CN118543035A - External program controlled charging device - Google Patents
External program controlled charging device Download PDFInfo
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- CN118543035A CN118543035A CN202411008824.3A CN202411008824A CN118543035A CN 118543035 A CN118543035 A CN 118543035A CN 202411008824 A CN202411008824 A CN 202411008824A CN 118543035 A CN118543035 A CN 118543035A
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- 239000002184 metal Substances 0.000 claims description 19
- 238000000338 in vitro Methods 0.000 claims description 17
- 230000005404 monopole Effects 0.000 claims description 4
- 238000004891 communication Methods 0.000 abstract description 22
- 230000005855 radiation Effects 0.000 abstract description 9
- 238000003780 insertion Methods 0.000 description 20
- 230000037431 insertion Effects 0.000 description 20
- 238000010586 diagram Methods 0.000 description 12
- 238000001727 in vivo Methods 0.000 description 9
- 230000000694 effects Effects 0.000 description 5
- 238000005516 engineering process Methods 0.000 description 3
- 230000006872 improvement Effects 0.000 description 3
- 230000008878 coupling Effects 0.000 description 2
- 238000010168 coupling process Methods 0.000 description 2
- 238000005859 coupling reaction Methods 0.000 description 2
- 230000007423 decrease Effects 0.000 description 2
- 230000005672 electromagnetic field Effects 0.000 description 2
- 230000003993 interaction Effects 0.000 description 2
- 238000000034 method Methods 0.000 description 2
- 230000004048 modification Effects 0.000 description 2
- 238000012986 modification Methods 0.000 description 2
- 210000005036 nerve Anatomy 0.000 description 2
- 238000010146 3D printing Methods 0.000 description 1
- 230000009286 beneficial effect Effects 0.000 description 1
- 230000005540 biological transmission Effects 0.000 description 1
- 210000004556 brain Anatomy 0.000 description 1
- 230000005684 electric field Effects 0.000 description 1
- 230000001788 irregular Effects 0.000 description 1
- 210000000278 spinal cord Anatomy 0.000 description 1
- 230000001515 vagal effect Effects 0.000 description 1
- 238000004804 winding Methods 0.000 description 1
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- Y—GENERAL TAGGING OF NEW TECHNOLOGICAL DEVELOPMENTS; GENERAL TAGGING OF CROSS-SECTIONAL TECHNOLOGIES SPANNING OVER SEVERAL SECTIONS OF THE IPC; TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
- Y02—TECHNOLOGIES OR APPLICATIONS FOR MITIGATION OR ADAPTATION AGAINST CLIMATE CHANGE
- Y02E—REDUCTION OF GREENHOUSE GAS [GHG] EMISSIONS, RELATED TO ENERGY GENERATION, TRANSMISSION OR DISTRIBUTION
- Y02E60/00—Enabling technologies; Technologies with a potential or indirect contribution to GHG emissions mitigation
- Y02E60/10—Energy storage using batteries
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Abstract
The invention relates to the field of medical equipment, in particular to an external program-controlled charging device, wherein a battery and a charging coil are axially staggered, when the battery is used as an antenna radiator, the interference of the charging coil on communication electromagnetic waves can be reduced, the whole structure is more compact, the miniaturization is facilitated, a first gain structure and a second gain structure are further arranged, the directional radiation capacity of the battery is improved, and the communication performance of the external program-controlled charging device and the internal implanted medical equipment is enhanced.
Description
Technical Field
The invention relates to the field of medical equipment, in particular to an in-vitro program-controlled charging device.
Background
The in-vitro program-controlled charging device is a medical device for charging and communicating with in-vivo implantable medical equipment. Implantable medical devices include neurostimulators, including deep brain electrical stimulators, implantable spinal cord electrical stimulators, implantable sacral nerve electrical stimulators, implantable vagal nerve electrical stimulators, and the like.
The in-vitro program-controlled charging device is used for carrying out data interaction with the implanted medical equipment in a wireless communication mode, and the antenna is one of key components in a wireless communication system. The in-vitro program-controlled charging device can also charge the in-vivo implantable medical equipment in a near-field coupling mode, and the charging coil is one of key components in a charging system. With miniaturization of the external program-controlled charging device, the distance between the antenna and the battery and the charging coil is inevitably reduced, so that the interference of the battery and the charging coil on the antenna is increased, the performance of the antenna is reduced, and the communication quality between the external program-controlled charging device and the implanted medical equipment is poor.
Disclosure of Invention
In view of the above, the invention provides an in-vitro program-controlled charging device, which solves the problem of poor communication quality between a miniaturized in-vitro program-controlled charging device and implanted medical equipment.
