DESC:FIELD OF THE INVENTION
The present invention relates generally to devices for assisting the people with hearing impairment. More particularly, the present invention relates to a device for assisting hearing and for testing deafness.
BACKGROUND OF THE INVENTION
Hearing loss affects millions of people in the world. Hearing loss adversely affects a person's quality of life and psychological well-being. Individuals with hearing impairment often withdraw from social interactions to avoid frustrations resulting from inability to understand conversations. Hearing impairment causes increased stress levels, reduced self-confidence, reduced sociability and reduced effectiveness in the workplace.
The human ear generally comprises three regions the outer ear, the middle ear, and the inner ear. The outer ear generally comprises the external auricle and the ear canal, which is a tubular pathway through which sound reaches the middle ear. The outer ear is separated from the middle ear by the tympanic membrane (eardrum). The middle ear generally comprises three small bones, known as the ossicles, which form a mechanical conductor from the tympanic membrane to the inner ear. Finally, the inner ear includes the cochlea, which is a fluid-filled structure that contains a large number of delicate sensory hair cells that are connected to the auditory nerve. It is known that the normal perception of sounds results from the transmission of sound waves to an organ called the cochlea situated in the inner ear. More precisely, the acoustic signals or sound waves are picked up by the outer ear, and then transmitted to the middle-ear through the tympanic membrane in order to be perceived by the cochlea which is immobilized in the skull. As a result, a nerve impulse is generated and transmitted to the brain through the auditory nerve.
Hearing loss can also be classified in terms of being conductive, sensorineural, or a combination of both. Conductive hearing impairment typically results from diseases or disorders that limit the transmission of sound through the middle ear. Most conductive impairments can be treated medically or surgically. Purely conductive hearing loss represents a relatively small portion of the total population having hearing impairment.
Sensorineural hearing losses occur mostly in the inner ear and account for the vast majority of hearing impairment (estimated at 90-95% of the total population having hearing impairment). Sensorineural hearing impairment (sometimes called “nerve loss”) is largely caused by damage to the sensory hair cells inside the cochlea. Sensorineural hearing impairment occurs naturally as a result of aging or prolonged exposure to loud music and noise. This type of hearing loss cannot be reversed, nor can it be medically or surgically treated; however, the use of properly fitted hearing devices can improve the individual's quality of life.
The conventional air propagation hearing aid devices work by amplification of the sound signal, notably by means of a loudspeaker placed in the outer ear canal.
Other hearing aid devices are bone conduction hearing aids and their function is to excite the cochlea by vibrating the skull. Such devices comprise a transmitter part and a receiver transducer part comprising a vibrating element which is placed either against the skin, usually behind the ear, under a certain pressure, or actually in contact with the bone in the mastoid area.
However, said devices have not proven to be satisfactory. Indeed, the apparatuses using a vibrator placed against the skin require strong pressures in order to be efficient (i.e. to transmit the vibrations through the skin) and consequently, they can only be worn for relatively short periods, in order not to cause pain or in some cases, epidermal lesions.
In addition, the direct bone conduction devices necessitate a surgical operation in order to be fitted. And furthermore, the use of such devices raises several serious problems of maintenance such as charging or replacement of the batteries, reaction of the bone subjected to vibrations, adjustment, replacement in case of breakdowns.
The other kind of devices include sound bite hearing devices. Even though sound bite hearing devices are comparatively better than bone anchored hearing aid devices, the clarity and purity of sound signal at output questions sound bite hearing devices growth. In sound bite hearing devices, since one module is fitted inside the mouth, some restrictions are there to drink and eat. And also, the risk of aspiration and swallowing of oral device are high.
SUMMARY OF THE INVENTION
According to an aspect of the invention, a hearing assisting device, comprises a vibrator and a connector to transmit the sound vibrations to the inner ear. The vibrator is configured for generating sound vibrations and said vibrator having housing containing a receiving unit configured to pick and convert sound waves to electric signals, an amplifying unit coupled to the receiving unit configured to convert and amplify the electric signals to digital signals, and an actuating unit coupled with said amplifying unit having a conducting coil coated with Gold and Aluminium, being positioned between a pair of magnets, wherein said actuating unit is configured to generate sound vibrations. The connector is connected with the vibrator and configured for coupling out the sound vibrations from the vibrator, such that when a deaf user bites the tip of connector, the coil vibrations get transferred through the teeth, to transmit the sound vibrations to the inner ear through skull bones, facial nerves and blood vessels.
