CN207265741U - Plane enhancement magnetism resonance ejection coil based on capsule endoscope wireless charging - Google Patents
Plane enhancement magnetism resonance ejection coil based on capsule endoscope wireless charging Download PDFInfo
- Publication number
- CN207265741U CN207265741U CN201720781644.8U CN201720781644U CN207265741U CN 207265741 U CN207265741 U CN 207265741U CN 201720781644 U CN201720781644 U CN 201720781644U CN 207265741 U CN207265741 U CN 207265741U
- Authority
- CN
- China
- Prior art keywords
- coil
- resonance
- driving
- capsule endoscope
- magnetic sheet
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Active
Links
Abstract
The utility model discloses the plane enhancement magnetism resonance ejection coil based on capsule endoscope wireless charging in field of medical device, including the power supply of drive circuit input terminal is connected to, the output terminal of drive circuit is connected with driving coil Lt0, drive circuit and driving coil Lt0Between be connected with driving resonant capacitance Ct0, it is characterised in that driving coil Lt0It is fixed on around snail shape is set as on the first magnetic sheet, driving coil Lt0It is correspondingly arranged on resonance device on one side, resonance device bag is by resonance coil Lt1Both ends are connected into the first resonant capacitance Ct in circuit1, resonance coil Lt1It is fixed on around snail shape is set as on the second magnetic sheet, driving coil Lt0With resonance coil Lt1Opposite arrangement, resonance coil Lt0And Lt1Using compact snail cable architecture, front and rear to introduce with high initial magnetoconductivity ferroxcube magnetic sheet and be close to resonance coil, the utility model is simple in structure, and circuit is easily designed and processing is realized, available in capsule endoscope.
Description
Technical field
A kind of capsule endoscope is the utility model is related to, more particularly to a kind of capsule endoscope charge coil.
Background technology
Wireless charging technology is widely used in biologic medical field.In the capsule endoscope of painless stomach detection, wireless charging
Power technology can solve the limitation of traditional button cell power capacity, using the teaching of the invention it is possible to provide continual and steady DC voltage, is ensureing
The work of normal table plays an important roll capsule endoscope in complex environment in enteron aisle, while is provided for effective diagnosis
Ensure.
In the application of capsule endoscope wireless charging, transmitting coil effectively produces drive circuit as system core part
Raw alternating electric field changes into alternating magnetic field, is in turn coupled on capsule endoscope three-dimensional receiving coil, and pass through rectifier
Continual and steady dc power output is produced with voltage-stablizer, there is provided capsule endoscope steady operation guarantee.It is typically based in capsule
The transmitting coil of sight glass wireless charging application mainly includes two kinds of forms：(1) solenoid coil；(2) Helmholtz coil.Helical
Pipeline circle as shown in Figure 1, circuit structure is simple, realize by easily designed and processing.But its major defect is that drive circuit produces
Electric field is by the magnetic field after solenoid coil in operation of capsule endoscope regional space skewness, therefore receiving circuit produces
Dc power produce the unstable feature of output power as locus is different, it is impossible to ensure continuing for capsule endoscope
Effectively work；Moreover, this output power unstability feature adds tissue or skin under transmitting coil
Undermined risk, continue to increase especially with exciting current in coil, the risk of damage of tissue or skin
Continuing to increase.The non-uniform shortcoming of magnetic field intensity spatial distribution produced based on solenoid, Helmholtz coil pass through conducting wire
Single solenoid coil is separated as shown in Fig. 2, realize that two coils produce magnetic field and are overlapped in same direction at the same time,
So as to solve the problems, such as that solenoid coil exists, uniform magnetic field intensity in operation of capsule endoscope region is realized, is reduced
The risk that tissue or skin come to harm.But the magnetic field that equivalent two transmitting coils of Helmholtz produce exists
Certain phase difference, during magnetic field intensity is superimposed, partial magnetic field energy loss, to capsule endoscope wireless charging system
Efficiency maximize have very big influence.In Helmholtz coil application, in order to improve magnetic induction intensity, generally pass through increase
Coil turn, but increasing the number of turn means the inductance increase of coil, it is necessary to the drive of bigger for identical driving current
Dynamic voltage, increases drive circuit design difficulty.
