CN103344927B - Magnetic resonance radio frequency coil and magnetic resonance imaging system - Google Patents
Magnetic resonance radio frequency coil and magnetic resonance imaging system Download PDFInfo
- Publication number
- CN103344927B CN103344927B CN201310259994.4A CN201310259994A CN103344927B CN 103344927 B CN103344927 B CN 103344927B CN 201310259994 A CN201310259994 A CN 201310259994A CN 103344927 B CN103344927 B CN 103344927B
- Authority
- CN
- China
- Prior art keywords
- coil
- magnetic resonance
- electric capacity
- unit coil
- radio
- 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 present invention relates to a kind of magnetic resonance radio frequency coil, resonance, in resonant frequency f0, comprises the first half arranged in parallel and the latter half; Described the first half and the latter half comprise respectively and being parallel to each other and the spaced unit coil being no less than 3, are coupled between adjacent described unit coil by electric capacity or inductance; In the conductor of each described unit coil, series connection is no less than 1 electric capacity.The present invention also discloses a kind of magnetic resonance imaging system.The present invention owing to arranging breakpoint in coil-conductor, and accesses electric capacity at breakpoint place, thus changes the magnetic distribution in radio-frequency coil, obtains magnetic resonance imaging more clearly.
Description
Technical field
The present invention relates to magnetic resonance imaging system, particularly relate to a kind of magnetic resonance radio frequency coil and magnetic resonance imaging system.
Background technology
Magnetic resonance imaging system generates the two dimension of sample or the equipment of 3-D view according to Magnetic resonance imaging principle, and common nuclear magnetic resonance imaging system generally comprises: produce static uniform magnetic field B
0magnet; Be positioned at this static uniform magnetic field B
0in rf coil system, comprise the radio-frequency sending coil for excited sample, and for receiving the RF receiving coil of the resonance signal that sample sends; Gradient system, for the gradient in sample space generation magnetic field, is convenient to imaging coding; And computer generated image system, for the signal that RF receiving coil is collected, be processed into the visual pattern be convenient to doctor and observed.
The electrical structure of radio-frequency coil mainly comprises the coil case made by conductive material, and the inductance be connected in coil case and electric capacity.In working order, receiving coil is around the checked position of patient, its output impedance is mated with Back end data collecting device, and coil inside has uniform magnetic distribution at the operating frequencies, the resonance signal of drawing has good signal to noise ratio (S/N ratio), thus obtains clear distortionless sample image at System Back-end.Usually around radio-frequency coil, have magnet, gradient coil, radio-frequency shielding fence, the conductor in these three kinds of devices often affects the distribution of current in radio-frequency coil, thus affects the magnetic distribution in radio-frequency coil.Therefore along with the continuous rising of radio-frequency coil frequency of utilization in magnetic resonance imaging system, in radio-frequency coil, the homogeneity of distribution of current and controllability need new technology to adjust.
In the magnetic resonance imaging system adopting permanent-magnet, radio-frequency sending coil needs to produce uniform radio-frequency field, will have power efficiency high as far as possible simultaneously.A kind of structure of radio-frequency sending coil, for forming right three-dimensional circular list structure more, often organize between strip structure and connect with electric capacity, when it raises near magnet or frequency of operation, in the coil of many groups of arrangements, each strip structure is as unit coil, because the impact of the magnetic Field Coupling by other unit is different, the electric current caused in unit is not identical, in this unit, distribution of current is uneven, cause the magnetic field of generation also uneven, the sample image of final acquisition has the change of obvious light and shade, and imaging effect can be caused very poor in some special applications.
Summary of the invention
Fundamental purpose of the present invention is to overcome the deficiencies in the prior art part, a kind of magnetic resonance radio frequency coil and magnetic resonance imaging system are provided, make the electric current in radio-frequency coil more evenly or can be effectively controlled, thus ensure that magnetic resonance imaging system can provide sample image more clearly.
