Cochlear implant hearing aid system

Abstract

This application discloses a cochlear implantable hearing aid system, comprising: an external unit; an implantable unit; wherein the external unit includes: a power supply unit connected to a switching unit via a first path, wherein the switching unit is connected to ground via a second path and its output is connected to a first coil, and the switching unit is configured to function as a switching element, configured to switch between switching states, wherein the switching states include a first state in which current is applied to the first coil and a second state in which no current is applied to the first coil, wherein an encoded audio signal is provided to the switching unit as a control signal, wherein the first coil is inductively connected to a second coil disposed in the implantable unit; a measurement unit connected to at least one of the first and second paths and configured to measure a dissipated current occurring in relation to the switching state of the switching unit; wherein the resonant frequency of the inductive link between the first and second coils is adjusted based on at least one measured dissipated current.

Description

Technical Field

[0001] This invention relates to cochlear implant hearing aid systems. More specifically, this invention relates to a system having a dissipative current measurement unit and a method for a cochlear implant hearing aid system having a dissipative current measurement unit. Background Technology

[0002] Cochlear implants (CIs) are devices that contain electrodes inserted into the inner ear (cochlea) to restore hearing in people suffering from severe to profound hearing loss. CIs bypass most of the functional auditory chain and generate a train of electrical impulses within the cochlea to initiate action potentials from hair cells. These devices are therefore mostly considered biofitted electronic machines. Depending on their implementation, they may be fully implanted or consist of two main parts. The first part is a sound processor, typically placed near the ear. It contains a microphone that captures ambient sound, which is processed in real time into a series of codes usable by the second part implanted within the patient. The implant receives power and sound information from the sound processor via radio frequency and generates electrical impulses that are sent into the cochlea via electrodes within the cochlea.

[0003] Reducing power loss in sound processors is a topic of great interest, but it is often very difficult to achieve. Moreover, determining the power loss itself is often an even greater challenge before reducing it.

[0004] Therefore, a solution is needed that addresses at least some of the problems mentioned above. Summary of the Invention

[0005] According to one aspect, a cochlear implantable hearing aid system is disclosed. The system includes an external unit configured to receive acoustic sound and process the acoustic sound into an encoded audio signal, and an implantable unit configured to receive the encoded audio signal. Furthermore, the external unit includes a power supply unit connected to a switching unit via a first path, wherein the switching unit is connected to ground via a second path and its output is connected to a first coil. The switching unit is configured to function as a switching element, configured to switch between switching states, wherein the switching states include a first state in which current is applied to the first coil and a second state in which no current is applied to the first coil. The encoded audio signal is provided to the switching unit as a control signal, and the first coil is inductively connected to a second coil disposed in the implantable unit. The system also includes a measurement unit connected to at least one of the first and second paths and configured to measure a dissipated current occurring in relation to the switching state of the switching unit. Based on at least one measured dissipated current, the resonant frequency of the inductive link between the first and second coils is adjusted.

[0006] This enables the resonant frequency to be adjusted based on the measured dissipation current (also referred to below as the tuning of the switching unit).

[0007] Specifically, the aforementioned cochlear implant hearing aid system also enables the measurement of the tuning / detuning (absence / presence of dissipated current) of the switching unit. Therefore, by using a single measurement result, it is possible to directly determine which type of first and second coils (antennas) are used to establish the inductive link between the external unit and the implantable unit, thereby addressing the issue of patients with different skin thicknesses, for example, by differentiating between skin thickness ranges of 1mm to 6mm and 4mm to 11mm.

[0008] In particular, the cochlear implant hearing aid system enables monitoring of resonant frequency adjustments, and even continuous monitoring of these adjustments during the use of the cochlear implant hearing aid system—a feature unique to cochlear implant hearing aid systems. This leads to further improvements in system power efficiency, as the induction link becomes more efficient due to its ability to continuously adjust the resonant frequency (keeping the resonant frequency of the first coil consistent with or nearly consistent with the target resonant frequency). Specifically, the resonant frequency of the first coil is adjusted to minimize at least one measured dissipated current.

[0009] As a result of continuous monitoring of the resonant frequency adjustment, the adjustment of the resonant frequency (tuning of the switching unit) can be performed in real time, thereby further reducing power loss.

[0010] Furthermore, the first path also includes a shunt resistor, and the measuring unit can be configured to measure the dissipated current across the shunt resistor. Additionally, the measuring unit may include an amplifying element configured to amplify the current measured by the measuring unit.

[0011] Optionally, the second path may also include a third coil inductively coupled to the fourth coil, and the measuring unit includes the fourth coil and may be further configured to measure the induced current in the fourth coil and derive the dissipated current therefrom. Optionally, the measuring unit may also be configured to include an amplifying element configured to amplify the induced current in the fourth coil. Furthermore, the measuring unit may be configured to include a resistor connected to the output of the amplifying element and a capacitor, one terminal of which is connected to the connection between the output of the amplifying element and the resistor, and the other terminal is connected to ground.

[0012] Each of the measurement unit configurations outlined above simplifies the design of the measurement unit by utilizing existing components in the switching unit and / or cochlear implant hearing aid system. Specifically, by using existing components, it avoids adding new components to the switching unit / cochlear implant hearing aid system, which would complicate the design of the measurement unit.

[0013] In addition, this also enables the measurement unit to avoid affecting the switching unit that adjusts the resonant frequency, and to avoid the measurement unit generating parasitic resistance to the circuitry that constitutes the switching unit / cochlear implant hearing aid system.

[0014] In addition, the switching unit may be, for example, a Class E amplifier.

[0015] This theoretically gives the switching unit 100% efficiency, meaning there is no power loss and therefore no dissipated current in the transistors that make up the Class E amplifier.

[0016] According to at least one embodiment, the resonant frequency of the induction link can be adjusted based on at least one measured dissipation current by selectively connecting at least one additional switched capacitor to the circuit constituting the switching unit.

