CN100558296C - High frequency winding assembly and MR imaging apparatus - Google Patents
High frequency winding assembly and MR imaging apparatus Download PDFInfo
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- CN100558296C CN100558296C CNB2005101216771A CN200510121677A CN100558296C CN 100558296 C CN100558296 C CN 100558296C CN B2005101216771 A CNB2005101216771 A CN B2005101216771A CN 200510121677 A CN200510121677 A CN 200510121677A CN 100558296 C CN100558296 C CN 100558296C
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Abstract
High frequency winding assembly of the present invention has the 1st high frequency coil, the 2nd high frequency coil and the 3rd high frequency coil.The 1st high frequency coil receives the 1st magnetic resonance signal from subject.The 2nd high frequency coil receives from the 1st magnetic resonance signal of subject and at least one of the 2nd magnetic resonance signal.The 3rd high frequency coil receives at least one from the 1st magnetic resonance signal, the 2nd magnetic resonance signal and the 3rd magnetic resonance signal of subject.And the 3rd high frequency coil has at least one the different shape with the 1st high frequency coil and the 2nd high frequency coil, makes to improve the imaging region local sensitivity.
Description
Technical field
The present invention relates to a kind ofly collect based on the high frequency winding assembly of the magnetic resonance signal of magnetic resonance phenomenon and have the MR imaging apparatus of this high frequency winding assembly from the examinee.
Background technology
The nuclear magnetic resonance of being undertaken by magnetic resonance (MRI) camera head is that magnetic pumping is carried out in the nuclear spin that a kind of high-frequency signal that adopts its Larmor frequency is opposite to the examinee in the magnetostatic field, is carried out the camera method of composition by magnetic resonance (MR) signal that produces along with this excitation again.
In order to implement this camera method, magnetic resonance imaging apparatus have the static field magnet that produces magnetostatic field and according to the rules pulse sequence leaning magnetic field pulse and high frequency magnetic field pulse are put on examinee's mechanism.Wherein, the leaning magnetic field pulse by in the internal diameter that is disposed at static field magnet and the gradient magnetic field coil that is connected with the leaning magnetic field power supply send to the examinee.In addition, for the high frequency magnetic field pulse too, by in the internal diameter that is disposed at static field magnet and the emission that is connected with emitter send to the examinee with high frequency coil.On the other hand, in order to receive the magnetic resonance signal that forms by the high-frequency signal that sends from the examinee, and will receive with high frequency coil be configured in the examinee near.Also emission can be made a coil with high frequency coil and reception with the high frequency coil dual-purpose, but in most cases, diagnose the position and adopt special-purpose the reception to use high frequency coil for difference.
For example, in order to obtain the sensitivity preferable image, with high frequency coil the region-of-interest that a plurality of surface coils (array coil) are disposed at the examinee is carried out imaging as receiving.For example, disclosed as the vertebra coil as Japanese kokai publication hei 5-261081 communique, propose a kind of the QD surface coils to be arranged in array coil on the axon direction.This array coil as shown in figure 30.
Here the QD surface coils is described.As shown in figure 31, QD coil 120 is with annular surface coil 121 and 8 font surface coils, 122 stacked coils.Because the high frequency magnetic field summation that produces mutually in the loop is 0, so can overlay configuration become decoupling zero (de-coupling) state.If when on A-A` line section, seeing the direction of the high frequency magnetic field B1 that 2 coils 121,122 produce, shown in figure 32, can see its quadrature on direction of principal axis.At this moment, independent mutually from coil 121,122 clutter separately, if signal is moved 90 ° and sue for peace, then SNR becomes as follows.
SNR=(B1 (loop)
2+ B1 (8 font)
2)
(1/2)
In Figure 33, show the feature of the SNR on 121,122 of each coils.That is, long dotted line is represented the SNR curve of loop type surface coils 121, and short dash line is represented the curve of 8 font surface coils 122, and solid line is for moving 90 ° of also curves of the SNR of the QD surface coils 120 of summation.The SNR of initial QD surface coils 120 equates that at the SNR of annular surface coil 121 and 8 font surface coils 122 place becomes 2
(1/2)SNR doubly, as can be seen, in very large range its SNR is higher than 2 coils 121,122.The SNR that uses such QD surface coils 120 can reach when using loop type surface coils and 8 font surface coils respectively is higher.
On the other hand, to whole abdominal part imaging the time, shown in TOHKEMY 2003-334177 communique, dispose a plurality of surface coils usually and surround those who are investigated, from whole abdominal part received signal.As this surface coils, as shown in figure 34, adopt disposed the array coil that a plurality of loop coils (loop coil) form along body surface more.
Like this, because dispose a plurality of surface coils, so can obtain image in each position sensitivity the best according to the imaging position.Yet on the other hand, owing to be necessary all to set coil for each position, so coil number increases, the operator need be according to each patient's variation, according to imaging position emat coil more.Becoming like this to possess a lot of coils, and is very loaded down with trivial details operation for the doctor at scene or technician.
Therefore, in the reception of prior art occasion, owing to, adopts different special-purpose array structures, so replacing array coil when operator (doctor or technician) need change at each imaging position for the kind at each imaging position with high frequency coil.This replacing operation is very numerous and diverse and time-consuming for the operator.Therefore, the burden of operator's beamhouse operation not only, and become the low big reason of patient's prescription on individual diagnosis rate.
In recent years, developed the scheme that adopts following manner to make the SNR raising of QD surface coils, that is, a plurality of loop coils are disposed in decoupling zero mutually, and will be positioned at the loop coil and the 8 font coil overlay configuration that are crossed as 8 fonts of its central part.To organize this coil more and be provided in and set on the orthogonal direction of direction with loop coil and the forming array coil places this array coil on the top board, and come examinee's vertebra is carried out imaging.
Yet because there is individual variation in the examinee, most cases is, faces upward when lying towards top board the examinee, and its vertebra can be positioned at apart from top board, i.e. deep (far away) position of array coil.For example, this position may become 10cm.In this case, under the situation of above-mentioned 8 font coils are only overlapping with the central part loop coil and the coil that is configured to, exist from the signal collection insufficient sensitivity of the vertebra of depths and the low problem of SNR.
On the other hand, when adopting vertebra shown in Figure 35 to use coil, 4 QD surface coils QD1, QD2, QD3, QD4 are set up in parallel in the axon direction.Yet, shared reception at the magnetic resonance signal that the axon direction is emitted from the each several part of long vertebra by a plurality of surface coils, like this because the imaging scope is wide, so it is limited to improve the degree of local pick-up sensitivity.
In addition, the consideration coil unit that will set 4 similar face coils uses along the direction configuration that intersects with the axon direction.In view of the above, can receive the signal that the vertebra part is emitted, can improve relevant this partial imaging sensitivity by 4 surface coils.
Yet, when with 4 similar face coil configuration during, because the distance of outer surface coil and vertebra will become greatly, so can not obtain enough sensitivity at last in the direction of intersecting with the axon direction.That is,, probably can not reach the raising of the enough imaging sensitivity of being envisioned although have 4 surface coils.
