Adaptive closed-loop cochlear implant system based on brain-computer interface and in-vivo implant part

Abstract

The application provides a brain-computer interface-based adaptive closed-loop cochlear implant system and an in-vivo implanted part. The system comprises an in-vivo implanted part, and an extra-corporeal sound processor part connected with the in-vivo implanted part through a radio frequency transceiver coil, receiving the electroencephalogram signal output by the in-vivo implanted part, and sending the adjusted electrical signal to the in-vivo implanted part through the radio frequency transceiver coil. The application acquires the electroencephalogram signal of a user, and wirelessly transmits the electroencephalogram signal to the extra-corporeal sound processor part. Through the analysis of the electroencephalogram signal by the extra-corporeal sound processor part, the user's use experience is understood in time, and the T value and C value of the in-vivo implanted part are adjusted correspondingly, so that the real-time monitoring of the auditory cortex nerve signal is realized, the actual needs of the user are met, the subjective reaction of the user is not relied on, the T value and C value of the in-vivo implanted part are adaptively adjusted through a scientific and effective way, and the user experience is enhanced.

Description

Technical Field

[0001] This application belongs to the field of medical electronic device technology and relates to an adaptive closed-loop cochlear implant system based on brain-computer interface and its implanted part. Background Technology

[0002] In existing technologies, cochlear implants consist of an external sound processor and an internal implant. The sound processor includes a speech processing unit, a transmitting coil, a regulating magnet, and a behind-the-ear battery, while the internal implant includes a receiving coil, an implanted magnet, a decoding stimulator, and implanted electrodes. The sound processor converts ambient sound into electrical signals, which are then transmitted wirelessly to the implant. The internal decoding stimulator receives the signals, decodes them, and stimulates the corresponding frequency electrodes on the implant. This electrical stimulation of the spiral ganglion terminals (auditory nerve) on the cochlear basilar membrane generates action potentials, activating the auditory nerve pathway. The stimulation ultimately reaches the relevant area of ​​the auditory cortex in the brain, resulting in hearing. During cochlear implant tuning, it is necessary to set the minimum stimulation current intensity threshold (T-value) and the maximum current intensity comfort threshold (C-value) that the patient can perceive for each electrode channel. Therefore, improving the flexibility of cochlear implant parameter settings to adapt to user needs and environmental changes has become a pressing technical problem. Utility Model Content

[0003] This application provides an adaptive closed-loop cochlear implant system based on a brain-computer interface and its implanted portion, which solves the technical problem in the prior art that the parameters in the cochlear implant cannot be flexibly set.

[0004] In a first aspect, embodiments of this application provide an adaptive closed-loop cochlear implant system based on a brain-computer interface, comprising: an in vivo implanted part; and an external sound processor part, wherein the external sound processor part is connected to the in vivo implanted part via a radio frequency transceiver coil, receives the electroencephalogram (EEG) signals output by the in vivo implanted part, and transmits the adjusted electrical signals to the in vivo implanted part via the radio frequency transceiver coil.

[0005] In one implementation of the first aspect, the external sound processor portion includes a transmitting coil for wirelessly transmitting the electroencephalogram (EEG) signals and electrical signals.

[0006] In one implementation of the first aspect, the external sound processor further includes an EEG data analysis module, which receives the EEG signal transmitted by the transmitting coil and outputs the analysis result corresponding to the EEG signal.

[0007] In one implementation of the first aspect, the external sound processor further includes a potential analysis module, the input of which is connected to the output of the EEG data analysis module.

[0008] In one implementation of the first aspect, the external sound processor further includes a voice processing module, wherein a first input terminal of the voice processing module is connected to the output port of the potential analysis module.

[0009] In one implementation of the first aspect, the external sound processor portion further includes a power module connected to a second input terminal of the voice processing module.

[0010] In one implementation of the first aspect, the voice processing module further includes a third input terminal for inputting ambient sound.

[0011] In the adaptive closed-loop cochlear implant system based on a brain-computer interface provided in this application embodiment, an external sound processor is connected to the implanted part via a radio frequency transceiver coil. This external processor receives the electroencephalogram (EEG) signals output by the implanted part and transmits the adjusted electrical signals to the implanted part via the same coil. By acquiring the user's EEG signals and sending them to the external sound processor, the system analyzes these signals to understand the user's actual needs and adjusts the T and C values ​​of the implanted part accordingly. This enables real-time monitoring of auditory cortex EEG signals, greatly satisfying the user's actual needs. It does not rely on the user's subjective reactions and dynamically adjusts the T and C values ​​of the implanted part in a scientifically effective manner, achieving adaptive adjustment and improving the user experience.