[0017] Alternatively, according to another embodiment, the switching unit may further include at least one of a first switched capacitor and a second switched capacitor, wherein the first switched capacitor is connected in parallel with a first circuit element, and the second switched capacitor is connected in series with a second circuit element. Furthermore, the resonant frequency is adjusted based on at least one measured dissipation current by selectively connecting at least one of the first and second switched capacitors to the circuit constituting the switching unit.

[0018] Furthermore, the switching unit may also include a transistor element, wherein the output of the transistor element is connected to ground via a first circuit element and to a first coil via a second circuit element. Additionally, the first circuit element may be a third capacitor, and the second circuit element may be a fourth capacitor.

[0019] Using a switched capacitor to adjust the resonant frequency during the monitoring process mentioned above enables real-time adjustment of the switching unit's tuning.

[0020] According to another aspect, a method for a cochlear implant hearing aid system is disclosed. The cochlear implant hearing aid system includes an external unit that receives acoustic sound and processes the acoustic sound into an encoded audio signal, and an implantable unit that receives the encoded audio signal. The method includes the steps of: providing power from a power supply unit to a switching unit in the external unit via a first path, wherein the switching unit is connected to ground via a second path and its output is connected to a first coil. Furthermore, the switching unit serves as a switching element for switching between switching states, wherein the switching states include a first state in which current is applied to the first coil and a second state in which no current is applied to the first coil. The encoded audio signal is provided to the switching unit as a control signal, and the first coil is inductively connected to a second coil disposed in the implantable unit. The method further includes the step of: measuring a dissipated current occurring across at least one of the first and second paths in relation to the switching state of the switching unit. The method further includes: adjusting the resonant frequency of the inductive link between the first and second coils based on at least one measured dissipated current.

[0021] This allows the method to adjust the resonant frequency based on the measurement of at least one dissipation current.

[0022] Specifically, as can be deduced above, the aforementioned method for cochlear implant hearing aid systems also enables the measurement of tuning / detuning of the switching unit and the monitoring of resonant frequency adjustments, especially during the use of the cochlear implant hearing aid system, which is unique to cochlear implant hearing aid systems. Therefore, the aforementioned method leads to a further improvement in the system's power efficiency because the inductive link becomes more efficient due to continuous adjustment of the resonant frequency, enabling real-time adjustment of the resonant frequency and thus further reducing power loss.

[0023] In addition, the method may include the steps of: measuring a first dissipated current across a shunt resistor included in a first path, and / or measuring a second dissipated current based on a current induced in a fourth coil inductively coupled to a third coil, wherein the third coil is included in a second path.

[0024] This allows the method of the present invention to measure dissipated current by developing existing components of the switching unit and / or cochlear implant hearing aid system. Specifically, by applying the method of the present invention to existing components, the addition of new components to the switching unit / cochlear implant hearing aid system can be avoided, resulting in a more simplified measurement.

[0025] This also enables measurements that avoid affecting the tuning of the switching unit, and measurements that avoid introducing parasitic resistance into the circuitry that constitutes the switching unit / cochlear implant hearing aid system.

[0026] Furthermore, the method of the present invention may also include the step of: deriving a weighted dissipation current from the measured first and second dissipation currents based on a pre-determined weighting algorithm. Additionally, the method includes: adjusting the resonant frequency of the induction link based on the derived weighted dissipation current.

[0027] This enables an increase in the accuracy of resonant frequency adjustment (tuning of the switching unit).

[0028] Furthermore, the method of the present invention may also include the step of adjusting the resonant frequency of the induction link based on at least one measured dissipation current by selectively connecting at least one additional switched capacitor to the circuit constituting the switching unit.

[0029] Optionally, the switching unit also includes at least one of a first switched capacitor and a second switched capacitor, wherein the first switched capacitor is connected in parallel with a first circuit element and the second switched capacitor is connected in series with a second circuit element. The method may further include the step of adjusting the resonant frequency of the induction link based on at least one measured dissipation current by selectively connecting at least one of the first and second switched capacitors to the circuit constituting the switching unit.

[0030] The switching unit may be a Class E amplifier and also includes a transistor element, wherein the output of the transistor element is connected to ground via a first circuit element, and its output is connected to a first coil via a second circuit element. Furthermore, the first circuit element may be a third capacitor, and the second circuit element may be a fourth capacitor.

[0031] The method of using switched capacitors to adjust the resonant frequency during the monitoring process mentioned above enables real-time adjustment of the tuning of the switching unit. Attached Figure Description

[0032] Various aspects of the invention will be best understood from the following detailed description taken in conjunction with the accompanying drawings. For clarity, these drawings are schematic and simplified, showing only the details necessary for understanding the invention while omitting other details. Throughout the specification, the same reference numerals are used for the same or corresponding parts. Features of each aspect may be combined with any or all features of other aspects. These and other aspects, features, and / or technical effects will be apparent from and illustrated in the following figures, wherein:

[0033] Figure 1 A schematic diagram of a cochlear implant hearing aid system according to a first embodiment of the present invention is shown;

[0034] Figure 2 A schematic diagram of a cochlear implant hearing aid system according to a first embodiment of the present invention is shown;

[0035] Figure 3 A schematic diagram of a cochlear implant hearing aid system according to a second embodiment of the present invention is shown;

[0036] Figure 4 A schematic diagram of a cochlear implant hearing aid system according to a second embodiment of the present invention is shown;

[0037] Figure 5 A schematic diagram of a cochlear implant hearing aid system according to a second embodiment of the present invention is shown;

[0038] Figure 6 A schematic diagram of a cochlear implant hearing aid system according to a third embodiment of the present invention is shown;

[0039] Figure 7 The tuning of the E-stage amplifier via switched capacitors is shown; and

[0040] Figure 8 A method for using a cochlear implant hearing aid system according to an embodiment of the present invention is shown. Detailed Implementation

[0041] The detailed description below, taken in conjunction with the accompanying drawings, serves as a description of various different configurations. This detailed description includes specific details to provide a thorough understanding of several different concepts. However, it will be apparent to those skilled in the art that these concepts can be implemented without these specific details. Several aspects of the apparatus and method are described by various different blocks, functional units, modules, elements, circuits, steps, processes, algorithms, etc. (collectively, “elements”). Depending on the specific application, design constraints, or other reasons, these elements may be implemented using electronic hardware, computer programs, or any combination thereof.

