CN1310343A - RF coil and magnetic resonance imaging method and equipment - Google Patents
RF coil and magnetic resonance imaging method and equipment Download PDFInfo
- Publication number
- CN1310343A CN1310343A CN 00102385 CN00102385A CN1310343A CN 1310343 A CN1310343 A CN 1310343A CN 00102385 CN00102385 CN 00102385 CN 00102385 A CN00102385 A CN 00102385A CN 1310343 A CN1310343 A CN 1310343A
- Authority
- CN
- China
- Prior art keywords
- electric channel
- electric
- plane
- channel
- parallel
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Granted
Links
Images
Landscapes
- Magnetic Resonance Imaging Apparatus (AREA)
Abstract
In order to provide orthogonal RF coil with excellent frequency characteristic and magnetic resonant imaging method and equipment with the coil, two coil loops are so combined that the two connection channels 606 and 608 are not overlapped and the said coil loop includes the perpendicular and crossed main channels 602 and 604 connected serially to the connection channels 606 and 608.
Description
The present invention relates to RF (radio frequency) coil and MR imaging method and equipment, specifically, relate to and be used for producing a RF coil in RF magnetic field and using the MR imaging method and the equipment of this RF coil along the direction of the annular surface that is parallel to coil.
The static magnetic field direction is referred to as vertical magnetic field type MR imaging apparatus usually perpendicular to a kind of MR imaging apparatus of the body shaft of the object of a discussion, this equipment produces the static magnetic field space of an opening, and the RF coil that therefore can utilize the annular surface with a pole shoe surface that is parallel to the static magnetic field generation unit is as the RF coil that produces RF magnetic field.The direction in the RF magnetic field that such RF coil produces is parallel to the annular surface of coil, thereby forms the RF magnetic field perpendicular to the static magnetic field direction.A kind of like this RF coil is disclosed in the applicant's United States Patent (USP) the 5760583rd.
On the other hand, the RF coil that also has another kind of type, be referred to as quadrature RF coil, it is constituted by a kind of of two RF coils, and the vector in the RF magnetic field by the correspondence that produced by two RF coils is synthetic, and the intensity in the RF magnetic field that is provided has been improved, and perhaps can reduce the RF magnetic field that the driving energy of each coil just can produce expectation strength.
An object of the present invention is to provide a kind of quadrature RF coil with good frequency rerum natura, and the MR imaging method and the equipment that use this RF coil.
By first aspect of the present invention, a kind of RF coil is provided, comprising: when 3 orthogonal directions were expressed as x direction, y direction, z direction respectively, first electric channel extended in the x direction; Second electric channel is parallel to first electric channel in the x-y plane; The 3rd electric channel is parallel to first electric channel in the x-z plane; The 4th electric channel is parallel to the 3rd electric channel in being parallel to a plane on x-y plane, and is parallel to second electric channel in being parallel to a plane on x-z plane; The 5th electric channel first to fourth electric channel that is connected in series, so that first and second electric channel carries the corresponding electric current of equidirectional, the 3rd and the 4th electric channel carries the corresponding electric current with the equidirectional of the current opposite in direction of first and second electric channel; The 6th electric channel extends along the y direction in the x-y plane; The 7th electric channel is parallel to the 6th electric channel in the x-y plane; The 8th electric channel is parallel to the 6th electric channel in the y-z plane; The 9th electric channel is parallel to the 8th electric channel in being parallel to a plane on x-y plane, and is parallel to the 7th electric channel in being parallel to a plane on y-z plane; With, the tenth electric channel the 6th electric channel to the nine electric channels that are connected in series, so that the 6th and the 7th electric channel carries the corresponding electric current of equidirectional, the 8th and the 9th electric channel carries the corresponding electric current with the equidirectional of the current opposite in direction of the 6th and the 7th electric channel; Wherein the 5th electric channel and the tenth electric channel are at z direction non-overlapping copies mutually.
By second aspect of the present invention, provide a kind of as at the described RF coil of first aspect, wherein one of the 5th and the tenth electric channel is arranged in another inside of the 5th and the tenth electric channel on x-y plane, and in the 5th and the tenth electric channel another is arranged in the inside of one of the 5th and the tenth electric channel on the plane that is parallel to the x-y plane.
