CN105823997A - Magnetic field generator and magnetic resonance equipment with same - Google Patents
Magnetic field generator and magnetic resonance equipment with same Download PDFInfo
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- CN105823997A CN105823997A CN201610354927.4A CN201610354927A CN105823997A CN 105823997 A CN105823997 A CN 105823997A CN 201610354927 A CN201610354927 A CN 201610354927A CN 105823997 A CN105823997 A CN 105823997A
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- 238000003384 imaging method Methods 0.000 abstract description 5
- 230000009286 beneficial effect Effects 0.000 abstract description 2
- 239000003990 capacitor Substances 0.000 abstract 2
- 239000004020 conductor Substances 0.000 description 7
- 239000002184 metal Substances 0.000 description 5
- 230000008878 coupling Effects 0.000 description 4
- 238000010168 coupling process Methods 0.000 description 4
- 238000005859 coupling reaction Methods 0.000 description 4
- 230000000694 effects Effects 0.000 description 4
- 230000009471 action Effects 0.000 description 3
- 238000000034 method Methods 0.000 description 3
- 238000010276 construction Methods 0.000 description 2
- 238000010586 diagram Methods 0.000 description 2
- 238000005516 engineering process Methods 0.000 description 2
- 230000005284 excitation Effects 0.000 description 2
- 229910052755 nonmetal Inorganic materials 0.000 description 2
- 238000005481 NMR spectroscopy Methods 0.000 description 1
- 230000008859 change Effects 0.000 description 1
- 230000005672 electromagnetic field Effects 0.000 description 1
- 230000004907 flux Effects 0.000 description 1
- 239000011888 foil Substances 0.000 description 1
- 238000000265 homogenisation Methods 0.000 description 1
- 239000004615 ingredient Substances 0.000 description 1
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- 238000002955 isolation Methods 0.000 description 1
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- G—PHYSICS
- G01—MEASURING; TESTING
- G01R—MEASURING ELECTRIC VARIABLES; MEASURING MAGNETIC VARIABLES
- G01R33/00—Arrangements or instruments for measuring magnetic variables
- G01R33/20—Arrangements or instruments for measuring magnetic variables involving magnetic resonance
- G01R33/28—Details of apparatus provided for in groups G01R33/44 - G01R33/64
- G01R33/38—Systems for generation, homogenisation or stabilisation of the main or gradient magnetic field
- G01R33/385—Systems for generation, homogenisation or stabilisation of the main or gradient magnetic field using gradient magnetic field coils
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- G—PHYSICS
- G01—MEASURING; TESTING
- G01R—MEASURING ELECTRIC VARIABLES; MEASURING MAGNETIC VARIABLES
- G01R33/00—Arrangements or instruments for measuring magnetic variables
- G01R33/20—Arrangements or instruments for measuring magnetic variables involving magnetic resonance
- G01R33/28—Details of apparatus provided for in groups G01R33/44 - G01R33/64
- G01R33/42—Screening
- G01R33/421—Screening of main or gradient magnetic field
- G01R33/4215—Screening of main or gradient magnetic field of the gradient magnetic field, e.g. using passive or active shielding of the gradient magnetic field
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Abstract
The invention relates to a magnetic field generator and a magnetic resonance device with the magnetic field generator, which comprises a gradient magnetic field generator and a high-frequency resonance cavity antenna, wherein the high-frequency resonance cavity antenna comprises a capacitor, a first high-frequency shielding layer and a second high-frequency shielding layer which are respectively and electrically connected with the corresponding ends of the capacitor, and a filling medium layer in a resonance cavity between the first high-frequency shielding layer and the second high-frequency shielding layer, the gradient magnetic field generator is an embedded gradient magnetic field generator, and the second high-frequency shielding layer shields the embedded part and the non-embedded part of the gradient magnetic field generator. The magnetic field generator adopts the design of eddy current removal, so that the eddy current loss can be effectively reduced, and the efficiency is improved; the gradient magnetic field generator is embedded into the resonant cavity of the high-frequency resonant cavity antenna, so that the efficiency of the transmitting coil can be improved under the same thickness, and the performance of the gradient coil is not influenced, thereby being beneficial to the imaging quality; with the same efficiency, space is saved, cost is saved, or the space for the patient can be larger for magnets manufactured at the same cost.
