Charger and charging system

Abstract

The utility model discloses a charger and a charging system in the technical field of medical instruments, the charger is used for charging an implantable device, the implantable device is used for being implanted into the skull of a user, the implantable device comprises a receiving coil, the charger comprises a transmitting coil, the transmitting coil is used for being coupled with the receiving coil, and the receiving coil is used for receiving the transmitting coil. At least part of the transmitting coil is in an arc shape, and the arc shape is at least matched with the skull of the user. By adopting the transmitting coil adaptive to the radian of the human skull, the radian of the human skull and the shape of the nerve stimulator can be better matched, so that the distances from the surface of the receiving coil to the surface of the transmitting coil are equal everywhere in the receiving area, and the magnetic flux variation in the receiving area is improved; the coupling coefficient between the transmitting coil and the receiving coil is improved, and the induction voltage and current of the receiving coil are improved, so that the charging efficiency is improved.

Description

Technical Field

[0001] The utility model relates to the technical field of medical equipment, in particular to a charger and a charging system. Background Art

[0002] Class III active implantable neurostimulators are medical devices used to stimulate the nervous system. They are implanted in the body to provide electrical stimulation to specific nerves or nerve bundles in order to treat or improve certain neurological diseases.

[0003] The power sources for the three types of active implantable neurostimulators are divided into disposable non-rechargeable power sources and rechargeable power sources.

[0004] When a Class III active implantable neurostimulator that uses a non-rechargeable power source is implanted in the human body, a large-capacity power supply battery is required to ensure that the system is continuously used within its effective service life to meet the expected service life of the product. The large-capacity power supply battery is large in size, which increases the overall size of the Class III active implantable neurostimulator, increasing the risk of trauma to the patient during the operation. In addition, the use of a larger Class III active implantable neurostimulator will reduce the patient's comfort.

[0005] When a Class III active implantable neurostimulator using a rechargeable power source is implanted in the human body, since it can be charged, it is only necessary to ensure that the system can be used continuously within a limited period. Therefore, the size of the battery can be greatly reduced, and the overall size of the Class III active implantable neurostimulator can be smaller, reducing the trauma and discomfort caused to the patient during the operation.

[0006] The three common types of active implantable neurostimulators are deep brain neurostimulators, which are usually implanted in the chest and transmit stimulation signals to the brain nucleus through wires. However, after long-term use, the wires may be displaced, which will inevitably affect the use effect of the deep brain neurostimulator. On the other hand, if the deep brain neurostimulator is directly implanted into the skull, given the particularity of the brain structure, charging the stimulator with an existing charger will have a certain impact and will reduce the charging efficiency of the neurostimulator. Therefore, the utility model proposes a charger and a charging system to solve the above technical problems. Utility Model Content

[0007] The utility model aims to provide a charger and a charging system, which are used to make the distance from the surface of the receiving coil to the surface of the transmitting coil equal or substantially the same everywhere in the receiving area, thereby increasing the change of magnetic flux in the receiving area and thus improving the charging efficiency.

[0008] The purpose of the utility model is achieved by the following technical solutions:

[0009] On the one hand, the utility model introduces a charger for charging an implantable device, wherein the implantable device is implanted into a user's skull, the implantable device includes a receiving coil, and the charger includes:

[0010] A transmitting coil, the transmitting coil is used to couple with the receiving coil, at least a part of the transmitting coil is arc-shaped, and the arc is at least adapted to the skull of the user.

[0011] Furthermore, the transmitting coil includes at least one layer of a planar structure formed by winding a wire, and the planar structure is arranged in an arc surface.

[0012] Furthermore, the length of the arc or chord of the maximum cross-section of the transmitting coil is greater than or equal to 80 mm, and the radius of the maximum cross-section of the transmitting coil is greater than or equal to 60 mm and less than or equal to 100 mm.

[0013] Furthermore, the radius of the uniform area of ​​the transmitting coil does not exceed the sum of the radius of the receiving coil and a preset error tolerance offset.

[0014] Furthermore, the ratio of the maximum value of the field intensity difference in the uniform area of ​​the transmitting coil to the average value of the field intensity does not exceed 0.3.

[0015] Furthermore, the ratio of the area of ​​the transmitting coil to the area of ​​the receiving coil is in the range of 8-20.

[0016] Furthermore, the orthographic projection shape of the transmitting coil is circular or elliptical, and the length of the arc or chord of the maximum cross-section of the transmitting coil is less than or equal to 160 mm.

[0017] Furthermore, the charger also includes:

[0018] A magnetic isolation sheet is arranged on a side of the transmitting coil facing away from the receiving coil, and has a curved surface structure matching the arc shape of the transmitting coil.

