Photoelectric artificial cochlea

Abstract

The invention discloses a photoelectric artificial cochlea, which comprises an extracorporeal machine and an implant, and is characterized in that the extracorporeal machine is configured to receive an original sound signal, process the original sound signal into a first analog signal or a conversion signal of the first analog signal, and transmit the first analog signal or the conversion signal to the implant; the implant comprises a stimulator, the stimulator comprises a photoelectric hybrid chip, the photoelectric hybrid chip is configured to receive an input signal and modulate a carrier optical signal by using the input signal to output a modulated carrier optical signal, the modulated carrier optical signal is an analog signal, and the input signal is a first analog signal or a conversion signal of the first analog signal; the implant comprises an optical fiber electrode, and the optical fiber electrode is implanted from the round window of the human ear, is arranged in the drum step, extends from the cochlea bottom to the cochlea top and directly acts on the auditory neuron, so that the high-frequency component of the modulated carrier optical signal is preferentially demodulated at the cochlea bottom, and the low-frequency component of the modulated carrier optical signal is preferentially demodulated at the cochlea top. Therefore, the photoelectric artificial cochlea system which is low in power consumption, high in fidelity and accurate in directional stimulation is realized.

Description

Technical Field

[0001] The present application relates to the technical field of cochlear implants, and in particular to a photoelectric cochlear implant. Background Art

[0002] A cochlear implant is an implantable medical device that replaces the function of a damaged cochlea and restores hearing to patients with severe sensorineural hearing loss. Traditional cochlear implants directly stimulate auditory neurons within the cochlea through an electrode array. However, these implants suffer from issues such as a limited number of channels, severe signal interference, rigid electrodes that can damage cochlear tissue, and poor metal material biocompatibility, limiting both the auditory restoration effect and the long-term stability of the implant.

[0003] In recent years, the application of optical technologies in the medical field has been increasing, such as fiber optic sensing and optogenetics. Optical cochlear implants, which utilize optical technologies in cochlear implants, can, to a certain extent, address the aforementioned issues. However, existing solutions combining optical technologies with cochlear implants are still immature and suffer from issues such as low integration, limited stimulation accuracy, and unstable performance of finished products, making it difficult to achieve ideal auditory reconstruction results.

[0004] Therefore, there is an urgent need for an efficient optoelectronic cochlear implant that can achieve requirements such as low power consumption, high fidelity, and precise directional stimulation. Summary of the Invention

[0005] In view of this, the present application discloses a photoelectric cochlear implant to solve the above technical problems. The photoelectric cochlear implant includes an external device and an implant, wherein the external device is configured to receive an original sound signal from the outside, process the original sound signal into a first analog signal or a conversion signal of the first analog signal, and transmit it to the implant; the implant includes a stimulator, which includes an optoelectronic hybrid chip, which is configured to receive an input signal, modulate a carrier optical signal using the input signal to output a modulated carrier optical signal, wherein the modulated carrier optical signal is an analog signal, and the input signal is the first analog signal or a conversion signal of the first analog signal; the implant also includes a fiber optic electrode, which is implanted from the round window of the human cochlea, arranged in the scala tympani, extending from the cochlear base to the cochlear apex, and directly acts on auditory neurons, so that the high-frequency component of the modulated carrier optical signal is preferentially demodulated at the cochlear base, and the low-frequency component of the modulated carrier optical signal is preferentially demodulated at the cochlear apex.

[0006] Optionally, the optical fiber electrodes are led out from the stimulator, and the number of the optical fiber electrodes is greater than or equal to one.

[0007] Optionally, the optical fiber electrode has a first region and a second region, the first region has no coating, and the second region has a coating, so as to achieve directional light emission; wherein the first region is the side of the outer surface of the optical fiber electrode facing the mordial axis, the second region is the side of the outer surface of the optical fiber electrode facing away from the mordial axis, and the area of ​​the first region is smaller than the area of ​​the second region.

[0008] Optionally, a silicone material is coated above the coating of the second region; in the second region, the thickness of the silicone near the first end of the optical fiber electrode is greater than the thickness of the silicone near the second end of the optical fiber electrode, so as to improve the rigid support capacity of the optical fiber electrode during the implantation process; wherein, when the optical fiber electrode is implanted in the scala tympani, the first end of the optical fiber electrode is close to the cochlear base, and the second end of the optical fiber electrode is close to the cochlear apex.

[0009] Optionally, the optical fiber electrode comprises a flexible packaging structure, and the flexible packaging structure is configured to cover the second end of the optical fiber electrode.

[0010] Optionally, the wavelength of the carrier optical signal is between 1550 nm and 1850 nm.

[0011] Optionally, the external machine includes a signal acquisition module, a signal processing module and a signal transmitting module connected in sequence, and the implant also includes a signal receiving module matching the signal transmitting module; wherein, the signal acquisition module is configured to receive the original sound signal and output the original sound signal to the signal processing module, the signal processing module is configured to process the original sound signal into a first analog signal or a converted signal of the first analog signal, the signal transmitting module is configured to transmit the first analog signal or the converted signal of the first analog signal to the signal receiving module, and the signal receiving module is configured to transmit the first analog signal or the converted signal of the first analog signal to the stimulator.

