Cochlear implant system with measurement unit

Abstract

A cochlear implant system with a measurement unit is disclosed, the cochlear implant system comprising: an external unit configured to receive an acoustic sound and to process the acoustic sound into an encoded audio signal; an implantable unit configured to receive the encoded audio signal; a pulse generation unit configured to generate a first electrical pulse of a first pulse duration and a second electrical pulse of a second pulse duration different from the first pulse duration based on the encoded audio signal; an electrode array comprising a plurality of electrodes, wherein at least one of the plurality of electrodes is configured to receive at least the first electrical pulse and the second electrical pulse; a capacitor connected to at least one of the plurality of electrodes; a measurement unit configured to measure a first electrical voltage based on the first electrical pulse and a second electrical voltage based on the second electrical pulse across the connection of the at least one of the plurality of electrodes and the capacitor; and an evaluation unit configured to calculate a voltage difference between the measured first and second electrical voltages.

Description

Technical Field

[0001] This invention relates to cochlear implant hearing systems and methods for using cochlear implant hearing systems. More specifically, this invention relates to the aforementioned system / method having a measurement unit configured to test the electrical characteristics of circuit elements of the cochlear implant, such as DC blocking capacitors, in relation to patient safety. 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] Because the implanted portion of the CI system is not easily accessible, inspecting it is extremely difficult. The only possible method is to perform a self-test. The CI includes voltage measurement circuitry, which, thanks to an analog-to-digital converter (ADC), can be used to check multiple voltages within the implant. The measurement results can be transmitted externally via a telemetry channel. For example, this circuitry can be used to measure the electrode's impedance by sending a known current into the electrode and measuring the resulting voltage. This measurement is primarily used to detect any electrode short circuits (very low impedance, meaning the resistivity is solely due to the electrode leads) or open circuits (infinite impedance, meaning current cannot flow through the circuit).

[0004] To ensure patient electrical safety during the generation of current pulses, any current pulse generated by CI is immediately balanced with an opposite current pulse containing the same charge. Any imbalanced stimulation can lead to an irreversible Faraday electrochemical reaction, resulting in apoptosis. A simplified representation of the stimulation waveform, whether or not it damages tissue, is shown in... Figure 1 Provided by China.

[0005] Figure 1 The left side shows the stimulus that will damage biological tissue because of the imbalance between the anodic and cathodic pulses. Figure 1 The right side shows an electrical device that does not contain errors that would lead to a safer stimulus, because the anode and cathode pulses are balanced.

[0006] In theory, it is possible to create a device that produces a perfectly balanced phase. In reality, all electrical devices have a tendency to err. Some CI devices attempt to generate pulses as balanced as possible, but the error between the anode and cathode phases can be as high as 10-15%. To avoid any DC components and to completely eliminate the risk or imbalance caused by the aforementioned errors, CI manufacturers insert DC blocking capacitors, which compensate for this difference at the end of the pulse. Some devices even send only a single active pulse and use a capacitor to completely discharge the active phase of the pulse, thus ensuring perfect charge balance. Figure 2 An example of automatic balancing from a DC blocking capacitor is shown.

[0007] Figure 2 The left side shows a real-world stimulus with an error in its cathode phase, resulting in a charge imbalance. Capacitors are used to discharge excess positive or negative charges. Figure 2 The right side also shows a pulse waveform that uses a DC blocking capacitor to ensure complete charge balance.

[0008] Currently, all CI manufacturers use DC blocking capacitors to ensure charge balance (see, for example, see below). Figure 2 Although the number of capacitors and how they are connected to the CI electrodes vary between manufacturers, they all share the same problem. If the DC blocking capacitor fails, the safety of CI electrical stimulation is compromised. Two types of capacitor failure can be observed. First, an open-circuit capacitor, resulting in no electrical stimulation at the electrode to which it is connected. Consequently, CI may become partially unusable. Second, a leaky capacitor, where electrical stimulation still occurs, but the capacitor no longer functions as a DC blocking capacitor. This results in a charge imbalance, thus affecting patient safety.

