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WO2025143324A1 - Module d'électrode, dispositif d'aide à l'audition le comprenant, et son procédé de fabrication - Google Patents

Module d'électrode, dispositif d'aide à l'audition le comprenant, et son procédé de fabrication Download PDF

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Publication number
WO2025143324A1
WO2025143324A1 PCT/KR2023/021883 KR2023021883W WO2025143324A1 WO 2025143324 A1 WO2025143324 A1 WO 2025143324A1 KR 2023021883 W KR2023021883 W KR 2023021883W WO 2025143324 A1 WO2025143324 A1 WO 2025143324A1
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WIPO (PCT)
Prior art keywords
electrode
cochlea
module
therapeutic composition
electrode module
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Pending
Application number
PCT/KR2023/021883
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English (en)
Korean (ko)
Inventor
장종문
문경활
최종진
장정훈
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Ajou University Industry Academic Cooperation Foundation
Korea Institute of Materials Science KIMS
Original Assignee
Ajou University Industry Academic Cooperation Foundation
Korea Institute of Materials Science KIMS
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Application filed by Ajou University Industry Academic Cooperation Foundation, Korea Institute of Materials Science KIMS filed Critical Ajou University Industry Academic Cooperation Foundation
Priority to PCT/KR2023/021883 priority Critical patent/WO2025143324A1/fr
Publication of WO2025143324A1 publication Critical patent/WO2025143324A1/fr
Pending legal-status Critical Current
Anticipated expiration legal-status Critical

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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M31/00—Devices for introducing or retaining media, e.g. remedies, in cavities of the body
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N1/00—Electrotherapy; Circuits therefor
    • A61N1/02—Details
    • A61N1/04—Electrodes
    • A61N1/05—Electrodes for implantation or insertion into the body, e.g. heart electrode
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N1/00—Electrotherapy; Circuits therefor
    • A61N1/18—Applying electric currents by contact electrodes
    • A61N1/32—Applying electric currents by contact electrodes alternating or intermittent currents
    • A61N1/36—Applying electric currents by contact electrodes alternating or intermittent currents for stimulation
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N1/00—Electrotherapy; Circuits therefor
    • A61N1/18—Applying electric currents by contact electrodes
    • A61N1/32—Applying electric currents by contact electrodes alternating or intermittent currents
    • A61N1/36—Applying electric currents by contact electrodes alternating or intermittent currents for stimulation
    • A61N1/372—Arrangements in connection with the implantation of stimulators
    • B—PERFORMING OPERATIONS; TRANSPORTING
    • B29—WORKING OF PLASTICS; WORKING OF SUBSTANCES IN A PLASTIC STATE IN GENERAL
    • B29C—SHAPING OR JOINING OF PLASTICS; SHAPING OF MATERIAL IN A PLASTIC STATE, NOT OTHERWISE PROVIDED FOR; AFTER-TREATMENT OF THE SHAPED PRODUCTS, e.g. REPAIRING
    • B29C64/00—Additive manufacturing, i.e. manufacturing of three-dimensional [3D] objects by additive deposition, additive agglomeration or additive layering, e.g. by 3D printing, stereolithography or selective laser sintering
    • B29C64/10—Processes of additive manufacturing
    • B29C64/171—Processes of additive manufacturing specially adapted for manufacturing multiple 3D objects
    • B—PERFORMING OPERATIONS; TRANSPORTING
    • B29—WORKING OF PLASTICS; WORKING OF SUBSTANCES IN A PLASTIC STATE IN GENERAL
    • B29C—SHAPING OR JOINING OF PLASTICS; SHAPING OF MATERIAL IN A PLASTIC STATE, NOT OTHERWISE PROVIDED FOR; AFTER-TREATMENT OF THE SHAPED PRODUCTS, e.g. REPAIRING
    • B29C64/00—Additive manufacturing, i.e. manufacturing of three-dimensional [3D] objects by additive deposition, additive agglomeration or additive layering, e.g. by 3D printing, stereolithography or selective laser sintering
    • B29C64/30—Auxiliary operations or equipment
    • B29C64/386—Data acquisition or data processing for additive manufacturing
    • B29C64/393—Data acquisition or data processing for additive manufacturing for controlling or regulating additive manufacturing processes