Summary of the invention
The present invention proposes in order to solve above-mentioned the problems of the prior art, its objective is that providing a kind of can reduce the time that receives with high frequency coil of changing to examinee's different parts (being typically vertebra and abdominal part) imaging the time, and, can collect the high frequency winding assembly of magnetic resonance signal and have the MR imaging apparatus of this high frequency winding assembly with the suitableeest sensitivity at each position.
The invention provides a kind of high frequency winding assembly, have: 2 interior annular coils; 2 exterior annular coils that clip above-mentioned 2 interior annular coils and set, wherein above-mentioned 2 interior annular coils are littler than above-mentioned 2 exterior annular coils at least 4 that contain above-mentioned 2 interior annular coils and above-mentioned 2 the exterior annular coils toroidal width that set on the direction respectively, each above-mentioned toroidal and above-mentioned central shaft that sets the orthogonal direction of direction sees that from the direction of intersecting with above-mentioned toroidal anchor ring linearly shape sets.
The invention provides a kind of high frequency winding assembly, have: 2 loop coils in the outside are positioned at least 4 loop coils that clip inboard 2 toroidal positions and set, each above-mentioned toroidal central shaft that sets the orthogonal direction of direction with it sees that from the direction of intersecting with above-mentioned toroidal anchor ring linearly shape sets; With the 1st synthesis unit that is combined to inboard 2 above-mentioned loop coils output signal separately; The 2nd synthesis unit of 2 the above-mentioned loop coils in anti-phase synthetic outside output signal separately; The output signal of above-mentioned the 2nd synthesis unit is carried out being synthesized to the unit of the output signal of above-mentioned the 1st synthesis unit after the 90 degree phase shifts.
In order to achieve the above object, the high frequency winding assembly that the present invention relates to has: receive the 1st high frequency coil from the 1st magnetic resonance signal of subject; Reception is from least one side's of above-mentioned the 1st magnetic resonance signal of subject and the 2nd magnetic resonance signal the 2nd high frequency coil; Reception is from least one side of above-mentioned the 1st magnetic resonance signal and above-mentioned the 2nd magnetic resonance signal and the 3rd magnetic resonance signal of above-mentioned subject, and has the shape different with above-mentioned the 1st high frequency coil and at least one side of the 2nd high frequency coil and make the 3rd high frequency coil that improves local sensitivity in the photography zone.
In addition, high frequency winding assembly of the present invention, receive and be opposite in proper order in accordance with regulations the leaning magnetic field pulse that the examinee applied of magnetostatic field and the high frequency magnetic resonance signal that the high frequency magnetic field pulse produces accordingly in this examinee, wherein, have at least a plurality of along the 1st direction in abutting connection with the 1st high frequency coil that sets and textural respectively with the 2nd high frequency coil of these a plurality of the 1st high frequency coil decoupling zeros.
In addition, high frequency winding assembly of the present invention, upper coil assembly and lower coil assembly with relative configuration with the examinee who places magnetostatic field, and in this upper coil assembly and lower coil assembly, can receive the high frequency magnetic resonance signal that leaning magnetic field pulse that the examinee applied and high frequency magnetic field pulse is produced accordingly with order in accordance with regulations in this examinee, wherein, above-mentioned lower coil assembly has at least: a plurality of the 1st high frequency coils that set along the 1st direction adjacency; Textural respectively with the 2nd high frequency coil of these a plurality of the 1st high frequency coil decoupling zeros.
In addition, high frequency winding assembly of the present invention, upper coil assembly and lower coil assembly with relative configuration with the examinee who places magnetostatic field, and in this upper coil assembly and lower coil assembly, can receive the high frequency magnetic resonance signal that leaning magnetic field pulse that the examinee applied and high frequency magnetic field pulse is produced accordingly with order in accordance with regulations in this examinee, wherein, above-mentioned upper coil assembly has at least: a plurality of the 1st high frequency coils that set along the 1st direction adjacency; Textural respectively with the 2nd high frequency coil of these a plurality of the 1st high frequency coil decoupling zeros.
Further, the present invention also provides a kind of MR imaging apparatus that comprises the high frequency winding assembly with these structures.
Further, high frequency winding assembly of the present invention, receive and be opposite in proper order in accordance with regulations the leaning magnetic field pulse that the examinee applied of magnetostatic field and the high frequency magnetic resonance signal that the high frequency magnetic field pulse produces accordingly in this examinee, wherein, have a plurality of along prescribed direction in abutting connection with the loop coil that sets, and intersected the cross coil of shape of the number of times that is equal to or greater than above-mentioned a plurality of toroid number of turns with at least one the loop coil overlay configuration and having in these a plurality of loop coils.
Further, high frequency winding assembly of the present invention, receive and be opposite in proper order in accordance with regulations the leaning magnetic field pulse that the examinee applied of magnetostatic field and the high frequency magnetic resonance signal that the high frequency magnetic field pulse produces accordingly in this examinee, wherein, have a plurality of along prescribed direction in abutting connection with the loop coil that sets, and intersected 3 times or the cross coil of above shape with at least one the loop coil overlay configuration and having in these a plurality of loop coils.
In addition, in order to achieve the above object, high frequency winding assembly of the present invention, have 2 interior annular coils and clip above-mentioned 2 interior annular coils and 2 exterior annular coils setting, above-mentioned 2 interior annular coils are littler than the described loop coil in above-mentioned 2 outsides at least 4 that comprise above-mentioned 2 interior annular coils and 2 above-mentioned exterior annular coils toroidal width and the anchor ring areas that set on the direction respectively.
In addition, high frequency winding assembly of the present invention, have the 2nd synthesis unit in the 1st synthesis unit of at least 4 loop coils that set 2 exterior annular coils on the position that clips 2 interior annular coils, a homophase Synthetic 2 described exterior annular coil output signal separately, an anti-phase Synthetic 2 described exterior annular coil output signal separately, will the above-mentioned the 1st and the 2nd synthesis unit output signal separately mutual synthetic unit after either party's phase shift 90 is spent.
In addition, high frequency winding assembly of the present invention, have 2 interior annular coils and clip above-mentioned 2 interior annular coils and 2 exterior annular coils setting, above-mentioned 2 interior annular coils are littler than above-mentioned 2 exterior annular coils at least 4 that comprise above-mentioned 2 interior annular coils and 2 the above-mentioned exterior annular coils toroidal width that set on the direction respectively.
In addition, high frequency winding assembly of the present invention, have the 1st loop coil, and the 2nd loop coil that sets with above-mentioned the 1st loop coil adjacency, in above-mentioned the 1st loop coil and the 2nd loop coil is littler than another at above-mentioned the 1st loop coil and the above-mentioned the 2nd toroidal width and the anchor ring area that sets on the direction.
Further, the present invention also provides a kind of MR imaging apparatus that comprises the high frequency winding assembly with these structures.
Like this, according to high frequency winding assembly of the present invention and have the MR imaging apparatus of this high frequency winding assembly, not only can alleviate the burden in operator (doctor or the technician) preparation work, and can improve patient's prescription on individual diagnosis rate.