[0012] Secondly, embodiments of this application provide an implantable part, the implantable part comprising: an auditory cortex epidural electroencephalogram (EEG) acquisition electrode for acquiring EEG signals; a decoding stimulator electrical signal decoding module for receiving an electrical signal after parameter adjustment and outputting an electrical stimulus corresponding to the adjusted electrical signal; and an implantable electrode connected to the output end of the decoding stimulator electrical signal decoding module for transmitting the electrical stimulus to the spiral ganglion terminal on the cochlear basilar membrane.

[0013] In one implementation of the second aspect, the implanted portion includes a connector for connecting the decoding stimulator EEG signal acquisition control module to the auditory cortex epidural EEG acquisition electrode.

[0014] In one implementation of the second aspect, the implanted portion further includes a receiving coil, the input end of which is connected to the output end of the decoding stimulator EEG signal acquisition control module, and the output end of which is connected to the input end of the decoding stimulator electrical signal decoding module. Attached Figure Description

[0015] Figure 1 The diagram shown is a structural diagram of an adaptive closed-loop cochlear implant system based on a brain-computer interface provided in an embodiment of this application.

[0016] Figure 2 The diagram shown is a structural diagram of an external sound processor portion provided in an embodiment of this application.

[0017] Figure 3 The diagram shown is a structural diagram of another external sound processor portion provided in an embodiment of this application.

[0018] Figure 4 The diagram shown is a structural schematic of an implanted portion provided in an embodiment of this application.

[0019] Figure 5 The diagram shown is a structural schematic of another implantable portion provided in an embodiment of this application.

[0020] Figure 6 The diagram shown is a structural schematic of another adaptive closed-loop cochlear implant system based on a brain-computer interface, provided in an embodiment of this application.

[0021] Figure 7 The diagram shown is a structural schematic of another adaptive closed-loop cochlear implant system based on a brain-computer interface, provided in an embodiment of this application.

[0022] Component designation explanation

[0023] 100 Brain-computer interface-based adaptive closed-loop cochlear implant system 110 Implanted part 111 Auditory cortical epidural electroencephalography (EEG) electrodes 112 Decoding stimulator electrical signal decoding module 113 Implantable electrode 114 connector 115 Decoding stimulator EEG signal acquisition and control module 116 Decoding stimulator integrated module for EEG signal acquisition, control and decoding 120 External sound processor section 121 EEG data analysis module 122 Potential Analysis Module 123 Voice processing module 124 Power module 130 RF transceiver coil 131 transmitting coil 132 receiving coil Detailed Implementation

[0024] The following specific examples illustrate the implementation of this application. Those skilled in the art can easily understand other advantages and effects of this application from the content disclosed in this specification. This application can also be implemented or applied through other different specific embodiments, and various details in this specification can also be modified or changed based on different viewpoints and applications without departing from the spirit of this application. It should be noted that, unless otherwise specified, the following embodiments and features in the embodiments can be combined with each other.

[0025] Furthermore, the terms "first" and "second" are used for descriptive purposes only and should not be construed as indicating or implying relative importance or implicitly specifying the number of technical features indicated. Thus, a feature defined as "first" or "second" may explicitly or implicitly include one or more of that feature. In the description of this application, "at least one" or "more than one" means two or more, unless otherwise explicitly specified.

[0026] In this application, unless otherwise expressly specified and limited, the terms "installation," "connection," "linking," and "fixing," etc., should be interpreted broadly. For example, they can refer to a fixed connection, a detachable connection, or an integral part; they can refer to a mechanical connection or an electrical connection; they can refer to a direct connection or an indirect connection through an intermediate medium; they can refer to the internal communication of two components or the interaction between two components. Those skilled in the art can understand the specific meaning of the above terms in this application according to the specific circumstances.