The invention provides an in vitro program-controlled charging device, comprising:
A circuit board;
the battery comprises a first end part, a second end part and a side part, wherein the first end part and the second end part are arranged between the first end part and the second end part in the first direction, the battery is provided with a grounding connection part and a feeding connection part at intervals in the first direction, the grounding connection part and the feeding connection part are respectively connected with the circuit board, the circuit board feeds radio frequency signals to the battery, and the battery is used as an antenna radiator;
the charging coil is arranged in a staggered manner with the battery in the axial direction; and
The first gain structure and the second gain structure are respectively used for being coupled with the battery, the first gain structure is arranged at intervals with the first end part or the second end part, and the second gain structure is arranged at intervals with the side part.
Preferably, a distance between the ground connection portion and the feed connection portion in the first direction is L 1,0.1λ1≤L1≤0.3λ1;
the distance between the middle parts of the grounding connection part and the feed connection part and the first gain structure is L 2,0.1λ1≤L2≤0.25λ1,L2＞1/2L1, and lambda 1 is the wavelength of the center frequency in the resonance frequency range of the battery.
Preferably, the circuit board is provided with a grounding metal layer and a connecting edge, and the grounding metal layer is connected with the grounding connecting part;
The ground metal layer is provided with a ground stub extending out of the connecting edge and spaced from the first end or the second end, and the first gain structure includes the ground stub.
Preferably, the battery is disposed at intervals from the connecting side along the first direction, the distance between the battery and the connecting side is 0.01λ 1-0.1λ1, and λ 1 is the wavelength of the center frequency in the resonance frequency range of the battery.
Preferably, the grounding branch extends out of the connecting edge along the plane of the circuit board, the extending length of the grounding branch is greater than or equal to the length of the battery in a second direction, and the second direction is parallel to the extending direction of the grounding branch.
Preferably, the maximum length of the cross section of the battery in the direction perpendicular to the first direction is L 3,5mm≤L3 < 25mm.
Preferably, the battery charger further comprises a shell, wherein the circuit board, the charging coil and the battery are arranged in the shell, and the charging coil is axially overlapped with the circuit board;
The housing includes a lower case for contacting a human body, the battery first direction is parallel to a bottom surface of the lower case, and the second gain structure is disposed at an inner surface of the lower case.
Preferably, the vertical distance between the second gain structure and the battery is L 4,1/120λ2≤L4≤1/10λ2, and the λ 2 is a wavelength of a center frequency in a resonance frequency range of the second gain structure.
Preferably, the resonant frequency range of the second gain structure is within the resonant frequency range of the battery, the second gain structure is provided with a plurality of second gain structures, the plurality of second gain structures are arranged at intervals in the first direction perpendicular to the battery, and the plurality of second gain structures are the same as the vertical distance of the battery.
Preferably, the second gain structure is a monopole, dipole or loop antenna structure.
The in-vitro program-controlled charging device provided by the invention has the beneficial effects that:
The battery and the charging coil are axially staggered, the circuit board feeds radio frequency signals to the battery, when the battery is used as an antenna radiator, the influence of the charging coil on communication electromagnetic waves is reduced, the structure is more compact, the miniaturization is facilitated, the invention also provides a first gain structure and a second gain structure, the first gain structure and the second gain structure can be coupled with the battery, so that the energy coupled with the battery is radiated outwards, the first gain structure realizes electromagnetic field superposition, improves the directional radiation capability of the battery, and the second gain structure is mainly coupled with electromagnetic wave energy radiated by the battery in the direction of the second gain structure, so that electromagnetic waves are secondarily radiated to the in-vivo implanted medical equipment, and the communication performance of the in-vitro program-controlled charging device and the in-vivo implanted medical equipment is improved.
Drawings
The above and other objects, features and advantages of the present invention will become more apparent from the following description of embodiments of the present invention with reference to the accompanying drawings, in which:
Fig. 1 is a schematic diagram of an in vitro program-controlled charging device according to an embodiment of the invention.
Fig. 2 is an exploded view of an in vitro programmable charging device according to an embodiment of the invention.
FIG. 3 is a schematic cross-sectional view of an in vitro programmable charging device taken along line a-a in a top view in accordance with an embodiment of the invention.
FIG. 4 is a schematic cross-sectional view of an in vitro programmable charging device along line b-b in a side view in accordance with an embodiment of the invention.
Fig. 5 is a schematic diagram of three structures and a battery of a second gain structure of an in vitro program-controlled charging device according to an embodiment of the invention.
FIG. 6 is a graph showing the reflection coefficient versus frequency for different cell diameters in an embodiment of the invention.
Fig. 7 is a graph showing the insertion loss versus frequency for different cell diameters in an embodiment of the present invention.
Fig. 8 is a schematic diagram of gain in a direction away from a human body for different battery diameters in an embodiment of the invention.
Fig. 9 is a schematic diagram showing the relationship between the insertion loss and the frequency of the first gain structure according to the embodiment of the present invention.