[0009] Currently, there is no method for estimating the state (short-circuit or leakage capacitor) of the capacitors embedded in the CI. Therefore, a solution is needed that addresses at least part of the problems mentioned above. Summary of the Invention

[0010] According to one aspect of the present invention, a cochlear implant 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. The system further includes a pulse generation unit configured to generate a first electrical pulse of a first pulse duration and a second electrical pulse of a second pulse duration different from the first pulse duration based on the encoded audio signal. The system also includes an electrode array comprising a plurality of electrodes, wherein at least one of the electrodes is configured to receive at least the first and second electrical pulses, and a capacitor connected to at least one of the electrodes. The system further includes a measurement unit configured to measure a first voltage based on the first electrical pulse and a second voltage based on the second electrical pulse across the connection of at least one of the electrodes to the capacitor. The system further includes an evaluation unit configured to calculate the voltage difference between the measured first and second voltages.

[0011] This enables reliable assessment of the state of the capacitors in the cochlear implant system.

[0012] Furthermore, the evaluation unit of the cochlear implant system can be configured to determine at least one fault type, including at least one of the multiple electrodes, a capacitor, and the connection between at least one of the multiple electrodes and the capacitor. The at least one fault type is determined based on a calculated voltage difference.

[0013] This allows for a more detailed evaluation of the circuitry that makes up the cochlear implant system.

[0014] Furthermore, if the calculated voltage difference is zero, at least one fault type is determined, indicating a capacitor short circuit.

[0015] This enables reliable identification of short-circuited capacitors in cochlear implant systems.

[0016] In addition, the evaluation unit of the cochlear implant system can also be configured to derive the capacitance value of a capacitor based on a calculated voltage difference, wherein the derived capacitance value indicates at least one fault type associated with the capacitor.

[0017] In addition, if the obtained capacitance value exceeds a predetermined threshold of the capacitor's nominal capacitance value, at least one fault type associated with the capacitor indicates capacitor leakage.

[0018] This enables reliable identification of leakage capacitors in cochlear implant systems.

[0019] Furthermore, if the obtained capacitance value is equal to or lower than a predetermined threshold, the evaluation unit can also be configured to determine at least one fault type of at least one of the plurality of electrodes and at least one of the plurality of electrodes connected to the capacitor.

[0020] This allows for a more detailed evaluation of the circuitry that makes up the cochlear implant system.

[0021] Furthermore, the evaluation unit of the cochlear implant system can also be configured to derive voltage relationships over time, including the relationship between the duration of the electrical pulse and the voltage measured based on the electrical pulse. Additionally, the evaluation unit can be configured to derive at least one voltage relationship fault type based on the derived voltage relationships, including at least one voltage relationship fault type involving at least one of the plurality of electrodes, a capacitor, and the connection between at least one of the plurality of electrodes and the capacitor.

[0022] Furthermore, if the voltage relationship obtained over time is nonlinear, at least one voltage relationship fault type indicates at least one of the multiple electrodes, a capacitor, and the connection of at least one of the multiple electrodes to the capacitor.

[0023] This allows for a more detailed evaluation of the circuitry that makes up the cochlear implant system in alternative ways.

[0024] In addition, the capacitors in cochlear implant systems can be DC blocking capacitors.

[0025] In addition, the measurement unit of the cochlear implant system can also be configured to measure the first and second voltages at the end of the corresponding pulse duration.

[0026] Furthermore, the pulse generation unit of the cochlear implant system can also be configured to select the duration of the first and second pulses based on the nominal time constant corresponding to the connection with at least one of the plurality of electrodes and a capacitor.

[0027] This can improve the accuracy of the calculated / derived values.

[0028] Furthermore, the pulse generation unit can be configured to generate an electrical pulse based on at least one current intensity, wherein the measurement unit is further configured to perform measurements for each corresponding current intensity. Additionally, the evaluation unit is configured to calculate the voltage difference for each corresponding current intensity, and / or derive the capacitance value of the capacitor for each corresponding current intensity based on the calculated voltage difference. Furthermore, the evaluation unit is also configured to evaluate at least one calculated voltage difference and / or at least one derived capacitance value based on an error minimization method.

[0029] This allows for further improvement in the accuracy of the calculated / derived values.

[0030] Furthermore, at least one of the measurement unit and evaluation unit of the cochlear implantation system may be configured to be located within one or more processors, and the one or more processors may be configured to be located within at least one of the external unit and the implantable unit.

[0031] This allows for adjustments to the structure of the cochlear implant system.

