CN103744041B - A kind of coil device being applied to nuclear magnetic resonance - Google Patents
A kind of coil device being applied to nuclear magnetic resonance Download PDFInfo
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- CN103744041B CN103744041B CN201310733339.8A CN201310733339A CN103744041B CN 103744041 B CN103744041 B CN 103744041B CN 201310733339 A CN201310733339 A CN 201310733339A CN 103744041 B CN103744041 B CN 103744041B
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Abstract
The invention discloses a kind of coil device being applied to nuclear magnetic resonance, including power divider, upper magnet and lower magnet, also including two radio-frequency coil unit of longitudinal arrangement, upper radio shielding layer and lower radio shielding layer, described radio-frequency coil unit is connected with described power divider；Described upper radio shielding layer and described lower radio shielding layer lay respectively at the parallel to each other of the both sides up and down of described radio-frequency coil unit, described upper radio shielding layer and described lower radio shielding layer, and are separately mounted on upper magnet and lower magnet；Symmetric shape centered by described radio-frequency coil unit, upper radio shielding layer and lower radio shielding layer.The present invention can improve the conversion efficiency of radio-frequency coil unit, and will not be affected by gradient coil on gradient dish.
Description
Technical field
The present invention relates to a kind of coil device, especially relate to a kind of be applied to penetrating of magnetic resonance system
Frequently coil device.
Background technology
In modern medical skill, magnetic resonance imaging system has been a kind of conventional armarium.Penetrate
Frequently coil is as the indispensable part of magnetic resonance imaging system, and its performance is to magnetic resonance imaging system
Performance impact is the biggest.
Coil device mainly has orthogonal plate, two kinds of structures of vertical bar lead-type.China's publication number
CN101190127A, the patent document of entitled " radio-frequency coil of a kind of slab construction " discloses one
Plant orthogonal plate radio-frequency coil.China publication number CN1281183C, entitled " one is applied to magnetic
The coil device of resonance imaging system and manufacture method " patent document disclose a kind of vertical bar wire
The radio-frequency coil of type.
The structure of both radio-frequency coils of the prior art is the most more complicated, and conversion efficiency is not high enough.
For ensureing the performance of coil and opening, existing radio-frequency coil in use general the most all can near gradient coil,
When actual imaging, gradient coil can produce relatively more heats, and these heats can be transmitted to radio-frequency coil
On, the copper sheet of radio-frequency coil can expand with heat and contract with cold, and the inductance being so equivalent to coil there occurs change,
The resonant frequency that can cause radio-frequency coil changes.
Summary of the invention
Technical problem solved by the invention is to provide a kind of radio-frequency coil dress being applied to nuclear magnetic resonance
Put, it is possible to increase the conversion efficiency of radio-frequency coil unit, and will not be by gradient coil on gradient dish
Impact.
Technical scheme is as follows:
A kind of coil device being applied to nuclear magnetic resonance, including power divider, upper magnet and under
Magnet, also includes the radio-frequency coil unit of two longitudinal arrangements, upper radio shielding layer and lower radio shielding layer,
Described radio-frequency coil unit is connected with described power divider；The structure of described radio-frequency coil unit includes:
Shell, coil and metal forming；The described shell of nonmetallic materials be shaped as centrosymmetry shape, with institute
The shape stating coil adapts；Being provided with inside groove in the middle of the frame of described shell, outside is wound with described gold
Belong to the described coil arrangement of paper tinsel in described inside groove；Described upper radio shielding layer and described lower radio shielding layer
Lay respectively at the both sides up and down of described radio-frequency coil unit, described upper radio shielding layer and described lower radio frequency screen
The plane covering layer is parallel to each other, and is separately mounted on upper magnet and lower magnet；Described radio-frequency coil list
Symmetric shape centered by radio shielding layer first, upper and lower radio shielding layer.
Further: the geometric center of said two radio-frequency coil unit is with described upper magnet and the master of lower magnet
Magnetic field center is point-blank.
Further: upper gradient dish and descending stair scale are respectively embedded in described upper magnet and lower magnet, described
The lower surface of upper gradient dish and the upper surface of described descending stair scale respectively with upper magnet and lower magnet periphery height
Unanimously, described upper radio shielding layer and described lower radio shielding layer respectively with described upper gradient dish and described under
Gradient dish directly contacts.
Further: described upper radio shielding layer and lower radio shielding layer have size phase four corner positions
Same breach, described breach is 200～400mm in X-direction size range, the size range of Y-direction
It is 150～300mm.
