Patent Grant
9414173
The present invention pertains to fitting verification of hearing devices such as hearing aids and assistive listening devices.
A typical fitting of hearing device involve hearing test, calculation of initial device settings based on the results of the hearing test, programming the device with the initial settings, fine tuning the device if necessary, and verifying the fitting with additional measurements. The current invention deals with the verification part of the fitting.
A fitting verification is necessary when the fitting outcome cannot be subjectively measured completely during the fitting session. In such a case, a fitter needs to decide how much gain should be given to a patient based on fitter's professional knowledge about the patient and the hearing device. Once the fitter sets the target gain, he needs to verify that the patient indeed receives the amount intended. The factors that affect the accuracy of the gain received by a patient include patient's ear individual anatomy, accuracy of device modeling, and device variation.
There are a couple of methods for fitting verification. One is the functional gain measurements. The other is the real ear measurements with a probe microphone. The functional gain measurement involves testing patient's hearing thresholds twice at each frequency in the sound field, first without a hearing device to get the unaided thresholds, then with the hearing device the patient is going to use to get the aided thresholds. The function gains are defined as the differences between the unaided and aided thresholds. To get a functional gain measurement, a patient needs to be sat in a booth free of reverberation. The patient's ear must be at certain distance and height in relative to the speaker from which test sounds are produced. If it is desired to test for only one ear, the non-testing ear must be masked or blocked. If these conditions are not controlled carefully, the test result may not be accurate.
The real ear measurement involves measuring sound pressure level at or near the eardrum using a probe microphone. An unaided real ear response is obtained for a patient without wearing a hearing device and an aided real ear response is obtained with the hearing devices in patient's ear. The difference between the aided and unaided real ear responses is real ear insertion gain. The factors that can affect the accuracy of a real ear measurement include the positioning of the probe microphone in relative to the eardrum, the force pinched onto the probe by the insertion of the hearing devices, and the distance and direction between the ear and the speaker from which the test sounds are produced. Acoustic reverberation of the test room/booth may also affect the test consistency. These factors make the test-retest variation of the real ear measurement relatively large. In addition, the equipment for the real ear measurement is expensive and test procedure is cumbersome. As a result, less than 30% of hearing aid dispensing professionals regularly use the method for the fitting verification.
A new method is needed for simpler and more effective fitting verification.
The current invention is a new method that can be used to evaluate and verify a fitting for a hearing device on individual ears. It uses the hearing device itself as testing apparatus. No additional equipment is required other than the fitting computer and interface which are already required and exist for the device fitting. The fitting computer communicates with the hearing device though the fitting interface and acts to control the operation mode and settings of the device. The communication can be either wired or wireless connection. The test sounds are generated by the device and inserted at the front end of the sound processing and amplification circuit. The test sounds can be pure tone or narrow band noise at various frequencies and levels. They can also be the speech saved in the computer and injected into the device at the front end of the circuit. The test sounds are calibrated in reference to the input to the microphone—so called input referred calibration. The calibration process is well known in the art and beyond the scope of the current invention.
According the current invention, a method for fitting verification with in situ hearing test consists of at least two steps. One is to measure patient's unaided in situ hearing thresholds. The other is to measure patient's aided in situ hearing thresholds. To measure the unaided in situ thresholds, the sound processing and amplification circuit is configured in such that the device would theoretically produce an insertion gain of 0 dB if it operates to process sounds picked up by its microphone. The theoretical insertion gain modeling can be established by the manufacturer of the device based on laboratory tests for the average listeners. The unaided in situ thresholds are obtained by changing the level of test sounds generated by the device and applied at the input of the circuit. To measure the aided in situ thresholds, the circuit gain is set to values to be used by the patient in real life. The aided in situ thresholds are obtained by changing the level of test sounds generated by the device and applied at the input of the circuit. Once the unaided and aided in situ thresholds are obtained, the in situ functional gain can be calculated as the differences between the unaided and aided in situ thresholds. The in situ functional gain can be used to evaluate or verify if intended target gains have been achieved with the device.
The method for administering in situ hearing test can be either a manual procedure or an automated procedure. The manual procedure is well known in the art and is beyond the scope of the current invention. The automated procedure has been described in a separate invention by the current inventor and is also beyond the scope of the current invention.