The invention discloses a kind of magnetic resonance radio frequency coil, resonance is in resonant frequency f
0, comprise the first half arranged in parallel and the latter half; Described the first half and the latter half comprise respectively and being parallel to each other and the spaced unit coil being no less than 3, are coupled between adjacent described unit coil by electric capacity or inductance; In the conductor of each described unit coil, series connection is no less than 1 electric capacity.
In an embodiment of magnetic resonance radio frequency coil of the present invention, the electric capacity of connecting in described unit coil, be the two ends mutually insulated of the conductor that described unit coil disconnects at access point place overlap produce.
In one embodiment of the invention, in described the first half and the latter half, comprise 9 described unit coils respectively, 2 electric capacity of connecting respectively in each described unit coil; 2 electric capacity of described series connection are arranged in the symmetric position of described unit coil.
In another embodiment of magnetic resonance radio frequency coil of the present invention, 4 electric capacity of connecting respectively in each described unit coil.
As a special case of the present invention, 4 electric capacity of described series connection are distributed in the conductor of described unit coil equally spacedly.
The invention also discloses a kind of magnetic resonance imaging system, comprise and produce static uniform magnetic field B
0magnet; Be positioned at this static uniform magnetic field B
0in, resonance is in resonant frequency f
0radio-frequency coil; The gradient system of magnetic field gradient is produced at sample space; And for the computer generated image system that generates visual pattern and power-supply system.Described magnetic resonance imaging system, uses magnetic resonance radio frequency coil described above.
Magnetic resonance radio frequency coil disclosed by the invention, owing to arranging breakpoint in coil, and at breakpoint place access electric capacity, thus changes the magnetic distribution in radio-frequency coil, obtains magnetic resonance imaging more clearly.
Accompanying drawing explanation
Fig. 1 is the stereo circuit structural representation of the magnetic resonance radio frequency coil of one embodiment of the invention.
Fig. 2 is the stereo circuit structural representation of the embodiment of the present invention's unit coil.
Fig. 3 is the stereo circuit structural representation of the present invention by the radio-frequency coil of inductive coupling.
Fig. 4 is the circuit perspective view that the present invention has the unit coil of multiple access electric capacity.
Fig. 5 the present invention is the stereo circuit structural representation of the embodiment of another unit coil.
Embodiment
Below in conjunction with the drawings and specific embodiments, the present invention is described in further detail.
Be illustrated in figure 1 the stereo circuit structural representation of the magnetic resonance radio frequency coil of one embodiment of the invention, this radio-frequency coil 100 comprises the first half 200 and the latter half 300.In magnetic resonance imaging system, set up cartesian coordinate system, and make static magnetic field direction be direction along Z axis.Suppose that the latter half 300 of radio-frequency coil distributes in the plane of Z=0, then the first half 200 of radio-frequency coil is distributed in the plane of Z=L, and wherein L is constant, represents radio-frequency coil inner space spacing in z-direction.The first half 200 of radio-frequency coil and the latter half 300 similar are also parallel to each other, and comprise 5 spaced unit coils 101 respectively, and are interconnected by series capacitance C0 between unit coil 101.Also series capacitance C1 is comprised in each unit coil 101.Integrally, resonance is in the resonant frequency f0 of magnetic resonance imaging system for radio-frequency coil 100.
According to invention thought of the present invention, unit coil 101 is not defined as 5, can more than 5, or less individual.Each unit coil 101 interval each other is not defined as equidistantly, and can be such as that the close arrangement mode in both sides is dredged in centre, the interval between the unit coil 101 be namely larger, and the interval between the unit coil 101 at two ends is smaller, or conversely.