[0032] According to another aspect, a method for a cochlear implant system is disclosed, the cochlear implant 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 includes the steps of: generating a first electrical pulse with a first pulse duration and a second electrical pulse with a second pulse duration different from the first pulse duration based on the encoded audio signal. The method further includes the steps of: receiving at least the first and second electrical pulses through at least one of a plurality of electrodes included in an electrode array, wherein at least one of the plurality of electrodes is connected to a capacitor. The method further includes: measuring a first voltage based on the first electrical pulse and a second voltage based on the second electrical pulse across the connection of at least one of the plurality of electrodes to the capacitor. The method further includes: calculating the voltage difference between the measured first and second voltages.

[0033] This enables reliable assessment of the state of the capacitors in the cochlear implant system.

[0034] In addition, the method may also include the steps of: determining at least one fault type of at least one of the plurality of electrodes, a capacitor, and the connection between at least one of the plurality of electrodes and the capacitor based on the calculated voltage difference.

[0035] If the calculated voltage difference is zero, at least one fault type is determined, indicating a capacitor short circuit.

[0036] This enables reliable identification of short-circuited capacitors in cochlear implant systems.

[0037] In addition, the method may include the step of: deriving the capacitance value of the capacitor based on the calculated voltage difference, wherein the derived capacitance value may indicate at least one fault type associated with the capacitor.

[0038] If the obtained capacitance value exceeds a predetermined threshold of the capacitor's nominal capacitance value, at least one fault type associated with the capacitor indicates capacitor leakage.

[0039] In addition, if the obtained capacitance value is equal to or lower than a predetermined threshold, the method may further include the step of: determining at least one fault type of the connection between at least one of the plurality of electrodes and the capacitor.

[0040] This allows for a more detailed evaluation of the circuitry that makes up the cochlear implant system.

[0041] Furthermore, the method may also include the step of: deriving a voltage relationship over time, including the relationship between the duration of an electrical pulse and a voltage measured based on the electrical pulse. Additionally, the method may further include the step of: deriving at least one voltage relationship fault type based on the derived voltage relationship for at least one of the plurality of electrodes, a capacitor, and the connection between at least one of the plurality of electrodes and the capacitor.

[0042] If the voltage relationship obtained over time is nonlinear, at least one voltage relationship fault type indicates at least one of the multiple electrodes, a capacitor, and at least one of the multiple electrodes connected to a capacitor.

[0043] This allows for a more detailed evaluation of the circuitry that makes up the cochlear implant system in alternative ways.

[0044] Additionally, the method may include the step of measuring the first and second voltages at the end of the corresponding pulse duration.

[0045] In addition, the method may also include the step of selecting the duration of the first and second pulses based on the nominal time constant corresponding to the connection with at least one of the plurality of electrodes and a capacitor.

[0046] This can improve the accuracy of the calculated / derived values.

[0047] Furthermore, the method may include the steps of: generating an electrical pulse based on at least one current intensity, and measuring for each corresponding current intensity. Additionally, the method may include: calculating the voltage difference for each corresponding current intensity, and / or deriving the capacitance value of the capacitor for each corresponding current intensity based on the calculated voltage difference. Furthermore, the method may include: evaluating at least one calculated voltage difference and / or at least one derived capacitance value based on an error minimization method.

[0048] This allows for further improvement in the accuracy of the calculated / derived values. Attached Figure Description

[0049] 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:

[0050] Figure 1 The left side shows the stimulation that can damage biological tissue due to an imbalance between the anode and cathode pulses, while the right side shows an electrical device that does not contain errors and thus provides a safe stimulation.

[0051] Figure 2 The left side shows a real-world stimulus where the cathode phase contains errors, resulting in charge imbalance, with a capacitor used to discharge excess positive or negative charge. The right side shows a pulse waveform that uses a DC blocking capacitor to ensure complete charge balance.

[0052] Figure 3A simplified diagram of the output channel of a cochlear implantation system according to an embodiment of the present invention is shown;

[0053] Figure 4 A simplified diagram of the output channel of a cochlear implantation system according to an embodiment of the present invention, including a leakage capacitor, is shown.

[0054] Figure 5 A graph is shown illustrating the relationship between the output voltage measured over time by the cochlear implant for different leakage current values ​​of the capacitor according to an embodiment of the present invention.

[0055] Figure 6 A cochlear implantation system according to an embodiment of the present invention is shown;

[0056] Figure 7 A method for a cochlear implant system according to an embodiment of the present invention is shown. Detailed Implementation

[0057] 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.