By the 3rd aspect of the present invention, a kind of RF coil is provided, comprising: when 3 orthogonal directions were expressed as x direction, y direction, z direction respectively, first electric channel extended in the x direction; Second electric channel is parallel to first electric channel in the x-y plane; The 5th electric channel first and second electric channels that are connected in series are so that first and second electric channel carries the corresponding electric current of equidirectional; The 6th electric channel extends along the y direction in the x-y plane; The 7th electric channel is parallel to the 6th electric channel in the x-y plane; The tenth electric channel be connected in series the 6th electric channel and the 7th electric channel are so that the 6th and the 7th electric channel carries the corresponding electric current of equidirectional; Wherein the 5th electric channel and the tenth electric channel are at z direction non-overlapping copies mutually.
By the 4th aspect of the present invention, a kind of MR imaging method is provided, comprise the steps: when 3 orthogonal directions in the space of placing a research object are expressed as x direction, y direction, z direction respectively, to produce a static magnetic field in the z direction; In this space, produce gradient magnetic; In this space, produce a high frequency magnetic field; Measurement comes from the magnetic resonance signal in this space; The magnetic resonance signal that measures with basis produces an image; The step of generation high frequency magnetic field is wherein finished by using a RF coil, and said RF coil comprises: first electric channel extends in the x direction; Second electric channel is parallel to first electric channel in the x-y plane; The 3rd electric channel is parallel to first electric channel in the x-z plane; The 4th electric channel is parallel to the 3rd electric channel in being parallel to a plane on x-y plane, and is parallel to second electric channel in being parallel to a plane on x-z plane; The 5th electric channel first to fourth electric channel that is connected in series, so that first and second electric channel carries the corresponding electric current of equidirectional, the 3rd and the 4th electric channel carries the corresponding electric current with the equidirectional of the current opposite in direction of first and second electric channel; The 6th electric channel extends along the y direction in the x-y plane; The 7th electric channel is parallel to the 6th electric channel in the x-y plane; The 8th electric channel is parallel to the 6th electric channel in the y-z plane; The 9th electric channel is parallel to the 8th electric channel in being parallel to a plane on x-y plane, and is parallel to the 7th electric channel in being parallel to a plane on y-z plane; With, the tenth electric channel the 6th electric channel to the nine electric channels that are connected in series, so that the 6th and the 7th electric channel carries the corresponding electric current of equidirectional, the 8th and the 9th electric channel carries the corresponding electric current with the equidirectional of the current opposite in direction of the 6th and the 7th electric channel; Wherein the 5th electric channel and the tenth electric channel are at z direction non-overlapping copies mutually.
By the 5th aspect of the present invention, a kind of MR imaging apparatus is provided, comprise; When 3 orthogonal directions in the space of placing a research object are expressed as x direction, y direction, z direction respectively, be used for producing the static magnetic field generation device of a static magnetic field in the z direction; Be used in this space, producing the gradient magnetic generation device of gradient magnetic; Be used in this space, producing the high frequency magnetic field generation device of a high frequency magnetic field; Be used to measure the measurement mechanism of the magnetic resonance signal that comes from this space; With the image forming appts that produces an image according to the magnetic resonance signal that measures by measurement mechanism; High frequency magnetic field generation device wherein comprises a RF coil, and said RF coil comprises: first electric channel extends in the x direction; Second electric channel is parallel to first electric channel in the x-y plane; The 3rd electric channel is parallel to first electric channel in the x-z plane; The 4th electric channel is parallel to the 3rd electric channel in being parallel to a plane on x-y plane, and is parallel to second electric channel in being parallel to a plane on x-z plane; The 5th electric channel first to fourth electric channel that is connected in series, so that first and second electric channel carries the corresponding electric current of equidirectional, the 3rd and the 4th electric channel carries the corresponding electric current with the equidirectional of the current opposite in direction of first and second electric channel; The 6th electric channel extends along the y direction in the x-y plane; The 7th electric channel is parallel to the 6th electric channel in the x-y plane; The 8th electric channel is parallel to the 6th electric channel in the y-z plane; The 9th electric channel is parallel to the 8th electric channel in being parallel to a plane on x-y plane, and is parallel to the 7th electric channel in being parallel to a plane on y-z plane; With, the tenth electric channel the 6th electric channel to the nine electric channels that are connected in series, so that the 6th and the 7th electric channel carries the corresponding electric current of equidirectional, the 8th and the 9th electric channel carries the corresponding electric current with the equidirectional of the current opposite in direction of the 6th and the 7th electric channel; Wherein the 5th electric channel and the tenth electric channel are at z direction non-overlapping copies mutually.