[0042] Electronic hardware may include microprocessors, microcontrollers, digital signal processors (DSPs), field-programmable gate arrays (FPGAs), programmable logic devices (PLDs), gating logic, discrete hardware circuits, and other suitable hardware configured to perform the various functions described in this specification. The term "computer program" should be interpreted broadly as instruction, instruction set, code, code segment, program code, program, subroutine, software module, application, software application, software package, routine, subroutine, object, executable, thread of execution, program, function, etc., whether referred to as software, firmware, middleware, microcode, hardware description language, or other names.

[0043] Hearing devices may include hearing aids suitable for improving or enhancing a user's hearing ability, which are achieved by receiving sound signals from the user's environment, generating corresponding audio signals, possibly modifying the audio signals, and providing the possibly modified audio signals as audible signals to at least one ear of the user. "Hearing device" may also refer to devices such as headsets or headphones suitable for electronically receiving audio signals, possibly modifying the audio signals, and providing the possibly modified audio signals as audible signals to at least one ear of the user. The audible signals may be provided in the following forms: acoustic signals radiated into the user's outer ear; sound signals transmitted as mechanical vibrations through the bone structures of the user's head and / or through parts of the middle ear to the user's inner ear; and electrical signals transmitted directly or indirectly to the user's cochlear nerve and / or auditory cortex.

[0044] Hearing devices are suitable for wearing in any known manner. This may include: i) placing the unit of the hearing device behind the ear (having a tube for guiding acoustic signals into the ear canal or having a receiver / speaker positioned close to or within the ear canal), such as a behind-the-ear hearing aid; and / or ii) placing the hearing device wholly or partially within the user's auricle and / or ear canal, such as an in-the-ear hearing aid or a canal / deep-in-the-canal hearing aid; or iii) configuring the unit of the hearing device to be connected to a fixation device implanted into the skull, such as a bone-anchored hearing aid or a cochlear implant; or iv) configuring the unit of the hearing device as a unit that is wholly or partially implanted, such as a bone-anchored hearing aid or a cochlear implant.

[0045] A “hearing system” refers to a system comprising one or two hearing devices. A “binaural hearing system” refers to a system comprising two hearing devices adapted to collaboratively provide audible signals to both of a user’s ears. A hearing system or a binaural hearing system may also include an auxiliary device that communicates with at least one hearing device, which affects the operation of the hearing device and / or benefits from its functionality. A wired or wireless communication link is established between the at least one hearing device and the auxiliary device to allow the exchange of information (such as control and status signals, possibly audio signals). The auxiliary device may include at least one of the following: a remote control, a remote microphone, an audio gateway device, a mobile phone, a broadcasting system, a car audio system, a music player, or a combination thereof. The audio gateway device is adapted to receive multiple audio signals, such as from an entertainment device (e.g., a TV or music player), a telephone device (e.g., a mobile phone), or a computer (e.g., a PC). The audio gateway device is also adapted to select and / or combine appropriate signals from the received audio signals (or combinations of signals) to transmit to the at least one hearing device. The remote control is adapted to control the function and operation of the at least one hearing device. The remote control functionality can be implemented in a smartphone or another electronic device, which may run an application that controls the functionality of at least one hearing device.

[0046] Generally, a hearing device includes i) an input unit, such as a microphone, for receiving sound signals from the user's surroundings and providing a corresponding input audio signal; and / or ii) a receiving unit for electronically receiving the input audio signal. The hearing device also includes a signal processing unit for processing the input audio signal and an output unit for providing an audible signal to the user based on the processed audio signal.

[0047] The input unit may include multiple input microphones, for example, for providing direction-dependent audio signal processing. The aforementioned directional microphone system is adapted to amplify a target sound source among multiple sound sources in a user's environment. In one aspect, the directional system is adapted to detect (e.g., adaptive detection) the direction from which a specific portion of the microphone signal originates. This can be achieved using methods conventionally known. The signal processing unit may include an amplifier adapted to apply a frequency-dependent gain to the input audio signal. The signal processing unit may also be adapted to provide other suitable functions such as compression, noise reduction, etc. The output unit may include an output transducer, such as a loudspeaker / receiver, for providing airborne acoustic signals percutaneously or transdermally to the skull, or a vibrator for providing acoustic signals propagating through structures or fluids. In some hearing devices, the output unit may include one or more output electrodes for providing electrical signals, such as in cochlear implants.

[0048] "Cochlear implant hearing aid system" refers to a specific type of "hearing system" that includes an external unit and an implantable unit. The external unit receives acoustic sounds and processes them into coded audio signals, while the implantable unit receives the coded audio signals.

[0049] Now for reference Figure 1 It shows a schematic diagram of a cochlear implant hearing aid system according to a first embodiment of the present invention, namely a cochlear implant hearing aid system having a measuring unit configured to measure dissipated current.

[0050] Specifically, according to Figure 1 A cochlear implant hearing aid system 100 is disclosed. The system 100 includes an external unit 110 configured to receive acoustic sound and process the acoustic sound into an encoded audio signal (according to...). Figure 1 The diagram excludes the implantable unit 120 and the implantable unit 120 configured to receive encoded audio signals. Furthermore, the external unit 110 includes a power supply unit 111 connected to the switching unit 112 via a first path, wherein the switching unit 112 is connected to ground via a second path and its output is connected to the first coil 113. Additionally, the switching unit 112 is configured to function as a switching element, configured to switch between switching states, wherein the switching states include a first state where current is applied to the first coil 113 and a second state where no current is applied to the first coil 113. The encoded audio signal is provided to the switching unit 112 as a control signal, and the first coil 113 is inductively connected to a second coil 121 disposed in the implantable unit 120. The system 100 also includes a measurement unit 130 connected to the first path and configured to measure dissipated currents occurring in relation to the switching states of the switching unit 112, wherein the first path also includes a shunt resistor 114, and the measurement unit 130 is configured to measure the dissipated current across the shunt resistor 114. Based on the measured dissipation current, the resonant frequency of the induction link between the first and second coils 113 and 121 is adjusted.