Description of drawings
The block diagram of the schematic configuration of the MR imaging apparatus that Fig. 1 relates to for expression the present invention the 1st embodiment;
Fig. 2 is the pattern configurations figure that becomes a coil block of the surface coils that is adopted among the 1st embodiment;
Fig. 3 is assembled into the allocation plan of the pattern configurations of the cross coil in the coil block of the 1st embodiment for expression;
Fig. 4 is the key diagram of the magnetic line of force direction that cross coil produced shown in Figure 3;
The figure of the configuration example when Fig. 5 is used for vertebra the coil block of the 1st embodiment as the human body back side imaging at center for the direction explanation that produces with reference to the magnetic line of force;
Fig. 6 is the coil block that sets a plurality of the 1st embodiment coil configuration figure along the axon direction when forming the bottom high frequency winding assembly;
The pattern diagram that Fig. 7 installs for the decoupling zero circuit between a plurality of coil blocks of expression;
Fig. 8 is the figure of an example of expression decoupling zero circuit;
Fig. 9 will adopt the top high frequency winding assembly of coil block of the 1st embodiment and the figure that the bottom high frequency winding assembly is disposed at the axial plane of examinee's body for expression;
Figure 10 is used for the general flowchart of the processing of data is collected in each receiving channels selection/non-selection for expression;
Figure 11 makes the figure of bottom high frequency winding assembly (holding components) according to the crooked configuration example of examinee's back shape for expression;
Figure 12 is the ideograph of another coil configuration example of the coil block of the 1st variation of expression the 1st embodiment;
Figure 13 is the figure of another example of the decoupling zero circuit of the coil block of the 2nd variation of expression the 1st embodiment;
Figure 14 is used to carry out the figure of the coil configuration example of the cross coil decoupling zero each other between a plurality of coil blocks of the adjacency that the 3rd variation of the 1st embodiment relates to for expression;
Figure 15 is used to carry out the figure of the coil configuration example of the cross coil decoupling zero each other between a plurality of coil blocks of the adjacency that the 4th variation of the 1st embodiment relates to for expression;
Figure 16 is the figure of the top high frequency winding assembly of the 5th variation of expression the 1st embodiment;
Figure 17 is disposed at top high frequency winding assembly shown in Figure 16 and bottom high frequency winding assembly for expression the figure of the axial plane of examinee's body;
Figure 18 is the figure of the coil block of the 6th variation of expression the 1st embodiment;
Figure 19 is the figure of the MR imaging apparatus structure of expression the present invention the 2nd embodiment;
Figure 20 is the figure of the toroidal configuration status in the high frequency winding assembly among expression Figure 19;
Figure 21 is the toroidal anchor ring area among expression Figure 20 and the figure of lap area;
Figure 22 is the structure chart of the signal processing circuit of the high frequency winding assembly among expression Figure 19;
The figure of the axial section of the subject P when Figure 23 adopts MR imaging apparatus shown in Figure 19 that the subject vertebra is carried out imaging for expression and the position relation of high frequency winding assembly 107;
Figure 24 is the figure of the MR imaging apparatus structure of expression the present invention the 3rd embodiment;
Figure 25 is the figure of the state that sets of the coil groups of the high frequency winding assembly among expression Figure 24;
Figure 26 is the figure of the installment state of expression decoupling zero circuit;
The figure of the axial section of the subject P when Figure 27 adopts MR imaging apparatus shown in Figure 24 that subject vertebra and abdominal part are carried out imaging for expression and the position relation of high frequency winding assembly;
Figure 28 is the figure of the axial section of the example of the crooked high frequency winding assembly of expression;
Figure 29 is the figure of the axial section of the example of the crooked high frequency winding assembly of expression;
Figure 30 for the expression prior art the QD surface coils and be listed in the figure that the axon direction forms the example of array coil;
Figure 31 is the figure of the QD surface coils of expression prior art;
Figure 32 is the figure of the high frequency magnetic field of the QD surface coils generation of explanation prior art;
Figure 33 is the figure of the SNR of the QD surface coils of explanation prior art;
The for example abdominal part that Figure 34 surrounds the examinee for explanation disposes the figure of configuration example of the QD surface coils of a plurality of prior aries; And
Figure 35 is the figure of the QD surface coils structure of expression prior art.
The specific embodiment
With reference to the accompanying drawings high frequency winding assembly of the present invention and embodiment with MR imaging apparatus of this high frequency winding assembly are described.
The 1st embodiment
MR imaging apparatus below with reference to Fig. 1～9 couple the 1st embodiment of the present invention describes.
Fig. 1 shows the nuclear magnetic resonance (MRI: nuclear magnetic resonance) Zhuan Zhi schematic configuration that the 1st embodiment relates to.
This MR imaging apparatus have mounting examinee P platform for sleeping in portion, produce magnetostatic field the magnetostatic field generating unit, be used for to the magnetostatic field additional location information leaning magnetic field generating unit, the receiving and transmitting part of transmitting-receiving high-frequency signal, control system is all and reconstruct the control calculating part of image.
The magnetostatic field generating unit for example have the superconduct formula Magnet 1, provide the magnetostatic field power supply 2 of electric current to this Magnet 1, and at direction of principal axis (Z-direction) the generation magnetostatic field H of the peristome cylindraceous that imports examinee P (space use in diagnosis)
0In addition, be provided with the shim coil (not shown) in this Magnet portion.Platform portion for sleeping in can insert the top board T of mounting examinee P the peristome of Magnet 1 in the mode that can draw back.
The leaning magnetic field generating unit has the gradient magnetic field coil unit 3 that is contained in the Magnet 1.This gradient magnetic field coil unit 3 has and is used to produce mutually orthogonal X-direction, Y direction, and 3 groups of (kind) x of the leaning magnetic field of Z-direction, y, z coil 3x～3z.Leaning magnetic field portion also has to x, y, and z coil 3x～3z provides the leaning magnetic field power supply 4 of electric current.This leaning magnetic field power supply 4 is provided at x based on the control of sequencer 5 described later, y, the pulse current of generation leaning magnetic field among z coil 3x～3z.
By controlling by leaning magnetic field power supply 4 to x, y, the pulse current that z coil 3x～3z is provided is that 3 leaning magnetic fields of tieing up axle (X-axis, Y-axis, Z axle) directions synthesize with physical axis, can at random set change by mutually orthogonal slice direction leaning magnetic field Gs, phase-encoding direction leaning magnetic field G
E, and read direction (frequency coding direction) leaning magnetic field G
RThe logic direction of principal axis that forms.Slice direction, phase-encoding direction and each leaning magnetic field and the magnetostatic field H that read direction
0Overlaid.
Further, the control calculating part has sequencer (also being called sequence controller) 5, master computer 6, computing unit 10, memory element 11, display 12 and loader 13.Wherein, master computer 6 has according to saved software program (not shown) and provides the pulse train information command to sequencer 5, coordinates the function of the work of whole device simultaneously.
In addition, computing unit 10 is imported the numerical data (being also referred to as initial data or primary data) of receptor 8R output by sequencer 5, this numerical data is disposed in the k space (being also referred to as fourier space or frequency space) of its internal storage, every group of these data are carried out two dimension or three dimensional fourier transform and reconstruct being real space image.In addition, as required, computing unit 10 also can be handled and the Difference Calculation processing synthesizing about the data of image.In this synthetic processing, comprise each pixel is carried out additive operation, maximum projection (MIP) processing etc.
Below the reception in the above-mentioned formation is described in more detail with high frequency coil 7R.