Fig. 10 is a schematic diagram showing the relationship between the insertion loss and the frequency at different vertical distances between the second gain structure and the battery according to the embodiment of the present invention.
FIG. 11 is a graph showing the relationship between the insertion loss and the frequency for different numbers of second gain structures according to an embodiment of the present invention.
FIG. 12 is a graph showing the relationship between reflection coefficient and frequency when the second gain structure is configured with three gain structures according to an embodiment of the present invention.
Fig. 13 is a schematic diagram of gains in a direction facing away from a human body when the second gain structure is configured to be three in the embodiment of the present invention.
Reference numerals illustrate:
100. an in-vitro program-controlled charging device; 200. a human body;
1. A housing; 1-1, an upper shell; 1-2, a lower shell;
2. A circuit board; 2-1, a communication module; 2-2, a feed connection; 2-3, a grounding metal layer; 2-4, grounding branches; 2-5, a grounding connection part; 2-6, connecting edges;
3. A charging coil;
4. a battery; 4-1, a first end; 4-2, a second end;
5-1, 5-2, 5-3, a second gain structure.
Detailed Description
The present invention is described below based on examples, but the present invention is not limited to only these examples. In the following detailed description of the present invention, certain specific details are set forth in detail. The present invention will be fully understood by those skilled in the art without the details described herein. Well-known methods, procedures, flows, components and circuits have not been described in detail so as not to obscure the nature of the invention.
Moreover, those of ordinary skill in the art will appreciate that the drawings are provided herein for illustrative purposes and that the drawings are not necessarily drawn to scale. Unless the context clearly requires otherwise, the words "comprise," "comprising," and the like throughout the application are to be construed as including but not being exclusive or exhaustive; that is, it is the meaning of "including but not limited to". In the description of the present invention, it should be understood that the terms "first," "second," and the like are used for descriptive purposes only and are not to be construed as indicating or implying relative importance. Furthermore, in the description of the present invention, unless otherwise indicated, the meaning of "a plurality" is two or more.
Fig. 1 is a schematic diagram of an in vitro program-controlled charging device 100 according to an embodiment of the invention placed on a human body 200. Fig. 2 is an exploded view of the in vitro programmable charging device 100 according to an embodiment of the invention. Fig. 3 is a schematic cross-sectional view of an in vitro programmable charging device 100 along a-a in a top view in accordance with an embodiment of the invention. Fig. 4 is a schematic cross-sectional view of the external program control charging device 100 along b-b in a side view in accordance with an embodiment of the present invention.
The invention provides an in-vitro program-controlled charging device, which is shown in figure 1, is placed on the chest and can program and charge implanted medical equipment implanted on the chest. As shown in fig. 2-4, the in-vitro program-controlled charging device comprises a housing 1, wherein the housing 1 comprises an upper housing 1-1 and a lower housing 1-2, and the lower housing 1-2 is used for contacting with the skin of a human body 200 or placing a clothing surface. The casing 1 is internally provided with a circuit board 2, a charging coil 3 and a battery 4, the charging coil 3 and the battery 4 are respectively and electrically connected with the circuit board 2, the battery 4 provides working electric energy for the external program-controlled charging device 100, and the charging coil 3 is used for charging implanted medical equipment in the human body 200. The charging coil 3 is axially oriented toward the circuit board 2 such that the charging coil 3 is disposed overlapping the circuit board 2, preferably, the edge of the charging coil 3 does not exceed the edge of the circuit board 2. The circuit board 2 is provided with a connecting edge 2-6, the battery 4 is arranged outside the connecting edge 2-6 of the circuit board 2, preferably, the charging coil 3 does not exceed the connecting edge 2-6, the battery 4 and the circuit board 2 are arranged at intervals, and the charging coil 3 and the battery 4 are arranged in a dislocation mode in the axial direction. When the battery 4 is used as an antenna radiator, the communication influence of the charging coil 3 on the battery 4 can be reduced.
The battery 4 includes a first end 4-1, a second end 4-2, and a side portion disposed between the first end 4-1 and the second end 4-2 in a first direction, which may be a longitudinal direction of the battery 4 or a width or thickness direction of the battery 4, and when the battery 4 has a columnar structure, the first direction is preferably the longitudinal direction of the battery 4, and the second direction is preferably the width direction of the battery 4. In the present invention, the battery 4 is a non-button battery, the first direction is the X direction in the rectangular coordinate axis shown in fig. 4, and the second direction is the Y direction.