Description
Technical field
The present invention relates to a kind of magnetic field generator and there is the magnetic resonance equipment of this magnetic field generator.
Background technology
In modern medical service technology, MR imaging apparatus is a kind of conventional armarium, its principle is to utilize magnetic resonance phenomenon to wish the Density Distribution of part of inspection, relaxation time distribution etc. to detect tested human body or sample, and is demonstrated checked human body or the cross-section image of sample part or 3-D view by the data recorded with pictorial form.
In this magnetic resonance equipment, a main field magnet the static main field B produced0, with the gradient magnetic B being switched fast produced by a gradient coil system0Overlapping.And the gradient coil system producing gradient magnetic would generally induce eddy current in the Guan Bi conductor of periphery, slackening gradient magnetic, and make its time dependent curve distortion, this will the quality of infringement magnetic resonance image (MRI).Therefore, in the design of magnetic field generator, the design of corresponding anti-eddy current is important and necessary.
Between gradient coil and high frequency antenna, generally there is radioshielding layer, play isolation and eliminate the effect of the two coupling；Due to gradient magnetic B0Being substantially the magnetostatic field by specific Gradient distribution, radioshielding layer does not has shielding action to magnetostatic field, the high frequency magnetic field B only produced high frequency antenna1Play the effect of shielding；Thus the feature of this radioshielding layer is the gradient magnetic B allowing gradient coil system produce0High frequency antenna, the without hindrance imaging space acting on magnet center region can be passed；And radio-frequency (RF) magnetic field B produced by high frequency antenna1But being prevented from leaking into gradient coil to go, high-frequency electromagnetic field energy will not be dissipated in gradient coil, helps to maintain efficiency and the high frequency magnetic field distribution of high frequency antenna.
In the magnetic resonance system of permanent-magnet, conventional high-frequency emission antenna typically requires the space of 40-50mm, and gradient coil typically requires the space of 40-80mm, and for the gradient coil with active shield, gross thickness would generally be close to 80mm.According to traditional design requirement, gradient coil and high frequency antenna are each independently mounted in the middle of magnet, even if ignoring gap therebetween, gross thickness is also between 80-130mm.
The design principle of main field magnet is typically to be devoted to so that magnet size is the least, and the weight therefore reaching main field magnet keeps less and preferably makes main field homogenization；But, the gross thickness of existing high-frequency emission antenna and gradient coil is relatively big, and shared magnet spaces is relatively big, is unfavorable for that magnet cost reduces.
Summary of the invention
It is an object of the invention to provide and a kind of change over the magnetic field generator in magnetic field and there is the magnetic resonance equipment of this magnetic field generator for producing；Make magnetic field generator structure having high efficiency while the compactest；Reduce the size of magnet, reduce magnet weight, reduction magnet cost；Or under the magnet of identical cost, bigger to the imaging space of patient, open the most comfortable.
The technical solution of the present invention is: the magnetic field generator of a kind of magnetic resonance equipment, including gradient magnetic generator and high-frequency resonant cavity antenna, described high-frequency resonant cavity antenna includes the filled media layer in the resonator cavity between electric capacity, the first radioshielding layer electrically connected respectively and the second radioshielding layer and described first radioshielding layer and the second radioshielding layer with electric capacity each corresponding end；Described gradient magnetic generator is embedded gradient magnetic generator, and described second radioshielding layer shields the embedded part of described gradient magnetic generator and is not embedded into part.
As preferably: described gradient magnetic generator includes that X-gradient coil, Y-gradient coil and Z-gradient coil, described gradient magnetic generator are completely embedded into described high-frequency resonant cavity antenna；Described gradient magnetic generator is arranged in the resonator cavity between described first radioshielding layer and the second radioshielding layer.
As preferably: described gradient magnetic generator includes that X-gradient coil, Y-gradient coil and Z-gradient coil, described gradient magnetic generator are partially submerged into described high-frequency resonant cavity antenna, and described first radioshielding layer is arranged at the middle part of magnetic field generator.
As preferably: described first radioshielding layer and the second radioshielding layer place plane are parallel, the middle part of the Z-gradient coil of described gradient magnetic generator embeds in the resonator cavity between described first radioshielding layer and the second radioshielding layer.