Definitions

  • the human ear is composed of the outer ear, middle ear, and inner ear, and the main organ of the inner ear is the cochlea. Hair cells located inside the cochlea perform the function of converting mechanical stimuli into electrical signals.
  • a cochlear implant can be used to detect external sound signals and electrically stimulate the auditory nerve.
  • One of the main procedures for a cochlear implant is to insert an electrode array (CEA) for electrical stimulation into the cochlea.
  • CEA electrode array
  • EIT electrode insertion trauma
  • Conventional hearing aid devices have used flexible materials such as polymers to form electrode arrays in order to minimize physical stimulation to the cochlea, but there is still a problem of the interior of the cochlea being damaged by physical stimulation.
  • Another object of the present invention is to provide an electrode module capable of continuously administering a therapeutic drug (or a therapeutic composition) into the cochlea, a hearing assistance device including the same, and a method for manufacturing the same.
  • an electrode module inserted into a cochlea to assist hearing, the electrode module comprising: a module body having a communication hole formed inside the module body so as to be in communication with the outside through which a plurality of wires pass, a coupling pin extending outwardly and a coupling hole formed at an end of the coupling pin are provided on one side, and a coupling groove formed on the other side into which a coupling hole of another neighboring electrode module is coupled; and an electrode provided on the module body and electrically connected to one of the plurality of wires to emit current to the outside, the electrode module being connected to another neighboring electrode module in a ball joint manner.
  • the communication hole may be provided with a fixing member that fixes at least some of the plurality of wires to the inner wall of the communication hole.
  • the module body may be provided with a drug-receiving portion that releases a therapeutic composition to the outside over time.
  • the drug-receiving portion may be formed in multiple numbers along the outer surface of the module body in a grid-like pattern.
  • the therapeutic composition may be formed to continuously release the therapeutic composition for a predetermined period of time, including a biodegradable polymer and a therapeutic substance that can utilize the biodegradable polymer as a carrier.
  • a coupling hole is formed on the other side of the module body, which is connected to the coupling groove and whose diameter increases as it goes outward, and at least a part of the coupling pin of the neighboring electrode module can be positioned in the coupling hole.
  • the one side of the module body may include a curved portion formed to be convex toward the outside.
  • the coupling hole may include a first coupling hole in which at least a part of the coupling pin of the neighboring other electrode module is positioned, and a second coupling hole in which at least a part of the curved portion of the neighboring other electrode module is positioned.
  • the inner surface of the second coupling hole may have a shape corresponding to the outer surface of the curved portion.
  • a hearing assistance device for assisting hearing, comprising: a sound processor for converting sound into a predetermined signal; a transmitter provided outside the body for transmitting the signal to the outside; a receiver provided inside the body for receiving the signal transmitted by the transmitter; and an electrode array having a plurality of the above-described electrode modules and emitting a current corresponding to the signal received by the receiver.
  • the plurality of wires may be provided in multiple numbers corresponding to the number of electrodes of the plurality of electrode modules.
  • the module body can be connected in series with the module body of another neighboring electrode module.
  • the module body of the electrode module located at the shortest end among the plurality of electrode modules connected in series may have a convex portion formed to be convex toward the outside.
  • An electrode module according to an embodiment of the present invention, a hearing aid device including the same, and a method for manufacturing the same are configured such that a plurality of electrode modules inserted into the cochlea are connected to each other in a ball joint manner to provide rotational freedom in all directions, so that the electrode modules can be arranged in response to the spiral structure of the cochlea, thereby minimizing physical stimulation applied to the cochlea.