The battery 4 is arranged at intervals from the connecting sides 2-6 along the first direction, the distance between the battery 4 and the connecting sides 2-6 is 0.01λ 1-0.1λ1, and λ 1 is the wavelength of the center frequency in the resonance frequency range of the battery 4, wherein the resonance frequency range refers to a frequency band with the reflection coefficient below-10 dB between 1.7GHz and 3.3 GHz. The circuit board 2 is provided with a ground metal layer 2-3 and a communication module 2-1, and the battery 4 is provided with a feeding connection portion 2-2 and a ground connection portion 2-5 at intervals in a first direction, preferably, the feeding connection portion 2-2 and the ground connection portion 2-5 are located at one side of the battery 4 facing the connection side, the ground connection portion 2-5 is connected with the ground metal layer 2-3, and the feeding connection portion 2-2 is connected with the communication module 2-1. In the invention, the battery 4 is provided with a metal surface, the feed connection part 2-2 and the ground connection part 2-5 are arranged on the metal surface, the circuit board 2 feeds radio frequency signals to the metal surface of the battery, and the battery 4 serves as an antenna radiator.
In the case 1, the direction toward the lower case 1-2 may be set to be downward, the charging coil 3 is disposed below the circuit board 2, and the battery 4 is disposed on the side of the circuit board 2. Preferably, the battery 4 is parallel to the bottom surface of the lower case 1-2 in the first direction, ensuring communication with the implanted medical device in the body. The length of the battery in the first direction is at least 0.1λ 1, and the distance between the feeding connection part 2-2 and the grounding connection part 2-5 in the first direction of the battery 4 is L 1,0.1λ1≤L1≤0.3λ1,L1, which is too large or too small, resulting in a decrease in radiation efficiency, and λ 1 is the wavelength of the center frequency in the resonance frequency range of the battery 4. Wherein the distance between the feed connection part 2-2 and the ground connection part 2-5 in the first direction is the shortest connecting line distance between the two on the metal surface of the battery 4. The resonance frequency range f 1-f2,f3=(f1+f2)/2,λ1=c /f3,f3 of the battery 4 is the center frequency, and c is the speed at which the electromagnetic wave propagates in air.
In the present invention, the external program-controlled charging device 100 is further provided with a first gain structure for superposing the amplitude of the electromagnetic wave radiated by the battery 4, the first gain structure is used for coupling with the battery 4, and the first gain structure is arranged at a distance from the first end 4-1 or the second end 4-2. As shown in fig. 3-4, a part of the circuit board 2 extends from one end of the connecting edge 2-6 along the plane of the circuit board, the grounding metal layer 2-3 extends onto the part of the circuit board 2 extending from the connecting edge 2-6, so that the part of the grounding metal layer 2-3 extends out of the connecting edge 2-6 to form a grounding branch 2-4 spaced from the first end 4-1, and the grounding branch 2-4 is in a first gain structure. In other embodiments, the circuit board 2 may extend from the other end of the connecting edge 2-6, and the grounding branch 2-4 and the second end 4-2 are spaced, or the grounding connection portion 2-5 and the feeding connection portion 2-2 are interchanged in position, so as to adjust the positional relationship among the feeding connection portion 2-2, the grounding branch 2-4 and the grounding connection portion 2-5.
The length of the grounding branch 2-4 extending from the connecting side 2-6 is equal to or longer than the length of the battery 4 in the second direction (Y direction), preferably, the second direction is perpendicular to the first direction and parallel to the extending direction of the grounding branch 2-4. If the battery 4 is in a cylindrical structure, the extending length of the grounding branch 2-4 is larger than the diameter of the battery 4, so that the radiation power of the battery 4 is improved. In the invention, the grounding connection part 2-5 of the battery 4 is arranged on one side of the battery 4 facing the connection edge 2-6, but not on the grounding branch 2-4, so that a first gain structure overlapped with electromagnetic waves radiated by the battery 4 is formed at the end part of the first direction, the grounding branch 2-4 is coupled with the battery 4, and then coupled energy is radiated outwards, thereby realizing electromagnetic field overlapping of the grounding branch 2-4 and the battery 4 and improving the directional radiation capability of the battery 4. The distance between the feeding connection part 2-2 and the grounding connection part 2-5 in the first direction of the battery 4 is L 1,0.1λ1≤L1≤0.3λ1, the distance between the middle parts of the feeding connection part 2-2 and the grounding connection part 2-5 and the first gain structure is L 2,0.1λ1≤L2≤0.25λ1,L2＞1/2L1, the first gain structure and the battery 4 are arranged at intervals, the first gain structure radiates energy coupled with the battery 4, electromagnetic waves radiated by the first gain structure are overlapped with electromagnetic waves radiated by the battery 4, and the electromagnetic wave intensity is improved. L 2＜0.1λ1, or L 2＞0.25λ1, the gain effect becomes poor, and λ 1 is the wavelength of the center frequency in the resonance frequency range of the battery 4. It should be noted that, as will be understood by those skilled in the art, the phase of the electromagnetic wave radiated by the first gain structure is approximately the same as that of the electromagnetic wave radiated by the battery 4, and may have a phase difference within a certain range, for example ±15 degrees, so as to ensure that the electromagnetic waves (magnetic field and electric field) are at least partially overlapped, and still have the effect of improving the radiation efficiency of the battery 4.