[0058] 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.

[0059] 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.

[0060] 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.

[0061] 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.

[0062] 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.

[0063] 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.

[0064] "Cochlear implant 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 encoded audio, while the implantable unit receives the encoded audio signals.

[0065] Now for reference Figure 3 It shows a simplified diagram of the output channel of an implantable unit of a cochlear implantation system according to an embodiment of the present invention.

[0066] according to Figure 3 The pulse generating unit (current source) 31 generates a current I, which flows through the output capacitor 32 into the electrode 33 of the electrode array (not shown). As long as the pulse generating unit 31 is within the voltage compliance range, the current I remains constant over time. Therefore, the voltage V measured by the measurement unit 34 of the cochlear implant system is:

[0067] V(t) = I·t / C + Z·I

[0068] Where t is time, I is the current generated by pulse generation unit 31, C is the capacitor value, and Z is the electrode impedance.

[0069] In cases where the cochlear implant system malfunctions due to a leakage capacitor, according to Figure 3 The image can be clicked Figure 4 The modifications shown are as follows, wherein the elements with reference numerals 41, 43, and 44 correspond to the elements according to the figures. Figure 3It has elements with numbers 31, 33, and 34. Therefore, further descriptions of these elements are omitted.

[0070] Figure 4 A simplified diagram of the output channel of an implantable unit of a cochlear implantation system according to an embodiment of the present invention, including leakage capacitors 42a and 42b, is shown.

[0071] In this situation, according to Figure 4 The voltage V measured by the measurement unit 44 of the cochlear implant system becomes:

[0072] V(t) = R·I·(1–e -t / R·C )+Z·I

[0073] Where t is time, I is the current generated by pulse generation unit 41, C is the capacitor value, Z is the electrode impedance, and R is the leakage resistance.

[0074] Therefore, the output voltage with leakage capacitors 42a and 42b is lower than that with non-leakage capacitor 32, and it is non-linear over time, such as... Figure 5 As shown in the image.

[0075] Figure 5 The diagram illustrates the relationship between the output voltage measured by the measurement units 34 and 44 of the cochlear implantation system over time for different leakage current values ​​of capacitors 32, 42a, and 42b, according to an embodiment of the present invention.

[0076] Specifically, for an infinite leakage resistance (R = ∞), identify the linear behavior of the voltage measured over time, where the greater the deviation of the nonlinear behavior from the linear behavior, the lower the leakage resistance R (see [reference]). Figure 5 (R = 100 and R = 1000 in the example). For a zero leakage resistance (R = 0), there is no voltage change over time.

[0077] Therefore, stimulating electrodes 33 and 43 with two different pulse lengths (T1, T2) will yield two voltage measurements (VT1, VT2):

[0078] VT1 = I·T1 / C + Z·I

[0079] VT2=I·T2 / C+Z·I

[0080] Furthermore, by calculating the difference between the two voltage measurements, the Z component is eliminated from the equation, and the estimate of the capacitor value can be calculated using the following formula:

[0081] C = I·(T1-T2) / (VT1-VT2)

[0082] Therefore, if the result is significantly higher than the nominal capacitor value, considering measurement error, it proves that the capacitor is leaking (leakage capacitors 42a and 42b). If VT1 and VT2 are equal, then the capacitor is short-circuited.

[0083] Now, in accordance with the above, refer to Figure 6 The illustration shows a cochlear implantation system 600 according to one aspect of the present invention.

[0084] according to Figure 6 An electrode array 633 is disposed within the implantable unit 620. Specifically, the electrode array 633 is located within the recipient's cochlea and provides stimulation to the auditory nerve in the recipient's cochlea. The hair cells within the cochlea begin to move, signals are generated, and transmitted to the recipient's brain via the auditory nerve. The brain translates these signals into acoustic sounds that can be perceived and understood by the recipient.