As preferably: concave setting in the middle part of described second radioshielding layer, and the middle part of described second radioshielding layer be arranged in parallel with the first radioshielding layer respectively with periphery；The middle part of the Z-gradient coil of described gradient magnetic generator embeds in the resonator cavity between described first radioshielding layer and the second radioshielding layer, and the periphery of described second radioshielding layer is positioned at described Z-gradient coil upper surface.
As preferably: described gradient magnetic generator also includes Z shielding-gradient coil；Described second radioshielding layer and the first radioshielding layer be arranged in parallel；The middle part of the Z-gradient coil of described gradient magnetic generator embeds in the resonator cavity between described first radioshielding layer and the second radioshielding layer.
As preferably: described second radioshielding layer and the first radioshielding layer be arranged in parallel, and described second radioshielding layer medial recess is arranged, in described X-gradient coil and Y-gradient coil, the middle part of at least one gradient coil embeds the resonator cavity between described first radioshielding layer and the second radioshielding layer.
As preferably: described gradient magnetic generator also includes X shielding-gradient coil, Y shielding-gradient coil and Z shielding-gradient coil；Described second radioshielding layer and the first radioshielding layer be arranged in parallel；In in the X-gradient coil of described gradient magnetic generator, Y-gradient coil and Z-gradient coil, at least one embeds the resonator cavity between described first radioshielding layer and the second radioshielding layer.
As preferably: described second radioshielding layer and the first radioshielding layer be arranged in parallel, and described second radioshielding layer medial recess arrange, in described Z shielding-gradient coil and Y shielding-gradient coil at least one middle part embedding described first radioshielding layer and the second radioshielding layer between resonator cavity in.
A kind of magnetic resonance equipment, includes above-mentioned magnetic field generator.
Compared with prior art, beneficial effects of the present invention:
(1) magnetic field generator uses and goes vortex design, can effectively reduce eddy-current loss, improves efficiency；First radioshielding layer is set and the second radioshielding layer had both played good shielding action, be again a part for high-frequency resonant cavity antenna, save space；When other conditions are constant, the efficiency of high frequency antenna is by the first radioshielding layer and the effect of distance of the second radioshielding layer, and the biggest efficiency of distance is the highest；Gradient magnetic generator is embedded in the resonator cavity of high-frequency resonant cavity antenna, the space shared by gradient magnetic generator and high-frequency resonant cavity antenna duplexer, make use of available space to a greater extent, the compactest in structure；In the case of gross thickness is identical, increases the first radioshielding layer and the spacing of the second radioshielding layer than traditional scheme, thus improve the efficiency of high frequency antenna, and the performance of gradient coil does not has any impact, beneficially image quality；If the efficiency of high frequency antenna keeps equal, then the spacing of the first radioshielding layer and the second radioshielding layer can reduce, and that is to say that the gross thickness of magnetic field generator can be less；More compact construction saves space, reduces magnet weight, provides cost savings, makes shimming more preferable, beneficially image quality；Or the magnet that identical cost manufactures can be more comfortable more greatly to the space of patient.
(2) gradient magnetic generator is partially submerged into high-frequency resonant cavity antenna, and the first radioshielding layer is arranged at the middle part of magnetic field generator, and the second radioshielding layer is between the Z-gradient coil and X, Y-gradient coil of gradient magnetic generator；On the one hand such structure is easy to structure design and processing technique, and on the other hand, the conductor filled in high-frequency resonant cavity can cause reducing relative to the more energy loss of nonmetal medium and efficiency；Under some occasion, X, the wire density of Y-axis gradient coil is relatively big, they being coupled to loss that resonator cavity brings and the space shared by X, Y-axis gradient coil shares the efficiency raising brought to high-frequency resonant cavity offseting with high-frequency resonant cavity.
(3) gradient magnetic generator is mainly reflected in distribution and the efficiency of high frequency antenna of radio-frequency (RF) magnetic field to the impact of high frequency antenna and the radio-frequency (RF) magnetic field of generation thereof.The symmetrical design of gradient magnetic generator essentially eliminates the impact of the distribution on high frequency magnetic field；Eliminate gradient coil as much as possible and the coupling of high frequency antenna be will assist in the efficiency improving high frequency antenna.Concave setting in the middle part of second radioshielding layer, the middle part of the Z-gradient coil of gradient magnetic generator embeds in the resonator cavity between the first radioshielding layer and the second radioshielding layer, and the periphery of the second radioshielding layer is positioned at Z-gradient coil upper surface.This structure can mask the part of the gradient coil high density conductor bigger on the impact of high-frequency resonant cavity antenna as far as possible, and less for conductor in gradient coil space is shared to high-frequency resonant cavity antenna, the space expanding resonator cavity of relatively limits, thus improve quality factor and the efficiency of high-frequency resonant cavity antenna.