According to another aspect of the invention, a deafness testing device comprises the hearing assisting device and a display monitor. The hearing assisting device is mounted on the monitor. The deafness testing device is employed to check the audibility range of deafness and the range of frequency at which the patient has more deafness.
BRIEF DESCRIPTION OF THE DRAWINGS
The invention will now be described in greater detail with reference to an embodiment which is illustrated in the drawing figures:
Figure 1 is an exemplifying example application of a hearing assistance device, according to an embodiment of the present invention;
Figure 2 illustrates the hearing assistance device of Figure 1, according to an embodiment of the present invention;
Figure 3 is a block diagram showing working of the hearing assistance device, according to an embodiment of the present invention;
Figure 4 is a block diagram showing working example embodiment of the hearing assistance device, according to the present invention;
Figure 5 (a-e) show configuration of components of the hearing assistance device, according to an embodiment of the present invention;
Figure 6 is an exemplifying example application of a testing device, according to an embodiment of the present invention;
Figure 7 shows the testing device along with display monitor, according to an embodiment of the present invention;
Figure 8 shows components of the testing device, according to an embodiment of the present invention;
Figure 9 shows mounting of the hearing assistance device in the monitor, according to an embodiment of the present invention; and
Figure 10 shows components of the testing device, according to another embodiment of the present invention.
Throughout the drawings, it should be noted that like reference numbers are used to depict the same or similar elements, features, and structures.
DETAILED DESCRIPTION OF THE INVENTION
The present invention relates to a device for hearing assistance and deafness testing. The device has mainly two functions has a portable hearing aid for deaf people and has a medical testing equipment used by the doctors in medical laboratories to test the deafness of person.
The working principle of the device is based on conduction of sound signals from teeth towards Cochlea through skull bones, blood vessels and facial nerves.
Figure 1-2 shows different views of a hearing assistance device (A1), according to an embodiment of the present invention. The hearing assisting device (A1) comprises a vibrator (A2) and a connector (A8) to transmit the sound vibrations to the inner ear. The vibrator (A2) is configured for generating sound vibrations. The vibrator (A2) has a housing (A17) containing a receiving unit (A3) configured to pick and convert sound waves to electric signals. The receiving unit (A3) is coupled to an amplifying unit (A4) to convert and amplify the electric signals to digital signals. The amplifying unit (A4) is coupled to an actuating unit (A5) having a conducting coil (A6) coated with Gold and Aluminium, being positioned between a pair of magnets (A7), wherein said actuating unit (A5) is configured to generate sound vibrations. The connector (A8) is connected with the vibrator (A2) and configured for coupling out the sound vibrations from the vibrator (A2), such that when a deaf user bites the tip of connector (A8), the coil vibrations get transferred through the teeth, to transmit the sound vibrations to the inner ear through skull bones, facial nerves and blood vessels. Corresponding block diagram shown in figure 3 describe the working of hearing assistance device, according to an embodiment of the present invention.
Figure 4 show block diagram for the hearing assistance device (A1) according to the present invention. Accordingly, the hearing assistance device (A1) comprises a microphone (A3’) as a receiving unit (A3), an amplifier (A4’) as amplifying unit or processing unit (A4), a coil (A6) and a pair of magnets (A7) forming the actuating unit (A5), a bite structure (A8’) analogous to the connector (A8) and a battery (not shown). The microphone (A3’), amplifier (A4’) and battery are positioned on the rear side of the hearing assistance device (A1). The sound which is received by the microphone (A3’) can be amplified and passed on to the front end of the hearing assistance device (A1) which has a permanent magnet (A7), copper coil (A6) and bite structure (A8’) which is a C- shaped aluminum channel for the user to bite. When a user who is a deaf person bites the tip of C- shaped structure, the coil vibrations get transferred through the teeth. It passes towards the inner ear through skull bones, facial nerves and blood vessels.