As previously discussed first to the 5th aspect in either side of the present invention in, cross one another each electric channel is to preferably intersecting in the x-y plane, their intersection point is interlaced, thereby has improved by these electric channels the harmony between the corresponding RF magnetic field that produces.
In the present invention, because connect (TIE) passage, so reduced between the coil coupling by the generation of drift ability at z direction phase non-overlapping copies.
So, according to the present invention, can realize a quadrature RF coil with good frequency characteristic, and the MR imaging method and the equipment that use this RF coil.
From the description of following expression the preferred embodiments of the present invention in the accompanying drawings, other purpose of the present invention and advantage all will become obviously.
Fig. 1 is the calcspar according to an exemplary apparatus of one embodiment of the present of invention.
Fig. 2 is the synoptic diagram of expression according to the structure of a transmitting coil part in the equipment of one embodiment of the present of invention.
Fig. 3 is the synoptic diagram of expression according to the structure of a transmitting coil part in the equipment of one embodiment of the present of invention.
Fig. 4 is the synoptic diagram of expression according to the structure of a transmitting coil part in the equipment of one embodiment of the present of invention.
Fig. 5 is the synoptic diagram of the structure of the transmitting coil part partly in the indication equipment.
Fig. 6 is the synoptic diagram of expression by a typical pulse sequence of this equipment realization.
Describe embodiments of the invention in greater detail referring now to accompanying drawing.Fig. 1 is the calcspar according to a MR imaging apparatus of one embodiment of the present of invention.The structure representative of this equipment is according to an embodiment of equipment of the present invention, and the operation representative of this equipment is according to an embodiment of method of the present invention.
As shown in Figure 1, this equipment comprises a static magnetic field generation device 2, and static magnetic field generation device 2 produces a uniform static magnetic field in its inner space.An embodiment of these static magnetic field generation device 2 representatives static magnetic field generation device of the present invention.Static magnetic field generation device 2 comprises a pair of opposed facing and have the magnetic generator (not shown, as permanent magnet) of certain intervals in vertical direction, is used for producing static magnetic field (vertical magnetic field) in the space of being got involved.Obviously, this magnetic generator is not limited to permanent magnet, can also be superconducting electromagnet, common electromagnet, or analog.
In static magnetic field produces the inner space of part 2, be provided with respectively gradient coil part 4,4 vertically opposed facing and separated by a distance in a similar manner ' and transmitting coil part 6,6 '.An embodiment of transmitting coil part 6,6 ' representative RF coil of the present invention.The back is again to transmitting coil part 6,6 ' be described.
A research object 8 is placed on one becomes on the entablement 10, and by the carrying device (not shown) with this research object bring into relative transmitting coil part 6,6 ' between the space of inserting.The body shaft of research object 8 is perpendicular to the static magnetic field direction.Become entablement 10 to be fixed with a receiving coil part 106, receiving coil part 106 is surrounded a position of the research object 8 of wanting imaging.Receiving coil part 106 for example is the part that is used for the lumbar spine imaging, and be fixed to research object 8 hip joint around.Receiving coil part 106 not only can be placed on lumbar spine around, and any one position that can be placed on and want the desired site correspondence of imaging.
Gradient coil part 4,4 ' be connected with gradient-driven part 16.Gradient-driven part 16 to gradient coil part 4,4 ' provide drive signal to produce gradient magnetic.Gradient coil part 4,4 ' and gradient-driven part 16 represent an embodiment of gradient magnetic generation device of the present invention together.The gradient magnetic that produces has following 3: amplitude limit gradient magnetic, readout gradient magnetic field and phase encoding gradient magnetic field.