[0085] In addition, according to Figure 6 The schematic diagram shows a cochlear implant system 600 including an external unit 610 configured to receive acoustic sound and process the acoustic sound into an encoded audio signal, and an implantable unit 620 configured to receive the encoded audio signal. The system 600 also includes a pulse generation unit 631 configured to generate a first electrical pulse of a first pulse duration and a second electrical pulse of a second pulse duration different from the first pulse duration based on the encoded audio signal. The system 600 further includes an electrode array 633 comprising a plurality of electrodes 633a, 633b, and 633c, wherein at least one of the electrodes 633c is configured to receive at least the first and second electrical pulses, and a capacitor 632 including a capacitor connected to at least one of the electrodes 633c. The system 600 also includes a measurement unit 634 configured to measure a first voltage based on the first electrical pulse and a second voltage based on the second electrical pulse across the connection between at least one of the electrodes 633c and the capacitor 632. The system 600 further includes an evaluation unit 635 configured to calculate the voltage difference between the measured first and second voltages.

[0086] It should be noted that the elements marked with reference numerals 631, 632, 633 (633a, 633b, 633c) and 634 correspond to respectively Figure 3 The elements are labeled with reference numerals 31, 32, 33, and 34. It should also be noted that the evaluation unit 635 may be included within the implantable unit 620. Furthermore, the evaluation unit 635 may be incorporated as part of the measurement unit 634 and thus included within the implantable unit 620. Additionally, the evaluation results obtained through the evaluation unit 635 may be transmitted to other devices. Furthermore, the data output of the evaluation unit 635 may be further evaluated by other devices.

[0087] According to several different exemplary embodiments, the evaluation unit 635 of the cochlear implant system 600 may also be configured to determine at least one fault type of at least one of the plurality of electrodes 633c, capacitor 632, and the connection between at least one of the plurality of electrodes 633c and capacitor 632. The at least one fault type is determined based on a calculated voltage difference.

[0088] This allows for a more detailed evaluation of the circuitry that constitutes the cochlear implant system 600.

[0089] According to at least some exemplary embodiments, if the calculated voltage difference is zero, at least one fault type indicates that capacitor 632 is short-circuited.

[0090] This enables reliable identification of short circuits in capacitor 632 in the cochlear implant system 600.

[0091] According to several different exemplary embodiments, the evaluation unit 635 of the cochlear implantation system 600 may also be configured to derive the capacitance value of the capacitor 632 based on a calculated voltage difference, wherein the derived capacitance value indicates at least one fault type associated with the capacitor 632.

[0092] Additionally, according to at least a partial exemplary embodiment, if the obtained capacitance value exceeds a predetermined threshold of the nominal capacitance value of capacitor 632, at least one fault type associated with capacitor 632 indicates that capacitor 632 is leaking current.

[0093] This enables reliable identification of the leakage capacitor 632 in the cochlear implant system 600.

[0094] Furthermore, according to several different exemplary embodiments, if the obtained capacitance value is equal to or lower than a predetermined threshold, the evaluation unit 635 may also be configured to determine at least one fault type of the connection between at least one of the plurality of electrodes 633c and the capacitor 632.

[0095] This allows for a more detailed evaluation of the circuitry that constitutes the cochlear implant system 600.

[0096] Furthermore, according to several different exemplary embodiments, the evaluation unit 635 of the cochlear implant system 600 may also be configured to derive a voltage relationship over time, including the relationship between the duration of an electrical pulse and a voltage measured based on the electrical pulse. Further, the evaluation unit 635 is configured to derive at least one voltage relationship fault type based on the derived voltage relationship for at least one of the plurality of electrodes 633c, the capacitor 632, and the connection between the at least one of the plurality of electrodes 633c and the capacitor 632.

[0097] Furthermore, according to at least a partial exemplary embodiment, if the resulting voltage relationship over time is nonlinear, at least one voltage relationship fault type indicates at least one 633c of a plurality of electrodes, capacitor 632, and the connection between at least one 633c of a plurality of electrodes and capacitor 632.

[0098] This allows for a more detailed evaluation of the circuitry constituting the cochlear implant system 600 in alternative ways.

[0099] Furthermore, according to several different exemplary embodiments, the capacitor 632 of the cochlear implant system 600 may be a DC blocking capacitor.

[0100] In addition, according to several different exemplary embodiments, the measurement unit 634 of the cochlear implantation system 600 may also be configured to measure the first and second voltages at the end of the duration of the corresponding pulse.

[0101] Furthermore, according to at least some exemplary embodiments, the pulse generation unit 631 of the cochlear implantation system 600 may also be configured to select the first and second pulse durations based on a nominal time constant corresponding to the connection of at least one of the plurality of electrodes 633c and capacitor 632.