Further: the material of described upper radio shielding layer and lower radio shielding layer use double face copper or
Copper coin, its thickness range is 0.1～2mm, and its planar dimension is straight less than described upper magnet and lower magnet
Footpath.
Further: the number of turns of described metal forming is 1～8 circles, and described coil is 1～8 that coiling direction is identical
The coil of circle, couples with electric capacity between adjacent windings, and every turn coil is in series with electric capacity.
Further: described metal forming uses Copper Foil.
Compared with prior art, the technology of the present invention effect includes:
1, in the present invention, radio-frequency coil unit longitudinal arrangement, it is possible to increase the conversion effect of radio-frequency coil unit
Rate, and will not be affected by gradient coil on gradient dish.
2, in the present invention, radio shielding layer produce symmetrical radio frequency environment, have the advantage that (1)
Being produced symmetrical radio frequency environment by radio shielding layer, gradient coil is not owing to having between same radio-frequency coil unit
Heat transmits, and radio-frequency coil unit resonance frequency will not offset；(2) conversion efficiency is high, it is only necessary to
The lowest radio-frequency power can meet imaging requirements.
Accompanying drawing explanation
Fig. 1 is the structural representation of coil device in the present invention；
Fig. 2 is the structural representation of radio shielding layer in the present invention；
Fig. 3 is coiling and the connection diagram of radio-frequency coil unit coil in the present invention；
Fig. 4 is the profile of radio-frequency coil unit in the present invention.
Detailed description of the invention
Below with reference to the accompanying drawings and preferred embodiment, technical solution of the present invention is elaborated.
As it is shown in figure 1, be the structural representation of coil device in the present invention.
The structure of coil device includes: two radio-frequency coil unit 1 and two radio shielding layers (on
Radio shielding layer 2 and lower radio shielding layer 3), two radio-frequency coil unit 1 longitudinal arrangements, upper radio frequency
Screen layer 2 and lower radio shielding layer 3 lay respectively at the both sides up and down of radio-frequency coil unit 1, and on penetrate
Frequently the plane of screen layer 2 and lower radio shielding layer 3 is parallel to each other, upper radio shielding layer 2 and lower radio frequency screen
The structure covering layer 3 is identical.
Radio-frequency coil unit 1 centrosymmetry shape, radio-frequency coil unit 1 and the merit of magnetic resonance imaging system
Rate allotter connects.The plane of two radio-frequency coil unit 1 is parallel to each other, can move simultaneously, and penetrate
Frequently the center of coil unit 1 is just to magnet center, the same magnet of geometric center of two radio-frequency coil unit 1
Main field center the most point-blank.
Radio-frequency coil unit 1 is protected from environmental bigger, and the major function of radio shielding layer is to inciting somebody to action
Radio-frequency coil unit 1 provides a fixing radio frequency environment, radio-frequency coil unit 1 can be made to produce simultaneously
Radio-frequency field in Z-direction evenly.The more preferable copper of conductivity is used additionally, due to radio shielding layer, so
The radio-frequency coil unit 1 loss in this radio frequency environment reduces, and therefore can also improve radio-frequency coil unit 1
Efficiency.Wherein going up radio shielding layer 2 to be installed on upper magnet, lower screen layer 3 is installed on lower magnet,
Owing to the volume of upper magnet and lower magnet is relatively big, upper gradient dish and descending stair scale be respectively embedded in upper magnet and
Lower magnet, outside on it, the lower surface of gradient dish and the upper surface of descending stair scale are respectively with upper magnet and lower magnet
Enclose highly consistent, the above radio shielding layer 2 of institute and lower radio shielding layer 3 and upper gradient dish and descending stair scale
Directly contact.
As in figure 2 it is shown, be the structural representation of radio shielding layer in the present invention.
Upper radio shielding layer 2 and lower radio shielding layer 3 have equivalently-sized breach four corner positions
4, its X-direction size range is 200～400mm, and the size range of Y-direction is 150～300mm, lacks
Mouth 4 is by being formed after being removed 4 corners of upper radio shielding layer 2 and lower radio shielding layer 3, if
Put breach 4 and be to provide for sufficiently large and symmetrical radio frequency environment, so that radio-frequency coil unit 1 moves
Time, the radio frequency synthesis field of two radio-frequency coil unit 1 remains uniform field in magnet in certain limit
And efficiency keeps constant.