[0027] It should be noted that the illustrations provided in the following embodiments are only schematic representations of the basic concept of this application. Therefore, the drawings only show the components related to this application and are not drawn according to the actual number, shape and size of the components in the actual implementation. In the actual implementation, the shape, quantity and proportion of each component can be arbitrarily changed, and the layout of the components may also be more complex.

[0028] Current cochlear implants deliver electrical stimulation commands to the implant based on parameters (such as T-value and C-value) set during setup. However, setting these parameters relies on the user's subjective feedback and requires adjustment by a professional technician, which is time-consuming and challenging, especially for young prelingual deaf children who cannot provide feedback on sound perception, exhibiting low cooperation and difficulty in accurately answering questions in subjective assessments. Furthermore, for cochlear implant users of all ages, it is difficult for technicians to determine whether the current has been adjusted to the maximum current intensity (C-value) that the user can perceive at a particular frequency. Additionally, cochlear implant setup can only be performed in hospitals or specialized institutions (e.g., Neural response telemetry (NRT) or electrically evoked auditory brainstem response (EABR) testing), making real-time monitoring and adjustment impossible. Moreover, because patients' physiological conditions, structures, and subjective preferences change over time, parameters (T-value and C-value) may need frequent updates. However, for most cochlear implant users, after a year of use, the parameter settings are updated at most once a year, or even less frequently, which cannot adapt to changes in user needs and environment in a timely manner.

[0029] The primary method for objectively evaluating the effectiveness of cochlear implants and setting electrical stimulation parameters during initial setup involves using the implanted stimulation electrodes as recording electrodes to record the cochlear spiral ganglion response and the auditory brainstem response evoked by electrical stimulation. However, the auditory nerve from the cochlear spiral ganglion to the brainstem only represents the primary stage of the auditory pathway, and the above objective evaluation methods have not yet assessed the response of the auditory cortex—the higher auditory center. EEG caps placed on the scalp are also used to collect EEG data from the auditory cortex to objectively evaluate the auditory cortex's neural response to electrical stimulation in cochlear implant users. However, scalp EEG cap recording has three limitations: 1. The spatial resolution of the EEG cap is >1 cm; 2. The amplitude of the neural signals recorded by the EEG cap is weak due to the high impedance of the skull (approximately 17.7 kΩ); 3. The EEG signals recorded by the EEG cap have not yet been integrated with the cochlear implant system.

[0030] At least to address the aforementioned problems, this application provides an adaptive closed-loop cochlear implant system based on a brain-computer interface and its implanted portion. This adaptive closed-loop cochlear implant system includes: an implanted portion; and an external sound processor portion, which is connected to the implanted portion via a radio frequency transceiver coil. The external sound processor portion receives the electroencephalogram (EEG) signals output by the implanted portion and transmits the adjusted electrical signals to the implanted portion via the radio frequency transceiver coil. This solves the technical problem in existing technologies where there is a lack of flexibility in adjusting the T and C values ​​in the cochlear implant during the cochlear implant tuning process.

[0031] The technical solutions in the embodiments of this application will be described in detail below with reference to the accompanying drawings.

[0032] Figure 1 The diagram shown is a structural diagram of an adaptive closed-loop cochlear implant system based on a brain-computer interface, provided in an embodiment of this application. Figure 1 As shown, the adaptive closed-loop cochlear implant system 100 based on brain-computer interface provided in this application embodiment includes: an in vivo implanted part 110; and an external sound processor part 120. The external sound processor part 120 is connected to the in vivo implanted part 110 through a radio frequency transceiver coil 130, receives the electroencephalogram (EEG) signals output by the in vivo implanted part 110, and sends the electrical signals with adjusted parameters to the in vivo implanted part 110 through the radio frequency transceiver coil 130.

[0033] The radio frequency transceiver coil 130 includes a transmitting coil 131 and a receiving coil 132 to realize data transmission. The electroencephalogram (EEG) signals in the implanted part 110 are transmitted to the external sound processor part outside the body through the radio frequency transceiver coil 130, realizing the wireless transmission of EEG signals between the in-body and external devices, making it possible to monitor neural responses and further adjust parameters.

[0034] Figure 2 The diagram shown is a structural diagram of an external sound processor portion provided in an embodiment of this application. Figure 2 As shown, the external sound processor provided in this embodiment includes: an EEG data analysis module 121, a potential analysis module 122, a speech processing module 123, and a transmitting coil 131.