[0102] This can improve the accuracy of the calculated / derived values.

[0103] Furthermore, according to several different exemplary embodiments, the pulse generation unit 631 may also be configured to generate an electrical pulse based on at least one current intensity, wherein the measurement unit 634 is further configured to perform measurements for each corresponding current intensity. Additionally, the evaluation unit 635 is also configured to calculate the voltage difference for each corresponding current intensity, and / or derive the capacitance value of the capacitor 632 for each corresponding current intensity based on the calculated voltage difference. Furthermore, the evaluation unit 635 is also configured to evaluate at least one calculated voltage difference and / or at least one derived capacitance value based on an error minimization method.

[0104] The aforementioned error minimization method can be one of the following: a least squares-based method, a mean-based method, or a rule-based method.

[0105] This allows for further improvement in the accuracy of the calculated / derived values.

[0106] Furthermore, according to several different exemplary embodiments, at least one of the measurement unit 634 and the evaluation unit 635 of the cochlear implantation system 600 may also be configured to be disposed within one or more processors, and the one or more processors may be configured to be disposed within at least one of the external unit 610 and the implantable unit 620.

[0107] This allows for adjustments to the structure of the cochlear implant system 600.

[0108] Figure 7 A method for a cochlear implant system according to another aspect of the present invention is shown. Figure 7 The method can be based on Figure 6 The cochlear implant system 600 is implemented, but not limited to this. Furthermore, according to... Figure 6 The cochlear implant system 600 can perform according to Figure 7 The methods are, but not limited to, those described above.

[0109] Specifically, according to Figure 7 A method for a cochlear implant system 600, the cochlear implant system including an external unit 610 for receiving acoustic sound and processing the acoustic sound into an encoded audio signal, and an implantable unit 620 for receiving the encoded audio signal. The method includes step S710: generating a first electrical pulse of a first pulse duration and a second electrical pulse of a second pulse duration different from the first pulse duration based on the encoded audio signal. The method further includes step S720: receiving at least the first and second electrical pulses through at least one of a plurality of electrodes 633a, 633b, 633c included in an electrode array 633, wherein at least one of the electrodes 633c is connected to a capacitor 632. The method further includes step S730: measuring a first voltage based on the first electrical pulse and a second voltage based on the second electrical pulse across the connection of at least one of the electrodes 633c to the capacitor 632. The method further includes step S740: calculating the voltage difference between the measured first and second voltages.

[0110] This allows the method to reliably assess the state of the capacitor 632 in the cochlear implant system 600.

[0111] Furthermore, according to several different exemplary embodiments, the method may also include the step of: determining at least one fault type based on a calculated voltage difference, involving at least one electrode 633c, capacitor 632, and the connection between at least one electrode 633c and capacitor 632. If the calculated voltage difference is zero, the determined at least one fault type indicates that capacitor 632 is short-circuited.

[0112] This enables the method to reliably identify short-circuited capacitors 632 in the cochlear implant system 600.

[0113] Furthermore, according to at least a partial exemplary embodiment, the method may further include the step of: determining the capacitance value of capacitor 632 based on a calculated voltage difference, wherein the determined capacitance value may indicate at least one fault type associated with the capacitor. If the determined capacitance value exceeds a predetermined threshold of the nominal capacitance value of capacitor 632, at least one fault type associated with capacitor 632 indicates that capacitor 632 is leaking current.

[0114] Furthermore, according to several different exemplary embodiments, if the obtained capacitance value is equal to or lower than a predetermined threshold, the method may further include the step of: determining at least one fault type of the connection between at least one of the plurality of electrodes 633c and the capacitor 632.

[0115] This allows the method to further evaluate the circuitry constituting the cochlear implant system 600 in more detail.

[0116] Furthermore, according to at least a partial exemplary embodiment, the method may further include the step of: deriving a voltage relationship over time, including the relationship between the duration of an electrical pulse and a voltage measured based on the electrical pulse. Additionally, the method further includes the step of: determining at least one voltage relationship fault type based on the derived voltage relationship for at least one of the plurality of electrodes 633c, capacitor 632, and the connection between at least one of the plurality of electrodes 633c and capacitor 632. If the derived voltage relationship over time is non-linear, the at least one voltage relationship fault type indicates the connection between at least one of the plurality of electrodes 633c, capacitor 632, and the connection between at least one of the plurality of electrodes 633c and capacitor 632.