This reception can be used for the reception of the vertebra of examinee P and abdominal part both sides' magnetic resonance signal with high frequency coil 7R in the 1st embodiment, and, as constituting with the surface coils that signal collection is carried out in the suitableeest sensitivity respectively to vertebra and abdominal part.
Particularly, receive and to use high frequency coil 7R, shown in Fig. 1 pattern, have and be configured to such an extent that can obtain the top high frequency winding assembly 7U and the bottom high frequency winding assembly 7L (7L1,7L2,7L3,7L4) of view data of the desired area of examinee P.In fact each of this coil block 7U and 7L formed by a plurality of element coil of aftermentioned, and be sent to receptor 8R respectively by the magnetic resonance signal that each element coil receives.
Receptor 8R has the corresponding receiving channels of coil number with top high frequency winding assembly 7U and bottom high frequency winding assembly 7L, provides magnetic resonance signal by each surface coils to each receiving channels.Therefore, can be by the data of each receiving channels output digital quantity corresponding with magnetic resonance signal.
Give computing unit 10 by the data that this each receiving channels is collected via sequencer 5.Computing unit 10 reconstructs the collection data that receive and the view data of rise time.Reconstruct in the process at this, for example each receiving channels is reconstructed processing separately from receiving with the collected data of each coil of high frequency coil 7R, taking advantage of with square root computing to be synthesized by 2 is an image.
At this, bottom high frequency winding assembly 7L is set at and faces upward under the state of lying side (imaging region bottom) in the back of the examinee P of scanning, when for example the vertebra of examinee P being scanned, only uses these coil blocks 7L.Usually this bottom high frequency winding assembly 7L is arranged on the top board T.On the other hand, when the abdominal part as examinee's body is carried out imaging, along examinee P body surface top high frequency winding assembly 7U is set, and adopt among this top high frequency winding assembly 7U and the bottom high frequency winding assembly 7L:7L1～7L4 a part of coil block for example coil block 7L1 carry out the scanning of abdominal part.That is, in the 1st embodiment, a part of coil block among the high frequency winding assembly 7L of bottom is that 7L1 constitutes the scanning that is used for a plurality of bodies (cervical vertebra and abdominal part).
In the 1st embodiment, top high frequency winding assembly 7U and bottom high frequency winding assembly 7L1～7L4 are formed by a plurality of element coil respectively.The group of these a plurality of element coil is called coil block.
Fig. 2 represents the example of coil block.Each coil block by 3 loop coils (the 1st element coil 20,21,22) that are array-like configuration and with these loop coil 20～22 overlay configuration and textural be that the cross coil (the 2nd element coil) 23 of split constitutes.As an example of these element coil, for example form, and the support member of the regulation shape that is formed by plastic material keeps with FPC.
The signal that is detected by these element coil 20～23 is delivered to coaxial cable by the tuning integrated circuit of coil separately, is connected with receptor 8R independently of each other by this coaxial cable.
In order to suppress the electric coupling with the adjacent annular coil, making the summation of high frequency magnetic field in loop of mutual generation is 0, and loop coil 20～22 is configured to the loop coil adjacent to each other suitable width (with reference to the W1 among Fig. 2) that only overlaps each other each other on certain orientation.
In addition, as an example of cross coil 23,, forms the element coil of 28 fonts connections so that 1 coil-conductor intersects 3 times mode.That is, on certain orientation, make 3 winding wire cross parts and form 4 coil surfaces.And, in that to make loop coil group and cross coil set direction consistent with each other and make under the state that the center C of their direction overlaps, in 4 coil surfaces that cross coil 23 is made, make 2 coil surface S1, S2 of central part and loop coil 20～22 overlapping.At this moment, 2 coil surface S1, S2 of central authorities form the loop coil 21 of crossing over central authorities, and across adjacent loop coil 20,22.That is, 2 of the central part of cross coil 23 coil surfaces and loop coil 20～22 eclipsed scope W2 are set greatlyyer than the loop coil 21 of central authorities.In other words, overlapping scope W2 is not the loop coil 21 of central part, but the loop coil 20,22 that also is adjacent is also overlapping, and covers the imaging region that equates with 3 loop coil 20～22 essence.
Wherein, if the quantity of a plurality of loop coil 20～22 is N, then single line circle conductors cross is become multi-turn 8 fonts and the crossing number of the cross coil 23 that forms is at least N time.
Fig. 3 and Fig. 4 are the figure that shows in detail the high frequency magnetic field of cross coil 23 generations.In cross coil 23, during in direction of arrow upper reaches overcurrent, producing magnetic field B 1 shown in Figure 4 as shown in Figure 3.As the 1st embodiment, become greatly (promptly at cross coil 23 and 3 loop coil 20～22 overlapping areas W2, form the imaging region that equates with 3 loop coil 20～22 essence) time, because the loop coil 21 of array direction central part not only, and on the axle of the loop coil 20,22 that is adjacent, also produce roughly orthogonal magnetic field, by synthesizing processing with signal from cross coil 23, the SNR on 20～22 of each loop coils is improved.
In addition, cross coil 23 forms the form of continuous 28 font coils.For this reason, adjust the cross shaped head of this cross coil 23, the magnetic line of force that produced from this cross coil 23 can be made as zero with the flux of interlinkage of loop coil 20～23 respectively.That is, can form the magnetic decoupling-structure between cross coil 23 and each loop coil 20～22.
As mentioned above, cross coil 23 produces roughly orthogonal high frequency magnetic field and obtains QD (quadrature) effect on 3 loop coils 20～22 central shaft separately.For this reason, if will be synthetic, then the same mutually, can improve SNR on the central shaft of each loop coil 20～22 (SN than) with the QD surface coils by the detected data of each loop coil 20～22 and cross coil 23.The raising situation of this SNR with only the resulting SNR of structure that the cross coil 23 and the loop coil 21 of central authorities intersect is compared, (uprising) improves.Therefore, the coil block that forms by loop coil 20～22 and cross coil 23 be used for vertebra to examinee P when scanning with fine.That is, face upward when lying, because its vertebra is positioned at (far away) position (also there is individual variation in the examinee) darker than coil, so need higher SNR at examinee P.
Become the bottom high frequency winding assembly 7L1 (～7L4) configuration as shown in Figure 5 of coil block.The configuration example of this figure is to adopt being applicable to vertebra is carried out the configuration example of the occasion of imaging as the human body back side at center shown in the axial section.Bottom high frequency winding assembly 7L1～7L4 is disposed at examinee 2 the back side, shows loop coil 20,21,22 and cross coil 23.In Fig. 5, coil 20～23 for example adopts the FPC that 2 single faces install or the FPC of 1 two-sided installation to form, and is fixed and is supported in the plastic holding components SP.
In each of this bottom high frequency winding assembly 7L1～7L4, as Fig. 2, Fig. 3, and the explanation of Fig. 4, on the axle of all loop coils 20～22, the high frequency magnetic field that high frequency magnetic field that each loop coil 20～22 produces and cross coil 23 produce is quadrature basically.Therefore, the signal of each coil is carried out respectively that image conversion is handled and synthetic, compare with the occasion of only central loop coil 21 being carried out QDization, can obtain extensively regional high-quality SNR image certainly with the occasion that only adopts the loop coil imaging.