[0019] Furthermore, the charger also includes a housing and a circuit board;

[0020] The housing comprises a first accommodation space for accommodating the transmitting coil and a second accommodation space for accommodating the circuit board;

[0021] The first accommodating space is at least adapted to the transmitting coil;

[0022] The orthographic projection of the transmitting coil and the orthographic projection of the circuit board do not overlap.

[0023] Furthermore, the circuit board is a flexible circuit board.

[0024] Furthermore, the housing comprises:

[0025] Upper cover;

[0026] A lower cover is snap-connected with the upper cover, and the lower cover is arranged on a side of the transmitting coil facing the receiving coil, and the lower cover has a curved surface structure matching the user's skull.

[0027] Furthermore, the lower cover has a groove, the orthographic projection of the geometric center of the groove overlaps with the orthographic projection of the geometric center of the transmitting coil, and the groove matches the implantable device.

[0028] Furthermore, the thickness of the lower cover is less than or equal to 2 mm.

[0029] On the other hand, the utility model introduces a charging system, the charging system comprising:

[0030] An implantable device, the implantable device is used to be implanted in the skull of a user;

[0031] A charger is used to charge the implantable device.

[0032] Compared with the prior art, the beneficial effects of the present invention include at least:

[0033] Since the receiving coil has a curved surface structure that matches the curvature of the human skull, the use of a transmitting coil that is adapted to the curvature of the human skull can better match the curvature of the human skull and the shape of the neurostimulator, so that in the receiving area, the distance from the surface of the receiving coil to the surface of the transmitting coil is equal everywhere, thereby increasing the change in magnetic flux in the receiving area, increasing the coupling coefficient between the transmitting coil and the receiving coil, and increasing the induced voltage and current of the receiving coil, thereby achieving improved charging efficiency. In addition, the magnetic field generated by the arc-shaped transmitting coil is more concentrated on the inner arc surface of the transmitting coil, further improving the charging efficiency of the charger.

[0034] Furthermore, the use of a transmitting coil that is adapted to the curvature of the human skull can not only improve the charging efficiency, but also increase the user's comfort, so that the charger can better adapt to the head contour during use and reduce discomfort and pressure.

[0035] Furthermore, taking into account the size of the receiving coil, the weight of the charger, the tolerance offset and the size of the skull, the arc length of the maximum cross-section of the transmitting coil 1 is set to be greater than or equal to 80 mm, ensuring that there is sufficient contact area between the transmitting coil 1 and the receiving coil of the implantable device, thereby improving the charging efficiency and stability.

[0036] Furthermore, taking into account the sizes of different implantable devices and the differences in human skulls, technical personnel in this field can adjust the radius of the maximum cross-section within the range of 60mm-100mm, which not only ensures the coverage range of the transmitting coil, but also avoids the inconvenience caused to the user by the arc angle of the transmitting coil being too large or too small. BRIEF DESCRIPTION OF THE DRAWINGS

[0037] Figure 1 It is a structural explosion diagram of the charger according to the embodiment of the utility model.

[0038] Figure 2 It is a structural schematic diagram of a charger according to an embodiment of the utility model.

[0039] Figure 3 It is a structural schematic diagram of the orthographic projection of the transmitting coil of an embodiment of the utility model.

[0040] Figure 4 It is a structural schematic diagram of the maximum cross section of the transmitting coil of an embodiment of the utility model.

[0041] Figure 5 It is another structural explosion diagram of the charger according to the embodiment of the utility model.

[0042] In the figure: 1, transmitting coil; 2, circuit board; 3, magnetic isolation sheet; 4, shell; 41, upper cover; 42, lower cover; 421, groove; 6, cable; 51, first fixing glue; 52, second fixing glue. DETAILED DESCRIPTION

[0043] Example embodiments will now be described more fully with reference to the accompanying drawings. However, example embodiments can be implemented in a variety of forms and should not be construed as limited to the embodiments set forth herein; rather, these embodiments are provided to make the present invention more comprehensive and complete and to fully convey the concepts of example embodiments to those skilled in the art. The same reference numerals in the figures represent the same or similar structures, and thus their repeated description will be omitted.

[0044] The words expressing positions and directions described in the present utility model are all explained by taking the drawings as examples, but they can be changed as needed, and all the changes are included in the protection scope of the present utility model.

[0045] The bottom of the existing charger is a plane. Generally, the position of the neurostimulator implanted in the brain cannot be accurately found through the charger structure, so the charging process of coupling the charger and the neurostimulator can basically only rely on guessing whether they are accurately coupled, resulting in the user's failure to make the transmitting coil 1 and the receiving coil coaxial and concentric every time (the coaxial and concentric nature of the present invention means that the geometric center of the transmitting coil 1 overlaps the orthographic projection of the collective center of the receiving coil), resulting in low charging efficiency. A 60mW charger takes more than 15 hours to complete a neurostimulator charging cycle. The lengthy charging time seriously affects the user experience.

