WO2022228366A1

WO2022228366A1 - Cochlear implantation device and cochlea implant

Info

Publication number: WO2022228366A1
Application number: PCT/CN2022/088924
Authority: WO
Inventors: 郑浩; 王丞阳; 王�华
Original assignee: 微创投资控股有限公司
Priority date: 2021-04-30
Filing date: 2022-04-25
Publication date: 2022-11-03
Also published as: CN115253071A

Abstract

Provided in the present invention are a cochlear implantation device and a cochlea implant. The cochlear implantation device comprises a tubular structure formed by coiling a support monofilament, and a signal portion, wherein the tubular structure has an implantation state and a release state; in the implantation state, the tubular structure is configured to be disposed on an implantation guide device and is used to implant a cochlea along with the implantation guide device; during transition of the tubular structure from the implantation state to the release state, the tubular structure radially expands in a reducing manner; and the signal portion is disposed on the support monofilament and is used for sending or receiving signals. In this way, the cochlear implantation device can adapt to the individual difference of different cochleae, and ensure that the implanted signal portion can be closely attached to the cochlea, so as to ensure a good signal stimulation effect, improve the signal position accuracy, and improve the effect of use by a patient.

Description

Cochlear Implants and Cochlear Implants

technical field

The invention relates to the field of medical technology, in particular to a cochlear implant device and a cochlear implant.

Background technique

A cochlear implant is an implantable hearing aid device that includes an extracorporeal device part and an implantable device part. The extracorporeal device part consists of a microphone, a voice processor, and a signal transmitter for sending instructions to the implanted device part. The implantation device is composed of a signal receiving and decoding module and an array of signal parts. The doctor implants the signal part into the cochlea. The signal part array is, for example, an electrode array. Stimulation, so that patients with severe deafness have a certain sound perception. The auditory neurons are distributed on one side of the cochlear cavity. The closer the signal part is to the cochlear neurons and the more stable the relative position, the better the stimulation effect. Therefore, it is particularly important to ensure the adhesion and relative position stability between the signal part and the neurons in the cochlea.

However, in practical applications, due to individual differences in patients, the cross-sectional shape of the cochlea along the axial direction of different patients is different. As a result, the signal part is not in the predetermined position, thereby affecting the effect of signal stimulation; and because the signal part array does not fit closely with the cochlea, the signal part array cannot directly contact the inner wall of the cochlea, which will affect the stimulation effect. In the current technology, although the linearly arranged signal parts, such as electrodes, are bent and fitted to the inner wall of the cochlea after implantation in various ways, the unevenness of the inner wall of the cochlea in a local range will make part of the signal parts suspended and away from the inner wall of the cochlea , resulting in weakened signal stimulation effect, reduced accuracy, and affected the final use effect.

Therefore, we developed a new type of signal that can adapt to the individual differences of different cochleas. The implanted signal part is closely attached to the cochlea, so that the signal part can be in direct contact with the inside of the cochlea, which ensures excellent signal stimulation effect and improves the accuracy of the signal position. Improving the use effect has become an urgent problem to be solved by cochlear implant devices and cochlear implant manufacturers.

SUMMARY OF THE INVENTION

The purpose of the present invention is to provide a cochlear implant device and a cochlear implant, so as to solve the problem that the current cochlear implant device cannot adapt to different cochleas, and the signal part after implantation does not fit closely with the cochlea, causing the signal part to be in contact with the cochlea. The inside of the cochlea cannot be directly contacted, the signal stimulation effect is poor, the signal position accuracy is poor, and the use effect is not good.

In order to solve the above technical problems, the present invention provides a cochlear implant device, comprising: a tubular structure formed by coiling a stent monofilament, and a signal portion; the tubular structure has an implanted state and a released state, and in the implanted state In the inserted state, the tubular structure is used to be disposed on an implantation guide device, and used to implant a cochlea with the implantation guide device; when the tubular structure changes from the implanted state to the released state During the conversion process, the tubular structure is radially reduced and expanded; the signal portion is arranged on the stent monofilament and is used for sending or receiving signals.

