CN103344927A - Magnetic resonance radio frequency coil and magnetic resonance imaging system - Google Patents
Magnetic resonance radio frequency coil and magnetic resonance imaging system Download PDFInfo
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- CN103344927A CN103344927A CN2013102599944A CN201310259994A CN103344927A CN 103344927 A CN103344927 A CN 103344927A CN 2013102599944 A CN2013102599944 A CN 2013102599944A CN 201310259994 A CN201310259994 A CN 201310259994A CN 103344927 A CN103344927 A CN 103344927A
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Abstract
The invention relates to a magnetic resonance radio frequency coil which is resonant in the resonant frequency f0 and comprises an upper half portion and a lower half portion which are parallel to each other. The upper half portion comprises more than three unit coils which are parallel and arranged at intervals, the lower half portion comprises more than three unit coils which are parallel and arranged at intervals, and adjacent unit coils are coupled through a capacitor or an inductor. No less than one capacitor is connected in series in a conductor of each unit coil. The invention further discloses a magnetic resonance imaging system. Due to the fact that breakpoints are set in the coil conductors and capacitors are connected to the breakpoints, the electromagnetic field distribution in the radio frequency coil is changed, and clearer magnetic resonance images are obtained.
Description
Technical field
The present invention relates to magnetic resonance imaging system, relate in particular to a kind of magnetic resonance radio-frequency coil and magnetic resonance imaging system.
Background technology
Magnetic resonance imaging system is to generate the two dimension of sample or the equipment of 3-D view according to the 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 state uniform magnetic field B
0In rf coil system, comprise for the radio-frequency sending coil of excited sample and be used for receiving the RF receiving coil of the resonance signal that sample sends; Gradient system is used for producing field gradients at sample space, is convenient to the imaging coding; And the computer generated image system, be used for the signal of RF receiving coil collection, be processed into and be convenient to the visual pattern that the doctor observes.
The electrical structure of radio-frequency coil mainly comprises the coil case of being made by conductive material and is connected inductance and electric capacity in the coil case.In working order down, receiving coil is around patient's checked position, its output impedance and Back end data collecting device coupling, and having uniform electromagnetic field in frequency of operation lower coil inside distributes, the resonance signal of drawing has good signal-to-noise, thereby obtains clear distortionless sample image in the system rear end.Usually have magnet, gradient coil, radio-frequency shielding fence around radio-frequency coil, the conductor in these three kinds of devices often influences the distribution of current in the radio-frequency coil, thereby the electromagnetic field that influences in the radio-frequency coil distributes.Therefore along with the continuous rising of radio-frequency coil frequency of utilization in the magnetic resonance imaging system, the homogeneity of distribution of current and controllability need new technology to adjust in the radio-frequency coil.
In the magnetic resonance imaging system that adopts permanent-magnet, radio-frequency sending coil need produce uniform radio-frequency field, will have high as far as possible power efficiency simultaneously.A kind of structure of radio-frequency sending coil, be the right three-dimensional circular list structure of many compositions, connect with electric capacity between every group of strip structure, when its close magnet or frequency of operation rising, each strip structure is as unit coil in the coil that many groups are arranged, the difference that influences owing to the magnetic field coupling that is subjected to other unit, caused the electric current in each unit inequality, distribution of current is inhomogeneous in this unit, cause the magnetic field that produces also inhomogeneous, the final sample image that obtains has tangible light and shade to be changed, and can cause imaging effect 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 in the radio-frequency coil electric current more evenly or can be effectively controlled, thereby guarantee 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 and the latter half of being arranged in parallel; Described the first half and the latter half comprise respectively be parallel to each other and arrange at interval be no less than 3 unit coil, be coupled by electric capacity or inductance between the adjacent described unit coil; Series connection is no less than 1 electric capacity in the conductor of each described unit coil.
In an embodiment of magnetic resonance radio-frequency coil of the present invention, the generation that overlaps of the two ends mutually insulated of the conductor that the electric capacity of connecting in the described unit coil is described unit coil to be disconnected at access point place ground.
In one embodiment of the invention, comprise 9 described unit coils in described the first half and the latter half respectively, 2 electric capacity of connecting respectively in each described unit coil; 2 electric capacity of described series connection are arranged on 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 producing static uniform magnetic field B
0Magnet; Be positioned at this static state uniform magnetic field B
0In, resonance is in resonant frequency f
0Radio-frequency coil; Produce the gradient system of magnetic field gradient at sample space; And the computer generated image system and the power-supply system that are used for generating visual pattern.Described magnetic resonance imaging system uses magnetic resonance radio-frequency coil described above.
Magnetic resonance radio-frequency coil disclosed by the invention, because breakpoint is set in coil, and insert electric capacity at the breakpoint place, distribute thereby changed the electromagnetic field in the radio-frequency coil, obtained magnetic resonance imaging more clearly.