[0012] Optionally, the converted signal of the first analog signal is expressed as coded information; the optoelectronic hybrid chip includes a demodulation module, a photonic oscillator and a modulation module, the demodulation module is configured to demodulate the coded information into sound information and output the sound information to the modulation module, the photonic oscillator is configured to generate a carrier optical signal and transmit the carrier optical signal to the modulation module, and the modulation module is configured to modulate the carrier optical signal based on the sound information to output a modulated carrier optical signal.

[0013] Optionally, the modulation module is adapted to perform amplitude modulation, thereby loading the sound information into the carrier optical signal and making the modulated carrier optical signal an analog signal.

[0014] Optionally, the optical fiber electrode is a glass optical fiber, the diameter of the optical fiber electrode is between 125 μm and 300 μm, and the shape of the optical fiber electrode includes a straight line, an arc or a fully curved electrode.

[0015] In summary, the optoelectronic cochlear implant disclosed in this application has at least the following beneficial effects:

[0016] (1) This application utilizes an original fiber-optic electrode structure, combined with an optoelectronic hybrid chip to amplitude-modulate the carrier optical signal, and loads the analog sound signal into the optical signal for transmission and stimulation. Compared to traditional metal electrode arrays, which are limited to 12-24 channels, the number of fiber-optic electrode channels is theoretically unlimited, supporting continuous and precise analog signal transmission, thereby achieving higher frequency resolution and sound fidelity, significantly improving the quality of auditory restoration.

[0017] (2) A photonic oscillator generates a highly efficient carrier optical signal, which is modulated using analog amplitude modulation. This results in high optical signal transmission efficiency, eliminating the need for complex, high-power digital processing circuits within the implant, significantly reducing overall power consumption. The external device can be streamlined into a small transmitting unit, making it more portable and comfortable for the patient to wear.

[0018] (3) This application uses glass optical fiber as the optical fiber electrode material to replace traditional metal electrodes, which significantly reduces tissue irritation and immune response caused by metals, enhances the biocompatibility of the implant system, and is conducive to long-term stable use.

[0019] (4) This application uses a directional light-emitting structure design of the optical fiber electrode to retain only the light-transmitting area facing the modiolus, and sets a coating and silicone coating in the area facing away from the modiolus, thereby limiting the output of the light signal in a specified direction. Combined with the frequency mapping law of auditory neurons, it can achieve targeted and precise stimulation of specific neural segments, thereby improving signal transmission efficiency and stimulation selectivity.

[0020] (5) In this application, the fiber optic electrode is encapsulated with distal flexibility and designed so that the thickness of the silicone near the cochlear base is greater than that at the cochlear apex. This enhances the tail support performance, improves the control during the implantation process, and avoids folding or dislocation. At the same time, the fiber optic has a small diameter and good flexibility, which reduces pressure or damage to the physiological structure of the cochlea and improves implant safety.

[0021] (6) During the transmission of optical signals, there is no current crosstalk problem between traditional metal electrodes, and the channels do not interfere with each other, ensuring the independence and clarity of multi-channel stimulation signals, thereby improving the overall auditory signal processing capability and neural response accuracy. BRIEF DESCRIPTION OF THE DRAWINGS

[0022] The following is a brief introduction to the drawings used in describing the embodiments of this application.

[0023] Figure 1 A structural example diagram of an optoelectronic cochlear implant provided in an embodiment of the present application is shown.

[0024] Figure 2A schematic diagram showing the relationship between a fiber optic electrode and the cochlea provided in an embodiment of the present application is shown.

[0025] Figure 3 A structural example diagram of a fiber optic electrode provided in an embodiment of the present application is shown.

[0026] Figure 4 A structural example diagram of another optical fiber electrode provided in an embodiment of the present application is shown.

[0027] Figure 5 A structural example diagram of an optoelectronic hybrid chip provided in an embodiment of the present application is shown.

[0028] Figure 6 A waveform diagram of an original sound signal provided in an embodiment of the present application is shown.

[0029] Figure 7 A waveform diagram of an optical signal with a wavelength of 1550 nm provided in an embodiment of the present application is shown.

[0030] Figure 8 A waveform diagram of an AM modulated signal provided in an embodiment of the present application is shown.

[0031] Figure 9 A waveform diagram of a demodulated sound signal provided in an embodiment of the present application is shown. DETAILED DESCRIPTION

[0032] In order to more clearly illustrate the technical solutions of the embodiments of the present application, the specific implementation methods of the present application will be described below with reference to the accompanying drawings. The drawings described below are only some embodiments of the present application. For those skilled in the art, other drawings and other implementation methods can be obtained based on these drawings without any creative work. Adjustments and improvements made without departing from the concept of the present application are all within the scope of protection of the present application.

[0033] To simplify the drawings, only the parts related to the corresponding embodiments are schematically shown in each figure. They do not represent the actual structure of the product. In addition, to simplify the drawings and facilitate understanding, in some figures, only a portion of the components with the same structure or function are schematically depicted. In reality, more or fewer components with the same structure or function may exist.