Utility model content
The purpose of this utility model is to provide a kind of plane enhancement magnetism resonance based on capsule endoscope wireless charging
Transmitting coil, on the one hand improves the intra resonant cavity magnetic field intensity and magnetic field homogeneity of operation of capsule endoscope, reduces human body
Tissue or the risk that comes to harm of skin and the possibility that the work of capsule endoscope long-time normal table is effectively ensured；Separately
On the one hand, the driving voltage of transmitting coil is effectively reduced by the energy transmission mode of magnetic resonance, and then reduces drive circuit
Design difficulty.
What the purpose of this utility model was realized in：A kind of plane based on capsule endoscope wireless charging is enhanced
Magnetic resonance transmitting coil, including the power supply of drive circuit input terminal is connected to, the output terminal of the drive circuit is connected with driving
Coil Lt0, driving resonant capacitance Ct is connected between drive circuit and driving coil0, driving coil Lt0Around being set as snail
Shape is fixed on the first magnetic sheet, driving coil Lt0It is correspondingly arranged on resonance device on one side, the resonance device bag is by resonance coil
Lt1Both ends are connected into the first resonant capacitance Ct in circuit1, the resonance coil Lt1The second magnetic is fixed on around snail shape is set as
On piece, the driving coil Lt0With resonance coil Lt1Opposite arrangement.
Further as the utility model limits, the resonance coil Lt1With driving coil Lt0Specification and coiling side
To the identical and compact helix structure of use；The resonant capacitance Ct1With driving resonant capacitance Ct0Specification is identical, the first magnetic sheet
It is identical with the second magnetic sheet specification.
Further as the utility model limits, the resonance coil Lt1With driving coil Lt0Between be arranged in parallel.
Further as the utility model limits, the resonance coil Lt1With driving coil Lt0Distance D meet：D
=R, wherein, R is driving coil Lt0Radius.
Further as the utility model limits, and first magnetic sheet and the second magnetic sheet are selected with high magnetic permeability
Ferroxcube magnetic sheet.
Compared with prior art, the beneficial effects of the utility model are, the utility model passes through the drive in radiating circuit
Moving winding introduces the resonance coil with driving coil same size with respect to human body, by magnetic resonance principle and with high magnetic permeability
The magnetic induction line that ferroxcube magnetic sheet constraint transmitting coil produces, on the one hand effectively improves the intra resonant cavity of operation of capsule endoscope
Magnetic field intensity and magnetic field homogeneity, reduce tissue or risk that skin comes to harm and being effectively ensured in capsule is peeped
The possibility of mirror long-time normal table work；On the other hand, emission lines are effectively reduced by the energy transmission mode of magnetic resonance
The driving voltage of circle, and then reduce the design difficulty of drive circuit；Meanwhile the utility model is simple in structure, circuit is easily designed
Realized with processing.The utility model can be used in capsule endoscope.
Brief description of the drawings
Fig. 1 is the transmitting coil circuit theory schematic diagram of solenoid coil form in the prior art.
Fig. 2 is the transmitting coil circuit theory schematic diagram of Helmholtz coil form in the prior art.
Fig. 3 is the utility model circuit theory schematic diagram.
Fig. 4 is the utility model circuit equivalent schematic diagram.
Fig. 5 is the time domain waveform schematic diagram of the utility model.
Fig. 6 is the utility model coil equivalent structure schematic diagram.
Fig. 7 simplifies version schematic diagram for the utility model coil equivalent structure.
Embodiment
A kind of plane enhancement magnetism resonance ejection coil based on capsule endoscope wireless charging as shown in Figure 3, bag
The power supply for being connected to drive circuit input terminal is included, the output terminal of drive circuit is connected with driving coil Lt0, drive circuit is with driving
Driving resonant capacitance Ct is connected between coil0, driving coil Lt0It is fixed on the first magnetic sheet, drives around snail shape is set as
Coil Lt0It is correspondingly arranged on resonance device on one side, resonance device bag is by resonance coil Lt1Both ends are connected into first resonance in circuit
Capacitance Ct1, resonance coil Lt1It is fixed on around snail shape is set as on the second magnetic sheet, driving coil Lt0With resonance coil Lt1Phase
To arrangement, resonance coil Lt1With driving coil Lt0Specification is identical and uses compact helix structure；Resonant capacitance Ct1With driving
Resonant capacitance Ct0Specification is identical, and the first magnetic sheet is identical with the second magnetic sheet specification, resonance coil Lt1With driving coil Lt0Between put down
Row arrangement, resonance coil Lt1With driving coil Lt0Distance D meet：D=R, wherein, R is driving coil Lt0Radius, first
Magnetic sheet and the second magnetic sheet select the ferroxcube magnetic sheet with high magnetic permeability.
