to an EEPROM  58 , and the output of EEPROM  58  is connected to the input of EEPROM output buffer register  40  and a trim latch  60 . The output of trim latch  60  is connected to a third two-input multiplexer  62 , and the second input of third two-input multiplexer  62  is connected to the output of temporary trim register  32 . The output of third two-input multiplexer  62  provides trim signals to various circuits in hearing aid  10 .  
         [0045]     In the serial interface, SDA pin  12  is employed to input a serial data stream including various read and write instructions (described below) from the HI-PRO or external device to hearing aid  10  and to output data from hearing aid  10  both during testing and in the fitting process to determine whether the data in hearing aid  10  is as expected. SCLK pin  14  is used to input a serial clock that clocks in the instructions from the serial data input stream on SDA pin  12 .  
         [0046]     The present maximum clock rate from the HI-PRO device to the serial interface circuit is 7 kHz. It is anticipated, however, that the serial interface circuit will also interface to other devices such as IC testers, and as a result, the SDA and SCLK signals can operate at 1.5 MHz when receiving data from an external source. The serial interface circuit can drive output through SDA pin  12  having a 50-pf load at a 500 kHz clock rate.  
       DESCRIPTION OF THE INVENTION  
       [0047]      FIG. 2  is a test device  200  for at-home routine automatic diagnostic testing of a hearing aid, such as basic hearing aid  100  of  FIG. 1A . Test device  200  is composed of a top  201  and a base  202 . Included is a microphone  203  that captures test tones processed by hearing aid  100  and sends the tones via a connection  206  to a controller and DSP  230 . Controller and DSP  230  sends test tones via a speaker connection  205  to a speaker  204 , which plays the tones so that they are received by microphone  101  of basic hearing aid  100 . Controller and DSP  230  can also send tones to switch on/off basic hearing aid  100 .  
         [0048]     A plurality of indicator lights  210 ,  211 ,  212  and  214  in a light panel  215  are connected by a connector  216  to controller and DSP  230  and signal such messages as “Power on,” “Service hearing aid,” “Passed test,” etc., as appropriate to the diagnostic test results. A means for either AC power  220   a  or DC power  220   b  is connected to test device  200  by either a connection  221  or a connection  222 , respectively.  
         [0049]     An on/off switch  290  is used to turn test device  200  on and off, sending a signal through connector  291  to controller and DSP  230 . An adapter  250  may be used to ensure the proper physical fit of hearing aid  100  in proximity to microphone  203 .  
         [0050]     A serial connector  262   a  within hearing aid  100  connects hearing aid  100  to a serial connector  262   b  on test device  200  for diagnostic testing. An optional adapter serial connector  263  connects serial connectors  262   a  and  262   b  when optional adapter  250  is used. A quantity of soundproofing  280  is provided to ensure sound tightness, preventing ambient noise from interfering with diagnostic testing.  
         [0051]     The Internet  295  represents the capability to connect to the Internet, an intranet, or other similar network, in order to download test programs, ANSI calibration standards, and the like, and to upload test results to a central database for reference and analysis of patient files.  
         [0052]     In operation, top  201  is opened, hearing aid  100  (which has DSP  103  preprogrammed based upon a hearing test at the audiologist) is powered on and fit in base  202 , positioned above microphone  203  (optionally using adapter  250 , which provides the ability to fit many different sizes of hearing aids  100  in standard sized test device  200 ). Test device  200  is closed and soundproofing  280  ensures that test device  200  is soundproofed.  
         [0053]     On/off switch  290  is used to turn test device  200  on, and includes an indicator that indicates that test device  200  is switched on.  
         [0054]     Controller and DSP  230  controls the entire electronic operation of test device  200 . Controller and DSP  230  has been loaded with information about the user&#39;s specific hearing test results so that it may uniquely test that user&#39;s hearing aid  100 . Controller and DSP  230  draws power from either AC power  220   a  or DC power  220   b.    
         [0055]     Controller and DSP  230  may download current data and programs from a remote location via Internet  295 . Controller and DSP  230  can program hearing aid  100  through serial connector  262   a , which connects hearing aid  100  to serial connector  262   b  on test device  200  for diagnostic testing. Optional adapter serial connector  263  connects serial connectors  262   a  and  262   b  when optional adapter  250  is used. Controller and DSP  230  can erase and rewrite data table memory  130  of hearing aid  100  of  FIG. 1A .  