[0034] In this application, unless otherwise expressly specified and limited, ordinal numbers such as "first", "second", etc. are only used to distinguish and describe associated objects, and cannot be understood as indicating or implying the relative importance or order between associated objects; in addition, they do not represent the number of associated objects. "Multiple" includes two or more, and other quantifiers are similar. " / " is used to describe the relationship between associated objects, which indicates the "or" relationship between associated objects. "And / or" is used to describe the relationship between associated objects, which includes any combination relationship between associated objects, for example, "a and / or b" includes: "alone a", "alone b", or "a and b". "One or more" or "at least one" in multiple objects refers to any object or any combination of multiple objects, for example, "one or more of a1, a2, a3" or "at least one of a1, a2, a3" includes: "alone a1", "alone a2", "alone a3", "a1 and a2", "a1 and a3", "a2 and a3", or "a1, a2 and a3".

[0035] A cochlear implant is an implantable electronic device used to replace the hearing function lost due to hair cell damage in patients with severe or profound sensorineural hearing loss. The basic principle is to collect and process sound signals in vitro, and then transmit electrical stimulation signals to the electrode array implanted inside the cochlea. The electric current directly stimulates the remaining auditory neurons, thereby forming auditory perception in the brain. Although cochlear implant technology has been widely used in clinical practice and has successfully helped a large number of hearing-impaired patients recover some of their hearing ability, traditional cochlear implant systems still have a series of difficult-to-overcome limitations, which seriously restrict their auditory restoration quality, long-term stability and patient comfort.

[0036] First, the limited number of channels is a fundamental problem facing traditional cochlear implant technology. Existing metal electrode arrays are mainly made through precision machining and micro-welding processes. They are composed of multiple metal electrode rings, sheets or wires, and are flexibly encapsulated by silicone or polymers and implanted along the scala tympani channel in the cochlea. However, due to physical structural factors such as micromachining capabilities, electrode size, electrode spacing, and overall electrode array length, current commercial products generally only support 12 to 24 independent electrode channels. This number is far lower than the frequency resolution capability corresponding to the approximately 3,000 inner hair cells of the human ear's natural auditory system. Since each channel corresponds to one or a group of frequency bandwidths, the limitation on the number of electrode channels directly leads to uneven frequency coverage and significant frequency band overlap, which ultimately manifests as insufficient auditory resolution, loss of sound details, and sound quality distortion. It cannot meet the demand for high-quality auditory restoration, especially in noisy environments.

[0037] Secondly, the problem of signal interference between electrodes becomes increasingly prominent in multi-channel stimulation scenarios. As attempts are made to increase the number of channels to improve auditory accuracy, the distance between electrodes is inevitably reduced, making it easy for current diffusion and crosstalk to occur between adjacent electrodes. Specifically, the diffusion range of the stimulation current in the tissue fluid is much larger than the size of the electrode itself. When the electrodes are too dense, the electrical signals released by different channels may interfere with each other in the cochlear fluid environment, resulting in inaccurate stimulation of target neurons and even unnecessary activation of non-target neural groups. This signal interference not only reduces the stimulation effect, but also increases the ambiguity or discomfort of the patient's perception of sound. In addition, since the length and curvature of the electrode array are subject to the physical limitations of the cochlear geometry, adding more electrode contacts within a fixed length range itself presents a technical bottleneck, further limiting the system's evolution towards high resolution.

[0038] Third, the risk of mechanical damage during implantation is also a problem that is difficult to avoid with traditional metal electrode arrays. In traditional electrode structures, a large number of metal components are densely arranged in a limited space, and the encapsulation layer generally uses silicone or flexible polymers to achieve a certain degree of flexibility. However, as the number of channels increases and the metal density increases, the rigidity and diameter of the overall electrode array also increase, resulting in a decrease in its flexibility and a more bulky structure. In the cochlea, a physiological cavity with a highly spiral structure and a narrow space, rigid electrode arrays can easily cause irreversible physical damage to key tissues such as the basilar membrane, spiral ganglion, and vascular network during implantation. Once damage occurs, it may not only affect the fit and electrical stimulation efficiency of the electrode array, but may also further damage the patient's residual hearing, resulting in unsatisfactory postoperative hearing recovery. In addition, under long-term implantation, the accumulation of structural stress between the electrode array and the cochlear wall may also lead to chronic damage or electrode displacement, affecting its long-term stability.

[0039] Fourth, the biocompatibility of materials is also a key factor affecting the performance and safety of cochlear implants. Currently, most cochlear implants still use precious metals (such as platinum and gold) as electrode materials. Although these metals have a certain degree of inertness in the medical field, they may still cause tissue reactions or chronic inflammation in some patients. In particular, when there are tiny leaks, electrochemical reactions or mechanical wear at the metal and packaging interface, local inflammatory reactions or even fiber wrapping are likely to form, which in turn leads to increased electrode impedance and decreased electrical stimulation efficiency, ultimately affecting the patient's experience and device life. In the long run, this biocompatibility issue may also affect the long-term stability of the implant and increase the risk of secondary surgery.

[0040] At the same time, optical technology has developed rapidly in the medical field in recent years, and has shown broad application potential in cutting-edge fields such as fiber optic sensing, biospectral imaging, and optogenetics. In the development of cochlear implant technology, some scholars have also tried to replace electrical signals with optical signals to stimulate auditory neurons in a more precise and non-contact manner. This type of optical cochlear implant envisions using optical fibers to guide light signals of controllable wavelength and intensity, encoding sound information into the light signal through modulation, and transmitting it to the target area inside the cochlea through optical fibers or micro-light-emitting devices for stimulation. Compared with traditional electrical stimulation methods, light stimulation has higher spatial resolution, less signal interference, and better tissue selectivity, and is expected to break through many limitations of traditional cochlear implants.