[0051] Measuring element 135 is disposed in measuring unit 130 to schematically illustrate the measurements performed by measuring unit 130. Furthermore, the feedback control mechanism from measuring unit 135 to switching unit 112 is indicated. Figure 1 (The dashed arrow in the diagram) allows for continuous monitoring of resonant frequency adjustments. Furthermore, the second path includes at least one of a coil and a resistor.

[0052] This allows the resonant frequency to be adjusted based on the measured dissipation current.

[0053] Specifically, the aforementioned cochlear implant hearing aid system 100 also enables the measurement of the tuning / detuning of the switching unit 112. Therefore, by using a single measurement result, it is possible to directly determine which type of first and second coils 113, 121 are used to establish the inductive link between the external unit 110 and the implantable unit 120, thereby addressing the issue of patients having different skin thicknesses, for example, by differentiating between skin thickness ranges of 1 mm to 6 mm and 4 mm to 11 mm.

[0054] In particular, the cochlear implant hearing aid system 100 also enables monitoring of the adjustment of the resonant frequency, and even enables continuous monitoring of this adjustment during the use of the cochlear implant hearing aid system, which is unique to the cochlear implant hearing aid system 100. This leads to a further improvement in the power efficiency of the system 100, because the induction link becomes more efficient due to its ability to continuously adjust the resonant frequency (keeping the resonant frequency of the first coil 121 consistent with or nearly consistent with the target resonant frequency). Specifically, the resonant frequency of the first coil 121 is adjusted to minimize the measured dissipated current.

[0055] As a result of continuous monitoring of the resonant frequency adjustment, the adjustment of the resonant frequency (tuning of the switching unit 112) can be performed in real time, thereby enabling further reduction of power loss.

[0056] according to Figure 1 System 100 also simplifies the design of measurement unit 130 by utilizing existing components of switching unit 112 and / or cochlear implant hearing aid system 100. Specifically, by using existing components, it avoids adding new components to switching unit 112 / cochlear implant hearing aid system 100, which would complicate the design of measurement unit 130.

[0057] In addition, according to Figure 1 This system also enables the measurement unit 130 to avoid affecting the adjustment of the resonant frequency of the switching unit 112 (affecting the tuning of the switching unit). In addition, the aforementioned cochlear implant hearing aid system 100 also enables the measurement unit 130 to avoid generating parasitic resistance to the circuitry constituting the switching unit 112 / cochlear implant hearing aid system 100.

[0058] Figure 2 A schematic diagram of a cochlear implant hearing aid system 200 according to a first embodiment of the present invention is shown. Specifically, Figure 2 Unlike Figure 1 The point is that, compared to Figure 1 Measurement unit 130, Figure 2 The measurement unit 230 is shown to have alternative structures. Specifically, according to Figure 2 The measurement unit 230 may also include an amplifying element 231 configured to amplify the current to be measured by the measurement unit 230.

[0059] The amplification makes it easier to measure dissipated current and reduces measurement errors based on background noise. Regarding the quality of the inductive link between the first coil 113 and the second coil 121, the higher the measured current, the worse the inductive link quality, because more current is consumed from the power supply unit 111 to transmit the encoded audio signal.

[0060] refer to Figure 3The diagram illustrates a cochlear implant hearing aid system according to a second embodiment of the present invention, namely a cochlear implant hearing aid system having a measuring unit configured to measure dissipated current.

[0061] Specifically, according to Figure 3 A cochlear implant hearing aid system 300 is disclosed. The system 300 includes an external unit 310 configured to receive acoustic sound and process the acoustic sound into an encoded audio signal (according to...). Figure 3 The diagram excludes the implantable unit 320 and the implantable unit 320 configured to receive encoded audio signals. Furthermore, the external unit 310 includes a power supply unit 311 connected to the switching unit 312 via a first path, wherein the switching unit 312 is connected to ground via a second path and its output is connected to the first coil 313. Additionally, the switching unit 312 is configured to function as a switching element, configured to switch between switching states, wherein the switching states include a first state where current is applied to the first coil 313 and a second state where no current is applied to the first coil 313. The encoded audio signal is provided to the switching unit 312 as a control signal, and the first coil 313 is inductively connected to a second coil 321 disposed in the implantable unit 320. The system 300 also includes a measurement unit 330 connected to the second path and configured to measure dissipated currents occurring in relation to the switching states of the switching unit 312, wherein the second path includes a third coil 315 inductively coupled to a fourth coil 332, and the measurement unit 330 includes the fourth coil 332. The measuring unit 330 is also configured to measure the induced current in the fourth coil and derive the dissipated current therefrom. Based on the measured dissipated current, the resonant frequency of the induction link between the first and second coils 313 and 321 is adjusted.

[0062] Measuring element 335 is disposed in measuring unit 330 to schematically illustrate the measurements performed by measuring unit 330. Furthermore, the feedback control mechanism from measuring unit 335 to switching unit 312 is indicated. Figure 3 (The dashed arrow in the image) allows for continuous monitoring of resonant frequency adjustments.

[0063] Similar to the first embodiment, according to Figure 3 The system 300 enables real-time monitoring of resonant frequency adjustments, thereby further reducing power loss. Additionally, similar to the first embodiment, according to... Figure 3 The system 300 also simplifies the design of the measurement unit 330 by developing the switching unit 312 and / or existing components of the cochlear implant hearing aid system 300.

[0064] Furthermore, with Figure 1Similar to other embodiments, the system 300 also enables the measurement unit 330 to avoid affecting the adjustment of the resonant frequency (tuning of the switching unit) of the switching unit 312, and also enables the measurement unit 330 to avoid generating parasitic resistance to the circuitry constituting the switching unit 312 / cochlear implant hearing aid system 300.