Unit coil 101 is made up of Copper Foil or other conductors, and its shape is the annulus of similar rectangle, and distribution is distributed in X-axis successively, that is, the conductor of each unit coil 101 is distributed in the plane of X=C, and C is constant.Be illustrated in figure 2 the stereo circuit structural representation of a unit coil.In figure, the lines of similar rectangle represent conductor, and these conductors join end to end, and middle series capacitance, supposes to have inductance value L.Unit coil 101 circuit is similar to independently inductor capacitor resonant circuit, can be interconnected by series capacitance C0 between adjacent unit coil 101, to change the couple state between adjacent windings, at guarantee magnetic resonance radio frequency coil 100 resonance under the prerequisite of resonant frequency F0, the homogeneous current distribution on each unit coil 101 can also be made, and distribution of current in different units coil 101 is similar, the electromagnetic field distribution in the radio-frequency coil of the such gained imaging region in magnetic resonance imaging system just can be evenly.
Can be intercoupled by inductance between adjacent unit coil, as shown in Figure 3, each unit coil 101 does not have conductor to connect each other, is interconnected by electromagnetic field couples yet.Series capacitance C1 and C2 in each unit coil 101.This radio-frequency coil 100 comprises the first half 201 equally, and the latter half 301.In unit coil 101, the value of series capacitance C1 and C2 ensures that this radio-frequency coil 100 resonance is in the resonant frequency f0 of magnetic resonance imaging system.
Series capacitance in unit coil 101 also can be multiple, access electric capacity is disconnected in its suitable part forming conductor, the distribution of current in unit coil 101 can be changed, special distribution of current can obtain corresponding magnetic distribution, such as previously mentioned, uniform distribution of current often can obtain uniform magnetic distribution.As shown in Figure 4, in a unit coil 103, there are 4 series capacitances, are respectively C401, C402, C403, and C404, the value of four electric capacity can not be identical, and the distribution of electric capacity also can be arranged according to the distribution of current in test cell coil.As a special case, generally, the conductor length connecting series capacitance can be equal.
This patent arranges some breakpoints in the unit coil of bar shaped ring-type, then accesses electric capacity.The assembled arrangement of many groups unit of this unit coil, still can adopt the mode of above-mentioned electric capacity or inductive coupling between adjacent cells coil.
The quantity of breakpoint and the capacity of access electric capacity in unit, depend on the capacity, the current distributions of wish control and the physical dimension etc. of coil that connect electric capacity between frequency of operation, unit.Unit inductive length is longer or frequency is higher, the easier skewness of electric current, need the breakpoint quantity of increase more, can by testing respectively between the diverse location and different units of unit with little probe, if test result relatively evenly (or meeting the demands), then think that breakpoint is proper, if test result uneven (or not meeting the demands), corresponding breakpoint can be increased again in the centre position of two electric capacity.Breakpoint increases, and homogeneity can progressively improve.Due to the alternative of breakpoint quantity and capacitance, therefore radio-frequency coil structure of the present invention can be made to play its efficiency better high, the advantage that magnetic field homogeneity is good.After it is emphasized that breakpoint increases, coil cost can increase.
In one particular embodiment of the present invention, adopt tape conductor as winding wire, breakpoint is set in each coil unit but does not access capacity cell, but make the overlapped a part of area of the ribbon conductor at breakpoint place, insulation is kept between overlapping conductor, or separate with insulating medium, form actual distributed capacitance, this design can save the cost of coil.Be another unit coil circuit perspective view of the present invention as shown in Figure 5, in figure, the structure of C501 is a kind of structure of distributed capacitance.
The following describes the debug process of radio-frequency coil of the present invention.In of the present invention embodiment, the first half and the latter half of a composition radio-frequency coil use 9 unit coils 101 respectively, the working position of this radio-frequency coil is near conductive plane, when there is no series capacitance C1 in each unit coil, connect with series capacitance C0 between adjacent unit coil, after frequency of operation reaches 15MHz, can test electric current in each unit coil occurs obviously uneven, and what wherein can record the maximum current had in unit coil is more than 1.4 times of the minimum current had in unit coil.