Transmitting coil part 6,6 ' be connected with a radiating portion 18.Transmitter portion 18 to a drive signal of transmitting coil part 6,6 ' provide to produce RF magnetic field, whereby in spin of internal excitation of research object 8.Transmitting coil part 6,6 ' and transmitter portion 18 represent an embodiment of high frequency magnetic field generation device of the present invention together.
Receiving coil part 106 receives a magnetic resonance signal that is produced by the spin that excites in research object 8.Receiving coil part 106 is connected to the input end of receiver part 20, to the signal of receiver part 20 input receptions.
The output of receiver part 20 is connected to the input end of an analog to digital (A-D) converter part 22.A-D converter part 22 converts the output signal of receiver part 20 to digital signal.
Receiving coil part 106, receiver part 20 and A-D converter part 22 are represented an embodiment of measurement mechanism of the present invention together.The output of A-D converter part 22 is connected to a computing machine 24.
Computing machine 24 receives the digital signal that comes from A-D converter part 22, and with this signal storage in a storer (not shown).So, in storer, form a data space.This data space has constituted a bidimensional Fourier space.Computing machine 24 carries out the bidimensional inverse Fourier transform to these data in the Fourier space of this bidimensional, with the image of reconstruct research object 8.An embodiment of computing machine 24 representatives image forming appts of the present invention.
Computing machine 24 is connected to a control section 30.Control section 30 is connected to gradient-driven part 16, transmitter portion 18, receiver part 20 and A-D converter part 22.Control section 30 is according to the instruction control gradient-driven part 16, transmitter portion 18, receiver part 20 and the A-D converter part 22 that provide from computing machine 24, to realize magnetic resonance imaging.
Computing machine 24 links to each other with an operation part 34 with a display part 32.Display part 32 shows from image and several information of a reconstruct of computing machine 24 outputs.Operation part 34 is imported several orders and information operatings by operating personnel to computing machine 24.
Fig. 2 schematically represent transmitting coil part 6,6 ' structure.What Fig. 2 represented is the three-dimensional structure of the electric channel of a RF coil, it constituted transmitting coil part 6,6 ' major part.3 orthogonal directions in three dimensions are represented by x, y, z.The z direction is the static magnetic field direction.As shown in the figure, the electric channel of a transmitting coil part 6 is located on the x-y plane, another transmitting coil part 6 ' electric channel be located at previous x-y plane and separate on another x-y plane of certain distance in the z direction.
Transmitting coil part 6 has two parallel main channels 602,604 along the extension of x direction.Main channel 602,604 is represented the embodiment of first and second electric channels of the present invention respectively.
One end of main channel 602 is linked transmitter portion 18, and its other end is linked an end of main channel 604 through interface channel 606.Interface channel 606 arrives that side relative with a side at 604 places, main channel in the inner bending of x-y plane, and connects the other end of main channel 602 and an end of main channel 604.
Though interface channel 606 exemplarily has been expressed as an around the corner crooked straight line path of 90 °, but be not limited thereto, it can be a semicircular substantially line, or one from the main channel the suitable curve of 602 the other end a, end of 604 to the main channel.The like that will describe below this situation also will be applied to.
The other end of main channel 604 is connected to an end of interface channel 610 through interface channel 608, and interface channel 608 is folded on that side relative with a side at 602 places, main channel.Interface channel 610 connection transmitting coil parts 6,6 '.
Though interface channel 608 exemplarily has been expressed as an around the corner crooked straight line path of 90 °, but be not limited thereto, it can be a semicircular substantially line, or one from the main channel the suitable curve of 604 the other end a, end of 610 to the main channel.The like that will describe below this situation also will be applied to.
Transmitting coil part 6 also has two parallel main channels 612 and 614 in the extension of y direction. Main channel 612 and 614 represents the of the present invention the 6th and the embodiment of the 7th electric channel respectively.
One end of main channel 612 is linked transmitter portion 18, and its other end is linked an end of main channel 614 through interface channel 616.Interface channel 616 arrives that side relative with a side at 614 places, main channel in the inner bending of x-y plane, and connects the other end of main channel 612 and an end of main channel 614, and the structure of interface channel 616 surmounts the outside of interface channel 606 and 608.