[0065] Figure 4 A schematic diagram of a cochlear implant hearing aid system 400 according to a second embodiment of the present invention is shown. Specifically, Figure 4 Unlike Figure 3 The point is that, compared to Figure 3 Measurement unit 330, Figure 4 The measurement unit 430 is shown to have alternative structures. Specifically, according to Figure 4 The measuring unit 430 may also include an amplifying element 431 configured to amplify the current induced in the fourth coil 432.

[0066] also, Figure 5 A schematic diagram of a cochlear implant hearing aid system 500 according to a second embodiment of the present invention is shown. Specifically, Figure 5 Unlike Figure 3 and Figure 4 The point is that, compared to according to Figure 3 and 4 Measurement units 330 and 430, Figure 5 A measurement unit 530 with an alternative structure is shown. Specifically, compared to according to Figure 4 The measuring unit 430, according to Figure 5 The measurement unit 530 may also include a resistor 533 connected to the output of the amplification element 531 and a capacitor 534, one terminal of which is connected to the connection between the output of the amplification element 531 and the resistor 533, and the other terminal of which is connected to ground.

[0067] Similar to the first embodiment, the amplification makes it easier to measure dissipated current and reduces measurement errors based on background noise.

[0068] Specifically, regarding the basis Figure 5In the cochlear implant hearing aid system 500, at maximum efficiency (perfect tuning), theoretically there is no current in the drain (not shown) of the transistor in the switching unit 512, and therefore no dissipative current. However, if the switching unit is detuned, dissipative current appears in the transistor, resulting in power loss. The dissipative current flows through the third coil 515, and due to the inductive coupling between the third and fourth coils 515 and 523, a replica of this dissipative current is generated in the fourth coil 523. The amplifying element 531 provides impedance adjustment between the very low impedance of the fourth coil 532 and the measuring circuit including the resistor 533 and the capacitor 534. The amplifying element 531 amplifies the current in the fourth coil 532 (a replica of the generated dissipative current). The current in the fourth coil 532 is an AC current with a high frequency content. Therefore, measuring such a current is complex. Thus, after being amplified by the amplifying element 531, the resistor 533 and the capacitor 534 enable the generation of a DC voltage (the average value of the signal) from this AC current. Therefore, the voltage used to determine the dissipated current can be effectively measured across capacitor 534.

[0069] refer to Figure 6 This illustration shows a schematic diagram of a cochlear implant hearing aid system 600 according to a third embodiment of the present invention. Generally, the third embodiment is a combination of the first and second embodiments. Figure 6 A specific combination of the first and second embodiments is shown.

[0070] That is, according to Figure 6 A cochlear implant hearing aid system 600 is disclosed. The system 600 includes an external unit 610 configured to receive acoustic sound and process the acoustic sound into an encoded audio signal (according to...). Figure 6 The diagram excludes the implantable unit 620 and the implantable unit 620 configured to receive encoded audio signals. Furthermore, the external unit 610 includes a power supply unit 611 connected to the switching unit 612 via a first path, wherein the switching unit 612 is connected to ground via a second path and its output is connected to the first coil 613. Additionally, the switching unit 612 is configured to function as a switching element, configured to switch between switching states, wherein the switching states include a first state in which current is applied to the first coil 613 and a second state in which no current is applied to the first coil 613. The encoded audio signal is provided to the switching unit 612 as a control signal, and the first coil 613 is inductively connected to a second coil 621 disposed in the implantable unit 620.

[0071] The system 600 also includes a first measurement unit 630a connected to the first path and configured to measure a first dissipated current that occurs in relation to the switching state of the switching unit 612. The first measurement unit 630a also includes a first amplification element 631a configured to amplify the current measured by the first measurement unit 630a. The first path also includes a shunt resistor 614, and the first measurement unit 630a is configured to measure the first dissipated current across the shunt resistor 614.

[0072] Furthermore, the system 600 includes a second measuring unit 630b connected to the second path and configured to measure a second dissipated current associated with the switching state of the switching unit 612. The second path includes a third coil 615 inductively coupled to the fourth coil 632b, and the second measuring unit 630b includes the fourth coil 632b. Additionally, the second measuring unit 630b includes a second amplifying element 631b configured to amplify the current induced in the fourth coil 632b. Furthermore, the second measuring unit 630b includes a resistor 633b connected to the output of the second amplifying element 631b and a capacitor 634b, one terminal of which is connected to the connection between the output of the second amplifying element 631b and the resistor 633b, and the other terminal of the capacitor 634b is connected to ground. Furthermore, the second measuring unit 630b is configured to measure the current induced in the fourth coil 632b and derive the second dissipated current therefrom.

[0073] A first measuring element 635a is disposed in a first measuring unit 630a to schematically illustrate the measurement performed by the first measuring unit 630a, and a second measuring element 635b is disposed in a second measuring unit 630b to schematically illustrate the measurement performed by the second measuring unit 630b. Furthermore, the feedback control mechanism from the measuring units 635a and 635b to the switching unit 612 is indicated. Figure 6 (The dashed arrow in the image) enables continuous monitoring of resonant frequency tuning and / or further evaluation / assessment of the measured dissipation current.

[0074] according to Figure 6 The cochlear implant hearing aid system 600 shown adjusts the resonant frequency of the inductive link between the first and second coils 613, 621 based on at least one of the first and second measured dissipation currents.

[0075] In addition to the first and second embodiments, according to Figure 6 The cochlear implant hearing aid system 600 also essentially enables the comparison of first and second measured dissipation currents to improve the tuning of the switching unit 612 based on the comparison results. For example, according to Figure 6System 600 enables the calculation of a weighted dissipation current from the measured first and second dissipation currents based on a pre-determined weighting algorithm. Therefore, for example, the influence of background noise can be reduced. Consequently, the resonant frequency of the inductive link can be adjusted based on the calculated weighted dissipation current.

[0076] The aforementioned predetermined weighting algorithm is, for example, but not limited to, the following algorithms: averaging the first and second measured dissipation currents (50% weight for each measured current), selecting only the highest / lowest measured dissipation current (100% weight for a measured current), or weighting the first and second measured dissipation currents relative to their respective measured intensities.