The electric capacity C0 connected between original adjacent cells coil is increased and is twice, then the position increase connecting series capacitance C0 relative between unit coil arranges a breakpoint, access the electric capacity C1(i.e. the most twice C0 of identical capacity), namely each unit coil adopts structure as shown in Figure 2.The electric capacity that two sizes are original 2 times is employed because each unit coil is equivalent to, after two capacitances in series, the capacitance of equivalence is constant, the resonance frequency of the radio-frequency coil therefore formed is with originally identical, the electric current on each coil unit is tested with little test probe, current test results shows that the unevenness between unit can reach less than 1.1 times, and effect clearly.If the carefully capacity of each access electric capacity of adjustment, unevenness also can reduce further.
This is because the magnetic field that coil produces is directly proportional to the electric current on coil, if therefore difference between current is apart from larger, the electromagnetic field so produced also has larger deviation, the electromagnetic field of final formation is exactly a uneven electromagnetic field, if current deviation is very little, the final electromagnetic field formed is just more even.
If the electromagnetic field produced is uneven, significantly bright change is just there will be in magnetic resonance imaging, and there are some special sequences, the such as functional imaging of fat suppression class, if electromagnetic field is uneven, will cause imaging failure, under identical parameter, subregion adipose tissue signal can not be suppressed.
The foregoing is only preferred embodiment of the present invention, not in order to limit the present invention, all any amendments done within the spirit and principles in the present invention, equivalent replacement and improvement etc., all should be included within protection scope of the present invention.
Claims (9)
1. a magnetic resonance radio frequency coil, resonance is in resonant frequency f
0, comprise the first half arranged in parallel and the latter half; Described the first half and the latter half comprise respectively and being parallel to each other and the spaced unit coil being no less than 3, are coupled between adjacent described unit coil by electric capacity or inductance; It is characterized in that:
In the conductor of each described unit coil, series connection is no less than 1 electric capacity;
In magnetic resonance imaging system, set up cartesian coordinate system, and make static magnetic field direction be direction along Z axis; Suppose that the latter half of described radio-frequency coil is distributed in the plane of Z=0, then the first half of radio-frequency coil is distributed in the plane of Z=L, and wherein L is constant;
Described unit coil is made up of Copper Foil or other conductors, and its shape is the annulus of similar rectangle, and be distributed in X-axis respectively successively, that is, the conductor of each unit coil is distributed in the plane of X=C, and C is constant.
2. magnetic resonance radio frequency coil as claimed in claim 1, is characterized in that, the electric capacity of connecting in described unit coil, is the generation that overlaps of the two ends mutually insulated of the conductor that described unit coil disconnects at access point place ground.
3. magnetic resonance radio frequency coil as described in claim 1 or 2, is characterized in that, comprise 9 described unit coils respectively in described the first half and the latter half, 2 electric capacity of connecting respectively in each described unit coil; 2 electric capacity of described series connection are arranged in the symmetric position of described unit coil.
4. magnetic resonance radio frequency coil as claimed in claim 3, is characterized in that, 4 electric capacity of connecting respectively in each described unit coil.
5. magnetic resonance radio frequency coil as claimed in claim 4, it is characterized in that, 4 electric capacity of described series connection are distributed in the conductor of described unit coil equally spacedly.
6. a magnetic resonance imaging system, comprises and produces static uniform magnetic field B
0magnet; Be positioned at this static uniform magnetic field B
0in, resonance is in resonant frequency f
0radio-frequency coil; The gradient system of magnetic field gradient is produced at sample space; And for the computer generated image system that generates visual pattern and power-supply system; It is characterized in that:
The radio-frequency coil of described magnetic resonance, comprises the first half arranged in parallel and the latter half; Described the first half and the latter half comprise respectively and being parallel to each other and the spaced unit coil being no less than 3, are coupled between adjacent described unit coil by electric capacity or inductance; And
In the conductor of each described unit coil, series connection is no less than 1 electric capacity;
In magnetic resonance imaging system, set up cartesian coordinate system, and make static magnetic field direction be direction along Z axis; Suppose that the latter half of described radio-frequency coil is distributed in the plane of Z=0, then the first half of radio-frequency coil is distributed in the plane of Z=L, and wherein L is constant;
Described unit coil is made up of Copper Foil or other conductors, and its shape is the annulus of similar rectangle, and be distributed in X-axis respectively successively, that is, the conductor of each unit coil is distributed in the plane of X=C, and C is constant.