  • the electrode module according to an embodiment of the present invention, the hearing aid device including the same, and the manufacturing method thereof are provided with a fixing part for fixing a wire passing through the inside of the electrode module, thereby preventing the wire from being twisted or tangled even when the electrode module is rotated.
  • a hearing assistance device including an electrode module according to an embodiment of the present invention and a method for manufacturing the same are provided with electrodes and/or drug receptacles only in at least some electrode modules selected from a plurality of electrode modules, thereby reducing manufacturing costs, preventing side effects, and efficiently performing hearing assistance and treatment.
  • FIG. 1 is a schematic drawing showing a state in which a hearing assistance device according to one embodiment of the present invention is mounted on a body.
  • FIGS 3 to 5 are schematic drawings showing the state in which the electrode array of the hearing aid device illustrated in Figure 1 is inserted into the cochlea. At this time, the configuration seen through the cochlea is indicated by a solid line, and only a portion of the electrode module inserted into the cochlea is illustrated.
  • Figures 6 and 7 are perspective views of a portion of the electrode array of the hearing aid device illustrated in Figure 1 from different angles.
  • Fig. 9 is a cross-sectional view taken along line A-A of Fig. 8.
  • FIGS. 11 and 12 are diagrams illustrating some examples of modifications of the electrode array of a hearing aid device according to one embodiment of the present invention.
  • Figure 13 is a flow chart of a method for manufacturing a hearing assistance device according to one embodiment of the present invention.
  • FIGS. 2 to 5 illustrate that a plurality of electrode modules (51) are inserted and placed throughout the outer portion (8a), middle portion (8b), and inner portion (8c) of the cochlea (8)
  • the plurality of electrode modules (51) may be partially placed in a predetermined portion of the cochlea (8).
  • the predetermined portion may be a portion where hair cells are damaged and nerve cells need to receive electrical stimulation by the electrode array (50).
  • the length of the electrode array (50) may be formed to be shorter than the entire length of the cochlea (8), so that the electrode module (51) may be inserted into the outer part (8a) and the middle part (8b) of the cochlea (8), but the electrode module (51) may not be inserted into the inner part (8c).
  • the physical stimulation that may occur when the electrode module (51) located at the outermost side among the plurality of electrode modules (51) enters the inside of the cochlea (8) can be minimized.
  • the electrode (54) is a plate-shaped conductive object having a thin thickness, and may be provided on one side of the module body (52), for example, the lower side based on FIG. 7. In FIG. 7, the electrode (54) is illustrated so that its surface is exposed to the outside, but may also be provided so as to be mounted inside the module body (52).
  • the electrode (54) emits current in response to an electrical signal generated from the receiver (30). The emitted current applies an electrical stimulus to the nerve cells inside the cochlea.
  • the electrode (54) may be made of platinum (Pt), gold (Au), titanium nitride (TiN), etc., but is not limited thereto, and may be made of various conductive materials having properties suitable for a living body.
  • a module body (52) of an electrode module (51) may be formed with a protrusion (56, 58) and an insertion portion (57, 59) to be connected in a ball joint manner to a module body (52) of another neighboring electrode module (51).
  • a protrusion (56, 58) that protrudes outward is formed, and on the other side of the module body (52), for example, on the left side, an insertion portion (57, 59) into which a protrusion (56, 58) of another neighboring module body (52) can be inserted is formed.
  • the protrusions (56, 58) and the insertions (57, 59) are arranged in a parallel manner centered on the module body (52), but are not limited thereto, and if the electrode array (50) can be easily inserted into the interior of the cochlea (8), the protrusions (56, 58) and the insertions (57, 59) may be arranged misaligned at a predetermined angle.
  • the protrusions (56, 58) may be formed of a coupling pin (56) and a coupling hole (58).
  • the coupling pin (56) extends outward from one side of the module body (52). At this time, the coupling pin (56) may have a tapered shape whose diameter decreases as it goes outward, but is not limited thereto.
  • a coupling hole (58) is provided at the outer end of the coupling pin (56).