[0041] However, the current research on the practical application of optical technology in cochlear implants is still in its early stages. Although some animal experiments have shown that optical stimulation of auditory neurons is feasible, there are still many challenges in truly realizing an efficient, low-power, implantable, and controllable optoelectronic cochlear implant system. Current research generally has problems such as low system integration, large chip size, imperfect signal modulation mechanism, and unstable optical fiber output, making it difficult to achieve the reliability, repeatability, and high-performance output required for commercial products. In addition, the transmission, modulation, emission, and coupling mechanisms of optical signals must be completed under limited size and power consumption conditions, which places extremely high demands on system design. Therefore, there is an urgent need for a new optoelectronic cochlear implant solution with high integration, efficient modulation method, flexible structure, and good biocompatibility to give full play to the advantages of optical stimulation and promote the development of cochlear implant technology towards a new generation. In view of the various deficiencies in the above-mentioned existing technologies, the core concept of this application is to design corresponding optical fiber electrodes by utilizing the characteristics of the human cochlea itself (different areas have different degrees of acceptance of signal frequencies); and, by controlling the properties of the signal transmitted in the cochlear implant (that is, setting it to an analog signal), to achieve low power consumption, high fidelity and precise directional stimulation and other requirements.

[0042] The following description is given with reference to the accompanying drawings.

[0043] Please refer to Figure 1 , which shows an example diagram of the structure of an optoelectronic cochlear implant provided by an embodiment of the present application. Figure 1As shown, the optoelectronic cochlear implant 100 includes an external device 110 and an implant 120. The external device 110 is configured to receive an original sound signal from the outside, process the original sound signal into a first analog signal or a conversion signal of the first analog signal, and transmit it to the implant 120; the implant 120 includes a stimulator 124, the stimulator 124 includes an optoelectronic hybrid chip 1242, the optoelectronic hybrid chip 1242 is configured to receive an input signal, modulate a carrier optical signal using the input signal to output a modulated carrier optical signal, the modulated carrier optical signal is an analog signal, and the input signal is the first analog signal or a conversion signal of the first analog signal; the implant 120 also includes an optical fiber electrode 126, the optical fiber electrode 126 is implanted from the round window of the human cochlea, is arranged in the scala tympani, extends from the cochlear base to the cochlear apex, and directly acts on auditory neurons so that the high-frequency component of the modulated carrier optical signal is preferentially demodulated at the cochlear base, and the low-frequency component of the modulated carrier optical signal is preferentially demodulated at the cochlear apex.

[0044] Please refer to Figure 2 , which shows a schematic diagram of the relationship between a fiber optic electrode and the cochlea provided in an embodiment of the present application. Figure 2 As shown, the fiber optic electrode is implanted from the round window of the cochlea, located in the scala tympani, and can extend from the base of the cochlea to the top of the cochlea; the length can also be trimmed according to the actual situation of the patient's cochlea.

[0045] The optoelectronic hybrid cochlear implant system disclosed in this application mainly includes an external device, an optoelectronic hybrid chip and an optical fiber electrode. The external device is used to collect the original sound signal from the external environment, perform signal processing and encoding on it, and then transmit the processed continuous analog sound signal to the optoelectronic hybrid chip implanted in the body. The transmission method can be wireless transmission, for example. Figure 1 In the embodiment, the external device 110 further includes a signal transmitting module 116, and the implant 120 further includes a signal receiving module 122. Exemplarily, the signal transmitting module 116 is a transmitting coil, and the signal receiving module 122 is a receiving coil. In addition to electromagnetic induction coupling (i.e., coil wireless transmission), other transmission methods such as infrared or laser optical communication, ultrasonic wireless transmission, and magnetic resonance coupling can also be used. When coil wireless transmission is used, the signal acquisition module 112 is configured to receive the original sound signal and output the original sound signal to the signal processing module 114. The signal processing module 114 is configured to process the original sound signal into a first analog signal or a conversion signal of the first analog signal. The signal transmitting module 116 is configured to transmit the first analog signal or the conversion signal of the first analog signal to the signal receiving module 122. The signal receiving module 122 is configured to transmit the first analog signal or the conversion signal of the first analog signal to the stimulator 124. Wherein, as Figure 1As shown, the signal acquisition module 112, signal processing module 114, and signal transmission module 116 are connected in sequence; and the signal processing module 114 can perform encoding operations to convert the original sound signal into a converted signal of the first analog signal. That is, the converted signal of the first analog signal is expressed as encoded information. Unlike the digital signal commonly used in traditional systems, the analog signal transmission path used in this application helps to fully preserve the details and dynamic changes of the sound signal, thereby improving the quality of sound reproduction.

[0046] The optoelectronic hybrid chip within the implant receives and demodulates analog sound signals transmitted by an external device, generating a carrier optical signal. The chip modulates the carrier optical signal and embeds the demodulated sound information into the optical signal, creating a modulated carrier optical signal. This modulated optical signal is then output via optical fiber electrodes and directly acts on auditory neurons within the cochlea, achieving highly precise and targeted neural stimulation.