Further, the hearing assistance device (A1) can comprise a wireless communication board which can be used to connect with mobile phone either through Wi-Fi or Bluetooth. The mobile phone can have an application with control for frequency modulating and intensity adjusting. For example, if the user is not able to hear the surrounding voice, using mobile application user can connect to mobile phone and adjust the frequency of voice. Based on the change in frequency, the pitch of voice changes but the content remains same. Similarly, if the user is not able to hear the surrounding voice clearly, user can connect to mobile phone and adjust the intensity of voice. The decibel value of sound changes and make the deaf person hear clear. Connecting the hearing assistance device to the mobile phone also gives a user provision to get entertained by hearing songs, movies, news etc.
Figure 5 (a-e) shows configuration of components in a hearing assistance device (A1), according to an embodiment of the present invention. The various components of the device (A1) are explained in detail as below:
The microphone (A3’) picks the different sounds in the environment and converts them to electric signals that can be identified by the processor. Sound signal is a message signal, it can be either a voice, or music, or news etc. Microphones are able to differentiate sounds, such as speech and background noise, and process them towards the amplifier unit.
The processor or amplifier (A4’) acts as the motherboard of the device. It takes the electric signals received from the microphone and converts them into digital signals that can be manipulated. The signal from the amplifier is carried by an output coil.
The battery (not shown in figure) (3V, 250-500mAh) is the power source for the other electronic components. The battery can be charged through charging port (A20) port from outside. In a preferred embodiment, to meet the high power requirement combination of a super capacitor and the battery circuitry can be employed in the hearing assisting device (A1).
The hearing assistance device (A1) is made up of high powerful Neodymium magnets (A7) placed on top and bottom of coil (A6). The Neodymium magnet (A7) is so powerful which is capable of generating strong magnetic field between gold coated copper coils (A6). So, a small vibration at tip of device (A1) is enough to transfer high frequency sounds. The user does not feel any vibration at teeth even though vibrations are happening at the end of device (A1), which make the user comfortable to use. The user can bite the device (A1) little firmly to hear the sound with fine and filtered clarity.
The coil (A6) is a gold coated copper coil placed in between high power neodymium magnets (A7). The vibration of the coil (A6) depends on the sound passed through the amplifier (A4’) and this vibration is passed on to the C- shaped aluminum channel. The coil (A6) has been designed to a spiral shape where the efficiency of electromagnetic induction would be high. Two coils are spirally arranged such that the intersection of these coils becomes the ground which comes at center and the other two ends become the main connection.
The permanent magnet (A7) is mounted firmly on to the bracket (A10). The bracket (A10) is a type of metal shield which is used for shielding static or low frequency magnetic fields. The loss of magnetic flux will be minimum because of the materials used in Mu-metal. Mu-metal consists of 77% Ni, 16% Iron, 5% Copper, 2% Chromium.
A center ball design (A11) picks the vibrations from gold coil (A6) towards the C-shaped gear end. C-shaped gear end helps the user to bite the device and conduction is possible through this end.
A C-shaped Aluminium Cap (A12) is an initial part of transmission system. The sound vibration from gold coil (A6) is transmitted towards the connector channel through this Al-cap. The Mu-metal is fixed on to the transmission system by using a screw point (A13) arrangement.
A screw (A14) is used to fix the bracket of magnet on screw point 2 (13) arrangement. Under the screw, a grip is also there to tight the system. The screw is tightened in opposite direction to the normal screw tightening, with the objective of not loosening the connector channel on gradual vibration. A hole (A15) is the portion on the device in which the screw (A14) is fixed. An elbow stand (A16) is used to fix the coil in between magnets by keeping ample distance.
An Aluminum frame (A9) covers from C-shaped cap (A12) to C-shaped Gear. The thickness is smaller at both ends and higher at center. The small thickness helps to transmit the sound vibrations to the other end without any loses. The user will not feel any severe vibration since the frame is thicker and fixed on its center.
The hearing assistance device housing (A17) is made up of plastic material and in a circular shape. The device is set ON/OFF using a power button (A18) and the LED displays when the switch is ON. Long press on the button sets the Wi-Fi ON. The volume can be increased or decreased using a volume control (A19) button.
The hearing assistance device is provided with a screw and socket design to detach the C-shaped gear from the device. The user can replace the gear channel on a long run. This design assists in easy coupling of gear channel in the device. The screw is tightened in opposite direction to the normal screw tightening, with the objective of not loosening the gear channel on gradual vibration.