Above-mentioned bottom high frequency winding assembly 7L1～7L4 is disposed at long axis direction (the axon direction of examinee P: Z-direction) of platform top board T for sleeping in shown in Figure 6.That is 4 bottom high frequency winding assembly 7L1～7L4 and being located at and the setting on the orthogonal direction of direction of loop coil 20～22 and cross coil 23.Thus, 4 bottom its orthogonal directions of high frequency winding assembly 7L1～7L4 consistent with the long axis direction (the axon direction of examinee P) of top board T and by mounting on top board T.
For two dimension magnetic decoupling zero between the adjacency coil that sets two-wayly, each surface coils is configured to only overlapped Rack.For loop coil, be difficult in order to prevent decoupling zero between coil that incline direction sets and carry out overlay configuration.Therefore, as shown in Figure 7, for example, adding decoupling zero circuit 55 respectively between loop coil 51 and the loop coil 52 and between loop coil 50 and loop coil 54.
Fig. 8 is the figure of an example of the decoupling zero circuit of presentation graphs 7.Inductance component L 1, L2 are connected in series with for example loop coil 52 and 53 respectively, by the part of overlapped configuration inductance component L 1, L2, and can decoupling zero between loop coil.
In the 1st embodiment, top high frequency winding assembly 7U also has the roughly the same structure with each bottom high frequency winding assembly 7L1～7L4.Fig. 9 illustrates the example that disposes this top high frequency winding assembly 7U along the abdominal part of examinee P.In the rear side of examinee P, dispose array-like bottom high frequency winding assembly 7L1～7L4 usually.So the coil block of the part of bottom high frequency winding assembly 7L1～7L4 is for example cooperated on 7L1 and top high frequency winding assembly 7U and can be carried out the collection of abdominal part signal.At this moment, Sheng Xia bottom high frequency winding assembly 7L2～7L4 does not carry out signal collection.
The described signal collection that do not carry out can be on receptor 8R multiplexer to be set, perhaps can in receptor 8R or computing unit 10, select non-selection to handle, make and do not adopt the magnetic resonance signal of sending here from remaining bottom high frequency winding assembly 7L2～7L4 according to software.
In Figure 10, show an example of the step when in receptor 8R or computing unit 10, selecting non-selection to handle according to software.Computing unit 10 reads in expression and image-forming condition and imaging position conditions such as (vertebra or the abdominal paries) information (step S1) of the receiving channels of definite selection (or non-selection) accordingly from master computer 6.Then, computing unit 10 judges whether commencing signal collection (step S2), if send the collection sign on, then receiving channels is switched to initial channel (step S3).
Here, receiving channels is set to the coil that belongs to upper and lower high frequency winding assembly 7U, 7L1～7L4.That is, in the 1st embodiment, because each coil block of upper and lower high frequency winding assembly 7U, 7L1～7L4 adopts Fig. 2 configuration structure, so have 4 channels * 5 group=20 channels.
In addition, if adopting the non-selection of described selection handles, still dispose with bottom high frequency winding assembly 7L1～7L4 from beginning at first at top high frequency winding assembly 7U, and when measuring vertebra, also can be only the collection data of the receiving channels that passed through bottom high frequency winding assembly 7L1～7L4 be optionally handled.
As mentioned above, according to the 1st embodiment, in receiving with high frequency coil 7R, the coil block of bottom high frequency winding assembly 7L1～7L4 can wish that the position carries out imaging to a plurality of examinee P a plurality of usually under the state that is equipped on top board T at least.That is, when the vertebra to certain examinee P carries out imaging, can adopt the magnetic resonance signal of bottom high frequency winding assembly 7L1～7L4 reception from the examinee.At this moment, each bottom high frequency winding assembly 7L1～7L4 not only constitutes as surface coils, and shown in Fig. 2,4, also disposes the cross coil 23 that covers the zone that equates with imaging region essence that loop coil 20～22 is born.Like this, in all loop coils 20～22, can bring into play the QD effect, so, with dispose the occasion that cross coil 23 makes central annular coils (loop coil 21 in Fig. 2 example) only have the QD effect as prior art and compare, the SNR of each bottom high frequency winding assembly 7L1～7L4 significantly improves, and sensitivity uprises.So, can collect the signal put of deep-seated more than examinee P.Therefore, even examinee P is fat slightly, vertebra is positioned at from top board T position far away, but also SNR carries out imaging to vertebra well.
Further, when shifting to other examinee P the abdominal part imaging, bottom high frequency winding assembly 7L1～7L4 can also be arranged on top high frequency winding assembly 7U the abdominal part side of examinee P under original state.Like this, bottom high frequency winding assembly 7L1～7L4 is positioned at the rear side of examinee P, and top high frequency winding assembly 7U is positioned at the abdominal part front side.At this moment,, select the collection signal of coil block 7L1 for example initial among the high frequency winding assembly 7L1～7L4 of bottom, do not select the collection signal of coil block 7L2～7L4 in addition according to the software processes of above-mentioned Figure 10.The result is that for abdominal part, top high frequency winding assembly 7U and bottom high frequency winding assembly 7L1 are positioned at and surround the abdominal part front-back direction, can carry out the good imaging of SNR to abdominal part.At this moment, top high frequency winding assembly 7U can also be configured to only be made of loop coil, and, in the coil block of bottom high frequency winding assembly 7L1, can adopt the collection signal of coil block 20～22, in view of the above, can only carry out imaging to abdominal part with loop coil.
Like this,, also bottom high frequency winding assembly 7L1～7L4 can be configured to the state of setting usually even change the imaging position of examinee P, and when abdominal part changes, can dual-purpose bottom high frequency winding assembly 7L1 wherein.Promptly, in brief, to the different parts (being typically the vertebra abdominal part) of examinee P when carrying out imaging, will be as formation partially mutual commonization of a plurality of receptions with the surface coils of high frequency coil 7R, and can be so that signal collection is carried out in the suitableeest sensitivity in each position.
Like this, for the operator, the reception of each examinee or each imaging position being changed other kinds reduced significantly with the desired time of high frequency coil 7R.Therefore, can reduce the operator and spend in the workload that imaging is prepared, also can improve patient's prescription on individual diagnosis rate.In brief, even examinee's different parts (being typically vertebra and abdominal part) is carried out imaging, the time that replacing receives with high frequency coil tails off, and, can collect magnetic resonance signal with the suitableeest sensitivity to each position, can improve patient's prescription on individual diagnosis rate.
The 1-1 variation
Figure 11 is the same with the Fig. 9 that has stated, and expression changes the figure of the example of coil block configuration to examinee P.Make it to conform with examinee's bodily form by crooked support member SP, the body surface of coil block and examinee P is connected airtight, can obtain the SNR better pictures.
Example when Figure 12 represents 4 loop coils are arranged.For mutual decoupling zero, loop coil 30,31,32,33 is configured to only overlapping Rack.The cross coil 34 of this moment for each loop coil electrolysis coupling, be configured on each loop coil current path and intersect.In view of the above, equally, on each loop coil axle separately, the high frequency magnetic field direction that high frequency magnetic field direction that each loop coil produces and cross coil 34 produce is essentially 90 °, with only use loop coil to compare at 30,31,32,33 o'clock by appending cross coil 34, can obtain the high image of SNR.