  • the insertion portion (57, 59) may be formed of a joining hole (57) and a joining groove (59).
  • the joining groove (59) is formed in a shape corresponding to the shape of the joining portion (58).
  • the joining hole (57) has one end connected to the joining groove (59) and the other end connected to the outside, and has a shape in which the diameter increases as it goes outward.
  • a coupling hole (58) of another neighboring electrode module (51) is coupled to the coupling home (59), and at least a part of a coupling pin (56) of another neighboring electrode module (51) is positioned in the coupling hole (57).
  • the coupling pin (56) can rotate freely inside the coupling hole (57)
  • the outer surface of the coupling pin (56) and the inner surface of the coupling hole (57) have a similar overall shape, but the inner diameter of the coupling hole (57) (i.e., the diameter of the cross-section of the coupling hole (57)) is formed to be larger than the outer diameter of the coupling pin (56) at the corresponding position (i.e., the diameter of the cross-section of the coupling pin (56)).
  • a first opening (58a) is formed in the coupling hole (58)
  • a second opening (59a) is formed in the inner wall of the coupling groove (59)
  • a communication hole (53) connecting the first opening (58a) and the second opening (59a) is formed inside the module body (52). That is, the communication hole (53) is communicated with the outside through the first and second openings (58a, 59a).
  • a plurality of wires (42) pass through the communication hole (53) and the first and second openings (58a, 59a).
  • the communication hole (53) may be formed of a first communication hole (53a) positioned adjacent to the electrode (54) and a second communication hole (53b) formed along the length direction inside the protrusion (56, 58).
  • the first and second communication holes (53a, 53b) are connected to each other.
  • a plurality of wires (42) are provided corresponding to the number of electrodes (54) of the plurality of electrode modules (51). Each wire (42) electrically connects an electrode (54) of one of the plurality of electrode modules (51) and a receiver (30).
  • the wire (42) connected to the electrode (54) of the electrode module (51) is branched from the plurality of wires (42).
  • the branched wires (42a, 42b) extend toward the electrode (54) of the electrode module (51) to electrically connect the electrode (54) and the receiver (30).
  • both ends of the communication hole (53) i.e., the first and second openings (58a, 59a)
  • the communication hole (53) are positioned on the inner walls of the coupling port (58) and the coupling groove (59), respectively, so that the communication hole (53) can be directly connected to the communication hole (53) of another neighboring electrode module (51).
  • the plurality of communication holes (53) can form a path that is parallel to the arrangement direction of the plurality of electrode modules (51).
  • the wire (42) can be bent along the arrangement direction of the plurality of electrode modules (51) without excessive deformation, and the electrical signal generated from the receiver (30) can be stably transmitted to the electrode (54).
  • a fixing member (44) for fixing a plurality of wires (42) passing through the communication hole (53) may be provided on the inner wall of the communication hole (53). Accordingly, even if the electrode module (51) rotates relative to another adjacent electrode module (51), twisting and distortion of the wires (42) passing through the interior of the electrode module (51) can be prevented.
  • the fixing member (44) is provided on the inner wall of the second communication hole (53b). In this way, the fixing member (44) is positioned in the second communication hole (53b) which is located further from the electrode (54) than the first communication hole (53a), so that the remaining wires (42) can be stably fixed to the inner wall of the communication hole (53) without interfering with the wiring of the wires (42a, 42b) branched to be connected to the electrode (54).
  • a drug receiving portion (55) is provided on the upper side of the module body (52).
  • the drug receiving portion (55) includes a drug receiving groove (55a) formed in the inner direction of the module body (52) and a therapeutic composition (55b) received in the drug receiving groove (55a).
  • the therapeutic composition (55b) means a composition in which a plurality of substances are mixed.
  • the drug receiving portion (55) is formed to continuously release the therapeutic composition (55b) to the outside of the module body (52) for a predetermined period of time as time passes.