Optionally, the tubular structure is formed by at least two stent monofilaments spiraling along different trajectories.

Optionally, at least one of the signal parts is provided on at least one of the stent monofilaments.

Optionally, each of the stent monofilaments is provided with one signal portion, the lengths of each of the stent monofilaments are equal, and each of the signal portions is arranged equidistantly along the axial direction of the stent monofilament.

Optionally, the signal portion is disposed at the intersection of the two stent monofilaments, and the signal portion is located closer to the outer side of the tubular structure.

Optionally, the tubular structure is formed by braiding at least two stent monofilaments, and each stent monofilament has a different number of signal parts.

Optionally, each of the stent monofilaments is provided with at least one of the signal parts.

Optionally, the cochlear implant device further includes a wire, the wire is connected to the signal part; the stent monofilament includes a stent monofilament body and a wire groove, and the wire groove is along the stent monofilament body. The axial extension is arranged, and the wire is arranged in the wire groove.

Optionally, the signal part is disposed on the monofilament body of the stent and is located outside the wire groove.

Optionally, the signal part includes an electrical signal component and/or an optical signal component; the electrical signal component includes an electrode, and the optical signal component includes an LED and/or a light intensity sensor.

Optionally, the stent monofilament further includes a medicine groove, and the medicine groove is used for accommodating medicine.

Optionally, the support monofilament includes an optical fiber, and the signal portion includes an optical fiber light transmission port, and the optical fiber light transmission port is used for light transmission.

Optionally, the stent monofilament further includes a stent monofilament body and an optical fiber groove, the optical fiber groove is extended along the axial direction of the stent monofilament body, and the optical fiber is disposed in the optical fiber groove.

In order to solve the above technical problem, the present invention also provides a cochlear implant, comprising: the above-mentioned cochlear implant device and an extra-cochlear implant device, wherein the extra-cochlear implant device is signally connected to the cochlear implant device.

In a cochlear implant device and a cochlear implant provided by the present invention, the cochlear implant device includes a tubular structure formed by coiling a stent monofilament, and a signal portion; the tubular structure has an implanted state and a released state state in which the tubular structure is used to be disposed on an implantation guide device and used to implant a cochlea with the implantation guide device; in the implanted state, the tubular structure is formed by the implantation state During the transition to the release state, the tubular structure expands in a radially variable diameter; the signal portion is arranged on the stent monofilament and is used for sending or receiving signals. This arrangement enables the cochlear implant device to adapt to the individual differences of different cochleas, to ensure that the implanted signal part fits closely with the cochlea, to ensure excellent signal stimulation effect, to improve the accuracy of the signal position, and to improve the patient's use effect.

Description of drawings

Those of ordinary skill in the art will appreciate that the accompanying drawings are provided for a better understanding of the present invention and do not constitute any limitation on the scope of the present invention. in:

FIG. 1 is a schematic diagram of the cochlear implant device provided in the first embodiment and the second embodiment.

FIG. 2 is a schematic diagram of the cochlear implant device provided in the first embodiment after being implanted into the cochlea.

FIG. 3 is an expanded schematic diagram of the cochlear implant device provided in the first embodiment of the present invention being implanted into the cochlea.

FIG. 4 is a schematic diagram of a plurality of stent monofilaments provided in the first embodiment.

FIG. 5 is a schematic diagram of a cross-section of a stent monofilament provided in the first embodiment.

In the attached picture:

A-tubular structure;

10 - cochlea;

100- stent monofilament, 110- stent monofilament body, 120- wire guide;

200 - Signal Department;

300-wire.

Detailed ways

In order to make the objects, advantages and features of the present invention clearer, the present invention will be further described in detail below with reference to the accompanying drawings and specific embodiments. It should be noted that the accompanying drawings are all in a very simplified form and are not drawn to scale, and are only used to facilitate and clearly assist the purpose of explaining the embodiments of the present invention. Furthermore, the structures shown in the drawings are often part of the actual structure. In particular, each drawing needs to show different emphases, and sometimes different scales are used.