Description of drawings
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 a unit coil of the present invention.
Fig. 3 is the stereo circuit structural representation of the present invention by the radio-frequency coil of inductive coupling.
The circuit perspective view of the unit coil of Fig. 4 a plurality of access electric capacity for the present invention has.
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 as 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 the static magnetic field direction be the direction along the Z axle.Suppose that then the first half 200 of radio-frequency coil is distributed on the plane of Z=L on the plane of the latter half 300 distribution Z=0 of radio-frequency coil, wherein L is constant, represents the spacing of radio-frequency coil inner space on the Z direction.The first half 200 of radio-frequency coil and the latter half 300 structures are similar and be parallel to each other, and comprise 5 unit coils 101 that arrange at interval respectively, and interconnect by series capacitance C0 between the unit coil 101.Also comprise series capacitance C1 in each unit coil 101.Radio-frequency coil 100 is done as a whole, and resonance is in the resonant frequency f0 of magnetic resonance imaging system.
According to invention thought of the present invention, unit coil 101 is not defined as 5, can be more than 5, perhaps still less.Each unit coil 101 interval each other is not defined as equidistantly, for example can be the middle close arrangement mode in both sides of dredging, and namely the interval between Zhong Jian the unit coil 101 is bigger, and the interval between the unit coil 101 at two ends is smaller, perhaps conversely.
Can intercouple by inductance between the adjacent unit coil, as shown in Figure 3, each unit coil 101 does not have conductor to connect each other, interconnects 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 and the latter half 301 equally.The value of series capacitance C1 and C2 guarantees that these radio-frequency coil 100 resonance are in the resonant frequency f0 of magnetic resonance imaging system in the unit coil 101.
Series capacitance in the unit coil 101 also can be a plurality of, disconnect access electric capacity in its suitable part that constitutes conductor, can change the distribution of current in the unit coil 101, special distribution of current can obtain corresponding electromagnetic field and distribute, for example as previously mentioned, distribution of current often can obtain uniform electromagnetic field distribution uniformly.As shown in Figure 4,4 series capacitances are arranged in a unit coil 103, be respectively C401, C402, C403, and C404, the value of four electric capacity can be inequality, and the distribution of electric capacity also can arrange according to the distribution of current in the test cell coil.As a special case, generally speaking, the conductor length that connects series capacitance can equate.
This patent arranges some breakpoints in the unit coil of bar shaped ring-type, insert electric capacity then.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 the adjacent cells coil.
The capacity of the quantity of breakpoint and access electric capacity in the unit depends on the capacity that connects electric capacity between frequency of operation, the unit, the current distributions of desire control and the physical dimension of coil etc.The unit inductive length is more long or frequency is more high, the more easy skewness of electric current, need the breakpoint quantity of increase more many, can be by testing respectively between the diverse location of unit and different units with little probe, if test result is (perhaps meeting the demands) relatively evenly, think that then breakpoint is proper, if test result inhomogeneous (perhaps not meeting the demands) then can increase corresponding breakpoint again in the centre position of two electric capacity.Breakpoint increases, and homogeneity can progressively improve.Because therefore the alternative of breakpoint quantity and capacitance can make radio-frequency coil structure of the present invention bring into play its efficient height, the advantage that magnetic field homogeneity is good better.After it is emphasized that breakpoint increases, the coil cost can increase.
In a specific embodiment of the present invention, adopt tape conductor as winding wire, breakpoint is set in each coil unit does not still insert capacity cell, but the overlapped a part of area of the ribbon conductor that makes the breakpoint place, keep insulation between the overlapping conductor, perhaps separate with insulating medium, form actual distributed capacitance, this design can be saved the cost of coil.Be another unit coil circuit perspective view of the present invention as shown in Figure 5, the structure of C501 is a kind of structure of distributed capacitance among the figure.
The following describes the debug process of radio-frequency coil of the present invention.In an embodiment of the present invention, form the first half and the latter half of a radio-frequency coil and use 9 unit coils 101 respectively, the working position of this radio-frequency coil is near conductive plane, when not having series capacitance C1 in each unit coil, connect with series capacitance C0 between the adjacent unit coil, after frequency of operation reaches 15MHz, can test electric current in each unit coil and occur obviously inhomogeneously, what wherein can record the maximum current that has in the unit coil is more than 1.4 times of minimum current that have in the unit coil.
The capacitor C 0 that connects between the original adjacent cells coil increased be twice, between unit coil, connect the relative position increase of series capacitance C0 then a breakpoint is set, the capacitor C 1(of access same capability i.e. the most twice C0), namely each unit coil adopts structure as shown in Figure 2.Because each unit coil equivalence is original 2 times electric capacity for having used two sizes, the capacitance of equivalence is constant after two capacitances in series, therefore the resonance frequency of the radio-frequency coil that forms is with identical originally, test electric current on each coil unit with little test probe, the testing current result shows that the unevenness between the unit can reach below 1.1 times, and effect is very obvious.If carefully adjust the capacity that each inserts electric capacity, unevenness also can further reduce.