(4) the symmetric design of magnetic field generator structure so that excitation easily realizes, the coupling energy automotive resistance major part between excitation passage, remaining fraction, can easy method remove.
(5) magnetic field generator can produce linear gradient fields and uniform radio-frequency field in the region near high-frequency resonant cavity antenna, and saves space, and quality factor are high.
Accompanying drawing explanation
Fig. 1 is the schematic diagram of the gradient coil of the magnetic field generator of magnetic resonance equipment of the present invention；
Fig. 2 is the structural representation of the first embodiment of the magnetic field generator of magnetic resonance equipment of the present invention；
Fig. 3 is metal forming schematic diagram in Fig. 2 high-frequency resonant cavity antenna；
Fig. 4 is the structural representation of the second embodiment of the magnetic field generator of magnetic resonance equipment of the present invention；
Fig. 5 is the structural representation of the 3rd embodiment of the magnetic field generator of magnetic resonance equipment of the present invention；
Fig. 6 is the perspective view of the 3rd embodiment of the magnetic field generator of magnetic resonance equipment of the present invention；
Fig. 7 is the structural representation of the 4th embodiment of the magnetic field generator of magnetic resonance equipment of the present invention；
Fig. 8 is the structural representation of the 5th embodiment of the magnetic field generator of magnetic resonance equipment of the present invention.
Primary clustering symbol description:
Gradient magnetic generator 10, high-frequency resonant cavity antenna 20, electric capacity 22, the first radioshielding layer 24, the second radioshielding layer 26, filled media layer 28.
Detailed description of the invention
Below in conjunction with the accompanying drawings the present invention is further described:
Fig. 1, Fig. 2, Fig. 3 show first embodiment of the present invention.
Refer to shown in Fig. 1 to Fig. 3, the magnetic field generator of this magnetic resonance equipment, including gradient magnetic generator 10 and high-frequency resonant cavity antenna 20, high-frequency resonant cavity antenna 20 includes electric capacity 22, the filled media layer 28 in resonator cavity between corresponding end respective with electric capacity 22 electrically connects respectively the first radioshielding layer 24 and the second radioshielding layer 26 and the first radioshielding layer 24 and the second radioshielding layer 26, gradient magnetic generator 10 is to be embedded in the resonator cavity of high-frequency resonant cavity antenna 20, second radioshielding layer 26 extends outside centered by gradient magnetic generator 10 center, second radioshielding layer 26 shields gradient magnetic generator 10.
Magnetic field generator uses and goes vortex design, can effectively reduce eddy-current loss, improves efficiency；First radioshielding layer 24 is set and the second radioshielding layer 26 had both played good shielding action, be again the ingredient forming high-frequency resonant cavity antenna 20, save space；When other conditions are constant, the efficiency of high-frequency resonant cavity antenna 20 is by the first radioshielding layer 24 and effect of distance of the second radioshielding layer 26, and the biggest efficiency of distance is the highest；Gradient magnetic generator 10, by producing respectively based on three axle X under Dikal coordinate system, Y, the gradient coil composition of the gradient magnetic of Z-direction, is called X-axis gradient coil, Y-axis gradient coil, Z axis gradient coil；Gradient magnetic generator 10 is embedded in the resonator cavity of high-frequency resonant cavity antenna 20, and from Gauss law, by the clean magnetic flux of any closed surface always 0, the magnetic line of force always closes；Then, space and high-frequency resonant cavity antenna 20 shared by gradient magnetic generator 10 share, and make use of available space to a greater extent, the compactest in structure；In the case of gross thickness is identical, increases the first radioshielding layer 24 and spacing of the second radioshielding layer 26 than traditional scheme, thus improve the efficiency of high frequency antenna, and the performance of gradient coil does not has any impact, beneficially image quality；If the efficiency of high-frequency resonant cavity antenna 20 keeps equal, then the first radioshielding layer 24 can reduce with the spacing of the second radioshielding layer 26, that is to say that the gross thickness of magnetic field generator can be less；More compact construction saves space, reduces magnet weight, provides cost savings, makes shimming more preferable, beneficially image quality；Or the magnet that manufactures of identical cost can be bigger, open the most comfortable to the space of patient.