As used in this specification, the singular forms "a," "an," and "the" include plural referents unless the content clearly dictates otherwise. As used in this specification, the term "or" is generally employed in its sense including "and/or" unless the content clearly dictates otherwise. Furthermore, in the following description, numerous specific details are set forth in order to provide a more thorough understanding of the present invention. It will be apparent, however, to one skilled in the art that the present invention may be practiced without one or more of these details. In other instances, some technical features known in the art have not been described in order to avoid obscuring the present invention.

The following description is made with reference to the accompanying drawings.

[Example 1]

Please refer to FIGS. 1 to 5 , FIG. 1 is a schematic diagram of the cochlear implant device provided in the first embodiment and the second embodiment; FIG. 2 is a schematic diagram of the cochlear implant device provided in the first embodiment after the cochlear implantation 3 is a schematic diagram of the development of the cochlear implant device provided by the first embodiment of the cochlear implantation; Schematic diagram of the cross section.

Referring to FIG. 1 , the cochlear implant device includes a stent monofilament 100 and a signal portion 200 .

As shown in FIG. 1 , the stent monofilament 100 is coiled to form a tubular structure A. The stent monofilament 100 is preferably a sheet metal wire, for example. Of course, the stent monofilament 100 is not limited to a sheet shape, nor is it limited to a metal material. For example, the cross section of the stent monofilament 100 is a circular or oval structure, and the stent monofilament 100 can be made of a polymer material, such as It is fiber or fiber material, etc. When the stent monofilament 100 is coiled and arranged to form the tubular structure A, the stent monofilament 100 can be coiled or braided along a mandrel (not shown). The monofilament 100 is wound and braided on the mandrel, and finally a stent of a tubular structure A with a diameter of 8 mm is formed. The mandrel can be a metal mandrel. Of course, in practice, the staff can select a mandrel with an appropriate diameter and shape according to the actual size requirements of the patient's cochlea 10, and control the radial mechanical extrusion characteristics of the stent monofilament 100 at different positions by controlling the size of the mandrel at different positions. and so on, so as to satisfy the real situation in the cochlea 10 of the patient.

It should be understood that the tubular structure A formed by the stent monofilament 100 can be radially compressed or radially expanded, and the tubular structure A is radially expanded so that the tubular structure A can match the cochlea radial dimension. At the same time, the tubular structure A can be elongated or shortened along its axial length. As shown in FIG. 2 , the tubular structure A can also be bent along its axial direction to match the helical structure of the cochlea 10 , so that the tubular structure A has an implanted state and a released state. In the implanted state, the tubular structure A is intended to be placed on an implantation guide (not shown), and used to implant a cochlea 10 with the implantation guide. The implantation guide device is, for example, a bendable rod-shaped structure, and the stent monofilament 100 can be arranged spirally on the implantation guide device. During the transition of the tubular structure A from the implanted state to the released state, the axis of the tubular structure A expands helically to match the helical structure of the cochlea 10 . The expansion means that the tubular structure A expands along its own radial direction, and after the tubular structure A enters the release state, the tubular structure A can be in close contact with the cochlea 10 , so that the tubular structure A is arranged in such a way that the tubular structure A is in accordance with the patient's condition. When the inner size of the cochlea is unfolded, the radial size of itself is adjusted in real time, and the unfolded tubular structure A is closely fitted with the inner wall of the cochlea, so that each part of the stent monofilament 100 can be closely attached to the inner wall of the natural cavity of the patient's cochlea 10, This further solves the problem that the cochlear electrode does not fit closely with the inner wall of the cochlea.