Figure 13 is the figure of other examples of the decoupling zero circuit of presentation graphs 7.In series dispose electric capacity 63,64 respectively with loop coil 51 and 52, capacitance bridge 62 is installed between this electric capacity.Capacitor C 1, the C2 of the capacitor by adjusting capacitance bridge 62 can realize decoupling zero.
Figure 14 is the figure that expression is used for the configuration example of decoupling zero between the cross coil of Fig. 6.By making the only overlapping suitable area of cross coil 70 and cross coil 71, can make the interlinkage flux between mutual coil is zero, can realize decoupling zero.
Figure 15 is the figure that expression is used for another configuration example of the decoupling zero between the cross coil of Fig. 6.Wherein, only make cross coil 72,73 and the two outer loops orthogonal direction of axon direction only overlapping suitable amplitude on the axon direction.In view of the above, can make the interlinkage flux between mutual coil is zero, can realize decoupling zero.
Figure 16 and Figure 17 are the figure of other examples of expression coil block configuration of the present invention.In order also to have the function to the vertebra imaging, the coil block that is arranged at examinee P back can have cross coil 23 and loop coil 20,21,22, places the surface coils of abdominal part side not use cross coil.At this moment, as Figure 16 and shown in Figure 17, place the coil block of abdominal part side also can only constitute by loop coil 80,81,82.
In addition, in the coil configuration example of Fig. 9, Figure 16, Figure 17 explanation, also constitute and be used for situation the abdominal part imaging with being used for a part to the coil block of vertebra imaging.Wherein, as mentioned above, cross coil 23 is in order especially the good imaging of SNR to be carried out and additional parts in the vertebra zone.Therefore, during to the abdominal part imaging, can not use yet, can also only select to adopt the collection data of the loop coil 20～22 in the coil configuration of Fig. 9, Figure 16, Figure 17 explanation even have cross coil.Even that is that abdominal part center SNR is not improved because use cross coil, but surround the loop coil that the examinee covers, so be effective owing to existing.If the receiving channels of collection data to be processed increases too much, then can cause the increase of data volume and computation time, thereby, also need suitably to avoid this problem.As the example that this selection is handled, the processing that can adopt above-mentioned Figure 10 to put down in writing.
Figure 18 represents another example of coil block configuration of the present invention.The coil block of this variation is as shown in the drawing, have N loop coil 91～95 and 1 cross coil 96, but the intersection number of times of cross coil 96 lacks than N.Like this, than toroid number of turns occasion still less, the size (intersection number of times) that can adjust cross coil improves the zone of sensitivity to cater to the need at the crossing number of cross coil.
Further, can also be out of shape the signal processing method of surface coils.In above-mentioned the 1st embodiment, receive data sampling as receiving channels independently respectively from the received signal of each surface coils output, but also the synthetic distributor circuit that the signal from several surface coils is synthesized or distributes can be set in advance.In view of the above, can sample, can realize the variation of signal processing the data after synthetic distributor circuit has carried out synthetic allocation process by this.
The 2nd embodiment
Figure 19 is the figure of structure of the MR imaging apparatus of expression the 2nd embodiment.
This MR imaging apparatus has static field magnet 101, gradient magnetic field coil 102, gradient magnetic field coil drive circuit 103, the platform 104 that crouches, emission part 105, emission high frequency coil 106, receives with high frequency winding assembly 107, acceptance division 108, data collection portion 109, computer 110, sequence controller 111, display 112 and control station 113.
Be inserted in the cavity (imaging mouth) of gradient magnetic field coil 102 under the state of subject P in the top board 104A that is loaded on the platform 104 that crouches.Top board 104A is supported by base portion 104B, moves up at its long axis direction (left and right directions among Figure 19) and upper and lower.Usually, platform 104 for sleeping in is arranged to the central axes of its long axis direction and static field magnet 101.
High frequency winding assembly 107 mountings are in top board 104A.The magnetic resonance signal guiding acceptance division 108 that high frequency winding assembly 107 will send from subject.Acceptance division 108 will carry out detection after will being amplified by the magnetic resonance signal that high frequency winding assembly 107 imports.Data collection portion 109 collects from the magnetic resonance signal of acceptance division 108 outputs and carries out the A/D conversion.Computer 110 carries out image according to the magnetic resonance signal from 109 outputs of data collection portion and reconstructs processing.
As shown in figure 20, high frequency winding assembly 107 contains 4 loop coil 107A, 107B, 107C, 107D.The anchor ring of these loop coils 107A, 107B, 107C, 107D is towards same direction, and the anchor ring that is configured to two adjacency is all overlapped each other.Below, the direction that as above like that sets loop coil 107A, 107B, 107C, 107D is called sets direction.Like this, for setting direction, loop coil 107B, 107C are positioned at the inboard, and 107A, 107D are positioned at the outside that clips loop coil 107B, 107C.In addition, loop coil 107A, 107B, the mutual electric insulation of 107C, 107D.
For with the above-mentioned central shaft that sets the orthogonal direction of direction of loop coil 107A, 107B, 107C, 107D, it is desirable to see be equipped on the straight line from the direction that the anchor ring with them intersects.But, wait from designing the problem that exists, the situation that is difficult to strictly dispose is point-blank also arranged, so indentation sets more or less.
In addition, loop coil 107A, 107B, 107C, 107D can be provided on the same laminar substrate.
Set anchor ring width W 107B, the W107C of loop coil 107B, the 107C of direction, littler than anchor ring width W 107A, the W107D of loop coil 107A, the 107D of this direction.In addition, in the 2nd embodiment, width W 107B and W107C equate, and width W 107A is equal with W107D, as long as but satisfy above-mentioned condition, their do not wait passable respectively yet.
All has identical width W 7 with any of anchor ring width of loop coil 107A, 107B, 107C, 107D on setting the orthogonal direction of direction.Therefore, anchor ring area S107B, the S107C of loop coil 107B, 107C are littler than anchor ring area S107A, the S107D of loop coil 107A, 107D.Wherein, area S107A, S107B, S107C, S107D are the area of the dash area of Figure 21 (a)～(d).With the anchor ring width that sets loop coil 107A, 107B on the orthogonal direction of direction, 107C, 107D can be different.
In order to prevent that 2 loop coils from producing electric coupling, 2 toroidal coil surface laps are set to desired value, so that the summation of altofrequency magnetic field in anchor ring that produces is 0 mutually.
Shown in Figure 21 (e), the area of 3 overlapping portions all is Sn respectively.At this moment, loop coil 107A, 107B, 107C, 107D for example can determine size by following formula, and resulting k1, k2 are 0.35～0.65.
k1＝S107A/(S107B+S107C-Sn)
k2＝S107D/(S107B+S107C-Sn)
As shown in figure 22, high frequency winding assembly 107 further contains 180 degree distribution/ synthesizer 107E, 107F and 90 degree distribution/synthesizer 107G.
Signal SB, the SC that loop coil 107B, 107C exported is input to 180 degree distribution/synthesizer 107E by tuning integrated circuit (not shown) by coaxial cable etc.180 degree distribution/synthesizer 107E are with homophase and anti-phase signal SB, SC are synthesized respectively.The signal SE that 180 degree distribution/synthesizer 107E will obtain as the synthetic result of homophase outputs to 90 degree distribution/synthesizer 107G.The signal that 180 degree distribution/synthesizer 107E will obtain as anti-phase synthetic result is delivered to acceptance division 108 as anti-phase composite signal.