[0047] The fiber optic electrode is made of glass fiber material with excellent biocompatibility. It has the characteristics of small diameter and good flexibility, and can be successfully implanted inside the scala tympani of the cochlea. This application uses the natural selectivity of neurons in the cochlea to signals of different frequencies to achieve spatial separation stimulation of high-frequency and low-frequency sound signals. Because it adopts continuous analog signal modulation and is not limited by the number of traditional electrode channels, the system can theoretically achieve fine auditory stimulation of unlimited channels, avoid crosstalk between channels, and further improve the sound restoration and auditory experience. Among them, Figure 1 As shown, the signal receiving module 122, the stimulator 124 and the optical fiber electrode 126 are connected in sequence; and the external device 110 and the implant 120 are respectively arranged on both sides of the skin.

[0048] For the human cochlea, because the auditory neurons do not respond to high-frequency optical carrier signals, but respond to modulated original sound signals, and the auditory neurons at the top of the cochlea output larger bioelectric signals for lower-frequency modulated signals (i.e., the low-frequency part of the original sound signal), and the auditory neurons at the bottom of the cochlea output larger bioelectric signals for higher-frequency modulated signals (i.e., the high-frequency part of the original sound signal), thereby achieving demodulation of the original sound signal. Therefore, the optical fiber electrode in this application outputs a high-frequency modulated signal at the cochlear base and a low-frequency modulated signal at the cochlear top, thereby conforming to the natural frequency selectivity of the auditory neurons, achieving spatial demodulation of the original sound signal, and improving the restoration degree and stimulation accuracy of the auditory signal. In other words, the optical fiber electrode outputs a modulated carrier optical signal containing complete frequency components, and the optical signal is distributed along the cochlea. Through the frequency selectivity of the cochlear neurons, a high-frequency signal response is induced at the cochlear base and a low-frequency signal response is induced at the cochlear top, thereby achieving natural demodulation and spatial separation stimulation of the original analog sound signal. The "output of high-frequency modulated signals at the base of the cochlea and output of low-frequency modulated signals at the apex of the cochlea" in this application is not determined by the structure or material of the optical fiber electrode itself, nor is it achieved by artificially setting a certain section of optical fiber to only output specific frequency signals. On the contrary, after the optical fiber electrode is implanted along the scala tympani of the cochlea, it will output a continuous modulated carrier optical signal containing full-band information. What really enables the spatial separation of different frequency signals in the cochlea is the natural frequency selectivity of the auditory neurons of the cochlea itself: neurons at the base of the cochlea are more sensitive to high-frequency signals, and neurons at the apex of the cochlea are more sensitive to low-frequency signals. Therefore, even if the same optical signal is output along the entire optical fiber electrode, neurons at each position will only respond to their sensitive frequency bands, thereby achieving spatial demodulation and restoration of the original sound signal.

[0049] In some embodiments of the present application, the optical fiber electrodes are led out from the stimulator, and the number of the optical fiber electrodes is greater than or equal to one.

[0050] The number of optical fiber electrodes can be only one. This is because the present invention adopts a technical path that combines continuous analog sound signal modulation with light stimulation, so that only one optical fiber electrode can carry complete sound frequency information and act on the entire auditory neurons of the cochlea. It should be noted that the number of optical fiber electrodes is not limited to one in this application, and can also be set to multiple according to actual use requirements to meet the stimulation needs of higher precision or specific application scenarios. However, the technical focus of this embodiment is that by adopting a light stimulation scheme that uses analog sound signal modulation, even if only one optical fiber electrode is used, effective stimulation of the entire auditory neurons of the cochlea can be achieved, thereby simplifying the structural design, reducing the complexity of implantation, and taking into account both stimulation accuracy and system stability.

[0051] Compared with the multi-metal electrode array commonly used in the prior art (usually containing 12 to 24 independent electrodes, each electrode corresponding to a stimulation channel), the technical solution of the present application no longer relies on the physical distribution method of "one electrode stimulating one frequency band", but instead utilizes the frequency selective response mechanism of the cochlear auditory neurons themselves, and emits a modulated light signal containing full-frequency information through a single optical fiber, so that neurons in different parts can automatically demodulate according to their sensitive frequencies, thereby achieving the effect of multi-channel stimulation.

[0052] In summary, the number of fiber electrodes in this application can be one because it uses a continuous analog sound signal to amplitude-modulate the optical carrier. The output modulated optical signal contains complete frequency information. After being distributed along the cochlea, frequency-selective auditory neurons automatically identify and respond to different frequency bands, thereby achieving spatial frequency separation stimulation. This solution significantly reduces the number of required electrodes, reduces implant trauma while avoiding interference between electrical signal channels, and has the advantages of higher biocompatibility and system simplification, which overall improves the safety, implantability, and sound reproduction quality of the cochlear implant system.