  • the plurality of materials include at least one of a biocompatible material, a biodegradable material, and a therapeutic material that uses a biocompatible material and/or a biodegradable material as a carrier.
  • the ratio between the biodegradable material (and/or, biocompatible material) and the therapeutic material is not particularly limited.
  • Biocompatible materials refer to materials that are substantially non-toxic to the human body, chemically inert, and non-immunogenic, and biodegradable materials refer to materials that can be decomposed in the body by body fluids or microorganisms.
  • the therapeutic substance is a substance administered for the treatment of tissue or nerve cells of the cochlea (8), and may include at least one of a steroid drug such as dexamethasone (DEX), an aminoglycoside antibiotic such as neomycin, and a neurotherapeutic drug such as brain-derived neurotrophic factor, but is not limited thereto.
  • a steroid drug such as dexamethasone (DEX)
  • an aminoglycoside antibiotic such as neomycin
  • a neurotherapeutic drug such as brain-derived neurotrophic factor
  • the biodegradable polymer may include, but is not limited to, at least one of Poly lactic acid (PLA), Poly lactic-co-glycolic acid (PLGA), Polyethylene glycol (PEG), Poly ethylene glycol diacrylate (PEGDA), Poly pyrrole (PPY), and Pentaerythritol diacrylate (PETA).
  • PLA Poly lactic acid
  • PLGA Poly lactic-co-glycolic acid
  • PEG Polyethylene glycol
  • PEGDA Poly ethylene glycol diacrylate
  • PY Poly pyrrole
  • a therapeutic agent using a biodegradable polymer as a carrier which may include at least one of the above-mentioned dexamethasone, neomycin, and brain-derived neurotrophic factor, but is not limited thereto.
  • the module body (52) can be manufactured using a 3D printing method using a mixture of a biocompatible polymer and a biocompatible photoinitiator as a photoresist.
  • the ratio between the biocompatible polymer and the biocompatible photoinitiator is not particularly limited.
  • the biocompatible polymer may include a silicone elastomer
  • the biocompatible photoinitiator may include, but is not limited to, at least one of irgacure 369, irgacure 2959, and 1,4-bis(4-(N,N-bis(6-(N,N,N-trimethylammonium)hexyl)amino)-styryl)-2,5 dimethoxybenzene tetraiodide (WSPI).
  • irgacure 369 irgacure 2959
  • WSPI 1,4-bis(4-(N,N-bis(6-(N,N,N-trimethylammonium)hexyl)amino)-styryl)-2,5 dimethoxybenzene tetraiodide
  • the therapeutic composition structure can be manufactured by a 3D printing process using a Direct Laser Writing (DLW) method that forms a structure by irradiating the photoresist with a laser of a specific wavelength to cause a chemical reaction. Since the DLW method of the 3D printing process is suitable for forming a fine structure, it can be used to manufacture the therapeutic composition structure according to the present embodiment.
  • DLW Direct Laser Writing
  • the therapeutic composition structure can be manufactured by a 3D printing process using the DLW method, which causes two-photon polymerization (2PP).
  • the mixture (or photoresist) used to manufacture the module body (52) using a 3D printing method may further include a therapeutic substance.
  • the therapeutic substance may be configured to be continuously released from the module body (52) for a predetermined period of time.
  • the mixture (or photoresist) used to manufacture the module body (52) using a 3D printing method may further include a biodegradable polymer in addition to the therapeutic material. Accordingly, as the module body (52) is biodegraded, the therapeutic material may be formed to be continuously released from the module body (52) for a predetermined period of time.
  • a therapeutic composition (55b) can be loaded into the drug receiving home (55a) using inkjet printing.
  • Figure 10 is a graph showing the cumulative amount of dexamethasone released from an experimental example over time when a photoresist was manufactured by mixing a biocompatible photoinitiator, a biodegradable polymer, and dexamethasone as a therapeutic agent, and the manufactured photoresist was formed into an experimental example using a 3D printing process.
  • a mixture of PEGDA and PETA in a volume ratio of about 7:3 was used as a degradable polymer.
  • (1) shows the cumulative amount of dexamethasone released from Experimental Example 1 over time after mixing dexamethasone at 0.3 wt% with the photoresist and manufacturing Experimental Example 1 in a cube shape.
  • the amount of therapeutic agent released per unit time can be controlled by controlling the amount of therapeutic agent mixed into the photoresist. For example, in order to increase the amount of therapeutic agent released per unit time, the amount of therapeutic agent mixed into the photoresist can be increased.