The maximum length of the cross section of the battery 4 in the vertical first direction is L 3,5mm≤L3 < 25mm, and when the maximum length of the cross section of the battery 4 is less than 5mm, the battery 4 is too thin, and the impedance bandwidth is narrow and is more than or equal to 25 mm. The cross-sectional shape of the battery 4 may be circular, square or rectangular, and the maximum length thereof may be a diameter if circular, a length of a side length of a long side or a diagonal line if rectangular, and two points of a straight line which are furthest apart on the cross-sectional profile if irregular.
The in-vitro program-controlled charging device 100 is further provided with second gain structures 5-1, 5-2 and 5-3 with resonance frequency ranges within the resonance frequency range of the battery 4, wherein the second gain structures 5-1, 5-2 and 5-3 are arranged on the side part of the battery 4 and are arranged at intervals with the side part of the battery 4. In the present invention, the second gain structures 5-1, 5-2, 5-3 are provided on the inner surface of the lower case 1-2, i.e., the second gain structures 5-1, 5-2, 5-3 are located below the battery 4. The second gain structures 5-1, 5-2, 5-3 mainly couple electromagnetic wave energy radiated by the battery 4 in a direction toward the second gain structures 5-1, 5-2, 5-3, thereby secondarily radiating electromagnetic waves to the in-vivo implantable medical device, and the second gain structures 5-1, 5-2, 5-3 improve communication performance of the in-vitro program-controlled charging device 100 and the in-vivo implantable medical device. In the invention, the second gain structures 5-1, 5-2 and 5-3 and the charging coil 3 are arranged on the same side of the circuit board 2, and when the second gain structures 5-1, 5-2 and 5-3 are close to the implanted medical equipment, the circuit board 2 cannot be arranged between the in-vivo coil and the in-vitro charging coil 3, and meanwhile, the communication and charging performance of the in-vitro program-controlled charging device 100 are ensured.
One or more second gain structures 5-1, 5-2, 5-3 may be provided, the length direction of the second gain structures 5-1, 5-2, 5-3 being parallel to the first direction of the battery 4. When a plurality of second gain structures 5-1, 5-2, 5-3 are provided, the lengths of the metal bodies among the second gain structures 5-1, 5-2, 5-3 are the same, the metal bodies are arranged at intervals in the first direction perpendicular to the battery 4, and the vertical distances between the plurality of second gain structures 5-1, 5-2, 5-3 and the battery 4 are the same, as shown in fig. 3, the vertical distance is denoted by L4. Preferably, the second gain structures 5-1, 5-2, 5-3 are at equal vertical distance from the battery 4, and 1/120λ 2≤L4≤1/10λ2,λ2 is the wavelength of the center frequency in the resonance frequency range of said second gain structures 5-1, 5-2, 5-3. In the present invention, the second gain structures 5-1, 5-2, 5-3 are located below the battery 4 in the housing 1, and the battery 4 is located at the side of the charging coil 3, and the plurality of second gain structures 5-1, 5-2, 5-3 are arranged below the battery 4 toward the side where the axis of the charging coil 3 is located, or when the battery 4 does not correspond to the center of the bottom surface of the lower housing 1-2, the plurality of second gain structures 5-1, 5-2, 5-3 are arranged toward the side where the center of the bottom surface of the lower housing 1-2, so that the distribution range of the plurality of second gain structures 5-1, 5-2, 5-3 is large, and the signal intensity of the external program-controlled charging device 100 to the in-vivo implantable medical device is further improved.
Fig. 5 is a schematic diagram of three structures of a second gain structure of the in vitro programmable charging device 100 and the battery 4 according to an embodiment of the invention.
As shown in fig. 5, in C1, the second gain structure 5-1 is a dipole structure, the length direction of the dipole structure is parallel to the first direction of the battery 4, the metal bodies of the three dipole structures have the same length and are arranged at intervals, and the dipole structure below the battery 4 is partially shielded. The second gain structure 5-2 in C2 is a monopole structure, and the length direction of the monopole structure is parallel to the first direction of the battery 4. The second gain structure 5-3 in C3 is a loop antenna structure, i.e. is formed by winding a metal wire into an approximate square, round, triangle, etc., and in the present invention is illustrated as a rectangle, the length direction of which is parallel to the first direction of the battery 4. The upper case 1-1 and the lower case 1-2 are made of plastic, and the second gain structures 5-1, 5-2, 5-3 are printed on the inner surface of the lower case 1-2 by flexible circuit technology, laser direct structuring technology, 3D printing technology, etc.