[0035] The transmitting coil 131 wirelessly transmits the received EEG signals to the EEG data analysis module 121. The EEG data analysis module 121 receives the EEG signals transmitted by the transmitting coil 131 and outputs the corresponding analysis results. The input terminal of the potential analysis module 122 is connected to the output terminal of the EEG data analysis module 121. The first input terminal of the speech processing module 123 is connected to the output port of the potential analysis module 122.

[0036] Specifically, the EEG data analysis module 121 can perform feature extraction, classification and other processing on the EEG signals, and transmit the frequency and amplitude information of the processed EEG signals to the potential analysis module 122.

[0037] In the potential analysis module 122, the amplitude of the event-related potentials (ERPs) in the auditory cortex of the EEG signal is used to determine whether the potential changes of the EEP signal are within the normal range of potential changes caused by perceptible sound. If the potential analysis module 122 detects that the potential change value of the EEG signal is lower or higher than the normal range of potential changes caused by perceptible sound based on the amplitude of the EEG signal, it sends an adjustment command to the speech processing module 123.

[0038] After receiving the adjustment command, the voice processing module 123 adjusts the electrical stimulation intensity (i.e., adjusts the T and C values) and transmits the adjusted electrical signal to the implanted part 110 via the radio frequency transceiver coil 130. This step achieves adaptive adjustment of the electrical stimulation intensity, improving the accuracy and efficiency of parameter setting. It solves problems in cochlear implant technology such as reliance on user subjective feedback for parameter setting, time-consuming and challenging adjustment processes, the limitation of adjustment to hospitals or specialized institutions, and the need for frequent parameter updates.

[0039] Adjusting the T and C values ​​includes increasing or decreasing them. Specifically, increasing or decreasing the T and C values ​​can be done by determining the corresponding mapping relationship according to the specific adjustment command, and this application does not impose any limitations on this.

[0040] Specifically, in the speech processing module 123, the intensity of electrical stimulation can be obtained through a specific mapping curve.

[0041] Figure 3This diagram shows a structural representation of another external sound processor component provided in one embodiment of this application. Figure 3 As shown, another external sound processor part also includes a power module 124, which is connected to the second input terminal of the voice processing module 123 and is used to provide power to the voice processing module 123.

[0042] Specifically, the voice processing module 123 also includes a third input terminal, which is used to input ambient sound.

[0043] Figure 4 The diagram shown is a structural schematic of an implanted portion provided in an embodiment of this application. Figure 4 As shown, the implanted portion 110 includes: an epidural EEG acquisition electrode 111 for acquiring EEG signals; a decoding stimulator electrical signal decoding module 112 for receiving the electrical signal after parameter adjustment and outputting the electrical stimulation corresponding to the adjusted electrical signal; and an implantable electrode 113 connected to the output of the decoding stimulator electrical signal decoding module 112 for transmitting the electrical stimulation to the spiral ganglion terminal (auditory nerve) on the cochlear basilar membrane, causing it to generate an action potential, activating the auditory neural pathway, and ultimately reaching the relevant area of ​​the auditory cortex of the brain, thereby generating hearing. The epidural electrode implanted in the relevant area of ​​the auditory cortex can acquire the response signals (auditory EEG signals) of the auditory cortex neuronal population to sound.

[0044] The implanted part 110 also includes a connector 114, which is used to connect the decoding stimulator EEG signal acquisition and control module 115 to the auditory cortex epidural EEG acquisition electrode 111, and to transmit the EEG signals acquired by the auditory cortex epidural EEG acquisition electrode 111 to the decoding stimulator EEG signal acquisition and control module 115.

[0045] Specifically, the decoding stimulator EEG signal acquisition control module 115 can perform signal preprocessing operations on the input EEG signal and transmit the preprocessed EEG signal to the receiving coil. For example, the signal preprocessing operations include removing noise from the EEG signal and removing other additional irrelevant signals.

[0046] The implanted part 110 also includes a receiving coil 132, the input end of which is connected to the output end of the decoding stimulator EEG signal acquisition and control module 115, and the output end of which is connected to the input end of the decoding stimulator electrical signal decoding module 112.

[0047] The decoding module 112 of the implanted part 110 receives the regulated electrical signal through the receiving coil 132, decodes the electrical signal to obtain electrical stimulation, and outputs the electrical stimulation to the implanted electrode 113. Thus, the electroencephalogram (EEG) signal in the implanted electrode 113 is regulated.