  • the inner diameter of the cochlea (8) decreases from the outer portion (8a) to the inner portion (8c).
  • the width and/or height of the module body (52) of the electrode module (51) located at the inner portion (8c) is formed to be smaller than the width and/or height of the module body (52) of the electrode module (51) located at the outer portion (8a). That is, the plurality of electrode modules (51) can be formed to have the width and/or height of the module body (52) decrease from the outer portion (8a) to the inner portion (8c) of the cochlea (8).
  • the cochlea (8) has an increasing curvature from the outer side (8a) to the inner side (8c).
  • the length of the module body (52) of the electrode module (51) located at the inner side (8c) is formed to be shorter than the length of the module body (52) of the electrode module (51) located at the outer side (8a). That is, the plurality of electrode modules (51) can be formed to have the module body (52) become shorter as they go from the outer side (8a) to the inner side (8c) of the cochlea (8).
  • the difference between the inner diameter of the coupling hole (57) and the outer diameter of the coupling pin (56) at the corresponding position may be formed to increase from the outer side (8a) to the inner side (8c) of the cochlea (8).
  • each of the plurality of electrode modules (51) by forming the shape of each of the plurality of electrode modules (51) to correspond to a part of the cochlea (8) into which the electrode module (51) is inserted, the physical stimulus applied to the cochlea (8) can be minimized.
  • the electrode (54) may be provided only in at least some of the module bodies (52) selected from among the plurality of electrode modules (51).
  • the hair cells of the cochlea (8) may be damaged only in a part of the cochlea (8) due to congenital or acquired causes, while the original function is maintained in other parts.
  • the electrical stimulation by the electrode array (50) needs to be applied only to the part where the hair cells are damaged.
  • the electrode (54) may be selectively provided only in the module body (52) located in the part where electrical stimulation needs to be applied among the plurality of electrode modules (51). For example, if only the hair cells in the inner part (8c) and the outer part (8a) of the cochlea (8) are damaged and the hair cells in the middle part (8b) maintain their original function, the electrode (54) may be provided only in the module bodies (52) of the electrode modules (51a, 51c) located in the inner part (8c) and the outer part (8a) among the plurality of electrode modules (51), and the electrode (54) may not be provided in the module body (52) of the electrode module (51b) located in the middle part (8b).
  • the user's hearing can be efficiently assisted, the manufacturing cost of the hearing assistance device can be reduced, and side effects due to electrical stimulation being applied to unnecessary parts can be prevented.
  • the shape of the cochlea (8) varies from person to person and is not standardized.
  • the cochlea (8) may include a first portion with a sharp increase in curvature or a decrease in diameter and a second portion with a gentler curvature or a larger diameter than the surrounding area.
  • administration of a large amount of therapeutic composition (55b) is required in the first part, and administration of the therapeutic composition (55b) is not required in the second part.
  • the drug receiving portion (55) may be selectively provided only in the module body (52) located in the portion where administration of the therapeutic composition (55b) is required.
  • different amounts of the therapeutic composition (55b) may be loaded in the drug receiving portions (55) of a plurality of electrode modules (51).
  • the manufacturing cost of a hearing aid device can be reduced, side effects caused by administering a therapeutic composition (55b) to an unnecessary part can be prevented, and efficient and intensive treatment can be performed.
  • the plurality of electrode modules (51) include first and second electrode modules (51), but the therapeutic composition (55b) mounted on the drug receiving portion (55) of the first electrode module (51) and the therapeutic composition (55b) mounted on the drug receiving portion (55) of the second electrode module (51) may include different materials.
  • a therapeutic composition (55b) containing an antibiotic such as neomycin may be loaded into the drug receiving portion (55) of the electrode module (51) located in the outer part (8a), and a therapeutic composition (55b) containing a substance for nerve healing such as a brain-derived neurotrophic factor may be loaded into the inner part (8c).