FIG. 6 is a graph showing the relationship between reflection coefficient and frequency for different cell diameters according to an embodiment of the present invention. Fig. 7 is a graph showing the relationship between insertion loss and frequency for different cell diameters in an embodiment of the present invention. Fig. 8 is a schematic diagram of gain in a direction away from a human body at different battery diameters in an embodiment of the invention.
In fig. 6-8, the battery 4 of the in-vitro program-controlled charging device 100 is cylindrical, and the first gain structure and the second gain structure 5-1, 5-2, 5-3 are not provided, so that the in-vitro program-controlled charging device 100 is in communication with the in-vivo and external devices. Fig. 6 shows the effect of different diameter cells 4 on the reflection coefficient, curve a corresponding to a cell 4 diameter of 1mm, curve B corresponding to a cell 4 diameter of 5mm, curve C corresponding to a cell 4 diameter of 15mm, and curve D corresponding to a cell 4 diameter of 25mm. It can be seen that there are two concave points on the reflection coefficient curve, and as the diameter of the battery 4 changes from 1mm, 5mm, 15mm to 25mm, the concave points located in the lower frequency band in the figure gradually deepen and then become shallow. When the diameter is not smaller than 5mm, the reflection coefficient of the frequency band between the two concave points is lower than 10dB, namely the impedance bandwidth of-10 dB is greatly expanded; when the diameter is equal to 25mm, the reflection coefficient of the frequency band between the two concave points is higher than 10dB, namely, the impedance bandwidth of-10 dB is narrowed, and when the diameter is larger than 25mm, the impedance bandwidth of the reflection coefficient smaller than-10 dB starts to be reduced. Thus, the maximum length of the cross section of the cell 4 is defined in the present invention as 5 mm.ltoreq.L 3 < 25mm.
As shown in fig. 7, the influence of the batteries 4 with different diameters on the insertion loss between the internal and external devices (the bluetooth communication mode is adopted between the internal implanted medical equipment and the external program-controlled charging device, the working frequency range is 2.4GHz-2.4835 GHz), the curve E corresponds to the diameter of the battery 4 being 1mm, the curve F corresponds to the diameter of the battery 4 being 5mm, the curve G corresponds to the diameter of the battery 4 being 15mm, and the curve H corresponds to the diameter of the battery 4 being 25mm. As the diameter of the battery 4 becomes larger, the value of the insertion loss on the vertical axis between 2.4GHz and 2.4835GHz becomes larger, and the insertion loss (transmission loss) decreases. The diameter of the battery 4 is less than or equal to L 3 and less than 25mm in the working frequency range of 2.4GHz-2.4835GHz, so that the use requirement can be met.
As shown in fig. 1 and 8, the lower casing 1-2 of the in-vitro program-controlled charging device 100 is attached to a human body, and the upper casing 1-1 faces away from the human body. The external program-controlled charging device 100 uses the battery 4 as an antenna radiator, and can communicate with both the implanted medical device in the body and other external devices, such as doctor program-controlled devices. Fig. 8 shows the gain effect of different cell 4 diameters on the side facing away from the human body. Curve I corresponds to a diameter of 1mm for the battery 4, curve J corresponds to a diameter of 5mm for the battery 4, curve K corresponds to a diameter of 15mm for the battery 4, and curve L corresponds to a diameter of 25mm for the battery 4. As the diameter increases, the gain becomes gentle, and a gain drop occurs, and the gain of the battery 4 at a diameter of 5mm < L 3 < 25mm can ensure communication between the in-vitro programmable charging device 100 and the implanted medical device.
Fig. 9 is a schematic diagram showing the relationship between the insertion loss and the frequency of the first gain structure according to the embodiment of the present invention. The cell diameter was chosen to be 15mm.
As shown in fig. 9, M is a plot of insertion loss versus frequency after the first gain structure is set, and G is a plot of insertion loss versus frequency without the first gain structure. The first gain structure is arranged, compared with the first gain structure which is not arranged, the insertion loss value on the vertical axis between 2.4GHz and 2.4835GHz is increased by 1.5dB, and the performance improvement is remarkable.
Fig. 10 is a schematic diagram showing the relationship between the insertion loss and the frequency of the second gain structure and the battery according to the embodiment of the invention. The diameter of the battery is selected to be 15mm, and a first gain structure is added.
As shown in fig. 10, the effect on the insertion loss of providing one second gain structure 5-1 at different distances from the battery 4 without providing the second gain structure 5-1 is shown. The curve M is not provided with the second gain structure 5-1, the curve N is that the vertical distance between the second gain structure 5-1 and the battery 4 is 1/120λ 2, the curve O is that the vertical distance between the second gain structure 5-1 and the battery 4 is 1/20λ 2, and the curve P is that the vertical distance between the second gain structure 5-1 and the battery 4 is 1/10λ 2. The value of the insertion loss on the vertical axis between 2.4GHz-2.4835GHz increases by 1.7dB when the distance is 1/20 lambda 2 compared to when the second gain structure 5-1 is not provided, the insertion loss when the second gain structure 5-1 is at a vertical distance of 1/10 lambda 2 from the battery 4 being close to when the second gain structure 5-1 is not provided. Therefore, the present invention sets the vertical distance between the second gain structure 5-1 and the battery 4 to be L 4,1/120λ2≤L4≤1/10λ2.