[0048] The implanted electrode 113 emits electrical stimulation, which is transmitted to the spiral ganglion terminals (auditory nerve) on the cochlear basilar membrane, generating action potentials, activating the auditory neural pathway, and ultimately reaching the relevant area of ​​the auditory cortex of the brain, thereby producing hearing. Simultaneously, the epidural EEG acquisition electrode 111 implanted in the relevant area of ​​the auditory cortex can acquire the response signals of the auditory cortex neuronal population to sound (auditory EEG signals).

[0049] Figure 5 The diagram shown is a structural schematic of another implantable portion provided in an embodiment of this application. Figure 5 As shown, another implanted part 110 also includes: a decoding stimulator EEG signal acquisition control and electrical signal decoding integrated module 116. The decoding stimulator EEG signal acquisition control and electrical signal decoding integrated module 116 is used to perform signal preprocessing operations on the EEG signals acquired by the auditory cortex epidural EEG acquisition electrodes 111 and to decode the electrical signals sent by the external sound processor to obtain electrical stimulation.

[0050] Among them, by Figure 5 It is known that the first input terminal of the integrated module 116 for EEG signal acquisition and control and electrical signal decoding of the decoder stimulator is connected to the connector 114, the second input terminal of the integrated module 116 for EEG signal acquisition and control and electrical signal decoding of the decoder stimulator is connected to the receiving coil 132, the first output terminal of the integrated module 116 for EEG signal acquisition and control and electrical signal decoding of the decoder stimulator is connected to the implanted electrode 113, and the second output terminal of the integrated module 116 for EEG signal acquisition and control and electrical signal decoding of the decoder stimulator is connected to the receiving coil 132.

[0051] In some implementations, the decoder stimulator EEG signal acquisition and control module 115 can be combined with the decoder stimulator electrical signal decoding module 112 to form an integrated module 116 for decoder stimulator EEG signal acquisition and control and electrical signal decoding. In other implementations, the decoder stimulator EEG signal acquisition and control module 115 may not be combined with the decoder stimulator electrical signal decoding module 112; in this case, the connector 114 transmits the EEG signal to the decoder stimulator EEG signal acquisition and control module 115. After preprocessing the EEG signal, the decoder stimulator EEG signal acquisition and control module 115 transmits the preprocessed EEG signal to the receiving coil 132.

[0052] Figure 5The functions and connections of the other structures in the other implanted portion 110 are the same as those described above. Figure 4 The structure and function of the implanted portion 110 are similar to those of the other structures, and will not be described in detail here.

[0053] Figure 6 The diagram shown is a structural schematic of another adaptive closed-loop cochlear implant system based on a brain-computer interface, provided in an embodiment of this application.

[0054] Depend on Figure 6 It is known that the EEG signal acquisition and control module 115 of the implanted part 110 acquires the neural response signal of the auditory cortex to electrical stimulation through the extradural electrode 111 of the auditory cortex; the neural response signal is wirelessly transmitted through the radio frequency transceiver coil 130 to the EEG data analysis module 121 and the potential analysis module 122 of the external sound processor part 120 for feature extraction and event-related potential assessment; the speech processing module 123 automatically adjusts the electrical stimulation intensity parameters according to the comparison results of the neural signal amplitude and the normal perception range; and the updated parameters are wirelessly transmitted through the radio frequency transceiver coil 130 to the electrical signal decoding module 112 of the decoder stimulator, and the spiral ganglion terminal on the cochlear basilar membrane is electrically stimulated through the implanted electrode 113 to complete the closed-loop control.

[0055] Figure 6 The functions and connections of the various structures in the cochlear implant system shown are similar to those of the various structures in the above embodiments, and have been described in detail in the above embodiments, so this application will not repeat them here.

[0056] Figure 7 The diagram shown is a structural schematic of another adaptive closed-loop cochlear implant system based on a brain-computer interface, provided in an embodiment of this application.

[0057] Figure 7 The functions and connections of the various structures in this application are similar to those of the various structures in the above embodiments, and have been described in detail in the above embodiments, so this application will not repeat them here.