[0077] Furthermore, according to several different exemplary embodiments, the switching units 112, 212, 312, 412, 512, and 612 may be, for example, Class E amplifiers.

[0078] Class E amplifiers are amplifiers designed to minimize losses using resonant loads, enabling theoretically 100% maximum efficiency. This is achieved by eliminating losses during the transistor switching performed by the transistors contained within the Class E amplifier. Therefore, if the current dissipated by the transistors is relatively small, the Class E amplifier is well-tuned (the resonant frequency is well-adjusted). However, if the current dissipated by the transistors includes, for example, large spike currents than in the well-tuned case, the Class E amplifier becomes detuned (the resonant frequency is incorrectly adjusted).

[0079] Therefore, the aforementioned Class E amplifiers theoretically make the switching units 112, 212, 312, 412, 512, and 612 100% efficient, which means there is no power loss and therefore no dissipated current.

[0080] refer to Figure 7 The invention illustrates a cochlear implant hearing aid system 700, wherein a switching unit 712 is a Class E amplifier, and the tuning of the Class E amplifier 712 is performed via switched capacitors 743 and 744.

[0081] In addition, such as Figure 7 As shown in the examples, according to several different exemplary embodiments, the resonant frequency of the induction link can be adjusted based on at least one measured dissipation current by selectively connecting at least one additional switched capacitor 743, 744 to the circuit constituting the switching units 112, 212, 312, 412, 512, 612, 712.

[0082] Furthermore, according to several different exemplary embodiments, the switching units 112, 212, 312, 412, 512, 612, and 712 may also include at least one of a first switched capacitor 743 and a second switched capacitor 744, wherein the first switched capacitor 743 may be connected in parallel with the first circuit element 741, and the second switched capacitor 744 may be connected in series with the second circuit element 742. Moreover, the resonant frequency can be adjusted based on at least one measured dissipation current by selectively connecting at least one of the first and second switched capacitors 743 and 744 to the circuit constituting the switching units 112, 212, 312, 412, 512, 612, and 712.

[0083] Furthermore, according to several different exemplary embodiments, the switching units 112, 212, 312, 412, 512, 612, and 712 may also include a transistor element 740, wherein the output of the transistor element 740 may be connected to ground via a first circuit element 741 and to a first coil 713 via a second circuit element 742. Additionally, the first circuit element 741 may be a third capacitor, and the second circuit element 742 may be a fourth capacitor.

[0084] Based on the continuous monitoring process outlined above, the tuning of switching units 112, 212, 312, 412, 512, 612, and 712 can be adjusted in real time.

[0085] Regarding switched capacitors 743 and 744, it should be understood that these two switched capacitors are used as examples, and that switching units 112, 212, 312, 412, 512, 612, and 712 may include more than two such switched capacitors at different locations in the circuit constituting switching units 112, 212, 312, 412, 512, 612, and 712. Furthermore, switched capacitors, for example, according to... Figure 7 Either of the first and second switching capacitors 743, 744 can be a structure in which multiple capacitors are connected together in parallel or in series, or any combination thereof. Therefore, the fine-tuning switching units 112, 212, 312, 412, 512, 612, 712 are enabled.

[0086] Furthermore, multiple switch-capacitor pairs can be connected in parallel and in parallel with capacitor C2; for example, a single switch-capacitor pair includes a switch and a capacitor. If the first switch-capacitor pair is on while the others are off, the resonant frequency increases; when the second switch-capacitor pair is on and the others are off, the resonant frequency increases even more. For example, it is ideal for a first skin thickness when the first switch-capacitor pair is on, and ideal for a second skin thickness when the second switch-capacitor pair is on, wherein the second skin thickness is greater than the first skin thickness.

[0087] refer to Figure 8This illustrates a method for a cochlear implant hearing aid system according to an embodiment of the present invention. Figure 8 The method can be based on separately Figure 1 The cochlear implant hearing aid systems 100, 200, 300, 400, 500, 600, and 700 are described in sections 2, 3, 4, 5, 6, and 7. However, the method is not limited to these. Furthermore, according to... Figure 1 The cochlear implant hearing aid systems 100, 200, 300, 400, 500, 600, and 700 are executable according to... Figure 8 However, cochlear implant hearing aid systems 100, 200, 300, 400, 500, 600, and 700 are not limited to this.

[0088] Specifically, Figure 8A method for a cochlear implant hearing aid system 100, 200, 300, 400, 500, 600, 700 is shown, wherein the cochlear implant hearing aid system includes an external unit 110, 210, 310, 410, 510, 610, 710 that receives acoustic sound and processes the acoustic sound into an encoded audio signal, and an implantable unit 120, 220, 320, 420, 520, 620, 720 that receives the encoded audio signal. The method includes step S810: in external units 110, 210, 310, 410, 510, 610, 710, the power from power supply units 111, 211, 311, 411, 511, 611, 711 is provided to switching units 112, 212, 312, 412, 512, 612, 712 via a first path, wherein switching units 112, 212, 312, 412, 512, 612, 712 are connected to ground via a second path and their outputs are connected to first coils 113, 213, 313, 413, 513, 613, 713. Furthermore, switching units 112, 212, 312, 412, 512, 612, 712 serve as switching elements for switching between switching states, wherein the switching states include a first state in which current is applied to the first coils 113, 213, 313, 413, 513, 613, 713 and a second state in which no current is applied to the first coils. Encoded audio signals are provided as control signals to switching units 112, 212, 312, 412, 512, 612, 712, and the first coils 113, 213, 313, 413, 513, 613, 713 are inductively connected to the second coils 121, 221, 321, 421, 521, 621, 721 disposed in implantable units 120, 220, 320, 420, 520, 620, 720. The method further includes step S820: measuring at least one of the dissipated currents occurring across the first and second paths in relation to the switching state of the switching units 112, 212, 312, 412, 512, 612, 712. The method further includes step S830: adjusting the resonant frequency of the inductive link between the first and second coils 113, 213, 313, 413, 513, 613; 121, 221, 321, 421, 521, 621, 721 based on at least one measured dissipated current.