As shown in FIG. 1 and FIG. 3 , the signal portion 200 is disposed on the stent monofilament 100 for sending or receiving signals. The signal unit 200 preferably includes, for example, electrical signal components and/or optical signal components. Preferably, the electrical signal component can be used for sending electrical signals or receiving signals in the cochlea. The optical signal component can be used to emit an optical signal. Both the electrical signal and the optical signal can stimulate the nervous system in the cochlea, and directly stimulate the auditory nerve to restore or reconstruct the hearing function of the deaf. The position of the signal portion 200 on the stent monofilament 100 is matched and set according to the position of the signal stimulation required by the cochlea 10 (for example, the position of the neuron). The structure of the stent monofilament 100 in the released state is simulated in vitro, and then the signal portion 200 is set according to the position of the desired signal stimulation. In this way, the signal part 200 on the stent monofilament 100 can be accurately positioned to the position of the required signal stimulation, so that the cochlear implant device can adapt to the individual differences of different cochleas, and can adapt to the unique unevenness of the inner wall of the cochlea of different patients. In addition, due to the tension effect of the stent monofilament 100 in the released state, the relative position of the signal portion 200 and the inner wall of the cochlea is fixed and stable, so that the signal portion 200 can be in direct contact with the interior of the cochlea 10 and closely Fitting, it is not easy to loosen and displace after surgery, so as to avoid the problem of easy displacement after cochlear surgery, improve the accuracy of the stimulation signal position, and improve the use effect of patients. In this embodiment, the signal part 200 includes electrodes, so that the electrode array mounted on the stent monofilament 100 is closely attached to the inner wall of the cochlea, so that the electrode array can better stimulate the auditory nerve.

The cochlear implant device may include one stent monofilament 100 , or may include two stent monofilaments 100 . Preferably, as shown in FIG. 1 , the cochlear implant device includes at least two stent monofilaments 100 , and the tubular structure A is formed by at least two stent monofilaments 100 spiraling along different trajectories. The monofilament 100 plays a supporting role in the entire tubular structure A. Compared with a single stent monofilament 100, the tubular structure A has a better radial support force, ensuring the stability of the tubular structure A inside the cochlea 10. sex. Understandably, the different trajectories indicate that the circling trajectories of each stent monofilament 100 are at least partially non-overlapping. That is, each stent monofilament 100 has a different spiral angle, so that the signal parts 200 on the stent monofilament 100 can be arranged in more positions, thereby improving the accuracy of signal stimulation. Preferably, the tubular structure A is formed by braiding at least two stent monofilaments 100 . More preferably, the number of signal parts 200 provided on each stent monofilament 100 is different. For example, one stent monofilament 100 is provided with one signal part 200 and the other stent monofilament 100 is provided with two signal parts 200 . Of course, when the stent monofilaments 100 are straightened, the length of one stent monofilament 100 may also be different from the length of the other stent monofilament 100. The staff calculates the integrated position of each signal portion 200 on the stent monofilament 100 according to the change of the cochlear diameter at the actual intra-cochlear implantation site in the patient's cochlea, and then calculates the integrated position of each signal portion 200 on the stent monofilament 100 through parameters such as the weaving combination process, the diameter of the target cochlea, and the signal size. . In the first embodiment, as shown in FIG. 1 , the tubular structure A is formed by braiding, for example, three stent monofilaments 100 , wherein each of the two stent monofilaments 100 is provided with a signal portion 200 , and one of them is not provided with a signal portion 200. The three stent monofilaments 100 are arranged in a staggered position, so that the signal portion 200 can be closely attached to the target position of the cochlea. More preferably, the signal portion 200 is disposed at the intersection of the two stent monofilaments 100 , and the signal portion 200 is located closer to the outside of the tubular structure A, so that the signal portion 200 can be closer to the cochlea target location. In fact, the signal part 200 needs to be close to the inner wall of the cochlea. If the signal part 200 is installed at the intersection of the two stent monofilaments 100, the signal part 200 needs to be installed on the stent monofilament 100 closest to the cochlea to avoid being affected by other stents. Monofilament 100 shades. Of course, in other embodiments, the number of the stent monofilament 100 and the signal portion 200 is not limited. The stent monofilaments 100 may be five, six, or eight, and the like. The number of signal parts 200 on each stent monofilament 100 may also be two, three, or four, etc. The distance between each signal part 200 on a single stent monofilament 100 is not limited, and can be determined according to the actual situation of the cochlea 10 Calculated. Preferably, each of the stent monofilaments 100 is provided with at least one of the signal parts 200 , so that each stent monofilament 100 can not only play a supporting role, but also play a role of carrying the signal part 200 .