[0117] This allows the method to evaluate the circuitry constituting the cochlear implant system 600 in more detail in an alternative manner.

[0118] Additionally, according to several different exemplary embodiments, the method may also include the step of measuring first and second voltages at the end of the duration of the corresponding pulse.

[0119] Furthermore, according to at least a partial exemplary embodiment, the method may also include the step of selecting the duration of the first and second pulses based on the nominal time constant corresponding to the connection of at least one of the plurality of electrodes 633c and capacitor 632.

[0120] This allows the method to improve the accuracy of the calculated / derived values.

[0121] Furthermore, according to several different exemplary embodiments, the method may further include the steps of: generating an electrical pulse based on at least one current intensity, and measuring for each corresponding current intensity. Additionally, the method may further include: calculating the voltage difference at each corresponding current intensity, and / or deriving the capacitance value of the capacitor at each corresponding current intensity based on the calculated voltage difference. Furthermore, the method may further include: evaluating at least one calculated voltage difference and / or at least one derived capacitance value based on an error minimization method.

[0122] This allows the method to further improve the accuracy of the calculated / derived values.

[0123] 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.

[0124] 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.

[0125] In another aspect, functionality may 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 executed 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.

[0126] The methods for cochlear implantation systems described above, including all corresponding exemplary embodiments, can be implemented in software.

[0127] 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.

[0128] In another aspect, a data processing system is disclosed, which includes a processor adapted to run a computer program so that the processor performs at least some (such as most or all) of the steps of the methods described above and in the claims.

[0129] As outlined above, the methods for cochlear implant systems described above, including all corresponding exemplary embodiments, can be implemented in software.

[0130] 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.

[0131] 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.

[0132] 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.

[0133] 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.

[0134] Therefore, the scope of this invention should be determined based on the claims.

Claims

1. A cochlear implantation system, comprising: An external unit is configured to receive acoustic sounds and process them into encoded audio signals; An implantable unit configured to receive encoded audio signals; The pulse generation unit is configured to generate a first electrical pulse with a first pulse duration and a second electrical pulse with a second pulse duration different from the first pulse duration based on an encoded audio signal; An electrode array comprising multiple electrodes, wherein at least one of the multiple electrodes is configured to receive at least a first electrical pulse and a second electrical pulse; A capacitor connected to at least one of a plurality of electrodes; The measuring unit is configured to be connected to a capacitor across at least one of a plurality of electrodes to measure a first voltage based on a first electrical pulse and a second voltage based on a second electrical pulse; and The evaluation unit is configured to calculate the voltage difference between the measured first and second voltages.

2. The cochlear implant system of claim 1, wherein the evaluation unit is further configured to determine at least one fault type of at least one of the plurality of electrodes, a capacitor, and the connection between at least one of the plurality of electrodes and the capacitor. At least one of the fault types is derived based on the calculated voltage difference.

3. The cochlear implant system according to claim 2, wherein, If the calculated voltage difference is zero, at least one fault type is determined, indicating a capacitor short circuit.

4. The cochlear implant system according to claim 1 or 2, wherein the evaluation unit is further configured to derive the capacitance value of the capacitor based on the calculated voltage difference. The resulting capacitance value indicates at least one type of fault associated with the capacitor.

5. The cochlear implant system according to claim 4, wherein, If the obtained capacitance value exceeds a predetermined threshold of the capacitor's nominal capacitance value, at least one fault type associated with the capacitor indicates capacitor leakage.

6. The cochlear implant system according to claim 5, wherein, If the obtained capacitance value is equal to or lower than the predetermined threshold, The evaluation unit is also configured to determine at least one fault type of at least one of the plurality of electrodes and at least one of the plurality of electrodes connected to the capacitor.

7. The cochlear implantation system according to any one of claims 1, 2, 3, 5, and 6, wherein the evaluation unit is further configured to: The voltage relationship over time is derived, including the relationship between the duration of the electrical pulse and the voltage measured based on the electrical pulse; and Based on the derived voltage relationships, at least one voltage relationship fault type is determined for at least one of the multiple electrodes, the capacitor, and the connection between at least one of the multiple electrodes and the capacitor.