[0046] In order to improve the coupling degree between the transmitting coil 1 of the charger and the receiving coil of the neurostimulator, improve the fault tolerance of the receiving alignment of the transmitting coil 1, and reduce the charging time of the neurostimulator, the utility model provides a charger and a charging system suitable for an implantable neurostimulator.

[0047] The charger of the utility model comprises a transmitting coil 1. Further, it may also comprise a magnetic isolation sheet 3, referring to Figure 1 In some preferred embodiments, the housing 4 and the circuit board 2 may also be included. Figure 2 and Figure 1 .

[0048] The transmitting coil 1 of the utility model is used to couple the receiving coil of the implantable device, and the implantable device is a neurostimulator that has been implanted in the brain or a neurostimulator that has not been implanted in the brain. In order to match the curvature of the human skull, the neurostimulator implanted in the brain can be set to an arc shape, and the neurostimulator has a curved surface structure that matches the curvature of the human skull. When used, in order to reduce the overall volume of the neurostimulator as much as possible, the receiving coil of the neurostimulator has a curved surface structure that matches the curvature of the human skull.

[0049] In the embodiments of the present specification, the neurostimulator is implanted at the top of the human brain, and the implantation depth is 3mm-15mm. Preferably, it can be 3mm, 5mm, 10mm, etc. The specific implantation depth is not limited in the embodiments of the present specification.

[0050] In an embodiment of the present specification, the neurostimulator is fixed on a human skull (i.e., the cerebral skull), wherein the neurostimulator at least partially protrudes from the surface of the skull. In order to match the curvature of the human skull and the protruding shape of the neurostimulator, at least a partial area of ​​the transmitting coil 1 is set to an arc shape, and the arc shape at least matches the user's skull. The inner arc surface of the arc faces the neurostimulator, so that the changing magnetic field generated by the transmitting coil 1 when powered is more concentrated in the direction of the inner arc surface, thereby increasing the magnetic flux change at the receiving coil in the neurostimulator and improving the coupling relationship between the transmitting coil 1 and the receiving coil.

[0051] Optionally, the entire plane of the transmitting coil 1 is a uniform arc structure.

[0052] In the embodiments of this specification, reference is made to Figure 3 The orthographic projection shape of the transmitting coil 1 is circular or elliptical, that is, the transmitting coil 1. Of course, it can also be other shapes as long as it can achieve a higher coupling relationship between the transmitting coil 1 and the receiving coil or match the internal structure of the charger.

[0053] When used, the arc length of the maximum cross section of the transmitting coil 1 can be greater than or equal to 80 mm and less than or equal to 160 mm.

[0054] In another embodiment of this specification, reference Figure 4 , the chord length D of the maximum cross section of the transmitting coil 1 can also be set to be greater than or equal to 80 mm and less than or equal to 160 mm according to actual needs. Preferably, the length of the arc or chord of the maximum cross section of the transmitting coil 1 can be set to 80 mm, 90 mm, 100 mm, 110 mm, 120 mm, 130 mm, 140 mm, 150 mm, or 160 mm according to the actual situation of the user.

[0055] In the embodiment of this specification, the radius R of the maximum cross-section of the transmitting coil 1 is set to a range of 40-120 mm. Further, the range of R can be set to 60-100 mm. Those skilled in the art can set R to 60 mm, 70 mm, 80 mm, 90 mm, or 100 mm according to the actual size of the user's skull. Figure 4 .

[0056] By limiting the size of the transmitting coil 1 as mentioned above, the arc-shaped design can adapt the magnetic field of the transmitting coil 1 to the user's skull, and then cooperate with the receiving coil in the stimulator, so as to improve the charging efficiency of the stimulator fixed on the skull.

[0057] In some preferred embodiments, the transmitting coil 1 includes at least one layer of a planar structure formed by winding a wire, and the planar structure is set as an arc surface. When applied, the transmitting coil 1 is a curved winding formed by winding copper wires in circles to form concentric circles, which can be completely planar or annular. Since the strength and stability of the magnetic field can be enhanced and the efficiency and stability of energy transmission can be improved by increasing the number of turns of the coil, the inner circle of the annular transmitting coil 1 should be set as small as possible so that the number of turns of the coil is sufficient to generate a magnetic field of sufficient strength, thereby ensuring the charging efficiency of the stimulator. In addition, reducing the inner circle of the annular transmitting coil 1 can also effectively control the concentration of the magnetic field, so that the magnetic field covers the receiving coil more evenly, thereby helping to improve the power supply efficiency. As an option, the inner circle radius of the annular transmitting coil does not exceed 5mm, preferably, it can be 1mm, 2mm, etc., and the outer circle radius can be 3cm, 4cm, 5cm, etc. The specific size needs to be adapted to the size of the charger itself.