         [0056]     Controller and DSP  230  runs programs that determine what data is written to data table memory  130  in order to program hearing aid  100 . Then controller and DSP  230  sends audio test sounds to speaker  204  using speaker connection  205 . Hearing aid  100 , via its DSP  103 , processes the test sounds and emits them from its own output speaker  105 . These sounds are received by microphone  203  and are sent through connection  206  back to controller and DSP  230 . The testing process continues as controller and DSP  230  sends out its entire series of test sounds and receives the entire series back. Controller and DSP  230  compares the actual test results with the expected test results, and diagnoses the status of hearing aid  100 . This status is sent to light panel  215  through connector  216 , and indicator lights  210 ,  211 ,  212  and  214  provide messages such as “Power on,” “Service hearing aid,” and “Passed test,” as appropriate to the test results.  
         [0057]     It should be noted that a program to debug test device  200  could be run without hearing aid  100  in test device  200  to ensure that test device  200  is working properly.  
         [0058]     In an alternative mode, test device  200  can be used as a storage unit for hearing aid  100 . For example hearing aid unit  100  can be switched off and placed inside test device  200 , which is sealed out by replacing the ambient air with a storage gas such as Nitrogen or Carbon Dioxide. This sealing and storing technique is well known in the art.  
         [0059]      FIG. 3  is a method  300  for testing hearing aids such as hearing aid  100  of  FIG. 1A  using an at-home routine automatic hearing aid tester that generates test tones, including the steps of:  
         [0060]     Step  301 : Setting Up Hearing Aid Tester  
         [0061]     In this step, test device  200  of  FIG. 2  is turned on. A debug test is run with the unit closed and no hearing aid  100  in the device to ensure that test device  200  is working properly. Top  201  is opened.  
         [0062]     Step  302 : Setting Up Hearing Aid to be Tested  
         [0063]     In this step, hearing aid  100  is removed from the user&#39;s ear, is turned on (if not already on), and is placed into test device  200 . Hearing aid  100  is then automatically calibrated, i.e. the audible sound receiving sensitivity of microphone  101  and output amplitude of speaker  105  are set to an optimal level for conducting the test. Methods of automatic calibration of hearing aid  100  are well known in the art, and those skilled in the art can easily suggest a known method for this step. If necessary, optional adapter  250  is used to ensure proper fit. Top  201  is closed.  
         [0064]     Step  310 : Loading Data from Memory of Hearing Aid to Tester  
         [0065]     In this step, test device  200  automatically downloads programming data from memory  107  of hearing aid  100 , storing the data in test device  200  to clear memory  107  in preparation for the diagnostic hearing aid test of the present invention.  
         [0066]     Step  320 : Writing Basic Test Data from Tester to Hearing Aid  
         [0067]     In this step, basic test data is written from test device  200  to memory  107  in preparation for the diagnostic hearing test.  
         [0068]     Step  330 : Running Basic Test  
         [0069]     In this step, the user initiates the test program, or alternatively the test program is automatically performed following Step  320 , which sends sounds (tones) at various amplitudes directly from controller and DSP  230  of test device  200  to speaker  204 . These tones are then received by microphone  101  of hearing aid  100 , output through output speaker  105 , then collected by microphone  203  of test device  200  and conveyed as test results to controller and DSP  230 .  
         [0070]     Step  340 : Passed Test? 
         [0071]     In this decision step, the test results are compared with standard hearing aid data stored in test device  200  to determine whether hearing aid  100  is functioning as intended when optimized for the user. This comparison step may be performed by a computer algorithm that compares a test result, such as a given frequency and amplitude, with the expected result, then calculates whether the test result is within tolerance. If hearing aid  100  is functioning within tolerance, method  300  proceeds to step  350 ; if not, method  300  proceeds to step  360 .  
         [0072]     Step  360 : Illuminating “Passed Test” Light  
         [0073]     In this step, controller and DSP  230  sends a signal to light panel  215  to illuminate indicator light  214  that indicates that hearing aid  100  has passed the test. Method  300  proceeds to step  370 .  
         [0074]     Step  360 : Illuminating “Need Service” Light  
         [0075]     In this step, controller and DSP  230  sends a signal to light panel  215  to illuminate indicator light  210  that indicates that hearing aid  100  needs service. This signals the user to seek professional maintenance of hearing aid  100  and test device  200  once method  300  is complete. In one embodiment, test device  200  can be connected to a system (not shown) that can directly notify an interested stakeholder or a hearing health professional if hearing aid  100  needs services. This can further prompt the hearing health professional to preemptively contact the user and suggest that the user visit the hearing health professional. The hearing health professional would then assess both hearing aid  100  and test device  200  and perhaps also the user&#39;s hearing, recommending remedial action. Method  300  proceeds to step  370 .  
         [0076]     Step  370 : Erasing Test Data from Hearing Aid  
         [0077]     In this step, test device  200  erases the test data from memory  107  of hearing aid  100 .  