The utility model is described further with reference to operation principle.
The utility model passes through in driving coil Lt0(launching resonance coil) introduces resonance line behind at a distance of D in human body
Enclose Lt1As resonance coil is received, so as to fulfill the enhancing of the performances such as intra resonant cavity magnetic induction intensity, uniformity, Fig. 4 institutes
Show；Launch resonance coil Lt0Alternating current i1 (t)=I1sin ω t are passed to, and then produce alternating magnetic field, receive resonance coil Lt1
Adjoin transmitting resonance coil Lt0, while the direction of winding of two coils is consistent, i.e., Same Name of Ends is consistent, it is assumed that inductance value L, resonance
Capacitance is C；Shown in Fig. 4, launch resonance coil Lt0Electric current i1 (t)=I1sin ω t are passed to, it is right in a cycle [0, T]
The time domain waveform answered is Fig. 5 (a)；Because transmitting resonance coil resonant frequency is ω, launch resonance coil inductance L under resonant condition
Energy exchange (I1 be corresponding current and the amplitude of voltage with V1) is constantly carried out with capacitance C, is met,
So the amplitude of capacitance Ct0 both end voltages is V1=ω LI1, corresponding phase relation can filling by inductance capacitance
Discharge process is drawn, is illustrated with reference to voltage and current on two resonance coils in a cycle [0, T]：
0-1/4T:Electric current i1 (t) is become by 0 turns to positive maximum, capacitance Ct0Port 1 discharge along current direction,
V11 ' (t) is changed into 0 from positive maximum；
1/4T-1/2T:Electric current i1 (t) is become by positive maximum turns to 0, capacitance Ct0Port 1 ' charge along electric current,
V11 ' (t) is become by 0 turns to reverse maximum；
1/2T-3/4T:Electric current i1 (t) is become by 0 turns to reverse maximum, capacitance Ct0Port 1 ' along current discharge,
V11 ' (t) is become by reverse maximum turns to 0；
3/4T-T:Electric current i1 (t) is become by reverse maximum turns to 0, capacitance Ct0Port 1 charge along current direction,
V11 ' (t) is become by 0 turns to positive maximum；
Because the winding mode of two resonance coils is consistent, i.e., Same Name of Ends is consistent, shown in Fig. 4, according to transformer theory simultaneously
Assuming that transformer ratio is k, it can calculate and receive the voltage at resonance coil capacitance both ends and be,
V22'(t)=kV11'(t)=ω kLIlsin ω t
Meanwhile in conjunction with the LC charge-discharge characteristics for receiving resonance coil, obtain receiving the electric current on resonance coil：
I2 (t)=kI1sin ω t；
Voltage, electric current temporal relationship are as shown in Figure 5 in two coils.
Wearable consideration for convenience at the same time, transmitting resonance coil and reception resonance coil use snail knot
Structure, such as Fig. 6, are analyzed for convenience, and snail cable architecture coil can be equivalent to a series of compact adjacent concentric circular coils,
As shown in fig. 7, and each circular coil passes to identical electric current with one heart.In order to ensure transmitting resonance coil and receive resonance line
The uniformity in intra resonant cavity magnetic field superposition is enclosed, r ≈ R are met when planar coil makes, i.e., all circular coils with one heart pass to
The magnetic induction intensity produced in space at any point during identical electric current is consistent, to ensure in two resonance coil axial magnetics
The uniformity of induction.
According to biot savart's law, electric current and magnetic induction intensity are one-to-one relationships in coil, receive resonance
After coil current determines, with reference to Helmholtz coil theory and biot savart's law is utilized to carry out intra resonant cavity magnetic field
Calculating；Because when k is close to 1, in order to ensure the uniformity of resonance coil and Helmholtz coil energy stores, corresponding resonance
The number of turn of chamber coil and Helmholtz coil is 2N.