Further plurality of grippers are provided on the device to detach the device without any mechanical damage. The grip is a protection part of device. Once the user removes the gear channel from device, chances of damage to transmission system & magnet-coil system is more.
In operation the sound received by the microphone (A3’) is amplified and passed on to the front end of the hearing assisting device (A1) which has a permanent magnet (A7), copper coil (A6) and a bite structure (A8’) which is a C- shaped aluminum channel for the user to bite. The gold coated copper coil (A6) which is placed in between high power neodymium magnets (A7) releases high energy electrons in very minimal vibration which the user can’t feel. These micro-vibrations due to rapid electron movement allows the transfer of high frequency sounds through the bite structure of hearing assisting device (A1). The user does not feel any vibration at teeth so that he /she can bite the device little firmly to hear the sound with fine and filtered clarity. The coil (A6) vibrates depending on the sound passed through the amplifier (A4’) and this vibration is passed on to the bite structure (A8’).
The device will check the audibility range of deafness and also the range of frequency where the patient has more deafness. The technology is based on biting the tip of device so that there will be minimal conduction loss in sound since sound is bypassed without having skin losses.
When deaf user bites the tip of bite structure (A8’), the coil (A6) vibrations get transferred through the teeth. From teeth towards the inner ear through skull bones, facial nerves and blood vessels. The cochlea (inner ear) is filled with a watery liquid, which moves in response to the vibrations. As the fluid moves, the cochlear partition also moves, thousands of hair cells sense the motion and convert that motion to electrical signals that are communicated via neurotransmitters to many thousands of nerve cells in brain.
The hearing assistance device (A1) can have different types of bite structures. The bite structure can vary based on usage, age of people, convenience etc.
The hearing assisting device (A1) of the present invention can be employed as a head band. The tension adjustable head band can have two tips of the C- shaped connector at two ends of the head band and both the ends are in physical contact with the temporal bones behind the ears. The vibrating signals from the device is passed to the inner ear through the ear bones instead of teeth in the normal device. This increases the usability of the device as there is no need for biting the tip of the device. Also, through this device the user can give real time voice feedback as the bite structure has no contact with teeth/mouth and the conduction happens through head and skull bones.
In further embodiment, the hearing assisting device (A1) of the present invention can be employed in an eye wear. The temple tips (ear piece) of the eye wear can be fitted with the connector tips. On wearing the eye wear the end of the connector comes in physical contact with the temporal bones behind the ears. The vibrating signals from the device passes to the inner ear through the ear bones.
The hearing assistance device (A1) according to the present invention can also be used by the audiologist as hearing diagnostic system or testing device to test the deafness of a person. The device can also be used in medical laboratories for regular checkup.
Figures 6-10 shows components of the device, according to another embodiment of the present invention. Accordingly, a deafness testing device (D1) comprises the hearing assisting device (A1) and a monitor (D2). The hearing assisting device (A1) is mounted on the display monitor (D2). The deafness testing device (D1) check the audibility range of deafness and the range of frequency at which the patient has more deafness. Display monitor (D2) monitors the parameters of deafness or level of impairedness. Deafness testing device (D1) can be miniaturized based on the functions of audiometer.
The testing device (D1) according to the present embodiment comprises a trigon Al-Channel which is analog to C-shaped Gear in hearing assistance device in terms of function. It’s a trigonal shaped Al-frame where the user bites and vibration is conducted through the teeth.
Further the testing device can have a valve amplifier as a replacement for normal amplifier. The valve amplifier uses vacuum tubes to increase the amplitude or power of a signal.
A panic button (D12) is provided on the top of the testing device (D1) where user can use the button to confirm the hearing. This is a signal button for doctors to understand that user can hear. The corresponding data can be fetched by the Wi-Fi unit of monitor and corresponding frequency and data can be displayed.
Al- Transmission frame is similar as that of hearing assisting device with only change is the trigon channel instead of C-Gear. The frame covers from C-shaped cap to C-shaped Trigon channel. The thickness is smaller at both ends and higher at center. The small thickness helps to transmit the sound vibrations to the other end without any loses. The user does not feel any severe vibration since the frame is thicker and fixed on its center.