Signal SA, the SD that loop coil 107A, 107D exported is input to 180 degree distribution/synthesizer 107F by tuning integrated circuit by coaxial cable (not shown) etc.180 degree distribution/synthesizer 107F homophases and anti-phase signal SA, SD are synthesized respectively.The signal that 180 degree distribution/synthesizer 107E will obtain as the synthetic result of homophase is delivered to acceptance division 108 as the homophase composite signal.The signal SG that 180 degree distribution/synthesizer 107E will obtain as anti-phase synthetic result outputs to 90 degree distribution/synthesizer 107G.
90 degree distribution/synthesizer 107G are synthesized to signal SE with after signal SG phase shift 90 degree.The signal that 90 degree distribution/synthesizer 107G will obtain as its synthetic result is as the QD signal, and will deliver to acceptance division 108 respectively as anti-QD signal with the signal of this QD signal inversion.
The subject P of Figure 23 when the vertebra of subject P being carried out imaging and the axial section figure of the position relation of high frequency winding assembly 107 by MR imaging apparatus shown in Figure 19.
As shown in figure 23, loop coil 107B, 107C and vertebra closely connect.The distance of loop coil 107A and 107D and vertebra is bigger than loop coil 107B, 107C's.The area of toroidal sensitivity and coil surface improves inversely.Yet the area of toroidal coil surface sluggishness scope more is narrow more.That is, loop coil 107B, 107C can be with the good magnetic resonance signal that vertebra sent of sensitivity reception from closely connecing.On the other hand, loop coil 107A and 107D can from away from the position receive from the magnetic resonance signal that vertebra sent.
Be altered to measure-alike occasion with loop coil 107A and the 107D of the 2nd embodiment in the size with loop coil 107B, 107C, the distance between the area of loop coil 107B, 107C and loop coil 107A, 107D and the vertebra is big than among the 2nd embodiment respectively.Therefore, for the magnetic resonance signal that sends from vertebra, the sensitivity of loop coil 107A, 107B, 107C, 107D all reduces.On the contrary, be altered to measure-alike occasion with loop coil 107B and the 107C of the 2nd embodiment in the size with loop coil 107A, 107D, loop coil 107A, 107D reduce the sensitivity of the magnetic resonance signal that sends from vertebra.
Therefore, the high frequency winding assembly 107 of the 2nd embodiment is compared with the loop coil situation side by side of 4 same sizes, and the SN ratio with the distant place both sides can be improved nearby.That is, obtain the partial imaging sensitivity of imaging object, further pass through loop coil 107A and 107D, can make SN ratio raising thus the imaging of imaging object near the additional imaging sensitivity imaging object by loop coil 107B and 107C.Imaging SN compares excellent images like this, efficiently.In addition, because aforesaid character, high frequency winding assembly 107 is fine in the occasion situation that is used for vertebra or abdominal part are carried out imaging.
In addition, according to the 2nd embodiment, synthesize owing to carry out QD, the SN of QD signal compares than with the output signal of each loop coil 107A, 107B, 107C, 107D and is improved.Therefore, in the few occasion of the number of channel of acceptance division 108, by using the QD signal, but channel seldom can be utilized efficiently and imaging SN compares excellent images.Particularly, if acceptance division 108 has 4 channels for adaptive high frequency winding assembly 107, then can use QD signal, anti-QD signal, homophase composite signal and anti-phase composite signal, if but have only 2 channels, QD signal and homophase composite signal or anti-phase composite signal then used.
The 3rd embodiment
Figure 24 be shown in the figure of structure of MR imaging apparatus of the 3rd embodiment.In addition, in Figure 24, the part identical with Figure 19 adopted same-sign, and omit its detailed description.
This MR imaging apparatus has static field magnet 101, gradient magnetic field coil 102, gradient magnetic field coil drive circuit 103, the platform 104 that crouches, emission part 105, emission high frequency coil 106, acceptance division 108, data collection portion 109, computer 110, sequence controller 111, display 112, control station 113 and receives with high frequency winding assembly 114,115.
Promptly the MR imaging apparatus of the 3rd embodiment has high frequency winding assembly 114,115, has replaced the high frequency winding assembly 107 of the 2nd embodiment.
High frequency winding assembly 114 by mounting in top board 104A.High frequency winding assembly 115 is disposed at the upside of gradient magnetic field coil 102 inboards.The magnetic resonance signal guiding acceptance division 108 that high frequency winding assembly 114,115 will send from subject.
As shown in figure 25, high frequency winding assembly 114 contains 4 coil groups 114A, 114B, 114C, 114D.Coil groups 114A, 114B, 114C, 114D have loop coil 107A, 107B, 107C, 107D respectively.And coil groups 114A, 114B, 114C, 114D are equipped on the direction that direction is intersected that sets with loop coil 107A, 107B, 107C, 107D.Coil groups 114A, 114B, 114C, 114D are configured to overlap each other between two of adjacency.The direction that sets of coil groups 114A, 114B, 114C, 114D is the axon direction of subject P for the long axis direction along top board 104A.
Make the direction that sets overlap each other between the loop coil of adjacency obliquely and be difficult to respect to coil groups 114A, 114B, 114C, 114D in order to prevent the coupling (coupling) between coil.Therefore, as shown in figure 26, between 2 loop coils that satisfy such relation, be provided with decoupling zero circuit 114E.Yet in Figure 26, only illustrate the decoupling zero circuit 114E between the loop coil 107A of the loop coil 107B of coil groups 114A and coil groups 114B, but between same other 2 loop coils, also be respectively equipped with the decoupling zero circuit.
Decoupling zero circuit 114E can have the such structure of example of Fig. 8 or Figure 13.The structure of high frequency winding assembly 115 is identical with high frequency winding assembly 107.
The axial section figure of the subject P when Figure 27 carries out imaging by MR imaging apparatus shown in Figure 24 to the vertebra of subject P and abdominal part for expression and the position relation of high frequency winding assembly 114,115.
Like this, according to the 3rd embodiment, by adopting high frequency winding assembly 114, can on the axon direction, carry out imaging with good SN ratio in the very wide scope to vertebra.In addition, by adopting high frequency winding assembly 115, can carry out imaging with good SN comparison abdominal part.
In addition, according to the 3rd embodiment, the axon direction and with also can be on the orthogonal direction to direction of principal axis corresponding to parallel imaging.
Above embodiment can carry out following all distortion and implement.
The loop coil width is narrow more, and the sensitivity of its width improves more, but the range of sensitivity of its width is narrow more.Therefore, even the area of anchor ring does not satisfy above-mentioned condition, also can obtain identical effect with above-mentioned the 2nd embodiment.But, preferably adopt the 2nd embodiment, because of it can carry out imaging with better SN ratio.
Shown in Figure 28 and 29, high frequency winding assembly 107,114,115 can set each loop coil with the state along curved surface.If so, shown in Figure 28 and 29, can be along subject P configuring high-frequency coil block 107,114,115, each loop coil can further closely connect with subject P.
Can respectively the output signal of loop coil 107A, 107B, 107C, 107D be delivered to acceptance division 108.And can in acceptance division 108, carry out as required be combined to, anti-phase synthetic or QD synthetic.The computer 110 that perhaps each output signal can be led respectively, and reconstruct independently after the processing according to these signals is taken advantage of and square root by trying to achieve 2 of 4 images obtaining therefrom, obtains 1 image.