[0058] In some embodiments of the present specification, in order to increase the magnetic flux density of the magnetic field, a transmitting coil 1 with multiple layered structures can be provided. This increases the number of turns of the coil in a certain area, thereby increasing the change in magnetic flux generated by the transmitting coil 1, increasing the transmission capacity of electric energy, and correspondingly increasing the amount of electric energy conversion of the receiving coil, thereby increasing the charging speed. The size of the coils in each layered structure is consistent, and then the multiple layers of coils are tightly stacked together to form the final transmitting coil 1, thereby reducing the space occupied by the coil and avoiding the large size of the charger.

[0059] In a further embodiment, since the charger is cooperated with the stimulator fixed on the skull, in order to avoid putting too much burden on the user's head, the weight of the charger should not be too large. The coil itself has a large weight, so the coil can be maintained in an appropriate number of layers, such as 1 layer, 2 layers, 3 layers, etc.

[0060] The beneficial effect of the above technical solution is: since the receiving coil has a curved surface structure that matches the curvature of the human skull, the use of a transmitting coil 1 that is adapted to the curvature of the human skull can better match the curvature of the human skull and the shape of the neural stimulator, so that in the receiving area, the distance from the surface of the receiving coil to the surface of the transmitting coil 1 is kept as consistent as possible everywhere, thereby increasing the magnetic flux change in the receiving area, increasing the coupling coefficient between the transmitting coil 1 and the receiving coil, and increasing the induced voltage and current of the receiving coil, thereby achieving improved charging efficiency.

[0061] In addition, the magnetic field generated by the arc-shaped transmitting coil 1 is more concentrated in the direction of the inner arc surface of the transmitting coil 1, further improving the charging efficiency of the charger.

[0062] Furthermore, taking into account the size of the receiving coil, the weight of the charger, the tolerance offset and the size of the skull, the length of the arc or chord of the maximum cross-section of the transmitting coil 1 is set to 80mm-160mm, which ensures that there is sufficient contact area between the transmitting coil 1 and the receiving coil of the implantable device, thereby improving the charging efficiency and stability, and avoids the charger being too heavy and reducing the user's comfort due to the large size of the transmitting coil.

[0063] Furthermore, taking into account the sizes of different implantable devices and the differences in human skulls, technicians in this field can adjust the radius of the maximum cross-section within the range of 60mm-100mm, which not only ensures the coverage of the transmitting coil 1, but also avoids the inconvenience caused by the arc angle of the transmitting coil 1 being too large or too small.

[0064] In the embodiments of the present specification, since the neurostimulator is fixed on the skull, when the patient performs the charging coordination by himself, there may be a positioning deviation when the charger and the neurostimulator are coaxially and centrally aligned, and it will also be difficult to achieve perfect alignment. In order to reduce the difficulty of operation and increase the charging speed of the user, the area of ​​the uniform zone of the transmitting coil 1 can be reasonably expanded so that fast charging can be performed in a wider matching position.

[0065] Therefore, the uniform area of ​​the transmitting coil refers to an area where the magnetic field strength is relatively uniformly distributed in the electromagnetic field generated by the coil, or an area where the magnetic field strength is greater than a preset strength in the electromagnetic field, or an area where the position deviation of the transmitting coil and the receiving coil is within a specified range. The preset strength may be related to the input power information of the transmitting coil, such as the input voltage, etc. Different input voltages correspond to different preset strengths. Generally, the greater the input voltage, the greater the preset strength. The specified range may represent a fixed position where the transmitting coil can be charged with the receiving coil.

[0066] Based on common sense, the charging coil (i.e., the transmitting coil) will generate a changing electromagnetic field near it after the input of alternating current, but as the distance from the charging coil increases, the density of the electromagnetic field gradually decreases. To a certain extent, the electromagnetic field gradually becomes sparser with increasing distance at a faster rate. Therefore, when charging, the receiving coil will be placed as close to the charging coil as possible to include the receiving coil in a denser electromagnetic field. Generally, only when the transmitting coil and the receiving coil are fully aligned, the area covered by the transmitting coil to the receiving coil is a uniform area. In order to reduce the difficulty of user alignment, the present application expands the range of the uniform area, thereby improving the user's convenience of operation.

[0067] It should be noted that the uniform area may be a circular area with the center of the transmitting coil as the center, and of course may also be related to the shape of the transmitting coil. When the transmitting coil is a non-circular structure, the uniform area may also be non-circular.

[0068] During the wireless charging process, the uniformity area of ​​the transmitting coil directly affects whether the receiving coil can effectively receive energy. Due to differences in user body positions and fault tolerance requirements, the radiation coil 1 of the charger of the utility model requires a larger uniformity area to reasonably expand the fault tolerance range to ensure the stability and safety of charging.