So enhanced wearable magnetic resonance coil resonance intracavitary portion magnetic field intensity of plane for the utility model patent
It can be expressed as
Wherein D be receive resonance coil distance of center circle, X be apart from the reference axis original heart away from；So in the case of identical distance of center circle,
Magnetic induction intensity can be expressed as inside Helmholtz coil,
R is normalized in D, X, i.e.,
D=dR
X=xR
So the expression formula after corresponding three kinds of different coils are normalized according to D, X is：
μ0NI/R is permanent number, and the high magnetic conductivity ferrite magnetic core that the utility model introduces effectively can be fettered and guided
The magnetic induction line that transmitting coil produces, which enters, receives resonance coil, and then launches resonance coil and receive the coupling between resonance coil
Coefficient k ≈ 1.SoThat is resonator coil and Helmholtz coil magnetic induction intensity phase
When can meet capsule wireless energy transmission demand.
Meanwhile can be determined for the voltage swing of magnetic resonance resonator by capacitance and inductance discharge and recharge relation, and because
Coil inductance is number of turn N functions, so transmitting resonance coil number of turn N correspond to inductance value L, so corresponding voltage swing is
Under the conditions of identical intra resonant cavity magnetic induction intensity, the input voltage size of solenoid coil and Helmholtz coil
It can be expressed as：
It is not difficult to find out, Helmholtz coil is higher to drive circuit voltage request, and is driven needed for resonance coil driving
2 times of dynamic voltage swing, considerably increase the design difficulty of transmitting resonance coil drive circuit.
The utility model is not limited to above-described embodiment, on the basis of technical solution disclosed in the utility model, this
The technical staff in field is according to disclosed technology contents, it is not necessary to which performing creative labour can be special to some of which technology
Sign makes some and replaces and deform, these are replaced and deformation is within the protection scope of the present utility model.
Claims (5)
1. a kind of plane enhancement magnetism resonance ejection coil based on capsule endoscope wireless charging, including it is connected to driving electricity
The power supply of road input terminal, the output terminal of the drive circuit are connected with driving coil Lt0, drive circuit and driving coil Lt0Between
It is connected with driving resonant capacitance Ct0, it is characterised in that driving coil Lt0It is fixed on around snail shape is set as on the first magnetic sheet,
Driving coil Lt0It is correspondingly arranged on resonance device on one side, the resonance device bag is by resonance coil Lt1Both ends are connected into circuit
First resonant capacitance Ct1, the resonance coil Lt1It is fixed on around snail shape is set as on the second magnetic sheet, the driving coil
Lt0With resonance coil Lt1Opposite arrangement.
2. the plane enhancement magnetism resonance ejection coil according to claim 1 based on capsule endoscope wireless charging,
It is characterized in that, the resonance coil Lt1With driving coil Lt0Specification and direction of winding it is identical and use compact spiral knot
Structure；The resonant capacitance Ct1With driving resonant capacitance Ct0Specification is identical, and the first magnetic sheet is identical with the second magnetic sheet specification.
3. the plane enhancement magnetism resonance ejection line according to claim 1 or 2 based on capsule endoscope wireless charging
Circle, it is characterised in that the resonance coil Lt1With driving coil Lt0Between be arranged in parallel.
4. the plane enhancement magnetism resonance ejection line according to claim 1 or 2 based on capsule endoscope wireless charging
Circle, it is characterised in that the resonance coil Lt1With driving coil Lt0Distance D meet：D=R, wherein, R is driving coil Lt0
Radius.