The monitor has a shell (D3) to store the liquid in which the trigon of the device is placed. The shell has thread (D5) for mechanical adjustments with device. The shell (D3) is placed and fixed in the hollow female portion of monitor (D6). Liquid (D23) can be Isopropyl alcohol or sterilizing fluid. The shell (D3) has a brushed (D4) structure which is very thin and flexible helps to clean the trigon channel of device.
Negative & Positive terminals (D7) & (D8) to charge the device while placed in monitor system. Negative & Positive terminals (D9) & (D10) in device to connect to monitor. Output Channel (D11) connects with the monitor to test the normal hearing (through air conduction) of a person.
Service port (D13) is used to fix the bracket of magnet on screw arrangement. Under the screw, a grip is also there to tight the system. The screw is tightened in opposite direction to the normal screw tightening, with the objective of not loosening the head on gradual vibration. Microphone (D14) for checking hearing capability of the user by placing a sound object in front of the microphone.
The monitor further has a charging port (D15), a HDMI port (D16) to connect to a computer, a touch display (D17), a power ON/OFF button (D18), and control units. The control units include auto controller (D19) to control frequency from 500 Hz to 20 KHz. When user press the panic button (D12), doctor will come to know the frequencies at which user can hear, controller (D20) to controls the intensity of sound. The intensity can be varied by rotating the knob. Signal selector (D21) determines whether signal is pure-tones, speech, noise, or pulsed tones. Output selector (D22) determines whether the test signal is presented through air conduction or by bone conduction.
In operation, the sound which is received by microphone will be amplified and passed on to the front end of the testing device which has a permanent magnet, copper coil and a bite structure which is a trigon shaped aluminum channel for the user to bite. The gold coated copper coil placed in between high power neodymium magnets vibrate depending on the sound passed through the amplifier and this vibration is passed on to the trigon aluminum channel. When a deaf person bites the tip of trigon shaped Al-structure, the coil vibrations get transferred through the teeth. It passes towards the inner ear through skull bones, facial nerves and blood vessels. The cochlea (inner ear) is filled with a watery liquid, which moves in response to the vibrations. As the fluid moves, the cochlear partition also moves; thousands of hair cells sense the motion and convert that motion to electrical signals that are communicated via neurotransmitters to many thousands of nerve cells in brain.
The doctor can place the device on left and right portion of teeth to check the left and right ear audibility of patient, and also can place at center to check the audibility of both the ear.
The heat assisting device according to the present invention further comprises an efficient heat dissipating module to remove the heat generated in the device, said module includes a heat monitor, a Peltier module and a coolant tank. One side of heat monitor is connected to a microprocessor and the other side to the Peltier module. A PID controller is employed to maintain the temperature of system at set value. A temperature sensor gives the voltage information and a PID feedback system corrects the increase in temperature.
The Peltier module is a semiconductor-based electronic component functions as a small heat pump. By applying DC power source to a TEC, heat is transferred from one side of the module to the other. It creates a cold and hot side. The heat detected by the heat monitor is analyzed by the Peltier module and based on this temperature information, cold temperature will be generated on the other side. This create a temperature differential on each side. One side gets hot and the other side gets cool.
The coolant from coolant tank absorbs the heat and provide the cooling effect through the Peltier module. The Peltier module keeps the system below room temperature within 08 seconds using the PID feedback controller. After the use of hearing assistance device, a fan in coolant tank will be set ON to remove heat from the entire system. The fan takes the air from outside and cools the hot air inside the modules. At the time the user bites the hearing assistance device, a low pressure sensor module will sense and set the coolant fan OFF. During this operational time, Peltier module system manages the heat management inside the device.
In a preferred embodiment, the device can replace the bone conduction oscillator system used by audiologist. The oscillator system produces vibrations during bone conduction threshold testing. The head part, and C-shaped Al- frame of the device can be detached and used as the bone conduction oscillator for threshold testing. The device is economical and convenient to use.
If both the ears of the person are defected due to conductive hearing loss, then a single bite at the tip of the device is enough to hear the sound. If a person having sensorineural hearing losses at only one ear, device can bypass the sound from the defected ear towards the teeth through the device and then transfers it towards the healthy cochlear part of the other ear, thereby possible to hear the sound accurately.