Simultaneously, because gradient magnetic generator 10 embeds high-frequency resonant cavity antenna 20, gradient magnetic generator 10 and high-frequency resonant cavity antenna 20 common resonant cavity space, the first radioshielding layer 24 and the second radioshielding layer 26 can effectively armoured magnetic field on gradient magnetic generator 10 and the impact of high-frequency resonant cavity antenna 20；And magnetic field generator uses and goes vortex design, can effectively reduce eddy-current loss, improve efficiency；Gradient magnetic generator 10 and the design of high-frequency resonant cavity antenna 20 common resonant cavity space, can reduce the size of magnet, reduce magnet weight, thus reduce magnet cost so that shimming is more preferable, beneficially image quality.
In the present embodiment, gradient magnetic generator 10 is completely embedded into high-frequency resonant cavity antenna 20；Gradient magnetic generator 10 is arranged in the resonator cavity between the first radioshielding layer 24 and the second radioshielding layer 26.
In the present embodiment, the first radioshielding layer 24 is circular or octagon and above centrosymmetry regular polygon.
In the present embodiment, the first radioshielding layer 24 and the second radioshielding layer 26 can be all metal foil surfaces.
In the present embodiment, the first radioshielding layer 24 and the second radioshielding layer 26 may select and offer stria, and multiple stria radially distributes.Metal forming is not cut off by stria completely, and polylith the first radioshielding layer 24 separated still links together at middle section, and ground connection, prevents Accumulating charge in metal forming, produces electric discharge phenomena；Radial stria, can angle arbitrarily, and the stria on the two sides of same metal forming sheet material is misaligned, is reducing the shield effectiveness that eddy-current loss has kept simultaneously.Being welded with electric capacity 22 on the both sides of corresponding stria makes stria both sides in the electrical connection of high band, forms high-frequency resonant cavity, produce high-frequency resonant magnetic field together with the electric capacity 22 between first radioshielding layer the 24, second radioshielding layer 26 and two-layer screen layer.
Fig. 4 shows second embodiment of the present invention.
Referring to shown in Fig. 4, this embodiment with the difference of first embodiment is:
Gradient magnetic generator 10 is partially submerged into high-frequency resonant cavity antenna 20, and the first radioshielding layer 24 is arranged at the middle part of magnetic field generator；First radioshielding layer 24 is parallel with the second radioshielding layer 26 place plane, and the second radioshielding layer 26 is between the Z-gradient coil and X, Y-gradient coil of gradient magnetic generator 10.Being dispersed with electric capacity 22 element between two-layer radioshielding layer, the two ends of electric capacity 22 element electrically connect with the first radioshielding layer 24 and the second radioshielding layer 26 respectively；First radioshielding layer 24 and the second radioshielding layer 26 and the electric capacity between them 22 element define resonator cavity.The Z-gradient coil of gradient magnetic generator 10 is embedded in the resonator cavity between the first radioshielding layer 24 and the second radioshielding layer 26.The structure of other parts is identical with previous embodiment, omits herein.
On the one hand such structure is easy to structure design and processing technique, and on the other hand, the conductor filled in high-frequency resonant cavity can cause reducing relative to the more energy loss of nonmetal medium and efficiency；Under some occasion, X, the wire density of Y-axis gradient coil is relatively big, they being coupled to loss that resonator cavity brings and the space shared by X, Y-axis gradient coil shares the efficiency raising brought to high-frequency resonant cavity offseting with high-frequency resonant cavity.
Fig. 5, Fig. 6 show the 3rd embodiment of the present invention.
Referring to shown in Fig. 5, Fig. 6, this embodiment with the difference of the second embodiment is: concave setting in the middle part of the second radioshielding layer 26, and the middle part of the second radioshielding layer 26 be arranged in parallel with the first radioshielding layer 24 respectively with periphery；The middle part of the Z-gradient coil of gradient magnetic generator 10 embeds in the resonator cavity between the first radioshielding layer 24 and the second radioshielding layer 26, and the periphery of the second radioshielding layer 26 is positioned at Z-gradient coil upper surface.The structure of other parts is identical with previous embodiment, omits herein.