[0053] Please refer to Figure 3 , which shows an example diagram of the structure of a fiber optic electrode provided in an embodiment of the present application. Figure 3 As shown, in some embodiments of the present application, the optical fiber electrode 126 has a first region and a second region, wherein the first region is uncoated and the second region is coated, to achieve directional light emission. The first region is the side of the outer surface of the optical fiber electrode 126 facing the modiolar axis, and the second region is the side of the outer surface of the optical fiber electrode 126 facing away from the modiolar axis. The area of ​​the first region is smaller than that of the second region. That is, the side of the optical fiber electrode 126 where the coating is removed faces the modiolar axis.

[0054] During the manufacturing process of the fiber optic electrode of this application, the outer surface of the optical fiber is coated. To achieve a directional light-emitting effect, laser etching, chemical etching, or plasma etching can be used to selectively remove the coating area on the side of the optical fiber's outer surface facing the worm shaft, forming a first region (i.e., an uncoated area) on this side; while the original coating is retained on the side facing away from the worm shaft, forming a second region (i.e., a coated area). Typically, the area of ​​the first region is smaller than that of the second region, and the removal range does not exceed half of the circumference of the optical fiber, thereby effectively controlling the direction of light emission.

[0055] This structural design allows for directional illumination of the light signal toward the modiolus (i.e., toward the auditory neurons), preventing light leakage. This directional illumination significantly improves light energy utilization, allowing the light signal to act more concentratedly on the target neural tissue, avoiding ineffective scattering of light energy or acting on non-target tissue, reducing energy loss and potential side effects, thereby enhancing stimulation accuracy and signal transmission efficiency. It also helps reduce the required laser power and improves the overall safety and biocompatibility of the system.

[0056] Please refer to Figure 4 , which shows an example diagram of the structure of another optical fiber electrode provided in an embodiment of the present application. Figure 4 As shown, in some embodiments of the present application, a silicone material (not shown) is coated above the coating of the second region; in the second region, the thickness of the silicone near the first end 126.1 of the optical fiber electrode 126 is greater than the thickness of the silicone near the second end 126.2 of the optical fiber electrode, so as to improve the rigid support capability of the optical fiber electrode 126 during implantation; wherein, when the optical fiber electrode 126 is implanted in the scala tympani, the first end 126.1 of the optical fiber electrode 126 is close to the cochlear fundus, and the second end 126.2 of the optical fiber electrode 126 is close to the cochlear apex. In some embodiments of the present application, the optical fiber electrode 126 includes a flexible packaging structure 1262, which is configured to cover the second end 126.2 of the optical fiber electrode.

[0057] For ease of description, the first end 126.1 of the optical fiber electrode 126 is referred to as the proximal end, that is, the end close to the cochlear base; the second end 126.2 of the optical fiber electrode 126 is referred to as the distal end, that is, the end close to the cochlear apex.

[0058] To improve the mechanical strength and long-term reliability of fiber optic electrodes in clinical applications, this application further proposes coating the outer surface of the optical fiber with a biocompatible silicone material to enhance the fiber's tensile strength and fatigue life. In this structure, the outer surface of the optical fiber is originally coated to control the direction of light emission. During the manufacturing process, the first area where the coating is removed (i.e., the side facing the modiolus) remains exposed and no longer coated with silicone to avoid affecting the effective emission and directional propagation of the optical signal.

[0059] Taking into account the internal spatial structure of the cochlear scala tympani and the mechanical strength of the optical fiber material, the preferred diameter of the optical fiber body ranges from 125μm to 300μm. If coated with silicone, the overall outer diameter is controlled between 300μm and 500μm to ensure good flexibility and implantability of the optical fiber electrode while not excessively compressing the internal tissues of the cochlea.

[0060] Furthermore, in order to adapt to the force characteristics of the electrode during the implantation process and provide good tail support, the present application adopts a silicone coating structure of unequal thickness. Specifically, the proximal area of ​​the optical fiber electrode close to the stimulator connection end is coated with thicker silicone, while the distal area away from the connection end is coated with thinner or not coated with silicone, so that the proximal size is slightly larger than the distal end. This design improves the rigidity of the proximal end of the electrode while ensuring that the distal end is soft and easy to penetrate into the cochlear apex, which helps to provide stable driving force and structural support during the implantation operation, reduce the risk of electrode bending, rebound or dislocation, and improve the smoothness and safety of the surgical operation.

[0061] Providing a flexible packaging structure (such as a silicone head) at the distal end of the fiber optic electrode can effectively buffer the mechanical contact of the fiber optic end during the implantation process, reducing the risk of damage to sensitive tissues inside the cochlea (such as the basilar membrane or perilymphatic space); and the flexible material has good compliance, which can improve the fit and stability of the electrode in the narrow area of ​​the cochlear apex and prevent postoperative displacement; in addition, the end packaging can also provide physical protection to prevent the fiber from breaking or collapsing, thereby improving the overall safety and durability of the implant system.

[0062] In some embodiments of the present application, the optical fiber electrode is a glass optical fiber, and the shape of the optical fiber electrode includes a straight line, an arc line, or a fully curved electrode.

[0063] By coating the outer surface of the optical fiber with bio-silicone, various implant electrode structures can be flexibly realized, such as linear, arc-shaped or fully curved electrodes, to meet the individual needs of different patients' cochlear anatomical structures and surgical pathways. Metal reinforcement materials can also be embedded in the silicone coating to enhance the overall mechanical strength and flexibility of the electrode. The metal material used has good biocompatibility, which improves the safety of long-term implantation. For example, the metal reinforcement part can be made of memory alloy material to give the electrode a shape memory function, which is convenient for making pre-formed fully curved electrodes of different sizes and curvatures, thereby improving the fit and ease of operation during implantation.