FIG. 11 is a graph showing the relationship between the insertion loss and the frequency for different numbers of second gain structures according to an embodiment of the present invention. The diameter of the battery is selected to be 15mm, and a first gain structure is added.
As shown in fig. 11, the curve Q is provided with three second gain structures 5-1, the curve O is provided with one second gain structure 5-1, the vertical distance between the second gain structure 5-1 and the battery 4 is 1/20λ 2, and the curve M is not provided with the second gain structure 5-1. After one or three second gain structures 5-1 are provided, the insertion loss is improved over the insertion loss without the second gain structures 5-1, and the improvement in insertion loss is more pronounced when the second gain structures 5-1 are provided with three than when one is provided at 2.4GHz-2.4835 GHz. Therefore, in the present invention, preferably, the second gain structure 5-1 is arranged in a spacing arrangement of three.
FIG. 12 is a graph showing the relationship between reflection coefficient and frequency when the second gain structure is configured with three gain structures according to an embodiment of the present invention.
As shown in fig. 12, the curve R sets three curves of reflection coefficient and frequency for the second gain structure 5-1, and the vertical distance between the second gain structure 5-1 and the battery 4 is 1/20λ 2. The impedance bandwidth of-10 dB ranges from 1.7GHz to 3.3GHz, and the impedance relative bandwidth of-10 dB is as high as 64%.
Fig. 13 is a schematic diagram of gains in a direction facing away from a human body when the second gain structure is configured to be three in the embodiment of the present invention.
As shown in fig. 13, the curve S is a relationship curve of gain versus frequency when the second gain structure 5-1 is set to three times, and the vertical distance between the second gain structure 5-1 and the battery 4 is 1/20λ 2. According to the impedance bandwidth range of-10 dB of FIG. 12, 1.7GHz-3.3GHz, the gain fluctuates by 4.5dB within the-10 dB impedance bandwidth.
In summary, the battery 4 is used as an antenna radiator, the position relation among the circuit board 2, the charging coil 3 and the battery 4 is adjusted, the influence of the charging coil 3 on the wireless communication performance of the battery 4 is reduced, the structure is more compact, and the miniaturization is facilitated. The first gain structure, namely the second gain structure 5-1, 5-2 and 5-3, of which the radiation electromagnetic wave can be overlapped with the radiation electromagnetic wave of the battery 4 and the resonance frequency range is in the resonance frequency range of the battery 4 is further arranged, the directional radiation capacity of the battery is improved by the first gain structure, the electromagnetic wave energy radiated by the battery in the direction towards the second gain structure 5-1, 5-2 and 5-3 is mainly coupled by the second gain structure 5-1, 5-2 and 5-3, the communication performance of the external program control charging device 100 and the internal implanted medical equipment is improved in the direction of secondarily radiating the electromagnetic wave to the internal implanted medical equipment, and the problem that the communication quality between the antenna and the internal implanted medical equipment is poor due to the fact that the antenna is closer to the battery 4 and the charging coil 3 after the traditional external program control charging device is miniaturized is solved.
The above description is only of the preferred embodiments of the present invention and is not intended to limit the present invention, and various modifications and variations may be made to the present invention by those skilled in the art. Any modification, equivalent replacement, improvement, etc. made within the spirit and principle of the present invention should be included in the protection scope of the present invention.
Unless specifically stated or limited otherwise, the terms "mounted," "connected," "secured" and the like should be construed broadly, as they may be fixed, removable, or integral, for example; either directly or indirectly, through intermediaries, or both, may be in communication with each other or in interaction with each other, unless expressly defined otherwise. The specific meaning of the above terms in the present invention can be understood by those of ordinary skill in the art according to the specific circumstances. Parallel, perpendicular, etc., are not absolute parallel and perpendicular, and may be offset by an angle, such as within 5 degrees or 10 degrees, without affecting function.
Claims (10)
1. An in vitro programmable charging device, comprising:
A circuit board;
The battery comprises a first end part, a second end part and a side part, wherein the first end part and the second end part are arranged between the first end part and the second end part in the first direction, the battery is provided with a grounding connection part and a feeding connection part at intervals in the first direction, the grounding connection part and the feeding connection part are respectively connected with the circuit board, the circuit board feeds radio frequency signals to the battery, and the battery is used as an antenna radiator;
the charging coil is arranged in a staggered manner with the battery in the axial direction; and
The first gain structure and the second gain structure are respectively used for being coupled with the battery, the first gain structure is arranged at intervals with the first end part or the second end part, and the second gain structure is arranged at intervals with the side part.