The method can be implemented as a software program for a computing platform that communicates with the hearing device via a wireless or wired connection. The computing platform can be a computer, smartphone, a tablet computer, or a designated control system for the hearing device. The hearing device can be any type of hearing devices that have a feature for producing in situ sounds at different frequencies and levels. Designing such a hearing device is well known in the art and is beyond the scope of the current invention. The patient's response can be registered via a medium such as a touch screen, push button, keyboard, mouse, or a remote control.
The above, as well as other advantages of the present invention, will become readily apparent to those skilled in the art from the following detailed description when considered in the light of the accompanying drawings in which:
The invention relates to hearing device fitting. More specifically, it relates to methods for fitting evaluations and verifications. The method can be implemented as a software program in a computing platform such as a computer, smartphone, or a designated control system for a hearing device. The invention will be readily understood by the following detailed description in conjunction with the accompanying drawings which form part of specific embodiments.
The standard equipment for fitting a hearing device to a patient includes a computing platform such as a computer or smartphone, a programming interface, and the hearing device itself. Technologies are also available to integrate the programming interface with the computing platform to make it possible for the computing platform to communicate to the hearing device directly. For example, a Bluetooth enabled computer can communicate with a Bluetooth enabled hearing device directly without a separate programming interface. The current invention uses the same equipment to do the fitting verification. The only additional requirement is that the hearing device to be used by the patient in real life is capable of generating in situ test sounds. The hearing device 200 shall be able to operate in two modes: normal mode and in situ test mode, as shown in
In the normal operation mode, the gain settings of the DSP 230 are set to the target gain with which the patient is going to use in real life. The target gain can be a gain calculated from the patient's hearing loss data using a published fitting formula as the NAL (National Acoustic Laboratory), or using a formula provided by the device manufacturer. It can also be a gain that the fitter believes will provide most benefit to the patient based on fitter's professional knowledge about the patient. In the in situ test mode (
Generally speaking, the fundamental functions and designs of the DSP 230 and Test Sound Generator 260 are well known in the art and beyond the scope of the current invention. The descriptions for
With reference to
After the first in situ hearing test, the methods operates to set device gain to the target gain the patient is going to use in real life (104). The target gain can be a gain calculated from the patient's hearing loss data using a published fitting formula as the NAL (National Acoustic Laboratory), or using a formula provided by the device manufacturer. It can also be a gain that the fitter believes will provide most benefit to the patient based on fitter's professional knowledge about the patient. After setting the device gain to the target gain, the method operates to conduct the second in situ hearing test (105). The procedure for the second in situ hearing test is the same as the first one except that the device gain is different. The second in situ hearing test produces the aided in situ thresholds which are saved at block 107. The difference between the unaided in situ thresholds and aided in situ thresholds are calculated (108) to obtain the in situ functional gains (109). Alternatively, the in situ functional gain can be calculated as the difference between patient's conventional unaided thresholds and the aided in situ thresholds. The conventional unaided threshold can be obtained using a standard audiometer which is available in almost all hearing clinics. The procedure to obtain the conventional unaided thresholds is a standard routine and most fitters are well trained to administer it. After the in situ functional gains are obtained, the method operates to set the device back to its normal operation mode (110) and come to an end (111).
The method can be implemented as a software program for a computing platform that communicates with the hearing device via wireless or a wired connection. The computing platform can be a computer, smartphone, a tablet computer, or a designated control system for the hearing device. The patient's response can be registered via a medium such as a touch screen, push button, keyboard, mouse, or a remote control.
The in situ functional gain obtained with the current invention is similar to the traditional functional gain and can used to evaluate how well the intended target gain has been achieved. The advantage of using the in situ functional gain is that it can be measured without additional equipment. Patients do not have to be moved to a sound approved booth and positioned at certain distance and height in relative to the sound field speaker. Therefore, the test results can be more consistent and reliable.
This application claims the benefit, under 35 U.S.C.§119(e) of U.S. Provisional Patent Application Ser. No. 61/849,124 filed on Jan. 22, 2013. Patent Application Ser. No. 61/849,124 is as of the filing date of this application. The contents of Application Ser. No. 61/849,124 are fully incorporated herein by reference.
| Number | Name | Date | Kind |
|---|---|---|---|
| 7695441 | Harrison et al. | Apr 2010 | B2 |
| 8308653 | Harrison et al. | Nov 2012 | B2 |
| 20100172524 | Durant | Jul 2010 | A1 |
| Number | Date | Country |
|---|---|---|
| WO2010132100 | Nov 2010 | WO |
| Number | Date | Country | |
|---|---|---|---|
| 61849120 | Jan 2013 | US |