Preferably, as shown in FIG. 4 , at least one signal portion 200 is provided on at least one of the stent monofilaments 100 , and the setting position of the signal portion 200 can be set according to actual requirements, so that the signal portion 200 able to provide stimulation signals. Preferably, as shown in FIG. 4 , each of the stent monofilaments 100 is provided with one of the signal parts 200 . When the stent monofilament 100 is straightened, the lengths of each of the stent monofilaments 100 are the same. Each of the signal parts 200 is arranged at equal distances along the axial direction of the stent monofilament 100, so that when each stent monofilament 100 is braided and combined, it is convenient to confirm the position of the signal part 200 on each stent monofilament 100, Improve weaving efficiency and weaving quality. In the first embodiment, each of the signal parts 200 is arranged at an interval of six millimeters along the axial direction of the stent monofilament 100 .

Preferably, as shown in FIG. 5 , the signal part includes an electrical signal component and/or an optical signal component; the electrical signal component includes an electrode, and the optical signal component includes an LED and/or a light intensity sensor. In the first embodiment, the signal unit 200 includes an electrical signal component, and the electrical signal component includes an electrode. The electrode is, for example, a thin electrode of platinum-iridium alloy with a length and width of 1 mm, which is connected to a wire 300 by welding. In another embodiment, the signal unit 200 includes an optical signal component including an LED and/or a light intensity sensor. Preferably, the optical signal component is connected to the wire 300 for receiving signals, and then stimulates the nerves of the cochlea by means of optical stimulation, so as to restore or reconstruct the hearing function of the deaf. The light signal component may be an LED, a light intensity sensor, or may include both an LED and a light intensity sensor. Likewise, the location and quantity of the optical signal components can be calculated according to the actual condition of the patient's cochlea. In other embodiments, the signal portion includes both electrical signal components and optical signal components.

As shown in FIG. 4 and FIG. 5 , the cochlear implant device further includes a wire 300 connected to the signal portion 200 . The wire 300 is, for example, a diameter of 30 microns with an insulating layer. Of course, the material of the wire 300 is not limited to gold wire, and can also be other materials capable of conducting electricity. Those skilled in the art can choose according to actual needs, which will not be repeated here. The wires 300 are used for transmitting electrical signals and the like, for example. The stent monofilament 100 includes a stent monofilament body 110 and a wire groove 120 . The wire groove 120 extends along the axial direction of the stent monofilament body 110 , and the wire 300 is disposed in the wire groove 120 . The wire guide 120 is not limited to a straight line along the axial direction of the stent monofilament body 110 , but is arranged following the shape of the stent monofilament body 110 , and is not limited to the axial direction strictly defined by the stent monofilament body 110 . , but represents the longitudinal direction of the strip-shaped stent monofilament body 110 . For example, the stent monofilament body 110 is a nickel-titanium alloy wire with a width and a thickness of 100 microns, the depth of the wire groove 120 is 50 microns, and the electrodes and the stent monofilament body 110 are adhered and integrated by an insulating material. The signal part 200 , the wire 300 and the stent monofilament 100 are integrated in this way to ensure that when the wire 300 is connected to the signal part 200 , the external structure size of the stent monofilament 100 will not be increased, and the influence of the misalignment or displacement of the wire 300 is prevented. The implantation position of the cochlear implant device ensures the stability of the cochlear implant device. Dimensions such as the depth, length, and width of the wire groove 120 can be set by those skilled in the art according to actual needs, and details are not described herein again. Optionally, the length of the wire slot 120 is matched according to the length of the actual wire, so as to avoid setting too many structures on the stent monofilament 100, thereby preventing the mechanical properties of the stent monofilament 100 from being affected by excessive structures.