[0069] Furthermore, in the embodiments of the present specification, the uniform area of ​​the transmitting coil 1 does not exceed the sum of the radius of the receiving coil and the preset fault tolerance offset. The preset fault tolerance offset refers to the fault tolerance range set in advance according to actual needs during the charging process. The fault tolerance range refers to the deviation range between the geometric center of the orthographic projection of the transmitting coil 1 and the geometric center of the orthographic projection of the receiving coil when the transmitting coil 1 is coupled to the receiving coil and the transmitting coil and the receiving coil meet the specified charging requirements. The charging requirement can be a charging efficiency of not less than 40%, 50%, 60%, etc., or the current intensity in the transmitting coil or the receiving coil reaches a certain value, such as 10mA, 15mA, 20mA, 25mA, etc. In one example, the receiving coil area is 600mm ^2 , the area ratio of the transmitting coil 1 to the receiving coil is calculated to be 8.37. At this time, the preset fault tolerance offset can be set to 10mm. In the actual test process, when the charging distance between the charger and the neurostimulator is 5mm, within the offset distance of 10mm, the minimum effective average charging current is 25-30mA, and the charging distance can be the vertical distance between the charger and the neurostimulator; when the charging distance between the charger and the neurostimulator is 15mm, within the offset distance of 10mm, the minimum effective average charging current is 20-30mA; it can be seen that within the offset distance of 10mm, the effective average charging current is greater than or equal to 20mA.

[0070] In the embodiments of this specification, the size of the receiving coil, the weight of the charger, the tolerance offset, and the size of the skull are comprehensively considered, and the area ratio of the transmitting coil 1 to the receiving coil is set to be greater than or equal to 8 and less than or equal to 20. This can ensure that the electromagnetic field of the transmitting coil 1 can completely cover the receiving coil, and the area with higher electromagnetic field density can cover the receiving coil (when the transmitting coil and the receiving coil are coaxial or the axis deviation is not large), thereby ensuring the efficiency of the energy conversion of the receiving coil, and also avoiding the size of the charger becoming larger due to the size of the transmitting coil being too large, which affects the user's use. Further, the coverage area ratio of the transmitting coil 1 to the receiving coil is set to 10-20, preferably, it can be 10, 15, 20, etc.

[0071] In some embodiments of the present specification, the ratio of the difference between the maximum value of the field strength and the minimum value of the field strength in the uniform area of ​​the transmitting coil 1 to the average value of the field strength is not greater than 0.3. Preferably, the ratio of the maximum value of the field strength difference in the uniform area of ​​the transmitting coil 1 to the average value of the field strength is in the range of 0-0.2. Those skilled in the art can set the ratio of the maximum value of the field strength difference in the uniform area of ​​the transmitting coil 1 to the average value of the field strength to 0.3, 0.2, 0.1, 0 according to actual conditions. By limiting the field strength of the electromagnetic field in the uniform area, the field strength in the uniform area can be made more uniform, so that a higher charging efficiency can be achieved at any position in the uniform area, thereby improving the user experience.

[0072] Exemplarily, experimental verification can be performed through the Maxwell 3D simulation design in Ansys Electronics Desktop. For example, the radius of the receiving coil is 10 mm, and the area ratio of the transmitting coil to the receiving coil is 8, that is, the radius of the transmitting coil is 80 cm, and the preset fault tolerance offset is set to 10 mm. In this way, through the above method, the radius of the uniform area of ​​the transmitting coil 1 does not exceed 20 mm. Here, the radius of the uniform area can be set to 20 mm. Then, with the center of the transmitting coil as the center of the circle or the center of the sphere, and 20 mm as the radius, the electromagnetic field of the uniform area of ​​the transmitting coil 1 is obtained, and multiple points are sampled on any radius of the uniform area of ​​the transmitting coil 1, and the field strength of the sampling point is recorded. The maximum field strength Bmax=354.751uTesla, the minimum field strength Bmin=93.520uTesla, and the average field strength Baverage=263.820uTesla are obtained, then (Bmax-Bmin) / Baverage≤0.3 is calculated, and the receiving coil has a good energy receiving capability in the uniform area.

[0073] The beneficial effect of the above technical solution is: in order to solve the problem of alignment deviation that may occur when the user uses the charger and the neurostimulator for coaxial and cocentric alignment, multiple factors such as the size of the receiving coil, the weight of the charger, the fault tolerance offset and the size of the skull are comprehensively considered. By reasonably setting the size of the transmitting coil 1, the area of ​​the uniform zone of the transmitting coil 1 is expanded, that is, the fault tolerance range is expanded, so that even if there is a certain alignment deviation, the charger can effectively power the neurostimulator, greatly improving the charging efficiency.