The hearing assisting device of the present invention can also be used as vibration sensor for seismographic activities, earth quake detection and hill scape soil erosion. The bite structure of the hearing assisting device can sense very small acoustic surface vibration which can be passed through the amplifier- magnetic system where it can be processed and converted into sound waves. It can be taken as graph or sound waves using a microphone/oscilloscope system. The principle is reverse to the principle of hearing assistance device where the vibrations are converted into sound waves. The frequency of mechanical vibrations ranges usually from a hundredth of Hz to a dozen or so kHz. Parameters of mechanical vibrations are measured with this device and can be used for the seismological studies.
Although there has been shown and described the preferred embodiment of the present invention, it will be readily apparent to those skilled in the art that modifications may be made thereto which do not exceed the scope of the appended claims. Therefore, the scope of the invention is only to be limited by the following claims.
,CLAIMS:
1. A hearing assisting device (A1), comprising:
a vibrator (A2) configured for generating sound vibrations, said vibrator (A2) having a housing (A17) containing:
a receiving unit (A3) configured to pick and convert sound waves to electric signals;
an amplifying unit (A4) coupled to the receiving unit (A3) configured to convert and amplify the electric signals to digital signals; and
an actuating unit (A5) coupled with said amplifying unit (A4) configured to generate sound vibrations, said actuating unit (A5) having a conducting coil (A6) coated with Gold and Aluminium, being positioned between a pair of magnets (A7); and
a connector (A8) configured for coupling out the sound vibrations from the vibrator (A2),
wherein the tip of connector (A8) configured to be bitten by a deaf user such that the coil vibrations get transferred through the teeth, to transmit the sound vibrations to the inner ear through skull bones, facial nerves and blood vessels of the deaf user.
2. The hearing assisting device (A1) as claimed in claim 1, wherein said connector (A8) is a bite structure with C- shaped aluminum trigon channel having a sharpened tip configured to be bitten by the user.
3. The hearing assisting device (A1) as claimed in claim 1, wherein said pair of magnets (A7) generate magnetic field between coated copper coils (A6) to create a strong electromotive force in the housing (A17), which releases high energy electrons in very minimal vibration to transfer high frequency sound signals.
4. The hearing assisting device (A1) as claimed in claim 1, further comprises a frequency modulating unit to adjust the frequency of voice, based on the change in frequency, the pitch of voice changes.
5. The hearing assisting device (A1) as claimed in claim 1, further comprises an intensity adjusting unit to adjust the intensity of voice, based on the change in intensity the decibel value of sound changes.
6. The hearing assisting device (A1) as claimed in claim 1, wherein said receiving unit (A3) is microphone (A3’).
7. The hearing assisting device (A1) as claimed in claim 1, wherein said magnet (A7) is made of Neodymium.
8. The hearing assisting device (A1) as claimed in claim 1, further comprises a heat dissipating module to remove the heat generated in the device, said module includes a heat monitor, a Peltier module and a coolant tank, wherein one side of heat monitor is connected to a microprocessor and the other side to the Peltier module.
9. The hearing assisting device (A1) as claimed in claim 1-8, is configured to work with a mobile phone.
10. The hearing assisting device (A1) as claimed in claim 1-9, wherein said device is a headband configured to have a tension adjustable band connected to a connector at each end of the head band, wherein the end of the connector is in physical contact with the temporal bones behind the ears, the vibrating signals from the device passes to the inner ear through the ear bones.
11. The hearing assisting device (A1) as claimed in claim 1-9, wherein said device is an eye wear configured to have a pair of ear piece fitted with the connector, wherein the end of the connector is in physical contact with the temporal bones behind the ears, the vibrating signals from the device passes to the inner ear through the ear bones.
12. A deafness testing device (D1) comprising the hearing assisting device (A1) as claimed in claim 1-9, wherein the hearing assisting device (A1) is mounted on a monitor (D2), the deafness testing device (D2) checks the audibility range of deafness and the range of frequency at which the patient has more deafness.
13. The deafness testing device (D1) as claimed in claim 12, wherein the monitor (D2) has a shell (D3) at the top center to receive the connector (A8) of the hearing assisting device (A1).