[0058] For example, the external sound processor part 120 is located on the outer side of the scalp, the decoder stimulator electrical signal decoding module 112, the decoder stimulator EEG signal acquisition and control module 115, and the decoder stimulator EEG signal acquisition and control and electrical signal decoding integrated module 116 in the implanted part 110 are located in the cranial groove, the implant electrode 113 in the implanted part 110 is located in the cochlea, and the auditory cortex epidural EEG acquisition electrode 111 in the implanted part 110 is located on the epidural surface of the auditory cortex in the relevant area.

[0059] In the adaptive closed-loop cochlear implant system and its implanted portion based on a brain-computer interface provided in this application embodiment, objective neural signals replace subjective feedback, significantly improving the accuracy and efficiency of parameter settings; it supports real-time monitoring and dynamic adjustment, adapting to physiological changes and environmental needs; the epidural electrode design overcomes the shortcomings of traditional scalp EEG caps, such as low spatial resolution and large signal attenuation, improving signal acquisition accuracy; the closed-loop control mechanism optimizes the comfort and clarity of the user's auditory experience. This system is particularly suitable for young children and users who cannot communicate effectively, and has significant clinical application value. Furthermore, in this application, the integration of brain-computer interface and closed-loop control technology achieves adaptive optimization of cochlear implant parameters, solving the technical problems of traditional technologies such as reliance on manual adjustment and delayed updates, providing a more intelligent and personalized auditory rehabilitation solution for hearing-impaired patients.

[0060] The descriptions of the processes or structures corresponding to the above figures each have their own emphasis. For parts of a process or structure that are not described in detail, please refer to the relevant descriptions of other processes or structures.

[0061] The above embodiments are merely illustrative of the principles and effects of this application and are not intended to limit this application. Any person skilled in the art can modify or alter the above embodiments without departing from the spirit and scope of this application. Therefore, all equivalent modifications or alterations made by those skilled in the art without departing from the spirit and technical concept disclosed in this application should still be covered by the claims of this application.

Claims

1. An adaptive closed-loop cochlear implant system based on a brain-computer interface, characterized in that, The system includes: Implanted portion; The external sound processor is connected to the implanted part via a radio frequency transceiver coil, receives the electroencephalogram (EEG) signals output by the implanted part, and sends the adjusted electrical signals to the implanted part via the radio frequency transceiver coil.

2. The cochlear implant system according to claim 1, characterized in that, The external sound processor includes a transmitting coil for wirelessly transmitting the electroencephalogram (EEG) signals and electrical signals.

3. The cochlear implant system according to claim 1, characterized in that, The external sound processor also includes an EEG data analysis module, which receives the EEG signals transmitted by the transmitting coil and outputs the analysis results corresponding to the EEG signals.

4. The cochlear implant system according to claim 3, characterized in that, The external sound processor also includes a potential analysis module, the input of which is connected to the output of the EEG data analysis module.

5. The cochlear implant system according to claim 4, characterized in that, The external sound processor also includes a voice processing module, the first input of which is connected to the output port of the potential analysis module.

6. The cochlear implant system according to claim 5, characterized in that, The external sound processor also includes a power module, which is connected to the second input terminal of the voice processing module.

7. The cochlear implant system according to claim 5, characterized in that, The voice processing module also includes a third input terminal, which is used to input ambient sound.

8. An implantable component, used in the adaptive closed-loop cochlear implant system based on a brain-computer interface as described in any one of claims 1 to 7, characterized in that, include: Auditory cortex epidural EEG acquisition electrodes are used to acquire EEG signals; The decoding module for the stimulator's electrical signal receives the electrical signal after parameter adjustment and outputs the electrical stimulation corresponding to the adjusted electrical signal. An implantable electrode is connected to the output of the electrical signal decoding module of the decoder stimulator, and is used to transmit the electrical stimulation to the spiral ganglion terminal on the cochlear basilar membrane.

9. The implantable portion according to claim 8, characterized in that, The implanted portion includes a connector for connecting the decoding stimulator EEG signal acquisition control module to the auditory cortex epidural EEG acquisition electrode.

10. The implantable portion according to claim 8, characterized in that, The implanted part further includes a receiving coil, the input end of which is connected to the output end of the decoding stimulator EEG signal acquisition and control module, and the output end of which is connected to the input end of the decoding stimulator electrical signal decoding module.

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