[0089] This enables the method of the present invention to measure dissipated current by developing existing components of the switching units 112,212,312,412,512,612,712 and / or cochlear implant hearing aid systems 100,200,300,400,500,600,700. Specifically, by applying the method of the present invention to existing components, the addition of new components to the switching units 112,212,312,412,512,612,712 / cochlear implant hearing aid systems 100,200,300,400,500,600,700 is avoided, resulting in a more simplified measurement.

[0090] Furthermore, according to several different exemplary embodiments, the method may also include the steps of: measuring a first dissipated current across a shunt resistor 114, 214, 614 included in a first path, and / or measuring a second dissipated current based on the current induced in a fourth coil 332, 432, 532, 632b inductively coupled to a third coil 315, 415, 515, 615, wherein the third coil 315, 415, 515, 615 is included in a second path.

[0091] This also enables measurements that avoid affecting the tuning of the switching units 112, 212, 312, 412, 512, 612, and avoid measurements that introduce parasitic resistance into the circuitry constituting the switching units 112, 212, 312, 412, 512, 612, 712 / cochlear implant hearing aid systems 100, 200, 300, 400, 500, 600, 700.

[0092] Furthermore, according to several different exemplary embodiments, the method of the present invention may also include the step of deriving a weighted dissipation current from the measured first and second dissipation currents based on applying a predetermined weighting algorithm. Additionally, the method may include adjusting the resonant frequency of the induction link based on the derived weighted dissipation current.

[0093] For example, the influence of background noise appearing in the measurement results may be reduced, and the combined evaluation of the first and second measured dissipation currents can increase the tuning accuracy of the switching units 112, 212, 312, 412, 512, 612, 712.

[0094] Furthermore, the method of the present invention may also include the step of adjusting the resonant frequency of the induction link based on at least one measured dissipation current by selectively connecting at least one additional switched capacitor to the circuit constituting the switching units 112, 212, 312, 412, 512, 612, 712.

[0095] Additionally, according to several different exemplary embodiments, the switching units 112, 212, 312, 412, 512, 612, 712 may further include at least one of a first switched capacitor and a second switched capacitor. The first switched capacitor is connected in parallel with a first circuit element, and the second switched capacitor is connected in series with a second circuit element. The method may further include the step of adjusting the resonant frequency of the induction link based on at least one measured dissipation current by selectively connecting at least one of the first and second switched capacitors to the circuit constituting the switching units 112, 212, 312, 412, 512, 612, 712. The switching units 112, 212, 312, 412, 512, 612, 712 may be Class E amplifiers and may further include transistor elements, wherein the output of the transistor element is connected to ground via a first circuit element, and its output is connected to a first coil via a second circuit element. The first circuit element may be a third capacitor, and the second circuit element may be a fourth capacitor.

[0096] This enables a method for real-time adjustment of the tuning of switching units 112, 212, 312, 412, 512, 612, and 712.

[0097] Cochlear implants typically include: i) an external portion for picking up and processing sound from the environment and determining a pulse sequence for electrode stimulation based on the current input sound; ii) a (typically wireless, such as inductive) communication link for simultaneously transmitting information about the stimulation sequence and transmitting energy to the implant portion; and iii) an implant portion that enables stimulation to be generated and applied to multiple electrodes, which may be implanted at different locations in the cochlea, thereby enabling stimulation of different frequencies within the auditory range. Such systems are described, for example, in US 4,207,441 and US 4,532,930.

[0098] On one hand, hearing devices include multi-electrode arrays, for example, in the form of a carrier comprising multiple electrodes adapted to be located in the cochlea and close to the user's auditory nerve. This carrier is preferably made of a flexible material to enable proper positioning of the electrodes in the cochlea, allowing the electrodes to be inserted into the recipient's cochlea. Preferably, the individual electrodes are spatially distributed along the length of the carrier, thereby providing a corresponding spatial distribution along the cochlear nerve in the cochlea when the carrier is inserted into the cochlea.

[0099] On the one hand, functionality can be stored or encoded as one or more instructions or codes on a tangible computer-readable medium. Computer-readable media include computer storage media suitable for storing computer programs including program code, which, when run on a processing system, cause the data processing system to perform at least some (e.g., most or all) of the steps of the methods described above.

[0100] By way of example, but not limitation, the aforementioned tangible computer-readable media may include RAM, ROM, EEPROM, CD-ROM or other optical disc storage, magnetic disk storage or other magnetic storage devices, or any other medium that can be used to execute or store required program code in the form of instructions or data structures and is accessible by a computer. As used herein, disks include compact discs (CDs), laser discs, optical discs, digital multipurpose discs (DVDs), floppy disks, and Blu-ray discs, wherein these disks typically magnetically copy data while simultaneously being optically copied using lasers. Combinations of the aforementioned disks should also be included within the scope of computer-readable media. In addition to being stored on tangible media, computer programs may also be transmitted via transmission media such as wired or wireless links or networks such as the Internet and loaded into data processing systems to run at locations other than tangible media.

[0101] Regarding the method described above, the resonant frequency adjustment can be implemented in software.

[0102] On one hand, the data processing system includes a processor adapted to run a computer program so that the processor performs at least some (or most or all) of the steps of the methods described above and in the claims.

[0103] When appropriately replaced by a corresponding process, the structural features of the apparatus described above, in detail in the "Detailed Description" section, and as defined in the claims can be combined with the method steps.

[0104] Unless explicitly stated otherwise, the singular forms “a” and “the” used herein include the plural forms (i.e., meaning “at least one”). It should be further understood that the terms “having,” “comprising,” and / or “including” as used in the specification indicate the presence of the stated features, integers, steps, operations, elements, and / or components, but do not preclude the presence or addition of one or more other features, integers, steps, operations, elements, components, and / or combinations thereof. It should be understood that, unless explicitly stated otherwise, when an element is referred to as “connected” or “coupled” to another element, it may be a direct connection or coupling to the other element, or there may be intermediate inserting elements. The term “and / or” as used herein includes any and all combinations of one or more of the listed related items. Unless explicitly stated otherwise, the steps of any method disclosed herein do not necessarily have to be performed in the exact order disclosed.