[0064] In terms of electrode size, the implantable length of the fiber optic electrode can be adjusted from 15mm to 31mm to accommodate varying cochlear lengths and implant depths. This length can be set to a number of fixed specifications based on pre-operative assessments, or a standard maximum length of 31mm can be manufactured. The doctor can then trim the electrode length as needed based on intraoperative examinations, enhancing surgical flexibility and personalized fit, thereby optimizing implant outcomes and the patient's post-operative hearing recovery experience.

[0065] Fiber optic electrodes are made of glass fiber, a material with excellent biocompatibility, making them more suitable for long-term implantation. Furthermore, the small diameter and flexibility of glass fiber facilitate penetration deep into the cochlea, minimizing mechanical damage to the tissue. Furthermore, glass fiber offers excellent optical transmission properties, enabling efficient transmission of modulated light signals, improving signal quality and stimulation accuracy.

[0066] Please refer to Figure 5 , which shows an example diagram of the structure of an optoelectronic hybrid chip provided by an embodiment of the present application. Figure 5 As shown, in some embodiments of the present application, the optoelectronic hybrid chip 500 includes a demodulation module 510, a photonic oscillator 520, and a modulation module 530. The demodulation module 510 is configured to demodulate the encoded information into sound information and output the sound information to the modulation module 530. The photonic oscillator 520 is configured to generate a carrier optical signal and transmit the carrier optical signal to the modulation module 530. The modulation module 530 is configured to modulate the carrier optical signal based on the sound information to output a modulated carrier optical signal. In some embodiments of the present application, the modulation module 530 is adapted to perform amplitude modulation to load the sound information into the carrier optical signal and make the modulated carrier optical signal an analog signal. Exemplarily, the wavelength of the carrier optical signal is between 1550nm and 1850nm.

[0067] In this embodiment, the specific structure of an optoelectronic hybrid chip is shown. The optoelectronic hybrid chip 500 includes a demodulation module 510, a photonic oscillator 520, and a modulation module 530. Both the demodulation module 510 and the photonic oscillator 520 are connected to the modulation module 530. In terms of modulation method, AM (amplitude modulation), FM (frequency modulation), and PM (phase modulation) can theoretically be used to modulate sound information. However, considering the structural characteristics of the optoelectronic cochlear implant and the biostimulation requirements of this application, AM modulation offers advantages. First, AM modulation's implementation mechanism is relatively simple, facilitating integration of the modulation module within the implant chip, reducing power consumption and volume, and improving system stability. Second, physiological studies have shown that, under constant pulse energy conditions, near-infrared light in the wavelength range of 1550nm to 1850nm can induce large-amplitude compound action potentials in the cochlear auditory nerve when modulated using AM, demonstrating that its stimulation efficiency within this wavelength range is superior to other modulation methods. Furthermore, AM modulation directly incorporates the sound signal into the light intensity, preserving the amplitude and waveform details of the original analog sound, contributing to a more natural auditory experience. In comparison, FM and PM are more suitable for high-speed, interference-resistant digital communications. In cochlear implant scenarios that require high-precision analog signal recovery, their demodulation complexity is relatively high, making it difficult to balance power consumption and signal fidelity.

[0068] After receiving the sound signal output by the demodulation module, the modulation module controls the intensity of the carrier optical signal so that its amplitude changes synchronously with the amplitude of the sound signal, thereby generating a modulated carrier optical signal. This modulation method can transmit the energy information of the sound signal to the cochlea in the form of light intensity with high fidelity, helping to effectively stimulate auditory neurons.

[0069] Please refer to Figures 6 to 9 ,in, Figure 6 shows a waveform diagram of an original sound signal provided by an embodiment of the present application; Figure 7 shows a waveform diagram of an optical signal with a wavelength of 1550 nm provided in an embodiment of the present application; Figure 8 shows a waveform diagram of an AM modulated signal provided by an embodiment of the present application; Figure 9 A waveform diagram of a demodulated sound signal provided in an embodiment of the present application is shown. Figure 8 The signal represented by the waveform diagram is the modulated carrier optical signal mentioned above. This signal is transmitted to the cochlear neurons through the optical fiber electrode implanted in the cochlea. It is an analog signal, not a digital signal. Figure 9 The signal represented by the waveform is the signal that the neuron finally receives.

[0070] From these waveforms, we can see that after the original sound signal is AM modulated with the carrier light signal, the modulated carrier light signal generated can be accurately demodulated by auditory neurons in different areas of the cochlea. Combined with the inherent frequency selectivity of the human cochlea in its anatomical structure, this demodulation process can restore sound information that is highly consistent with the original sound signal waveform, that is, Figure 9 The waveform and Figure 6 This result fully verifies that the optoelectronic cochlear implant system disclosed in this application has good signal fidelity performance, can accurately and efficiently transmit sound information to the user, and significantly improve the auditory restoration effect.