When setting a plurality of coil groups that is used for high frequency winding assembly 114, the quantity of the coil groups that is had can be arbitrarily.
Circuit shown in Figure 22 is also applicable to having in 4 identical toroidal high frequency winding assemblies.
Loop coil can be provided with 5 or more than.
When constituting high frequency winding assembly by 2 or 3 loop coils, if it is little that toroidal one of them area that sets the width of direction and anchor ring for above-mentioned loop coil of 2 of adjacency is compared with another, then can obtain effect same as the previously described embodiments.
In addition, the present invention is not limited to the form of the foregoing description, can the implementation phase in the scope that does not break away from its aim, its element made and specializes distortion.In addition, by being carried out suitable combination, the disclosed a plurality of elements of the foregoing description can form multiple invention.For example, in the whole elements shown in the embodiment, also can remove certain several element.Further, can also carry out appropriate combination to the element among the different embodiment.
Claims (21)
1, a kind of high frequency winding assembly has:
2 interior annular coils;
2 exterior annular coils that clip above-mentioned 2 interior annular coils and set, wherein
Above-mentioned 2 interior annular coils are littler than above-mentioned 2 exterior annular coils at least 4 that contain above-mentioned 2 interior annular coils and above-mentioned 2 the exterior annular coils toroidal width that set on the direction respectively,
Each above-mentioned toroidal and above-mentioned central shaft that sets the orthogonal direction of direction sees that from the direction of intersecting with above-mentioned toroidal anchor ring linearly shape sets.
2, high frequency winding assembly as claimed in claim 1,
At least 4 toroidal anchor ring areas that above-mentioned 2 each leisures of interior annular coil contain above-mentioned 2 interior annular coils and above-mentioned 2 exterior annular coils are littler than above-mentioned 2 exterior annular coils.
3, high frequency winding assembly as claimed in claim 2, the shape of 2 above-mentioned interior annular coils is basic identical each other.
4, high frequency winding assembly as claimed in claim 2, the shape of 2 above-mentioned exterior annular coils is basic identical each other.
5, require 2 described high frequency winding assemblies as power, also have:
The 1st synthesis unit of a homophase Synthetic 2 above-mentioned interior annular coil output signal separately;
The 2nd synthesis unit of an anti-phase Synthetic 2 above-mentioned exterior annular coil output signal separately;
The output signal of above-mentioned the 2nd synthesis unit is carried out being synthesized to the unit of the output signal of above-mentioned the 1st synthesis unit after the 90 degree phase shifts.
6, high frequency winding assembly as claimed in claim 2 is being equipped with a plurality of coil groups of being made up of above-mentioned at least 4 loop coils with above-mentioned setting on the direction that direction intersects.
7, high frequency winding assembly as claimed in claim 6, the direction of above-mentioned intersection are the axon direction.
8, high frequency winding assembly as claimed in claim 6, the direction of above-mentioned intersection are the health thickness direction.
9, high frequency winding assembly as claimed in claim 6, above-mentioned a plurality of coil groups are disposed on the same laminar substrate.
10, a kind of high frequency winding assembly has:
2 loop coils in the outside are positioned at least 4 loop coils that clip inboard 2 toroidal positions and set, each above-mentioned toroidal central shaft that sets the orthogonal direction of direction with it sees that from the direction of intersecting with above-mentioned toroidal anchor ring linearly shape sets;
With the 1st synthesis unit that is combined to inboard 2 above-mentioned loop coils output signal separately;
The 2nd synthesis unit of 2 the above-mentioned loop coils in anti-phase synthetic outside output signal separately;
The output signal of above-mentioned the 2nd synthesis unit is carried out being synthesized to the unit of the output signal of above-mentioned the 1st synthesis unit after the 90 degree phase shifts.
11, a kind of MR imaging apparatus is carried out imaging according to the magnetic resonance signal that sends from subject to above-mentioned subject,
Has high frequency winding assembly as claimed in claim 2, to receive above-mentioned magnetic resonance signal.
12, MR imaging apparatus as claimed in claim 11 is disposed at above-mentioned high frequency winding assembly the position of the back side of above-mentioned subject.
13, MR imaging apparatus as claimed in claim 11 further has the top board that is used for the above-mentioned subject of mounting, and above-mentioned high frequency winding assembly is installed on the above-mentioned top board.
14, a kind of MR imaging apparatus is carried out imaging according to the magnetic resonance signal that sends from subject to above-mentioned subject,
Have 2 groups of high frequency winding assemblies as claimed in claim 2, to receive above-mentioned magnetic resonance signal from 2 directions that clip above-mentioned subject.
15, a kind of MR imaging apparatus is carried out imaging according to the magnetic resonance signal that sends from subject to above-mentioned subject,
Has high frequency winding assembly as claimed in claim 10, to receive above-mentioned magnetic resonance signal.
16, MR imaging apparatus as claimed in claim 15 is disposed at above-mentioned high frequency winding assembly the position of the back side of above-mentioned subject.
17, MR imaging apparatus as claimed in claim 15 further has the top board that is used for the above-mentioned subject of mounting, and above-mentioned high frequency winding assembly is installed on the above-mentioned top board.
18, a kind of MR imaging apparatus is carried out imaging according to the magnetic resonance signal that sends from subject to above-mentioned subject,
Has high frequency winding assembly as claimed in claim 1, to receive above-mentioned magnetic resonance signal.
19, MR imaging apparatus as claimed in claim 18 is disposed at above-mentioned high frequency winding assembly the position of the back side of above-mentioned subject.
20, MR imaging apparatus as claimed in claim 18 further has the top board that is used for the above-mentioned subject of mounting, and above-mentioned high frequency winding assembly is installed on the above-mentioned top board.
21, a kind of MR imaging apparatus is carried out imaging according to the magnetic resonance signal that sends from subject to above-mentioned subject,
Have 2 groups of high frequency winding assemblies as claimed in claim 1, to receive above-mentioned magnetic resonance signal from 2 directions that clip above-mentioned subject.
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| JP5508906B2 (en) | 2009-04-24 | 2014-06-04 | 株式会社東芝 | Magnetic resonance imaging apparatus and RF coil |
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| CN1228291A (en) * | 1997-12-23 | 1999-09-15 | 通用电气公司 | RF coil apparatus for MR system |
| US6624633B1 (en) * | 1999-03-26 | 2003-09-23 | Usa Instruments, Inc. | Disjunct MRI array coil system |
| US20040135579A1 (en) * | 2001-02-23 | 2004-07-15 | Masahiro Takizawa | Magnetic resonance imaging apparatus and method |
| US20030094948A1 (en) * | 2001-11-22 | 2003-05-22 | Kazuya Okamoto | RF coil and magnetic resonance imaging apparatus |
| US20040196042A1 (en) * | 2003-01-21 | 2004-10-07 | Hiroyuki Fujita | Coil arrays for parallel imaging in magnetic resonance imaging |
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| JP2006141444A (en) | 2006-06-08 |
| CN1817304A (en) | 2006-08-16 |
| JP4891539B2 (en) | 2012-03-07 |
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