         [0078]     Step  380 : Writing User Data from Tester to Hearing Aid  
         [0079]     In this step, test device  200  writes the user&#39;s programming data stored in test device  200  in step  370  back into memory  107  of hearing aid  100 . Method  300  ends.  
         [0080]      FIG. 4  is a method  400  for testing hearing aids using the at-home routine automatic hearing aid with tones generated by the hearing aid, including the steps of:  
         [0081]     Step  405 : Setting Up Hearing Aid Tester  
         [0082]     In this step, test device  200  of  FIG. 2  is turned on. A debug test is run with the unit closed and no hearing aid  100  in the device to ensure that test device  200  is working properly. Top  201  opened.  
         [0083]     Step  410 : Setting Up Hearing Aid to be Tested  
         [0084]     In this step, hearing aid  100  is removed from the user&#39;s ear, is turned on (if not already on), and is placed into test device  200 . Hearing aid  100  is then automatically calibrated, i.e. the volume of microphone  101  and output speaker  105  are set to an optimal level for conducting the test. Methods of automatic calibration of hearing aid  100  are well known in the art, and those skilled in the art can easily suggest a known method for this step. If necessary, optional adapter  250  is used to ensure proper fit. Top  210  is closed.  
         [0085]     Step  415 : Retrieving Test Data from Memory of Hearing Aid  
         [0086]     In this step, hearing aid  100  is initialized by controller and DSP  230 , which causes hearing aid  100  to automatically generate tones and retrieve other user-personalized programming data from memory  107  in preparation for the diagnostic hearing aid test that has been optimized for the individual user.  
         [0087]     Step  420 : Writing Test Data from Hearing Aid to Tester  
         [0088]     In this step, test data retrieved in step  415  is written from memory  107  of hearing aid  100  to test device  200  in preparation for the diagnostic hearing test.  
         [0089]     Step  425 : Running Basic Test  
         [0090]     In this step, the user initiates the test program. The test program sends sounds (tones) at various amplitudes directly from output speaker  105  of hearing aid  100 . The sounds are received by microphone  203  of test device  200  and sent to controller and DSP  230 .  
         [0091]     Step  430 : Passed Test? 
         [0092]     In this decision step, the test results are compared with standard-hearing aid data stored in test device  200  to determine whether hearing aid  100  is functioning as intended when optimized for the user. This comparison step may be performed by a computer algorithm that compares a test result, such as a given frequency and amplitude, with the expected result, then calculates whether the test result is within tolerance. If hearing aid  100  is functioning within tolerance, method  400  proceeds to step  435 ; if not, method  400  proceeds to step  440 .  
         [0093]     Step  435 : Illuminating “Passed Test” Light  
         [0094]     In this step, controller and DSP  230  sends a signal to light panel  215  to illuminate indicator light  214  that indicates that hearing aid  100  has passed the test. Method  400  ends.  
         [0095]     Step  440 : Illuminating “Need Service” Light  
         [0096]     In this step, controller and DSP  230  sends a signal to light panel  215  to illuminate indicator light  210  that indicates that hearing aid  100  needs service. This signals the user to seek professional maintenance of hearing aid  100  and test device  200  once method  400  is complete. In one embodiment, test device  200  can be connected to a system (not shown) that can directly notify a hearing health professional if hearing aid  100  needs services. This can further prompt the hearing health professional to preemptively contact the user and suggest that the user visit the hearing health professional. The hearing health professional would then assess both hearing aid  100  and test device  200  and perhaps also the user&#39;s hearing, recommending remedial action. Method  400  ends.  
         [0097]      FIG. 5  is a block diagram showing the portions of hearing aid  10  (e.g., basic hearing aid  100  of  FIG. 1A ) including the serial interface, as explained as  FIG. 1B .  FIG. 5  shows the physical arrangement of hearing aid  100  (the top section of the diagram) and test device  200  (the bottom section of the diagram). In addition,  FIG. 5  shows a physical connection for diagnostic testing data interchange between serial connector  262   a  of hearing aid  100  and serial connector  262   b  of test device  200 . The program, basic test, and memory map are stored in EEPROM  58  of test device  200 .  
         [0098]     Microphone  101  of hearing aid  100  is shown opposite speaker  204  of test device  200 . Microphone  203  of test device  200  is shown opposite output speaker  105  of hearing aid  100 . Serial connectors  262   a  and  262   b  are physically connected.  
         [0099]     In this manner, an at-home diagnostic hearing aid testing and maintenance process can be performed. The diagnostic test is automatic and convenient, and can be conducted as frequently as daily. The diagnostic test provides updates on the status of the hearing aid status, such as “improper functioning” or “service required”.  
         [0100]     Although preferred embodiments of the present invention have been described and illustrated, it will be apparent to those skilled in the art that various modifications may be made without departing from the principles of the invention.