Magnetic resonance equipment works when, high-frequency resonant cavity antenna 20 is negligible on the impact of gradient magnetic generator 10, generally uses symmetric design and anti-vortex design to ensure.Gradient magnetic produced by gradient coil is the whole imaging space penetrating the region including that high frequency magnetic field covers, but it does not hinder the normal work of high-frequency emission antenna.And gradient magnetic generator 10 is mainly reflected in distribution and the efficiency of high frequency antenna of radio-frequency (RF) magnetic field to the impact of high frequency antenna and the radio-frequency (RF) magnetic field of generation thereof.The symmetrical design of gradient magnetic generator 10 essentially eliminates the impact of the distribution on high frequency magnetic field；Eliminate gradient coil as much as possible and the coupling of high frequency antenna be will assist in efficiency and the distribution of protection high frequency magnetic field improving high frequency antenna.This structure can mask the part of the gradient coil high density conductor bigger on the impact of high-frequency resonant cavity antenna 20 as far as possible, and less for conductor in gradient coil space is shared to high-frequency resonant cavity antenna 20, expand the space of resonator cavity more to greatest extent, thus improve quality factor and the efficiency of high-frequency resonant cavity antenna 20.
Fig. 7 shows the 4th embodiment of the present invention.
Referring to shown in Fig. 7, this embodiment with the difference of the second embodiment is: gradient magnetic generator 10 also includes Z shielding-gradient coil；Second radioshielding layer 26 be arranged in parallel with the first radioshielding layer 24；The middle part of the Z-gradient coil of gradient magnetic generator 10 embeds in the resonator cavity between the first radioshielding layer 24 and the second radioshielding layer 26, and the second radioshielding layer 26 now is planar design.Certainly, in X-gradient coil, Y-gradient coil, the middle part of at least one gradient coil also can embed in resonator cavity, now the medial recess design of the second radioshielding layer 26.In some occasion applied, the active shielding coils increasing Z axis gradient can preferably eliminate the eddy current that gradient coil produces.The structure of other parts is identical with previous embodiment, omits herein.
Fig. 8 shows the 5th embodiment of the present invention.
Referring to shown in Fig. 8, this embodiment with the difference of the second embodiment is: gradient magnetic generator 10 also includes X shielding-gradient coil, Y shielding-gradient coil and Z shielding-gradient coil；Second radioshielding layer and the first radioshielding layer be arranged in parallel；In in the X-gradient coil of gradient magnetic generator 10, Y-gradient coil and Z-gradient coil, at least one embeds the resonator cavity between the first radioshielding layer 24 and the second radioshielding layer 26, the second radioshielding layer 26 now is planar design.Certainly, in Z-shielded gradient coil and Y shielding-gradient coil, the middle part of at least one also can embed resonator cavity, now the medial recess design of the second radioshielding layer 26.The structure of other parts is identical with previous embodiment, omits herein.
A kind of magnetic resonance equipment, uses above-mentioned magnetic field generator to carry out medical examination；Two panels magnetic field generator generally can be used staggered relatively relative to magnet center；Around space in, the two superposition produces the gradient magnetic needed for nuclear magnetic resonance and high frequency magnetic field.
The foregoing is only presently preferred embodiments of the present invention, all impartial changes done according to scope of the invention as claimed and modification, all should belong to the covering scope of the claims in the present invention.
Claims (10)
1. a magnetic field generator, including gradient magnetic generator and high-frequency resonant cavity antenna, it is characterized in that, described high-frequency resonant cavity antenna includes the filled media layer in the resonator cavity between electric capacity, the first radioshielding layer electrically connected respectively and the second radioshielding layer and described first radioshielding layer and the second radioshielding layer with electric capacity each corresponding end；Described gradient magnetic generator is embedded gradient magnetic generator, and described second radioshielding layer shields the embedded part of described gradient magnetic generator and is not embedded into part.
Magnetic field generator the most according to claim 1, it is characterised in that described gradient magnetic generator includes that X-gradient coil, Y-gradient coil and Z-gradient coil, described gradient magnetic generator are completely embedded into described high-frequency resonant cavity antenna；Described gradient magnetic generator is arranged in the resonator cavity between described first radioshielding layer and the second radioshielding layer.