Upper radio shielding layer 2 and lower radio shielding layer 3 are placed in parallel in magnet centre position, upper radio frequency screen
Cover layer 2 and lower radio shielding layer 3 is strict centrosymmetry shape, preferably rectangle, annular or its change
Shape.It uses material to be double face copper or copper coin, and its thickness range is 0.1～2mm, its plane meter
The very little diameter less than magnet (upper magnet and lower magnet).
As it is shown on figure 3, be coiling and the connection diagram of radio-frequency coil unit 1 coil 6 in the present invention.
In radio-frequency coil unit 1, the metal forming loop of every turn coil 6 is series connection, and coiling direction is the most identical,
Radio-frequency coil unit 1 includes 1～8 coils 6 enclosed that coiling direction is identical, electricity consumption between adjacent windings 6
Hold 5 to couple.The electric capacity 5 that can connect one or more in the middle of every turn coil 6, the electricity of series connection
Holding 5 to be used for making each radio-frequency coil unit 1 be tuned in operating frequency, can also eliminate or reduce simultaneously has
The load impact on coil 6 during load.The head of coil 6 first lap and the tail of last lap pass through radio frequency electrical
Cable is connected on power combiner or power divider.
In radio-frequency coil unit 1, the geometry of coil 6 can be rectangle, ellipse or other
Centrosymmetry shape.Its geometric center with upper magnet and lower magnet main field center point-blank.
As shown in Figure 4, it is the profile of radio-frequency coil unit 1 in the present invention.Radio-frequency coil unit 1
Structure includes: shell 7, coil 6, metal forming 8；The shape of the shell 7 of nonmetallic materials can be long
Square, oval or some other centrosymmetry shape, adapts with the shape of coil 6.Inside groove position
In the middle of the frame of shell 7, the outside coil 6 being wound around metal forming 8 is arranged in inside groove, metal forming 8
The number of turns be 1～8 circle, can fully use 4 inside grooves of shell 7 to increase the number of turns.Wherein metal forming 8
Use the reasonable Copper Foil of electric conductivity.
By the distance between two radio-frequency coil unit 1 of regulation and the chi of each radio-frequency coil unit 1
Very little and shape, it is possible to obtain well radio frequency synthesis field homogeneity range, conversion efficiency is the highest simultaneously.Pass through
Theoretical Calculation and experimental verification, the number of turns of coil 6 is the most, and the radio frequency efficiency of coil device is the highest,
And after the number of turns is many to a certain extent, its efficiency declines.It is not additionally that the number of turns is got over for engineering viewpoint
Much the best.For radio frequency synthesis field uniformity, and the number of turns it doesn't matter, when its coordinate system definition as figure
When 1, the spacing between the uniformity of X-direction and two coils has relation, and coil 6 spacing is the most remote all
Even property is the best, and the uniformity of Y direction then can adjust by adjusting coil 6 size in the Y direction,
The uniformity of Z-direction then can be adjusted in the size of Z-direction by adjusting coil 6.
Claims (7)
1. it is applied to a coil device for nuclear magnetic resonance, including power divider, upper magnet
And lower magnet, it is characterised in that: also include the radio-frequency coil unit of two longitudinal arrangements, upper radio shielding
Layer and lower radio shielding layer, described radio-frequency coil unit is connected with described power divider；Described radio frequency
The structure of coil unit includes: shell, coil and metal forming；The shape of the described shell of nonmetallic materials
Centered by symmetric shape, adapt with the shape of described coil；In being provided with in the middle of the frame of described shell
Groove, outside is wound with the described coil arrangement of described metal forming in described inside groove；Described upper radio shielding
Layer and described lower radio shielding layer lay respectively at the both sides up and down of described radio-frequency coil unit, described upper radio frequency
The plane of screen layer and described lower radio shielding layer is parallel to each other, and is separately mounted to upper magnet and lower magnetic
On body；Symmetric shape centered by described radio-frequency coil unit, upper radio shielding layer and lower radio shielding layer.
A kind of coil device being applied to nuclear magnetic resonance, its feature
It is: in the geometric center of the said two radio-frequency coil unit main field with described upper magnet and lower magnet
The heart is point-blank.
A kind of coil device being applied to nuclear magnetic resonance, its feature
It is: upper gradient dish and descending stair scale are respectively embedded in described upper magnet and lower magnet, described upper gradient
The lower surface of dish and the upper surface of described descending stair scale are highly consistent with upper magnet and lower magnet periphery respectively,
Described upper radio shielding layer and described lower radio shielding layer respectively with described upper gradient dish and described descending stair scale
Directly contact.