Preferably, the signal portion 200 is disposed on, for example, the stent monofilament body 110 and outside the wire groove 120 , for example, the signal portion 200 is disposed when the groove of the wire groove 120 faces in a certain direction. On the one hand, the signal part 200 can be arranged on the monofilament body 110 of the stent to achieve close contact with the cochlea; The wires 300 in the grooves slide out, thereby optimizing the structure of the stent monofilament 100 and ensuring the quality of the stent monofilament 100 .

Preferably, the stent monofilament 100 further includes a medicine slot (not shown), and the medicine slot is used for accommodating medicine. The medicine groove is preferably extended along the axial direction of the stent monofilament 100. More preferably, the medicine groove is arranged through the wire groove 120. It can be understood that the wire groove 120 overlaps with the medicine groove. By setting, when processing the wire groove 120 and the medicine groove, the staff only needs to process one groove portion. More preferably, in the first embodiment, the groove part on one side of the signal part 200 is set as a wire groove 120 , and the groove part on the other side of the signal part 200 is set as a medicine groove. Of course, the staff can also set up a medicine groove on the stent monofilament 100, and the structure, size and position of the medicine groove can be set according to actual needs. When placing the drug, the staff will use fixed-point spraying to place some anti-inflammatory drugs or antibiotics. In actual use, the staff can also cover the surface of the stent monofilament 100 with a slow-release drug coating or a hydrophilic coating according to actual needs.

The following will specifically describe the processing process of the cochlear implant device provided in this embodiment with reference to FIGS. 1 to 5 :

First, use a nickel-titanium alloy sheet with a thickness of 100 microns to laser engrave grooves (conductor grooves and drug grooves) with a width and depth of 50 microns, and then cut them into stent monofilaments 100 with a width of 100 microns, and then pass the insulating material to make the signal The part 200 is adhesively integrated with the stent monofilament 100 .

Then, the wire 300 is placed in the wire groove 120 .

Finally, as shown in FIG. 4 , the integrated stent monofilament 100 , the signal portion 200 and the wire 300 are braided and integrated into a stent on a braiding machine, so that the signal portion 200 on the stent monofilament 100 is located in the same circumferential direction of the tubular structure A The positions of the wires 300 are linearly arranged and spaced equidistantly; the wires 300 are drawn from one end of the monofilament support 100 and connected together.

The present invention also provides a cochlear implant, which includes the above-mentioned cochlear implant device and an extra-cochlear implant device, and the extra-cochlear implant device is signally connected to the cochlear implant device. The cochlear implant has the beneficial effects of the cochlear implant device, which will not be repeated here. For the structures and principles of other components of the cochlear implant, reference may be made to the prior art, which will not be described here.

[Example 2]

Please refer to FIG. 1 . FIG. 1 is a schematic diagram of the cochlear implant devices provided in the first embodiment and the second embodiment.

The same parts of the cochlear implant device of the second embodiment and the first embodiment will not be described, and only the differences will be described below.

In the second embodiment, as shown in FIG. 1 , the stent monofilament 100 of the cochlear implant device includes an optical fiber, and the signal portion 200 includes an optical fiber light-transmitting port, and the optical fiber light-transmitting port is used for Translucent. The optical fiber can be directly set as the tubular structure A, and the optical signal of the optical fiber is optically stimulated through the optical fiber light-transmitting port. The optical fiber not only has the function of support, but also plays the role of light stimulation. In actual use, the staff can first enhance the strength of the optical fiber to ensure that it can meet the standard of supporting the cochlea.

Further, the stent monofilament 100 further includes a stent monofilament body 110 and an optical fiber groove, the optical fiber groove is extended along the axial direction of the stent monofilament body 110, the optical fiber is arranged in the optical fiber groove, and then The optical fiber with lower strength can be accommodated in the stent monofilament 100, so that the stent monofilament 100 has a supporting function, and ensures that the tubular structure A has a supporting function.