  • the manufacturing cost of the hearing aid device can be reduced, side effects caused by administering a different type of therapeutic composition (55b) to the area requiring treatment can be prevented, and efficient and intensive treatment can be performed.
  • FIGS. 11 and 12 are diagrams illustrating some examples of modifications of the electrode array of a hearing aid device according to one embodiment of the present invention.
  • the plurality of drug-receiving portions (155) may be formed with different densities in each portion of the electrode array (150).
  • the plurality of drug-receiving portions (155) may be formed with a higher density and more densely than in other electrode modules (151).
  • a protrusion (56, 58) is inserted to form an insertion part (257, 259) for ball joint type connection.
  • the insertion part (257, 259) includes a joining groove (259) and a joining hole (257).
  • each of the plurality of electrode modules by forming the shape of each of the plurality of electrode modules to correspond to a part of the cochlea into which the electrode module (51) is inserted, the physical stimulation applied to the cochlea can be minimized.
  • the part of each part of the cochlea where the electrode for emitting current is positioned is determined based on the structure and state of the analyzed cochlea (S300).
  • At least one electrode module having a drug receiving portion among a plurality of electrode modules can be selected.
  • a therapeutic composition accommodated in the drug receiving portion and a therapeutic substance included in the therapeutic composition can be selected.
  • a plurality of electrode modules are formed using a 3D printing process based on the determined shape of the electrode module, the position of the electrode, the position of the drug receiving portion, and the type of the therapeutic composition (S400).
  • the 3D printing process used to manufacture the electrode module can be a 3D printing process using the DLW method that utilizes two-photon polymerization. Accordingly, the microstructure of the electrode module to be inserted into a cochlea of a micro size can be easily formed.
  • the therapeutic composition (or therapeutic substance) can be continuously released from the electrode module over time, thereby enabling continuous administration of the drug (or therapeutic substance) to the cochlea without any additional separate components.
  • an electrode is mounted on an electrode module that is to be inserted into a portion where an electrode is to be positioned (i.e., an electrode module selected to have an electrode), and a drug-receiving groove is formed on an electrode module that is to be inserted into a portion where a therapeutic composition is to be administered (i.e., an electrode module selected to have a drug-receiving portion).
  • the user's hearing can be efficiently assisted, the manufacturing cost of the hearing assistance device can be reduced, and side effects due to electrical stimulation being applied to unnecessary parts can be prevented.
  • a drug (or a therapeutic composition) is loaded into the drug-receiving groove formed in the electrode module forming step (S400) (S500).
  • the drug (or a therapeutic composition) may be loaded using an inkjet method.
  • the therapeutic composition may include a biodegradable polymer and a therapeutic substance. Accordingly, the therapeutic composition may be continuously released from the drug-receiving portion for a predetermined period of time.
  • a specific type of drug (or therapeutic composition) determined in advance is loaded into the formed drug-receiving home. This allows the manufacturing cost of the hearing aid device to be reduced, side effects caused by other therapeutic compositions being administered to the area requiring treatment to be prevented, and efficient and intensive treatment to be performed.
  • a plurality of electrode modules formed in an electrode module forming step (S400) and loaded with a therapeutic composition in a drug loading step (S500) are connected according to an arrangement determined in a step of determining the positions of the electrode modules (S300) to form an electrode array (S600), and an audio processor, a transmitter, a receiver, and a wiring section are combined (S700).
  • the plurality of electrode modules are connected in a ball joint manner. Accordingly, according to the present embodiment, the plurality of electrode modules are given the freedom of relative rotation in all directions, so that the physical stimulation applied to the cochlea when and after the electrode array is inserted into the cochlea can be minimized.