A kind of coil device being applied to nuclear magnetic resonance, its feature
It is: described upper radio shielding layer and lower radio shielding layer have equivalently-sized lacking four corner positions
Mouthful, described breach is 200～400mm in X-direction size range, and the size range of Y-direction is
150～300mm.
5. a kind of radio-frequency coil dress being applied to nuclear magnetic resonance as described in any one of Claims 1-4
Put, it is characterised in that: the material of described upper radio shielding layer and lower radio shielding layer uses copper coin, and it is thick
Degree scope is 0.1～2mm, and its planar dimension is less than described upper magnet and the diameter of lower magnet.
A kind of coil device being applied to nuclear magnetic resonance, its feature
Being: the number of turns of described metal forming is 1～8 circles, described coil is 1～8 lines enclosed that coiling direction is identical
Circle, couples with electric capacity between adjacent windings, and every turn coil is in series with electric capacity.
A kind of coil device being applied to nuclear magnetic resonance, its feature
It is: described metal forming uses Copper Foil.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN201310733339.8A CN103744041B (en) | 2013-12-27 | 2013-12-27 | A kind of coil device being applied to nuclear magnetic resonance |
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| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN201310733339.8A CN103744041B (en) | 2013-12-27 | 2013-12-27 | A kind of coil device being applied to nuclear magnetic resonance |
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| Publication Number | Publication Date |
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| CN103744041A CN103744041A (en) | 2014-04-23 |
| CN103744041B true CN103744041B (en) | 2017-01-04 |
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| CN201310733339.8A Active CN103744041B (en) | 2013-12-27 | 2013-12-27 | A kind of coil device being applied to nuclear magnetic resonance |
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Families Citing this family (4)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN104155622B (en) * | 2014-08-26 | 2017-10-03 | 国家电网公司 | A kind of planar radio frequency coils for nuclear magnetic resonance |
| CN107621615B (en) * | 2017-09-28 | 2023-09-15 | 平康(深圳)医疗设备科技有限公司 | Embedded gradient and radio frequency integrated coil and magnetic resonance equipment with same |
| CN109696642B (en) * | 2018-12-29 | 2024-06-04 | 佛山瑞加图医疗科技有限公司 | Radio frequency coil device and magnetic resonance imaging system |
| CN112394308B (en) * | 2019-08-15 | 2024-01-30 | 西门子(深圳)磁共振有限公司 | Transmitting radio frequency coil unit and magnetic resonance system |
Citations (5)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN2221939Y (en) * | 1995-06-05 | 1996-03-13 | 深圳安科高技术有限公司 | Radio-frequency coil device for magnetic resonance imaging system |
| CN201617828U (en) * | 2010-04-22 | 2010-11-03 | 杜健军 | Radio-frequency coil device in magnetic resonance imaging system |
| CN102338862A (en) * | 2010-06-01 | 2012-02-01 | 高质电动有限公司 | RF coil assembly, protection method thereof, and magnetic resonance imaging system |
| CN102652027A (en) * | 2009-12-10 | 2012-08-29 | 皇家飞利浦电子股份有限公司 | Magnetic resonance -compatible electrical device with radio frequency shielding or an enclosure |
| CN103399284A (en) * | 2013-08-07 | 2013-11-20 | 深圳市特深电气有限公司 | Magnetic resonance composite coil and magnetic resonance imaging system |
Family Cites Families (1)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US9500727B2 (en) * | 2012-04-20 | 2016-11-22 | Regents Of The University Of Minnesota | System and method for control of RF circuits for use with an MRI system |
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Patent Citations (5)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN2221939Y (en) * | 1995-06-05 | 1996-03-13 | 深圳安科高技术有限公司 | Radio-frequency coil device for magnetic resonance imaging system |
| CN102652027A (en) * | 2009-12-10 | 2012-08-29 | 皇家飞利浦电子股份有限公司 | Magnetic resonance -compatible electrical device with radio frequency shielding or an enclosure |
| CN201617828U (en) * | 2010-04-22 | 2010-11-03 | 杜健军 | Radio-frequency coil device in magnetic resonance imaging system |
| CN102338862A (en) * | 2010-06-01 | 2012-02-01 | 高质电动有限公司 | RF coil assembly, protection method thereof, and magnetic resonance imaging system |
| CN103399284A (en) * | 2013-08-07 | 2013-11-20 | 深圳市特深电气有限公司 | Magnetic resonance composite coil and magnetic resonance imaging system |
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| CN103744041A (en) | 2014-04-23 |
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