The other end of main channel 614 through interface channel 618 be connected to interface channel 610 ' an end, interface channel 618 is folded on that side relative with a side at 612 places, main channel.Interface channel 610 ' connection transmitting coil part 6,6 '.The structure of interface channel 618 surmounts the outside of interface channel 606 and 608.
According to a kind of like this electric channel structure, main channel 602,604 and main channel 612,614 are vertical mutually in the x-y plane, and interface channel 616,618 is placed on the outside of interface channel 606,608 in the x-y plane.
Two of transmitting coil parts 6 ' have parallel along main channels 602 that the x direction is extended ', 604 '.Main channel 602 ', 604 ' respectively embodiment that represent third and fourth electric channel of the present invention.
Main channel 602 ' an end link transmitter portion 18, its other end through interface channel 606 ' link main channel 604 ' an end.Interface channel 606 ' in the inner bending of x-y plane is to that side relative with a side at 604 ' place, main channel, and connection main channel 602 ' the other end and main channel 604 ' an end.Main channel 604 ' the other end through interface channel 608 ' be connected to interface channel 610 ' an end, on that side of interface channel 608 ' be folded into and main channel 602 ' relative.
Two of transmitting coil parts 6 ' also have parallel in main channels 612 that the y direction is extended ' and 614 '.Main channel 612 ' and 614 ' respectively represent the of the present invention the 8th and the embodiment of the 9th electric channel.
Main channel 614 ' the other end through interface channel 618 ' be connected to interface channel 610 ' an end, on that side of interface channel 618 ' be folded into and main channel 612 ' relative.Interface channel 618 ' structure enter the inside of interface channel 606 and 608.
According to a kind of like this electric channel structure, main channel 602 ', 604 ' with main channel 612 ', 614 ' mutually vertical in the x-y plane, and in the x-y plane interface channel 616 ', 618 ' be placed on interface channel 606 ', 608 ' inside.
A kind of like this transmitting coil part 6,6 ' in, main channel 602,604,602 ', 604 ' by interface channel 606,608,606 ', 608 ', the continuous lines of 610 usefulness, one stroke is connected in series.This has just formed a wire loop (representing with solid line), and the direction of current that wherein flows through main channel 602,604 is identical, flow through main channel 602 ', 604 ' direction of current be identical but and flow through the current opposite in direction of main channel 602,604.Interface channel 606,608,606 ', 608 ', 610 embodiment that together represent the 5th electric channel of the present invention.
Similarly, main channel 612,614,612 ', 614 ' by interface channel 616,618,616 ', 618 ', 610 ' be connected in series with the continuous lines of a stroke.This has just formed a wire loop (dotted line), and the direction of current that wherein flows through main channel 612,614 is identical, flow through main channel 612 ', 614 ' direction of current be identical but and flow through the current opposite in direction of main channel 612,614.Interface channel 616,618,616 ', 618 ', 610 ' together embodiment that represent the tenth electric channel of the present invention.
Wire loop of representing with solid line and the wire loop that dots have orthogonal corresponding main channel in the x-y plane, therefore constituted one so-called " quadrature coil ".Therefore, by such two wire loops with the identical corresponding RF electric current of phase place are provided, and it is synthetic that vector is carried out in the corresponding RF magnetic field that these two wire loops produce, and just can obtain the RF magnetic field that intensity is improved.Yet, by providing such two to have the wire loop that phase place differs 90 ° corresponding RF electric current each other, and vector is carried out in the corresponding RF magnetic field that these two wire loops produce synthesize, just can obtain a RF magnetic field that in plane, rotates perpendicular to the z direction.
According to quadrature coil, the interface channel 606,608 that is constituted and interface channel 606 ', 608 ' have identical length, interface channel 606,608 and interface channel 606 ', 608 ' respectively be to separate inner passage on two x-y planes of certain distance in the z direction.Similarly, the interface channel 616,618 that is constituted and interface channel 616 ', 618 ' have identical length, interface channel 616,618 and interface channel 616 ', 618 ' be two external channels on the x-y plane.Therefore, two wire loops have identical total length.So the corresponding load condition with respect to transmitter portion 18 on two wire loops is identical, thereby can realize that balanced RF drives.