Magnetic field generator the most according to claim 1, it is characterized in that, described gradient magnetic generator includes X-gradient coil, Y-gradient coil and Z-gradient coil, described gradient magnetic generator is partially submerged into described high-frequency resonant cavity antenna, and described first radioshielding layer is arranged at the middle part of magnetic field generator.
Magnetic field generator the most according to claim 3, it is characterized in that, described first radioshielding layer and the second radioshielding layer place plane are parallel, and the middle part of the Z-gradient coil of described gradient magnetic generator embeds in the resonator cavity between described first radioshielding layer and the second radioshielding layer.
Magnetic field generator the most according to claim 3, it is characterised in that concave setting in the middle part of described second radioshielding layer, and the middle part of described second radioshielding layer be arranged in parallel with the first radioshielding layer respectively with periphery；The middle part of the Z-gradient coil of described gradient magnetic generator embeds in the resonator cavity between described first radioshielding layer and the second radioshielding layer, and the periphery of described second radioshielding layer is positioned at described Z-gradient coil upper surface.
Magnetic field generator the most according to claim 3, it is characterised in that described gradient magnetic generator also includes Z shielding-gradient coil；Described second radioshielding layer and the first radioshielding layer be arranged in parallel；The middle part of the Z-gradient coil of described gradient magnetic generator embeds in the resonator cavity between described first radioshielding layer and the second radioshielding layer.
Magnetic field generator the most according to claim 6, it is characterized in that, described second radioshielding layer and the first radioshielding layer be arranged in parallel, and described second radioshielding layer medial recess is arranged, in described X-gradient coil and Y-gradient coil, the middle part of at least one gradient coil embeds the resonator cavity between described first radioshielding layer and the second radioshielding layer.
Magnetic field generator the most according to claim 3, it is characterised in that described gradient magnetic generator also includes X shielding-gradient coil, Y shielding-gradient coil and Z shielding-gradient coil；Described second radioshielding layer and the first radioshielding layer be arranged in parallel；In in the X-gradient coil of described gradient magnetic generator, Y-gradient coil and Z-gradient coil, at least one embeds the resonator cavity between described first radioshielding layer and the second radioshielding layer.
Magnetic field generator the most according to claim 8, it is characterized in that, described second radioshielding layer and the first radioshielding layer be arranged in parallel, and described second radioshielding layer medial recess is arranged, in described Z shielding-gradient coil and Y shielding-gradient coil and X shielding-gradient coil in resonator cavity between at least one the middle part described first radioshielding layer of embedding and the second radioshielding layer.
10. a magnetic resonance equipment, it is characterised in that described magnetic resonance equipment includes the magnetic field generator described in right 1-9 any one.
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| Publication number | Priority date | Publication date | Assignee | Title |
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| CN109085520A (en) * | 2017-06-14 | 2018-12-25 | 西门子保健有限责任公司 | Magnetic resonance shield unit |
| CN110070973A (en) * | 2019-06-19 | 2019-07-30 | 西南应用磁学研究所 | A kind of high speed YIG bulk bandstop filter |
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| CN1550788A (en) * | 2003-03-25 | 2004-12-01 | Magnetic fields generator and magnetic resonance apparatus with the same | |
| CN1580804A (en) * | 2003-08-05 | 2005-02-16 | 西门子公司 | Magnetic field generator and magnetic resonator with same |
| CN1641373A (en) * | 2003-10-06 | 2005-07-20 | 西门子公司 | Magnetic fields generator and magnetic resonance device thereof |
| US20050162167A1 (en) * | 2004-01-23 | 2005-07-28 | Oliver Heid | Generator of a time-variable magnetic field and magnetic resonance device |
| 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 |
| CN205787069U (en) * | 2016-05-25 | 2016-12-07 | 杜健军 | Magnetic field generator and there is the magnetic resonance equipment of this magnetic field generator |
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| CN109085520A (en) * | 2017-06-14 | 2018-12-25 | 西门子保健有限责任公司 | Magnetic resonance shield unit |
| US10534051B2 (en) | 2017-06-14 | 2020-01-14 | Siemens Healthcare Gmbh | MR radio-frequency shielding unit |
| CN110070973A (en) * | 2019-06-19 | 2019-07-30 | 西南应用磁学研究所 | A kind of high speed YIG bulk bandstop filter |
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