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  • Optics & Photonics (AREA)
  • Mechanical Engineering (AREA)
  • Manufacturing & Machinery (AREA)
  • Physics & Mathematics (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Cardiology (AREA)
  • Anesthesiology (AREA)
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  • Electrotherapy Devices (AREA)

Abstract

L'invention concerne un dispositif d'aide à l'audition et son procédé de fabrication. Le dispositif d'aide à l'audition selon un aspect de la présente invention est un dispositif d'aide à l'audition servant à aider l'audition, et le dispositif d'aide à l'audition peut comprendre : un processeur de son pour convertir un son en un signal prédéfini ; un émetteur disposé à l'extérieur du corps pour émettre le signal vers l'extérieur ; un récepteur disposé à l'intérieur du corps pour recevoir le signal émit par l'émetteur ; et un réseau d'électrodes comprenant une pluralité de modules d'électrode reliés les uns aux autres d'une manière à rotule et insérés dans la cochlée, et émettant un courant correspondant au signal reçu par le récepteur.
PCT/KR2023/021883 2023-12-28 2023-12-28 Module d'électrode, dispositif d'aide à l'audition le comprenant, et son procédé de fabrication Pending WO2025143324A1 (fr)

Priority Applications (1)

Application Number Priority Date Filing Date Title
PCT/KR2023/021883 WO2025143324A1 (fr) 2023-12-28 2023-12-28 Module d'électrode, dispositif d'aide à l'audition le comprenant, et son procédé de fabrication

Applications Claiming Priority (1)

Application Number Priority Date Filing Date Title
PCT/KR2023/021883 WO2025143324A1 (fr) 2023-12-28 2023-12-28 Module d'électrode, dispositif d'aide à l'audition le comprenant, et son procédé de fabrication

Publications (1)

Publication Number Publication Date
WO2025143324A1 true WO2025143324A1 (fr) 2025-07-03

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PCT/KR2023/021883 Pending WO2025143324A1 (fr) 2023-12-28 2023-12-28 Module d'électrode, dispositif d'aide à l'audition le comprenant, et son procédé de fabrication

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WO (1) WO2025143324A1 (fr)

Citations (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP2011510750A (ja) * 2008-01-29 2011-04-07 クライマン、ギルバート・エイチ 薬物送達デバイス、キット及びそれらの方法
KR20130121591A (ko) * 2012-04-27 2013-11-06 주식회사 고영테크놀러지 볼 조인트를 이용한 수술도구용 관절
CN108353237A (zh) * 2015-10-30 2018-07-31 科利耳有限公司 可植入式刺激组件
KR20180099066A (ko) * 2017-02-28 2018-09-05 서울대학교산학협력단 전기자극법을 이용한 이명치료장치
US20200384262A1 (en) * 2016-12-01 2020-12-10 Advanced Bionics Ag Cochlear implants including electrode arrays and methods of making the same
KR20240022243A (ko) * 2022-08-11 2024-02-20 한국재료연구원 전극 모듈, 이를 포함하는 청력 보조 장치 및 이의 제조방법

Patent Citations (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP2011510750A (ja) * 2008-01-29 2011-04-07 クライマン、ギルバート・エイチ 薬物送達デバイス、キット及びそれらの方法
KR20130121591A (ko) * 2012-04-27 2013-11-06 주식회사 고영테크놀러지 볼 조인트를 이용한 수술도구용 관절
CN108353237A (zh) * 2015-10-30 2018-07-31 科利耳有限公司 可植入式刺激组件
US20200384262A1 (en) * 2016-12-01 2020-12-10 Advanced Bionics Ag Cochlear implants including electrode arrays and methods of making the same
KR20180099066A (ko) * 2017-02-28 2018-09-05 서울대학교산학협력단 전기자극법을 이용한 이명치료장치
KR20240022243A (ko) * 2022-08-11 2024-02-20 한국재료연구원 전극 모듈, 이를 포함하는 청력 보조 장치 및 이의 제조방법

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