7. magnetic resonance imaging system as claimed in claim 6, is characterized in that, the electric capacity of connecting in the described unit coil of described radio-frequency coil, is the generation that overlaps of the two ends mutually insulated of the conductor that described unit coil disconnects at access point place ground.
8. the magnetic resonance imaging system as described in claim 6 or 7, is characterized in that, comprises 9 described unit coils respectively in described the first half of described radio-frequency coil and the latter half, 2 electric capacity of connecting respectively in each described unit coil; 2 electric capacity of described series connection are arranged in the symmetric position of described unit coil.
9. magnetic resonance imaging system as claimed in claim 8, it is characterized in that, 4 electric capacity of connecting respectively in each described unit coil of described radio-frequency coil, 4 electric capacity of described series connection are distributed in the conductor of described unit coil equally spacedly.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN201310259994.4A CN103344927B (en) | 2013-06-26 | 2013-06-26 | Magnetic resonance radio frequency coil and magnetic resonance imaging system |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN201310259994.4A CN103344927B (en) | 2013-06-26 | 2013-06-26 | Magnetic resonance radio frequency coil and magnetic resonance imaging system |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| CN103344927A CN103344927A (en) | 2013-10-09 |
| CN103344927B true CN103344927B (en) | 2015-09-23 |
Family
ID=49279740
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CN201310259994.4A Active CN103344927B (en) | 2013-06-26 | 2013-06-26 | Magnetic resonance radio frequency coil and magnetic resonance imaging system |
Country Status (1)
| Country | Link |
|---|---|
| CN (1) | CN103344927B (en) |
Families Citing this family (5)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN103645452A (en) * | 2013-12-09 | 2014-03-19 | 深圳市特深电气有限公司 | Multi-channel radio frequency coil device and magnetic resonance imaging system using the device |
| CN105975731B (en) * | 2016-06-20 | 2019-01-25 | 中国科学院深圳先进技术研究院 | Magnetic resonance radio frequency coil emulation mode and its device |
| CN109521380B (en) * | 2017-09-19 | 2021-07-20 | 西门子(深圳)磁共振有限公司 | Telescopic magnetic resonance coil and magnetic resonance imaging device |
| CN109031172A (en) * | 2018-08-07 | 2018-12-18 | 上海辰光医疗科技股份有限公司 | Use the magnetic resonance radio frequency coil structure of distributed capacitor |
| CN113933770B (en) * | 2021-11-25 | 2022-06-28 | 浙江大学 | Component layout method and system based on radio frequency emission surface coil and coil |
Family Cites Families (8)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US4638253A (en) * | 1984-10-29 | 1987-01-20 | General Electric Company | Mutual inductance NMR RF coil matching device |
| JP3699219B2 (en) * | 1996-11-01 | 2005-09-28 | ジーイー横河メディカルシステム株式会社 | Bird cage coil for MRI |
| US6008649A (en) * | 1997-12-23 | 1999-12-28 | General Electric Company | RF coil apparatus for MR system with lateral B0 field |
| US7282915B2 (en) * | 2004-05-14 | 2007-10-16 | General Electric Company | Multi-turn element RF coil array for multiple channel MRI |
| CN2896298Y (en) * | 2005-07-18 | 2007-05-02 | 北京海思威科技有限公司 | Vertical-field magnetic resonance imaging system radio-frequency emitting coil |
| US7936170B2 (en) * | 2008-08-08 | 2011-05-03 | General Electric Co. | RF coil and apparatus to reduce acoustic noise in an MRI system |
| JP5179588B2 (en) * | 2008-08-18 | 2013-04-10 | 株式会社日立メディコ | High frequency coil and magnetic resonance imaging apparatus |