[0105] It should be understood that references to "an embodiment," "an embodiment," "an aspect," or "may" in this specification mean that a particular feature, structure, or characteristic described in connection with that embodiment is included in at least one embodiment of the invention. Furthermore, particular features, structures, or characteristics may be suitably combined in one or more embodiments of the invention. The foregoing description is provided to enable those skilled in the art to implement the various aspects described herein. Various modifications will be apparent to those skilled in the art, and the general principles defined herein may be applied to other aspects.

[0106] The claims are not limited to the aspects shown herein, but encompass the full scope consistent with the language of the claims, wherein, unless expressly stated, an element referred to in the singular does not mean "one and only one," but rather "one or more." Unless expressly stated, the term "some" means one or more.

[0107] Therefore, the scope of this invention should be determined based on the claims.

Claims

1. A cochlear implant hearing aid system, comprising: An external unit configured to receive acoustic sounds and process them into encoded audio signals; An implantable unit configured to receive encoded audio signals; The external unit includes The power supply unit is connected to the switching unit via the first path, wherein The switching unit is connected to ground via a second path and its output is connected to the first coil. The switching unit is configured to function as a switching element, switching between switching states, including a first state where current is applied to the first coil and a second state where no current is applied to the first coil. An encoded audio signal is provided to the switching unit as a control signal. The first coil is inductively connected to the second coil disposed in the implantable unit; A measurement unit is connected to a first path and configured to measure a first dissipated current that occurs in relation to the switching state of the switching unit, and a measurement unit is connected to a second path and configured to measure a second dissipated current that occurs in relation to the switching state of the switching unit. in The weighted dissipation current is derived from the measured first and second dissipation currents based on a pre-determined weighting algorithm. Based on the obtained weighted dissipation current, the resonant frequency of the induction link between the first and second coils is adjusted.

2. The cochlear implant hearing aid system according to claim 1, wherein the first path further includes a shunt resistor, and the measuring unit is further configured to measure a first dissipated current across the shunt resistor.

3. The cochlear implant hearing aid system of claim 2, wherein the measuring unit further includes an amplifying element configured to amplify the first dissipated current to be measured by the measuring unit.

4. The cochlear implant hearing aid system of claim 1, wherein the second path further includes a third coil inductively coupled to the fourth coil, and the measuring unit includes the fourth coil and is further configured to measure the current induced in the fourth coil and derive a second dissipated current therefrom.

5. The cochlear implant hearing aid system of claim 4, wherein the measuring unit is further configured to include an amplifying element configured to amplify the current induced in the fourth coil.

6. The cochlear implant hearing aid system of claim 5, wherein the measuring unit is further configured to include a resistor connected to the output of the amplifying element and a capacitor, one terminal of the capacitor being connected to the connection between the output of the amplifying element and the resistor, and the other terminal being connected to ground.

7. The cochlear implant hearing aid system according to claim 1, wherein the switching unit is a Class E amplifier.

8. The cochlear implant hearing aid system according to any one of claims 1-7, wherein the resonant frequency of the sensing link is adjusted by selectively connecting at least one additional switched capacitor to the circuit constituting the switching unit.

9. The cochlear implant hearing aid system according to claim 8, wherein the switching unit further comprises at least one of a first switched capacitor and a second switched capacitor, wherein The first switched capacitor is connected in parallel with the first circuit element, and The second switched capacitor is connected in series with the second circuit element; and The resonant frequency is adjusted by selectively connecting at least one of the first and second switched capacitors to the circuit constituting the switching unit.

10. The cochlear implant hearing aid system of claim 9, wherein the switching unit further comprises a transistor element, wherein the output of the transistor element is connected to ground via a first circuit element and to a first coil via a second circuit element; wherein the first circuit element is a third capacitor and the second circuit element is a fourth capacitor.

11. A method for a cochlear implant hearing aid system, the cochlear implant hearing aid system comprising an external unit for receiving acoustic sound and processing the acoustic sound into an encoded audio signal, and an implantable unit for receiving the encoded audio signal, the method comprising the steps of: In the external unit, power from the power supply unit is supplied to the switching unit via a first path, wherein the switching unit is connected to ground via a second path and its output is connected to the first coil, and the switching unit is used as a switching element to switch between switching states, wherein the switching states include a first state in which current is applied to the first coil and a second state in which current is not applied to the first coil, wherein the encoded audio signal is provided to the switching unit as a control signal, and wherein the first coil is inductively connected to a second coil disposed in the implantable unit. The first dissipated current, which is related to the switching state of the switching unit, is measured across the first path. The second dissipation current, which is related to the switching state of the switching unit, is measured across the second path. The weighted dissipation current is derived from the measured first and second dissipation currents based on a pre-determined weighting algorithm. and Based on the obtained weighted dissipation current, the resonant frequency of the induction link between the first and second coils is adjusted.

12. The method according to claim 11, further comprising the step of: The first dissipated current is measured across the shunt resistor included in the first path; and / or The second dissipated current is measured based on the current induced in a fourth coil that is inductively coupled to the third coil, wherein the third coil is included in the second path.

13. The method of claim 11, further comprising the step of: The resonant frequency of the induction link is adjusted by selectively connecting at least one additional switched capacitor to the circuit constituting the switching unit.

14. The method of claim 13, wherein the switching unit further comprises at least one of a first switched capacitor and a second switched capacitor, wherein the first switched capacitor is connected in parallel with the first circuit element, and the second switched capacitor is connected in series with the second circuit element; the method further comprises the step of: The resonant frequency of the induction link is adjusted by selectively connecting at least one of the first and second switched capacitors to the circuit constituting the switching unit. The switching unit is a Class E amplifier and also includes a transistor element, wherein the output of the transistor element is connected to ground via a first circuit element, and its output is connected to a first coil via a second circuit element; and / or The first circuit element is the third capacitor, and the second circuit element is the fourth capacitor.

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