8. The cochlear implant system according to claim 7, wherein, If the voltage relationship obtained over time is nonlinear, at least one voltage relationship fault type indicates at least one of the multiple electrodes, a capacitor, and at least one of the multiple electrodes connected to a capacitor.

9. The cochlear implantation system according to any one of claims 1, 2, 3, 5, 6 and 8, wherein the capacitor is a DC blocking capacitor.

10. The cochlear implantation system according to any one of claims 1, 2, 3, 5, 6 and 8, wherein the measuring unit is further configured to measure the first and second voltages at the end of the duration of the corresponding pulse.

11. The cochlear implantation system according to any one of claims 1, 2, 3, 5, 6 and 8, wherein the pulse generation unit is further configured to select the first and second pulse durations based on a nominal time constant corresponding to the connection with at least one of the plurality of electrodes and a capacitor.

12. The cochlear implant system according to any one of claims 1, 2, 3, 5, 6 and 8, wherein... The pulse generation unit can also be configured to generate an electrical pulse based on at least one current intensity; The measuring unit is also configured to measure each corresponding current intensity; and The evaluation unit is also configured to Calculate the voltage difference for each corresponding current intensity, and / or The capacitance value of the capacitor at each corresponding current intensity is obtained based on the calculated voltage difference; where The evaluation unit is also configured to evaluate at least one calculated voltage difference and / or at least one derived capacitance value based on an error minimization method.

13. The cochlear implantation system according to any one of claims 1, 2, 3, 5, 6 and 8, wherein at least one of the measurement unit and the evaluation unit is further configured to be disposed within one or more processors, and the one or more processors are configured to be disposed within at least one of the external unit and the implantable unit.

14. A method for a cochlear implant system, the cochlear implant 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: Based on the encoded audio signal, a first electrical pulse with a first pulse duration and a second electrical pulse with a second pulse duration different from the first pulse duration are generated; At least a first electrical pulse and a second electrical pulse are received by at least one of a plurality of electrodes included in an electrode array, wherein at least one of the plurality of electrodes is connected to a capacitor; The connection across at least one of the multiple electrodes to the capacitor measures a first voltage based on a first electrical pulse and a second voltage based on a second electrical pulse; Calculate the voltage difference between the measured first and second voltages.

15. The method of claim 14, further comprising: Based on the calculated voltage difference, at least one fault type is determined, including at least one of the multiple electrodes, the capacitor, and the connection between at least one of the multiple electrodes and the capacitor. If the calculated voltage difference is zero, at least one fault type is determined, indicating a capacitor short circuit.

16. The method of claim 15, further comprising the step of: The capacitance value of the capacitor is derived from the calculated voltage difference, wherein the derived capacitance value indicates at least one fault type associated with the capacitor. in, If the obtained capacitance value exceeds a predetermined threshold of the capacitor's nominal capacitance value, at least one fault type associated with the capacitor indicates capacitor leakage.

17. The method according to claim 16, wherein, If the obtained capacitance value is equal to or lower than a predetermined threshold, the method further includes the step of: Determine at least one fault type of at least one of the multiple electrodes and at least one of the multiple electrodes connected to the capacitor.

18. The method according to any one of claims 14-17, further comprising the step of: The voltage relationship over time is derived, including the relationship between the duration of the electrical pulse and the voltage measured based on the electrical pulse; and Based on the derived voltage relationships, at least one voltage relationship fault type is derived for at least one of the multiple electrodes, the capacitor, and the connection between at least one of the multiple electrodes and the capacitor; in If the voltage relationship obtained over time is nonlinear, at least one voltage relationship fault type indicates at least one of the multiple electrodes, a capacitor, and at least one of the multiple electrodes connected to a capacitor.

19. The method according to any one of claims 14-17, further comprising the step of: Measure the first and second voltages at the end of the corresponding pulse duration.

20. The method according to any one of claims 14-17, further comprising the step of: The durations of the first and second pulses are selected based on the nominal time constant corresponding to the connection with at least one of the multiple electrodes and a capacitor.

21. The method according to any one of claims 14-17, further comprising the step of: An electrical pulse is generated based on at least one current intensity; Measure the current intensity for each corresponding current. Calculate the voltage difference for each corresponding current intensity, and / or The capacitance value of the capacitor at each corresponding current intensity is obtained based on the calculated voltage difference; and at least one calculated voltage difference and / or at least one obtained capacitance value is evaluated based on an error minimization method.

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