| JP5368641B2 (en) * | 2010-08-17 | 2013-12-18 | 株式会社日立メディコ | High frequency coil and magnetic resonance imaging apparatus using the same |
-
2013
- 2013-06-26 CN CN201310259994.4A patent/CN103344927B/en active Active
Also Published As
| Publication number | Publication date |
|---|---|
| CN103344927A (en) | 2013-10-09 |
Similar Documents
| Publication | Publication Date | Title |
|---|---|---|
| CN103344927B (en) | Magnetic resonance radio frequency coil and magnetic resonance imaging system | |
| Lyu et al. | A method of using nonidentical resonant coils for frequency splitting elimination in wireless power transfer | |
| CN104422911B (en) | The operation method of magnetic resonance coil, magnetic resonance equipment and magnetic resonance system and coil | |
| CN103323700B (en) | A kind of high-temperature superconductive cable exchanges resistance test system and test method thereof | |
| US20180348316A1 (en) | Radio-frequency choke resonator assembly, coil cable and magnetic resonance imaging apparatus | |
| CN103645452A (en) | Multi-channel radio frequency coil device and magnetic resonance imaging system using the device | |
| CN104422912A (en) | Antenna Apparatus for Receiving Magnetic Resonance Signals | |
| CN105319429A (en) | Sensor devices and methods for use in sensing current through a conductor | |
| RU2566608C2 (en) | High-frequency antenna | |
| CN104703538A (en) | Magnetic resonance imaging device and antenna device | |
| Silva et al. | Operating frequency selection for low-power magnetic induction-based wireless underground sensor networks | |
| CN206301921U (en) | A kind of trapper for RF cable component | |
| CN101801170A (en) | Electric field shield and manufacturing method thereof | |
| CN204651134U (en) | Transformer and adapter | |
| CN103399284B (en) | Magnetic resonance compound coil and magnetic resonance imaging system | |
| TW201025642A (en) | Transmission apparatus | |
| Mao et al. | A polygonal double-layer coil design for high-efficiency wireless power transfer | |
| CN108037418A (en) | FLU Fault Location Unit, method and device | |
| Liotta et al. | A novel capacitive-inductive channel for wireless power and data transmission | |
| JP2013223338A (en) | Power transmission system | |
| Li et al. | Design Method of Primary Transmitting Coil for Realizing Large Uniform Magnetic Field Distribution | |
| CN105790435A (en) | Novel power network measurement and control system employing power carrier technology | |
| Zou et al. | Axial and radial offset characteristics of high temperature superconducting wireless power transfer system | |
| KR101373719B1 (en) | Manufacturing method of coaxial type ac cable | |
| CN108008264A (en) | Sensor for high voltage electric equipment partial discharge monitoring |
Legal Events
| Date | Code | Title | Description |
|---|---|---|---|
| C06 | Publication | ||
| PB01 | Publication | ||
| C10 | Entry into substantive examination | ||
| SE01 | Entry into force of request for substantive examination | ||
| C14 | Grant of patent or utility model | ||
| GR01 | Patent grant | ||
| CP02 | Change in the address of a patent holder | ||
| CP02 | Change in the address of a patent holder |
Address after: 518107 area 301c, building 201, 301, 501, 5, building 4, Jihui mould Industrial Park, Tianliao Avenue, Tianliao community, Yutang street, Guangming District, Shenzhen City, Guangdong Province Patentee after: Shenzhen RF Tech Co., Ltd. Address before: 518132 Guangdong Province, Shenzhen Guangming District Tian Liao Juhui Industrial Park 4 2 floor Patentee before: Shenzhen RF Tech Co., Ltd. |