CN201569734U - Radio-frequency coil for open magnetic resonance imaging system - Google Patents
Radio-frequency coil for open magnetic resonance imaging system Download PDFInfo
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- CN201569734U CN201569734U CN2009201984318U CN200920198431U CN201569734U CN 201569734 U CN201569734 U CN 201569734U CN 2009201984318 U CN2009201984318 U CN 2009201984318U CN 200920198431 U CN200920198431 U CN 200920198431U CN 201569734 U CN201569734 U CN 201569734U
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Abstract
The utility model relates to a radio-frequency coil for an open magnetic resonance imaging system, which is characterized by comprising an upper pole face and a lower pole face. The upper pole face consists of a plurality of first strip conduction bands arranged in parallel at intervals, the first ends of the first strip conduction bands are connected in sequence, and the second ends of the first strip conduction bands are separated from each other; the lower pole surface is arranged to be parallel to the upper pole face and consists of a plurality of second strip conduction bands arranged in parallel at intervals, the first ends of the second strip conduction bands are connected in sequence, and the second ends of the second strip conduction bands are separated from each other; and the first ends of the first strip conduction bands are connected with the first ends of the second strip conduction bands through coupling resonance capacitors, and the second ends of the first strip conduction bands are connected with the second ends of the second strip conduction bands through short-circuit capacitors. Compared with the prior art, the utility model can be used in the magnetic field which can make the imaging region obtain good uniformity in the open magnetic resonance imaging system.
Description
Technical field
The utility model relates to a kind of radio-frequency coil that is used for open type magnetic resonance imaging (MRI) system.
Background technology
Open type magnetic resonance imaging (MRI) system generally comprises open hollow yoke 1, the inside of hollow yoke 1 is symmetrical arranged the main magnet of being made by the permanent magnetism material 2, for focusing magnetic field, overcome permanent magnetic material performance difference, set up uniform magnetic field, generally then be formed into the image space being provided with on main magnet 2 opposed outer surface between magnetic homogenizing pole plate 3, the two magnetic homogenizing pole plates 3, shown in accompanying drawing 3.In open type magnetic resonance imaging (MRI) system, magnetic homogenizing pole plate more than 3 adopts radio-frequency coil.
Human body is put into imaging space, there is static magnetic field B0 in the imaging space, because atomic nucleus exists natural magnetic moments, under the effect of static magnetic field B0, atomic nucleus can be with the Rameau frequency f around the B0 precession, applies the radio-frequency field B1 that the direction frequency vertical with B0 is f1 (being produced by radio-frequency coil) this moment again, when f is identical with f1, will resonate, radio-frequency field is given atomic nucleus NE BY ENERGY TRANSFER.After radio-frequency field was removed, atomic nucleus can be launched the radiofrequency signal that frequency is f, is received by receiving coil.If apply gradient magnetic in this course again, just can obtain the space distribution information of human body, thus reconstruct the two dimension or the 3-D view of human body, and this process just is called magnetic resonance imaging.
In magnetic resonance imaging, the homogeneity of radio-frequency field B1 directly affects the homogeneity of image in the imaging region, has only radio-frequency field B1 to have good homogeneity, could produce uniform image.If radio-frequency field B1 is even inadequately in imaging region, when emission of radio frequency signals, the degree of atomic nucleus resonance will be different in imaging region, and the radiofrequency signal size of Chan Shenging is also different so, thereby the image that reconstruction is come out will bright dark inequality.When especially carrying out fat suppression, can not reach good effect owing to the inhomogeneous of radio-frequency field B1, so the homogeneity of radio-frequency coil is an one item important indicator in the image border.
An other important indicator of radio-frequency coil is exactly its conversion efficiency, if conversion efficiency is low, so just need more powerful radio-frequency power amplifier, can increase system cost so undoubtedly, in addition because emissive power is excessive, electronic devices and components in the radio-frequency coil will bear bigger voltage, electric current, might be subjected to certain injury.Secondly in order to prevent that excessive electromagnetic radiation from damaging patient or medical personnel, the size of radio-frequency field also there is strict restriction, so also do not allow emissive power excessive.
Main magnet and radio-frequency coil all are slab constructions in open type magnetic resonance imaging (MRI) system, thereby are that static magnetic field B0, gradient magnetic or radio-frequency field B1 are difficult to obtain good homogeneity.A kind of solenoid coil can produce higher inhomogeneity radio-frequency field, and conversion efficiency is also high, but its enclosed construction allows other people be difficult near patient or imaging region as medical personnel, the structure of this kind coil can allow some patient produce claustrophobia in addition, so solenoid coil is not suitable for using in open type magnetic resonance imaging (MRI) system.Other has the planar radio frequency coils of a kind of open type magnetic resonance imaging (MRI) system butterfly structure commonly used, and the field that the radio-frequency coil of this structure produces is very inhomogeneous, and efficient is also very low.