[0074] Furthermore, by maintaining the area ratio of the transmitting coil 1 to the receiving coil within a range of greater than or equal to 8 and less than or equal to 20, it is possible to have a uniform area of ​​the transmitting coil 1 with a larger area, that is, a certain fault tolerance rate, to ensure charging efficiency, and to avoid the adverse effects caused by an area ratio that is too large or too small. For example: if the area ratio of the transmitting coil 1 to the receiving coil is too large, the weight and volume of the transmitting coil 1 will increase, reducing the user's comfort; if the area ratio of the transmitting coil 1 to the receiving coil is too small, the preset fault tolerance offset of the charger will be too small, reducing the user experience.

[0075] Furthermore, the radius of the uniform area of ​​the transmitting coil 1 is set to not exceed the sum of the radius of the receiving coil and the preset fault tolerance offset, ensuring that the receiving coil can be completely within the uniform area of ​​the transmitting coil 1 even in the presence of alignment deviation, thereby ensuring the stability and safety of charging.

[0076] The circuit board 2 of the utility model is connected to the transmitting coil 1, and can accurately control the working parameters of the transmitting coil 1, such as current, frequency, etc., so as to achieve accurate management of the charging process and improve the safety and stability of charging.

[0077] In the embodiments of the present specification, the charger is also provided with a charging port connected to an external power source, and the charging port is connected to the transmitting coil, so that only a circuit board and a transmitting coil can be arranged inside the charger, thereby reducing the number of internal components of the charger, thereby improving the convenience of arranging the internal components of the charger, and also realizing a miniaturized charger.

[0078] In some other embodiments of the present specification, a power supply is further provided inside the charger, and the power supply may be a rechargeable battery. The charger also provides a charging port for delivering electrical energy to the power supply, so that the charger can be equivalent to a "mobile power supply" for the stimulator, wherein the energy storage capacity of the power supply can at least fully charge the battery inside the stimulator once, so that when charging the stimulator, the charger can be prevented from being connected to an external power supply, thereby limiting the use environment of the charger to a certain extent (i.e., it can only be charged in a place with a power supply), expanding the charging scenarios of the stimulator, and improving the user experience.

[0079] Furthermore, the circuit board may be a flexible circuit board to match the internal structure of the charger, thereby reducing the size of the charger.

[0080] In the embodiment of this specification, the orthographic projection of the transmitting coil 1 and the orthographic projection of the circuit board 2 may not overlap. Figure 5 The circuit board 2 is arranged on the side of the transmitting coil 1, at least not blocking the side of the transmitting coil 1 facing the receiving coil, so as to avoid the influence of the circuit board on the transmitting coil 1 causing magnetic field distortion and signal interference.

[0081] In some optional embodiments, in order to comply with a miniaturized and lightweight design, the shape of the circuit board 2 can be adapted to the remaining available space inside the charger.

[0082] Components for controlling the operation of the charger, such as control chips and capacitors, are arranged on the circuit board 2. The plane where the circuit board is located is substantially consistent with the plane where the transmitting coil is located, so that the circuit board has a first side facing the stimulator and a second side facing away from the stimulator. The components on the circuit board can be arranged on the second side. In this way, during the charging process, the charger will be close to the stimulator, that is, the first side of the circuit board will be closer to the stimulator. Therefore, the components are arranged on the second side facing away from the stimulator, so that the heat energy generated by the components during operation can be quickly released to the outside through the charger shell, thereby improving the heat dissipation effect of the charger. Furthermore, the shell of the charger facing away from the stimulator can be made of a material that is easy to dissipate heat or be provided with a corresponding heat dissipation structure, such as a heat dissipation hole.

[0083] The magnetic isolation sheet 3 of the utility model is arranged on the side of the transmitting coil 1 facing away from the receiving coil, that is, the outer arc surface of the transmitting coil 1, and the magnetic isolation sheet 3 has a curved surface structure matching the arc of the transmitting coil 1. When used, the orthographic projection of the magnetic isolation sheet 3 is circular or elliptical, and the heat isolation sheet 3 can be made of ferrite material or the like.

[0084] The beneficial effect of the above technical solution is as follows: a magnetic shielding sheet 3 is arranged on the outer arc surface of the transmitting coil 1, which can shield the magnetic field outside the outer arc surface of the transmitting coil 1 when the transmitting coil 1 is working, and prevent the transmitting coil 1 from generating a magnetic field in the direction of the outer arc surface, that is, all the magnetic fields generated by the transmitting coil 1 are directed to the inner arc surface of the transmitting coil 1, that is, in the direction of the receiving coil, thereby improving the magnetic field strength of the neurostimulator and further improving the charging efficiency.

[0085] The magnetic isolation sheet 3 , the circuit board 2 and the transmitting coil 1 of the utility model are arranged in a housing 4 , and the housing 4 has a curved surface structure matching the arc shape of the transmitting coil 1 .