2. The in-vitro programmable charging device according to claim 1, wherein a spacing between the ground connection and the feed connection in the first direction is L 1,0.1λ1≤L1≤0.3λ1;
the distance between the middle parts of the grounding connection part and the feed connection part and the first gain structure is L 2,0.1λ1≤L2≤0.25λ1,L2＞1/2L1, and lambda 1 is the wavelength of the center frequency in the resonance frequency range of the battery.
3. The in-vitro program-controlled charging device according to claim 2, wherein the circuit board is provided with a grounding metal layer and a connecting edge, and the grounding metal layer is connected with the grounding connecting part;
The ground metal layer is provided with a ground stub extending out of the connecting edge and spaced from the first end or the second end, and the first gain structure includes the ground stub.
4. An in vitro programmable charging device according to claim 3, wherein said battery is spaced from said connecting edge along said first direction by a distance of 0.01λ 1-0.1λ1.
5. The in-vitro programmable charging device of claim 3, wherein the grounding branch extends out of the connecting edge along the plane of the circuit board, and the extending length of the grounding branch is greater than or equal to the length of the battery in the second direction.
6. The in vitro programmable charging device according to claim 1, wherein the maximum length of the cross section of the battery in the direction perpendicular to the first direction is L 3,5mm≤L3 < 25mm.
7. The in-vitro programmable charging device of claim 1, further comprising a housing, wherein the circuit board, the charging coil, and the battery are disposed within the housing, wherein the charging coil is disposed axially overlapping the circuit board;
The housing includes a lower case for contacting a human body, the battery first direction is parallel to a bottom surface of the lower case, and the second gain structure is disposed at an inner surface of the lower case.
8. The in vitro programmable charging device of claim 1, wherein the second gain structure is perpendicular to the battery by a distance L 4,1/120λ2≤L4≤1/10λ2, and wherein λ 2 is a wavelength of a center frequency within a resonant frequency range of the second gain structure.
9. The in-vitro programmable charging device according to claim 1, wherein the resonance frequency range of the second gain structure is within the resonance frequency range of the battery, the second gain structure is provided in plurality, and in the first direction perpendicular to the battery, the plurality of second gain structures are arranged at intervals, and the plurality of second gain structures are the same as the vertical distance of the battery.
10. The in vitro programmable charging device of claim 1, wherein the second gain structure is a monopole, dipole or loop antenna structure.
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| Application Number | Priority Date | Filing Date | Title |
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| CN202411008824.3A CN118543035A (en) | 2024-07-26 | 2024-07-26 | External program controlled charging device |
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| Application Number | Priority Date | Filing Date | Title |
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| CN202411008824.3A CN118543035A (en) | 2024-07-26 | 2024-07-26 | External program controlled charging device |
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Citations (5)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US20050134520A1 (en) * | 2003-12-22 | 2005-06-23 | Prashant Rawat | Radio frequency antenna in a header of an implantable medical device |
| US20060247738A1 (en) * | 2005-04-29 | 2006-11-02 | Medtronic, Inc. | Actively cooled external energy source, external charger, system of transcutaneous energy transfer, system of transcutaneous charging and method therefore |
| CN103732284A (en) * | 2011-03-17 | 2014-04-16 | 布朗大学 | Implantable wireless neural device |
| CN110970725A (en) * | 2019-12-30 | 2020-04-07 | 湖南大学 | Implantable antenna for medical telemetry and implantable medical equipment |
| WO2024023645A1 (en) * | 2022-07-29 | 2024-02-01 | Medtronic, Inc. | Receive coil arrangements for leadless rechargeable epicardial pacemaker |
-
2024
- 2024-07-26 CN CN202411008824.3A patent/CN118543035A/en active Pending
Patent Citations (5)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US20050134520A1 (en) * | 2003-12-22 | 2005-06-23 | Prashant Rawat | Radio frequency antenna in a header of an implantable medical device |
| US20060247738A1 (en) * | 2005-04-29 | 2006-11-02 | Medtronic, Inc. | Actively cooled external energy source, external charger, system of transcutaneous energy transfer, system of transcutaneous charging and method therefore |
| CN103732284A (en) * | 2011-03-17 | 2014-04-16 | 布朗大学 | Implantable wireless neural device |
| CN110970725A (en) * | 2019-12-30 | 2020-04-07 | 湖南大学 | Implantable antenna for medical telemetry and implantable medical equipment |
| WO2024023645A1 (en) * | 2022-07-29 | 2024-02-01 | Medtronic, Inc. | Receive coil arrangements for leadless rechargeable epicardial pacemaker |
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