In sum, the homogeneity that solves the field of radio-frequency coil is crucial, and will take into account and keep radio-frequency coil to have high conversion efficiency.
The utility model content
Technical problem to be solved in the utility model is to provide a kind of homogeneity at above-mentioned prior art, and the higher radio-frequency coil that is used for open type magnetic resonance imaging (MRI) system of radio-frequency power conversion efficiency.
The utility model solves the problems of the technologies described above the technical scheme that is adopted: this is used for the radio-frequency coil of open type magnetic resonance imaging (MRI) system, it is characterized in that: comprise
Upper pole face is made up of some the first bar shaped conduction bands that parallel interval is provided with, and first end of the first bar shaped conduction band interconnects, and spaced-apartly between second end of the first bar shaped conduction band does not connect;
Lower pole face be arranged in parallel with upper pole face, and also some second bar shaped conduction bands that are provided with by parallel interval are formed, and first end of the second bar shaped conduction band interconnects, and spaced-apartly between second end of the second bar shaped conduction band does not connect;
Wherein, link to each other by the connection resonant capacitance between first end of first end of the first bar shaped conduction band and the second bar shaped conduction band, link to each other by short circuit capacitance between second end of second end of the first bar shaped conduction band and the second bar shaped conduction band.
Preferably, the connection resonant capacitance between first end of first end of the described first bar shaped conduction band and the second bar shaped conduction band is provided with a plurality of, and is arranged in parallel side by side.
Link to each other by described short circuit capacitance between second end of the second corresponding bar shaped conduction band on second end of every first bar shaped conduction band on the described upper pole face and the described lower pole face.
Improve the skeleton that described radio-frequency coil also comprises is that made by insulating material, be used to support upper pole face and lower pole face again.
Compared with prior art, advantage of the present utility model is: the radio-frequency coil that the utility model is provided is separately positioned on the two main magnet opposed outer surface of open type magnetic resonance imaging (MRI) system, the radio-frequency field of two radio-frequency coil generations is superimposed in imaging region like this, by adjusting width, conduction band quantity and the spacing of lower pole face discal patch shape conduction band in the upper pole face that be arranged in parallel in each radio-frequency coil and the distance between the lower pole face, the adjustment, can in imaging region, obtain homogeneity magnetic field preferably.
Description of drawings
Fig. 1 is the perspective view one of the utility model embodiment;
Fig. 2 is the perspective view two of the utility model embodiment;
Fig. 3 is the structural representation of open type magnetic resonance imaging (MRI) system commonly used;
Embodiment
Embodiment describes in further detail the utility model below in conjunction with accompanying drawing.
The radio-frequency coil that is used for open type magnetic resonance imaging (MRI) system shown in Fig. 1～3 comprises
Upper pole face is made up of some the first bar shaped conduction bands 4 that parallel interval is provided with, and first end of the first bar shaped conduction band 4 interconnects, and spaced-apartly between second end of the first bar shaped conduction band 4 does not connect;
Lower pole face be arranged in parallel with upper pole face, and also some second bar shaped conduction bands 5 that are provided with by parallel interval are formed, and first end of the second bar shaped conduction band 5 interconnects, and spaced-apartly between second end of the second bar shaped conduction band 5 does not connect;
Wherein, link to each other by a plurality of resonant capacitances that are arranged in parallel side by side 6 between first end of first end of the first bar shaped conduction band 4 and the second bar shaped conduction band 5, constitute an antiresonant circuit, make and form a resonator cavity between the lower pole face, by the reasonable distribution of resonant capacitance, just can on imaging region, obtain homogeneity magnetic field preferably; Link to each other by short circuit capacitance 7 between second end of the second corresponding bar shaped conduction band 5 on second end of every first bar shaped conduction band 4 on the upper pole face and the lower pole face, be convenient to transmission current and reflux forming between conduction band up and down;
Upper pole face and lower pole face do not have the skeleton 8 that the magnetic insulation material makes by low-loss and support;
The first bar shaped conduction band 4 and the second bar shaped conduction band 5 can be made with the Copper Foil that is laid on the skeleton.
Said structure, can prevent the generation of eddy current, by adjusting width, conduction band quantity and the spacing of lower pole face discal patch shape conduction band in the upper pole face that be arranged in parallel in each radio-frequency coil and the distance between the lower pole face, the adjustment, can in imaging region, obtain homogeneity magnetic field preferably.