[0086] refer to Figure 5 The shell 4 includes a first accommodation space for accommodating the transmitting coil 1 and a second accommodation space for accommodating the circuit board 2. The first accommodation space is at least adapted to the transmitting coil 1, and the second accommodation space is at least adapted to the circuit board 2. Further, the transmitting coil 1 can be set at the edge of the internal space of the shell 4, that is, the first accommodation space is set at the edge of the shell 4, so that the remaining space inside the shell 4 is the second accommodation space. In order to achieve the miniaturization effect of the charger and better adapt to the shape of the user's skull, it is necessary to efficiently utilize the second accommodation space. Therefore, the second accommodation space can be set to an L-shape, and then an L-shaped circuit board can be set to match it. For the specific structure, please refer to Figure 2 .

[0087] When in use, the housing 4 includes an upper cover 41 and a lower cover 42 that are mutually engaged. The upper cover 41 has a curved surface structure that matches the arc of the magnetic isolation sheet 3, and is disposed on the side of the magnetic isolation sheet 3 that faces away from the transmitting coil 1, and is connected to the magnetic isolation sheet 3 through the second fixing glue 52; the lower cover 42 has a curved surface structure that matches the arc of the user's skull or the transmitting coil 1, and is disposed on the side of the transmitting coil 1 that faces the receiving coil, and is connected to the transmitting coil 1 through the first fixing glue 51.

[0088] The curved surface setting of the upper cover 41 and the lower cover 42 makes the overall appearance of the charger a curved design, and the interior is also a curved space, so that it can adapt to the user's skull and the internal transmitting coil, so that the flexible circuit board can be adapted to the curved space.

[0089] In actual application, the neurostimulator implanted in the brain may form a protrusion on the top of the brain that is consistent with the shape of the neurostimulator. The protrusion has a positioning structure. Therefore, a groove 421 can be provided on the lower cover 42, and a matching structure that matches the positioning structure is provided on the groove 421. The groove 421 has a curved surface structure that matches the arc of the neurostimulator. In this way, when charging and aligning, the protrusion can be directly inserted into the groove. The positioning structure and the matching structure cooperate to achieve rapid positioning of the charger, thereby improving the efficiency of alignment. The forms of the positioning structure and the matching structure are not limited.

[0090] In some embodiments of the present specification, the orthographic projection of the geometric center of the groove 421 overlaps with the orthographic projection of the geometric center of the transmitting coil 1 , which facilitates rapid determination of the position of the transmitting coil 1 .

[0091] Of course, in some other embodiments, the position of the transmitting coil 1 in the charger can correspond to the position of the receiving coil in the stimulator, that is, when assembling the internal structure of the charger, the outer shell of the charger can be determined first, and then the position of the stimulator implanted in the skull can be simulated. When the outer shell of the charger is completely adapted to the skull, the projection of the receiving coil in the stimulator in the charger can be determined, and then the position of the transmitting coil in the charger can be adjusted according to the projection.

[0092] In some preferred embodiments, in order to ensure better charging efficiency, the thickness of the lower cover 42 is set to be less than or equal to 2 mm, which can reduce the impact of the charger shell on the electromagnetic field generated by the transmitting coil, and also allow the transmitting coil and the receiving coil to be sufficiently close.

[0093] The beneficial effects of the above technical solution are as follows: the shell 4 is set to a curved surface structure that matches the arc shape of the transmitting coil 1, which not only enhances the stability of the overall structure, but also can make full use of the internal space of the shell 4 to accommodate the magnetic isolation sheet 3, the circuit board 2 and the transmitting coil 1, forming a compact and complete charger as a whole, thereby minimizing the volume and weight of the charger, which not only improves the convenience of use of the charger, but also can maximize the area and weight of the transmitting coil 1 within a leisurely space and weight.

[0094] Furthermore, the use of a transmitting coil 1 adapted to the curvature of the human skull can not only improve the charging efficiency, but also increase the user's comfort, so that the charger can better adapt to the head contour during use and reduce discomfort and pressure.

[0095] Furthermore, the housing 4 is designed with upper and lower covers that are mutually engaged, making the assembly and disassembly of the charger more convenient. The upper cover 41 and the magnetic isolation sheet 3, and the lower cover 42 and the transmitting coil 1 are connected by fixing glue, respectively, to ensure the stable connection between the components.

[0096] Furthermore, in view of the protrusion that may be formed on the top of the brain by the neurostimulator, the utility model designs a groove 421 on the lower cover 42, so that the charger can better adapt to the shape of the brain implanted with the neurostimulator, ensuring a close fit between the transmitting coil 1 and the receiving coil, thereby further improving the charging efficiency. In addition, the geometric center of the groove 421 overlaps with the geometric center of the transmitting coil 1, ensuring the alignment accuracy during the charging process and optimizing the charging effect.