[0071] In summary, the analog signal is used for transmission and modulation processing in this application. Compared with the digital signal method commonly used in the prior art, it has higher fidelity and richer sound detail expression ability, and can more effectively restore the original sound characteristics. On this basis, by amplitude modulating the analog signal and combining it with a single optical fiber electrode to transmit the modulated carrier light signal, not only the system structure is simplified, but also the stability of the system and the safety of implantation are significantly improved. At the same time, utilizing the frequency selectivity of the cochlear auditory neurons in the anatomical structure, the present application scheme further proposes a method of outputting a high-frequency modulation signal at the base of the optical fiber electrode cochlea and a low-frequency modulation signal at the top of the cochlea to achieve spatial selective stimulation of high-frequency and low-frequency sound signals, thereby achieving a more natural auditory perception. The above-mentioned key technical features are closely related and cooperate with each other in this application to form a complete and efficient optoelectronic cochlear implant working mechanism, and none of them can be missing. For those skilled in the art, without the clear technical inspiration of this application, it is difficult to deduce the systematic technical solution proposed in this application based solely on the information such as analog signal processing, optical fiber transmission or cochlear frequency distribution that exists scattered in the prior art.

[0072] In the above embodiments, the description of each embodiment has its own emphasis. For parts that are not described or recorded in detail in a certain embodiment, reference can be made to the relevant description of other embodiments. In addition, the above embodiments can be freely combined as needed.

Claims

1. A photoelectric cochlear implant, characterized in that: The device comprises an external device and an implant, wherein the external device is configured to receive an original sound signal from the outside, process the original sound signal into a first analog signal or a conversion signal of the first analog signal, and transmit the first analog signal to the implant; The implant includes a stimulator, the stimulator includes an optoelectronic hybrid chip, the optoelectronic hybrid chip is configured to receive an input signal, modulate a carrier optical signal using the input signal to output a modulated carrier optical signal, the modulated carrier optical signal is an analog signal, and the input signal is the first analog signal or a converted signal of the first analog signal; The implant also includes a fiber optic electrode, which is implanted from the round window of the human cochlea, arranged in the scala tympani, extending from the base of the cochlea to the apex of the cochlea, and directly acts on auditory neurons so that the high-frequency component of the modulated carrier optical signal is preferentially demodulated at the base of the cochlea, and the low-frequency component of the modulated carrier optical signal is preferentially demodulated at the apex of the cochlea.

2. The optoelectronic cochlear implant according to claim 1, wherein: The optical fiber electrodes are led out from the stimulator, and the number of the optical fiber electrodes is greater than or equal to one.

3. The optoelectronic cochlear implant according to claim 1, wherein: The optical fiber electrode has a first region and a second region, the first region has no coating, and the second region has a coating to achieve directional light emission; The first region is the side of the outer surface of the fiber electrode facing the modiolus, and the second region is the side of the outer surface of the fiber electrode facing away from the modiolus, and the area of ​​the first region is smaller than that of the second region.

4. The optoelectronic cochlear implant according to claim 3, wherein: The coating of the second region is coated with a silicone material; In the second region, the thickness of the silicone near the first end of the optical fiber electrode is greater than the thickness of the silicone near the second end of the optical fiber electrode, so as to improve the rigid support capability of the optical fiber electrode during implantation; Wherein, when the optical fiber electrode is implanted in the scala tympani, the first end of the optical fiber electrode is close to the cochlear base, and the second end of the optical fiber electrode is close to the cochlear apex.

5. The optoelectronic cochlear implant according to claim 4, wherein: The optical fiber electrode includes a flexible packaging structure configured to cover the second end of the optical fiber electrode.

6. The optoelectronic cochlear implant according to claim 1, wherein: The wavelength of the carrier optical signal is between 1550nm and 1850nm.

7. The optoelectronic cochlear implant according to claim 1, wherein: The external device includes a signal acquisition module, a signal processing module and a signal transmission module connected in sequence, and the implant also includes a signal receiving module matched with the signal transmission module; Among them, the signal acquisition module is configured to receive the original sound signal and output the original sound signal to the signal processing module, the signal processing module is configured to process the original sound signal into the first analog signal or the converted signal of the first analog signal, the signal transmitting module is configured to transmit the first analog signal or the converted signal of the first analog signal to the signal receiving module, and the signal receiving module is configured to transmit the first analog signal or the converted signal of the first analog signal to the stimulator.

8. The optoelectronic cochlear implant according to claim 7, characterized in that: The converted signal of the first analog signal is expressed in the form of coded information; The optoelectronic hybrid chip includes a demodulation module, a photonic oscillator, and a modulation module. The demodulation module is configured to demodulate the encoded information into sound information and output the sound information to the modulation module. The photonic oscillator is configured to generate the carrier optical signal and transmit the carrier optical signal to the modulation module. The modulation module is configured to modulate the carrier optical signal based on the sound information to output the modulated carrier optical signal.

9. The optoelectronic cochlear implant according to claim 8, characterized in that: The modulation module is adapted to perform amplitude modulation, thereby loading the sound information into the carrier optical signal and making the modulated carrier optical signal an analog signal.

10. The optoelectronic cochlear implant according to claim 1, wherein: The optical fiber electrode is a glass optical fiber, the diameter of the optical fiber electrode is between 125 μm and 300 μm, and the shape of the optical fiber electrode includes a straight line, an arc or a fully curved electrode.

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