In use, on two main magnet 2 opposed outer surface in open type magnetic resonance imaging (MRI) system above-mentioned radio-frequency coil is set respectively, by the combination and the common resonant capacitance of regulating two radio-frequency coils of two radio-frequency coils up and down, radio-frequency field is well superposeed in the imaging center district, guaranteed the intensity of the radio-frequency field in imaging center district, thereby guaranteed that the utility model power conversion efficiency is higher, and all obtained good homogeneity in all directions.
Claims (4)
1. a radio-frequency coil that is used for open type magnetic resonance imaging (MRI) system is characterized in that: comprise
Upper pole face is made up of some the first bar shaped conduction bands that parallel interval is provided with, and first end of the first bar shaped conduction band interconnects, and spaced-apartly between second end of the first bar shaped conduction band does not connect;
Lower pole face be arranged in parallel with upper pole face, and also some second bar shaped conduction bands that are provided with by parallel interval are formed, and first end of the second bar shaped conduction band interconnects, and spaced-apartly between second end of the second bar shaped conduction band does not connect;
Wherein, link to each other by the connection resonant capacitance between first end of first end of the first bar shaped conduction band and the second bar shaped conduction band, link to each other by short circuit capacitance between second end of second end of the first bar shaped conduction band and the second bar shaped conduction band.
2. the radio-frequency coil that is used for open type magnetic resonance imaging (MRI) system according to claim 1 is characterized in that: the connection resonant capacitance between first end of first end of the described first bar shaped conduction band and the second bar shaped conduction band is provided with a plurality of, and is arranged in parallel side by side.
3. the radio-frequency coil that is used for open type magnetic resonance imaging (MRI) system according to claim 1 is characterized in that: link to each other by described short circuit capacitance between second end of the second corresponding bar shaped conduction band on second end of every first bar shaped conduction band on the described upper pole face and the described lower pole face.
4. according to the described radio-frequency coil that is used for open type magnetic resonance imaging (MRI) system of any claim in the claim 1～3, it is characterized in that: also comprise one that make by insulating material, as to be used to support upper pole face and lower pole face skeleton.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN2009201984318U CN201569734U (en) | 2009-10-12 | 2009-10-12 | Radio-frequency coil for open magnetic resonance imaging system |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN2009201984318U CN201569734U (en) | 2009-10-12 | 2009-10-12 | Radio-frequency coil for open magnetic resonance imaging system |
Publications (1)
| Publication Number | Publication Date |
|---|---|
| CN201569734U true CN201569734U (en) | 2010-09-01 |
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Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CN2009201984318U Expired - Lifetime CN201569734U (en) | 2009-10-12 | 2009-10-12 | Radio-frequency coil for open magnetic resonance imaging system |
Country Status (1)
| Country | Link |
|---|---|
| CN (1) | CN201569734U (en) |
Cited By (2)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN103959082A (en) * | 2011-05-10 | 2014-07-30 | 美时医疗控股有限公司 | Cryogenically cooled whole-body rf coil array and mri system having same |
| CN104698411A (en) * | 2015-02-13 | 2015-06-10 | 江苏麦格思频仪器有限公司 | Multichannel radio frequency coil for open type magnetic resonance imaging system |
-
2009
- 2009-10-12 CN CN2009201984318U patent/CN201569734U/en not_active Expired - Lifetime
Cited By (3)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN103959082A (en) * | 2011-05-10 | 2014-07-30 | 美时医疗控股有限公司 | Cryogenically cooled whole-body rf coil array and mri system having same |
| CN104698411A (en) * | 2015-02-13 | 2015-06-10 | 江苏麦格思频仪器有限公司 | Multichannel radio frequency coil for open type magnetic resonance imaging system |
| CN104698411B (en) * | 2015-02-13 | 2018-06-22 | 江苏麦格思频仪器有限公司 | For the Multi-channel radio-frequency coil of open type magnetic resonance imaging (MRI) system |
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Legal Events
| Date | Code | Title | Description |
|---|---|---|---|
| C14 | Grant of patent or utility model | ||
| GR01 | Patent grant | ||
| C56 | Change in the name or address of the patentee |
Owner name: XINGAOYI MEDICAL EQUIPMENT CO., LTD. Free format text: FORMER NAME: NINGBO XINGAOYI MAGNETIC MATERIAL CO., LTD. |
|
| CP03 | Change of name, title or address |
Address after: 315400 No. 555 smelting Road, Yuyao City, Zhejiang Province Patentee after: XINGAOYI MEDICAL EQUIPMENT CO., LTD. Address before: 315400 No. 777 Tan Xi Road, Yuyao, Zhejiang Patentee before: Ningbo Xingaoyi Magnetism Co., Ltd. |
|
| CX01 | Expiry of patent term | ||
| CX01 | Expiry of patent term |
Granted publication date: 20100901 |