This is because the magnetic field that coil produces is directly proportional with electric current on the coil, if therefore difference between current is apart from bigger, the electromagnetic field of Chan Shenging also has bigger deviation so, the final electromagnetic field that forms is exactly an inhomogeneous electromagnetic field, if current deviation is very little, the final electromagnetic field that forms just relatively evenly.
If the electromagnetic field that produces is inhomogeneous, significantly bright the variation will appear in magnetic resonance imaging, and some special sequences are arranged, the functional imaging of fat suppression class for example, if electromagnetic field is inhomogeneous, will cause the imaging failure, under the identical parameter, subregion adipose tissue signal can not be suppressed.
The above only is preferred embodiment of the present invention, not in order to limiting the present invention, all any modifications of doing within the spirit and principles in the present invention, is equal to and replaces and improvement etc., all should be included within protection scope of the present invention.
Claims (9)
1. magnetic resonance radio-frequency coil, resonance is in resonant frequency f
0, comprise the first half and the latter half of being arranged in parallel; Described the first half and the latter half comprise respectively be parallel to each other and arrange at interval be no less than 3 unit coil, be coupled by electric capacity or inductance between the adjacent described unit coil; It is characterized in that: series connection is no less than 1 electric capacity in the conductor of each described unit coil.
2. magnetic resonance radio-frequency coil as claimed in claim 1 is characterized in that, the generation that overlaps of the two ends mutually insulated ground of the conductor that the electric capacity of connecting in the described unit coil is described unit coil to be disconnected at the access point place.
3. as claim 1 or 2 described magnetic resonance radio-frequency coils, it is characterized in that, comprise 9 described unit coils in described the first half and the latter half respectively, 2 electric capacity of connecting respectively in each described unit coil; 2 electric capacity of described series connection are arranged on 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 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 producing static uniform magnetic field B
0Magnet; Be positioned at this static state uniform magnetic field B
0In, resonance is in resonant frequency f
0Radio-frequency coil; Produce the gradient system of magnetic field gradient at sample space; And the computer generated image system and the power-supply system that are used for generating visual pattern; It is characterized in that: the radio-frequency coil of described magnetic resonance comprises the first half and the latter half of being arranged in parallel; Described the first half and the latter half comprise respectively be parallel to each other and arrange at interval be no less than 3 unit coil, be coupled by electric capacity or inductance between the adjacent described unit coil; And series connection is no less than 1 electric capacity in the conductor of each described unit coil.
7. magnetic resonance imaging system as claimed in claim 6 is characterized in that, the generation that overlaps of the two ends mutually insulated ground of the conductor that the electric capacity of connecting in the described unit coil of described radio-frequency coil is described unit coil to be disconnected at the access point place.
8. as claim 6 or 7 described magnetic resonance imaging systems, it is characterized in that, comprise 9 described unit coils in described the first half of described radio-frequency coil and the latter half respectively, 2 electric capacity of connecting respectively in each described unit coil; 2 electric capacity of described series connection are arranged on the symmetric position of described unit coil.
9. magnetic resonance imaging system as claimed in claim 8 is characterized in that, 4 electric capacity of connecting respectively in the described unit coil of each of described radio-frequency coil, and 4 electric capacity of described series connection are distributed in the conductor of described unit coil equally spacedly.
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| CN201310259994.4A CN103344927B (en) | 2013-06-26 | 2013-06-26 | Magnetic resonance radio frequency coil and magnetic resonance imaging system |
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| CN201310259994.4A CN103344927B (en) | 2013-06-26 | 2013-06-26 | Magnetic resonance radio frequency coil and magnetic resonance imaging system |
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Cited By (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 |
| CN105975731A (en) * | 2016-06-20 | 2016-09-28 | 中国科学院深圳先进技术研究院 | Magnetic resonance radio frequency coil simulation method and 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 |
| CN109521380A (en) * | 2017-09-19 | 2019-03-26 | 西门子(深圳)磁共振有限公司 | Extension type magnetic resonance coil and MR imaging apparatus |
| CN113933770A (en) * | 2021-11-25 | 2022-01-14 | 浙江大学 | Component layout method and system based on radio frequency emission surface coil and coil |
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| Publication number | Priority date | Publication date | Assignee | Title |
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| CN109521380A (en) * | 2017-09-19 | 2019-03-26 | 西门子(深圳)磁共振有限公司 | Extension type magnetic resonance coil and MR imaging apparatus |
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| CN113933770A (en) * | 2021-11-25 | 2022-01-14 | 浙江大学 | Component layout method and system based on radio frequency emission surface coil and coil |
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| CN103344927B (en) | 2015-09-23 |
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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. |