[0097] Furthermore, under the premise of ensuring structural strength and stability, the thickness of the lower cover 42 is controlled within a range of less than or equal to 2 mm, which not only reduces the overall weight of the charger and reduces the pressure of the charger on the head, but also reduces the distance between the charger and the head, which helps to improve the transmission efficiency of the magnetic field and thus improve the charging performance.

[0098] In summary, this technical solution improves the stability, convenience and charging efficiency of the charger by optimizing the shell structure and design, providing users with a more comfortable and efficient charging experience. At the same time, this technical solution also demonstrates its innovation and practicality in medical equipment design, providing a strong guarantee for the long-term use of implantable devices such as neurostimulators.

[0099] The utility model can also provide a charging system comprising an implantable device and the above charger, wherein the implantable device is used to be implanted into the skull of a user; and the charger is used to charge the implantable device.

[0100] In some embodiments of the present specification, a control module may be further provided inside the charger, and the control module is configured to communicate with the implanted device to send program control information to the implanted device and / or obtain physiological signals of the user collected by the implanted device.

[0101] Although the embodiments of the utility model have been shown and described above, it can be understood that the above embodiments are exemplary and cannot be understood as limitations on the utility model. Ordinary technicians in the field can change, modify, replace and modify the above embodiments within the scope of the utility model without departing from the principles and purpose of the utility model. All of these changes should fall within the scope of protection of the claims of the utility model.

Claims

1. A charger, characterized in that: Used to charge an implantable device, the implantable device is used to be implanted in the user's skull, the implantable device includes a receiving coil, and the charger includes: A transmitting coil (1), the transmitting coil (1) is used to couple with the receiving coil, at least a part of the transmitting coil (1) is arc-shaped, and the arc is at least adapted to the skull of the user.

2. The charger according to claim 1, characterized in that: The transmitting coil (1) comprises at least one layer of a planar structure formed by winding a conducting wire, and the planar structure is arranged in an arc surface.

3. The charger according to claim 1, characterized in that: The length of the arc or chord of the maximum cross section of the transmitting coil (1) is greater than or equal to 80 mm, and the radius of the maximum cross section of the transmitting coil (1) is greater than or equal to 60 mm and less than or equal to 100 mm.

4. The charger according to claim 1, characterized in that: The radius of the uniform area of ​​the transmitting coil (1) does not exceed the sum of the radius of the receiving coil and a preset error tolerance offset.

5. The charger according to claim 1, characterized in that: The ratio of the maximum value of the field intensity difference in the uniform area of ​​the transmitting coil (1) to the average value of the field intensity does not exceed 0.

3.

6. The charger according to claim 1, characterized in that: The ratio of the area of ​​the transmitting coil (1) to the area of ​​the receiving coil is in the range of 8-20.

7. The charger according to claim 1, characterized in that: The orthographic projection shape of the transmitting coil (1) is circular or elliptical, and the length of the arc or chord of the maximum cross section of the transmitting coil (1) is less than or equal to 160 mm.

8. The charger according to claim 1, characterized in that: Also includes: A magnetic isolation sheet (3), the magnetic isolation sheet (3) being arranged on a side of the transmitting coil (1) facing away from the receiving coil, the magnetic isolation sheet (3) having a curved surface structure matching the arc shape of the transmitting coil (1).

9. The charger according to claim 1, characterized in that: It also includes a housing (4) and a circuit board (2); The housing (4) comprises a first accommodation space for accommodating the transmitting coil (1) and a second accommodation space for accommodating the circuit board (2); The first accommodating space is at least adapted to the transmitting coil (1); The orthographic projection of the transmitting coil (1) and the orthographic projection of the circuit board (2) do not overlap.

10. The charger according to claim 9, characterized in that: The circuit board (2) is a flexible circuit board.

11. The charger according to claim 9, characterized in that: The housing (4) comprises: Upper cover (41); A lower cover (42), the lower cover (42) being snap-connected with the upper cover (41), the lower cover (42) being arranged on a side of the transmitting coil (1) facing the receiving coil, and the lower cover (42) having a curved surface structure matching the skull of the user.

12. The charger according to claim 11, characterized in that: The lower cover (42) has a groove (421), the orthographic projection of the geometric center of the groove (421) overlaps with the orthographic projection of the geometric center of the transmitting coil (1), and the groove (421) matches the implantable device.

13. The charger according to claim 11, characterized in that: The thickness of the lower cover (42) is less than or equal to 2 mm.

14. A charging system, characterized in that: The charging system comprises: An implantable device, the implantable device is used to be implanted in the skull of a user; The charger according to any one of claims 1 to 13, wherein the charger is used to charge the implantable device.

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