5. the plane enhancement magnetism resonance ejection line according to claim 1 or 2 based on capsule endoscope wireless charging
Circle, it is characterised in that first magnetic sheet and the second magnetic sheet select the ferroxcube magnetic sheet with high magnetic permeability.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN201720781644.8U CN207265741U (en) | 2017-06-30 | 2017-06-30 | Plane enhancement magnetism resonance ejection coil based on capsule endoscope wireless charging |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN201720781644.8U CN207265741U (en) | 2017-06-30 | 2017-06-30 | Plane enhancement magnetism resonance ejection coil based on capsule endoscope wireless charging |
Publications (1)
| Publication Number | Publication Date |
|---|---|
| CN207265741U true CN207265741U (en) | 2018-04-20 |
Family
ID=61926290
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CN201720781644.8U Active CN207265741U (en) | 2017-06-30 | 2017-06-30 | Plane enhancement magnetism resonance ejection coil based on capsule endoscope wireless charging |
Country Status (1)
| Country | Link |
|---|---|
| CN (1) | CN207265741U (en) |
Cited By (2)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN107482789A (en) * | 2017-06-30 | 2017-12-15 | 扬州芯智瑞电子科技有限公司 | Plane enhancement magnetism resonance ejection coil based on capsule endoscope wireless charging |
| CN115105221A (en) * | 2022-08-30 | 2022-09-27 | 北京精准医械科技有限公司 | Nuclear magnetic development marking point structure, debugging tool and preparation method thereof |
-
2017
- 2017-06-30 CN CN201720781644.8U patent/CN207265741U/en active Active
Cited By (3)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN107482789A (en) * | 2017-06-30 | 2017-12-15 | 扬州芯智瑞电子科技有限公司 | Plane enhancement magnetism resonance ejection coil based on capsule endoscope wireless charging |
| CN115105221A (en) * | 2022-08-30 | 2022-09-27 | 北京精准医械科技有限公司 | Nuclear magnetic development marking point structure, debugging tool and preparation method thereof |
| CN115105221B (en) * | 2022-08-30 | 2022-11-08 | 北京精准医械科技有限公司 | Nuclear magnetic development marking point structure, debugging tool and preparation method thereof |
Similar Documents
| Publication | Publication Date | Title |
|---|---|---|
| CN100588025C (en) | Electromagnetic induction energy-storage system | |
| US9806536B2 (en) | Method and apparatus for wireless magnetic power transmission | |
| CN207265741U (en) | Plane enhancement magnetism resonance ejection coil based on capsule endoscope wireless charging | |
| CN104600877A (en) | Wireless power transmission device with sidesway adaptability and rotation adaptability | |
| CN103630858B (en) | A kind of shoulder coil and transmitting coil of magnetic resonance system | |
| Tang | A low-operating-voltage wireless intermediate-range scheme for energy and signal transmission by magnetic coupling for implantable devices | |
| JP2018518929A (en) | Wearable power receiving coil to transmit power wirelessly without electrical contact | |
| CN110247463B (en) | Wireless charging system | |
| CN207053261U (en) | Enhancement magnetism resonance ejection coil based on the application of capsule endoscope wireless charging | |
| CN205286357U (en) | Medical magnetic resonance device of superconductive popular style | |
| CN107482789A (en) | Plane enhancement magnetism resonance ejection coil based on capsule endoscope wireless charging | |
| Basar et al. | A wireless power transmission system for robotic capsule endoscopy: Design and optimization | |
| CN209593110U (en) | A kind of wireless power supply and capsule robot | |
| Yu et al. | The design and implementation of the wireless power transmission system of video capsule endoscopy | |
| WO2022198976A1 (en) | Magnetic control and wireless charging system | |
| Basar et al. | Resonant inductive power transfer system for freely moving capsule endoscope with highly uniform magnetic field | |
| CN107181328A (en) | The enhancement magnetism resonance ejection coil applied based on capsule endoscope wireless charging | |
| CN108987079A (en) | The multidirectional transmitting three dimensional coils of wireless power transmission and radio energy transmission system | |
| CN111064285B (en) | Wireless energy signal transmission system for implantable device | |
| CN103296780A (en) | Endoscopic capsule power supply system | |
| CN103715469A (en) | Wireless rechargeable battery | |
| JP2012023929A (en) | Resonance coil | |
| CN106655531A (en) | Electromagnetic conversion energy storage system | |
| Zhang et al. | Efficient Wireless Power Transfer based on Strongly Coupled Magnetic Resonance | |
| JP2012023299A (en) | Resonance coil |
Legal Events
| Date | Code | Title | Description |
|---|---|---|---|
| GR01 | Patent grant | ||
| GR01 | Patent grant |