It should be noted that, each embodiment focuses on the differences from other embodiments, and the same and similar parts between the various embodiments may be referred to each other. In addition, the different parts of the first embodiment and the second embodiment can be used in combination with each other. Combined to form the same tubular structure, the cochlear implant device can use electrical signals to stimulate the cochlear nerve, and can stimulate the cochlear nerve through optical signals, thereby laying a foundation for improving the patient's use effect.

To sum up, in the cochlear implant device and the cochlear implant provided by the present invention, the cochlear implant device includes a tubular structure formed by coiling a stent monofilament, and a signal portion; the tubular structure has An implanted state and a released state, in the implanted state, the tubular structure is used for being disposed on an implantation guide device, and used for implanting a cochlea with the implantation guide device; in the tubular structure by During the transition from the implanted state to the released state, the tubular structure is radially reduced in diameter and expanded; the signal portion is arranged on the stent monofilament and is used for sending or receiving signals. This arrangement enables the cochlear implant device to adapt to the individual differences of different cochleas, to ensure that the implanted signal part fits closely with the cochlea, to ensure excellent signal stimulation effect, to improve the accuracy of the signal position, and to improve the patient's use effect.

The above description is only a description of the preferred embodiments of the present invention, and is not intended to limit the scope of the present invention. Any changes and modifications made by those of ordinary skill in the field of the present invention based on the above disclosure all belong to the protection scope of the claims.

Claims

A cochlear implant device, characterized in that it comprises: a tubular structure formed by coiling a stent monofilament, and a signal portion;

The tubular structure has an implanted state and a released state, and in the implanted state, the tubular structure is configured to be disposed on an implantation guide device and used to implant a cochlea along with the implantation guide device; in During the transition process of the tubular structure from the implanted state to the released state, the tubular structure expands in a radially variable diameter;

The signal part is arranged on the support monofilament and is used for sending or receiving signals.
The cochlear implant device according to claim 1, wherein the tubular structure is formed by at least two of the stent monofilaments spiraling along different trajectories.
The cochlear implant device according to claim 2, wherein at least one of the signal portions is provided on at least one of the stent monofilaments.
The cochlear implant device according to claim 3, wherein each of the stent monofilaments is provided with one signal portion, each of the stent monofilaments has the same length, and each of the signal portions has the same length. They are arranged equidistantly along the axial direction of the stent monofilament.
The cochlear implant device according to claim 2, wherein the signal portion is disposed at the intersection of the two stent monofilaments, and the signal portion is located closer to the outer side of the tubular structure.
The cochlear implant device according to claim 2, wherein the tubular structure is formed by braiding at least two stent monofilaments, and the number of signal parts provided on each stent monofilament is different.
The cochlear implant device according to claim 2, wherein at least one signal portion is provided on each of the stent monofilaments.
The cochlear implant device according to claim 1, wherein the cochlear implant device further comprises a lead wire, the lead wire is connected to the signal part; the stent monofilament comprises a stent monofilament body and a lead wire The wire groove is arranged along the axial direction of the stent monofilament body, and the wire is arranged in the wire groove.
The cochlear implant device according to claim 8, wherein the signal portion is disposed on the stent monofilament body and is located outside the wire groove.
The cochlear implant device according to claim 1, wherein the signal part comprises an electrical signal part and/or an optical signal part; the electrical signal part comprises an electrode, and the optical signal part comprises an LED and/or Light intensity sensor.
The cochlear implant device according to claim 1, wherein the stent monofilament further comprises a medicine groove, and the medicine groove is used for accommodating medicine.
The cochlear implant device according to claim 1, wherein the support monofilament comprises an optical fiber, and the signal portion comprises an optical fiber light-transmitting port, and the optical fiber light-transmitting port is used to transmit light.
The cochlear implant device according to claim 12, wherein the stent monofilament further comprises a stent monofilament body and an optical fiber groove, the optical fiber groove extending along the axial direction of the stent monofilament body, and the The optical fiber is arranged in the optical fiber groove.
A cochlear implant, comprising: the cochlear implant device according to any one of claims 1-13 and an extra-cochlear implant device, the extra-cochlear implant device and the cochlear implant device signal connect.