If allow to a certain degree unbalanced, then as exemplary expression among Fig. 3, can with the interface channel 606,608,606 of the wire loop in two x-y planes, represented with solid line ', 608 ' be arranged on the interface channel 616,618,616 of the wire loop that dots ', 618 ' the inside.
Yet the quadrature coil loop does not always form on two x-y planes, and it can also only form on an x-y plane, shown in Fig. 4 is exemplary.
For example, can use Copper Foil as being manufactured on the conductor material that has the wire loop of the above pattern in the x-y plane.Use Copper Foil on insulating material (for example plastic substrate) to form and have the coil pattern of straight electric channel, for example the thickness of said electric channel is tens microns, and the width of electric channel is several centimetres or tens centimetres or bigger.
In this case, take the insulate main channel of two intersections of adequate measures.Yet the outside of another interface channel of one of two interface channels on this x-y plane or inner so the position of two interface channels will be separated from each other certain distance, for example equals the width of Copper Foil.Therefore, two wire loops are accounting for the most interface channel part phase non-overlapping copies of total length.Therefore, obviously reduced the coupling that produces by the drift ability between two wire loops, thereby the quadrature coil with outstanding frequency characteristic is provided.
In addition, the preferred practice is, two main channels intersect, and their intersection point is interlaced, shown in Fig. 5 is exemplary, and the balanced whereby corresponding RF magnetic field that produces by two wire loops.
The operational circumstances of equipment of the present invention is described below.This equipment is to operate under the control of control section 30.Below introduction relates to is imaging process by spin-echo technique, it is a special case of magnetic resonance imaging.Spin-echo technique has used as the pulse train shown in Fig. 6 is exemplary.
Fig. 6 is the synoptic diagram that is used to obtain a pulse train of width of cloth magnetic resonance signal (spin-echoed signal) image.Repeat this pulse train for example 256 times, can obtain to spin-256 width of cloth images of echoed signal.
By the execution of control section 30 gating pulse sequences and obtaining of spin-echoed signal.Yet magnetic resonance imaging is not limited to use spin-echo technique to realize, but obviously can adopt other several technology, for example can use gradient-echo technique.
Shown in Fig. 6 (6), this pulse train is divided into 4 cycles (a)-(d) along time shaft.At first, shown in (1) among the figure, realize that by 90 ° of pulse P90 RF excites in the cycle (a).It is by transmitting coil part 6,6 ' realization of being driven by transmitter portion 18 that RF excites.Since transmitting coil part 6,6 ' be the good quadrature RF coil of frequency characteristic, so RF excitation energy is finished extremely effectively with said structure.
Excite with RF, also will be shown in (2) apply amplitude limit gradient magnetic Gs.Applying of amplitude limit gradient magnetic Gs is gradient coil part 4,4 ' finish by being driven by gradient-driven part 16.Therefore excite with predetermined amplitude limit in the inside of research object 8 and (selective excitation) spin.
Subsequent, at the cycle shown in (3) (b), apply phase encoding gradient magnetic field Gp.Applying of phase encoding gradient magnetic field Gp also is gradient coil part 4,4 ' finish by being driven by gradient-driven part 16.Thereby realized the phase place rock sign indicating number of spin.
Still be in the phase encoding cycle, realize the phase place that redefines that spins by the amplitude limit gradient magnetic Gs shown in (2).In addition, shown in (4), readout gradient magnetic field Gr applied, so that spin redefines phase place.Applying of readout gradient magnetic field Gr also is gradient coil part 4,4 ' finish by being driven by gradient-driven part 16.
Then,, apply 180 ° of pulse P180, make spin oppositely at the cycle shown in (1) (c).Spin oppositely be by carry out the transmitting coil part 6,6 that RF drives ' finish by transmitter portion 18.Because transmitting coil part 6,6 ' be the good quadrature RF coil of frequency characteristic, so oppositely also the finishing extremely effectively of spin with said structure.
Then, in the cycle (d) shown in (4), apply readout gradient magnetic field Gr.This produces a spin-echoed signal MR from research object 8, shown in (5).
Spin-echoed signal MR is received by receiving coil part 106.Receiving coil part 106 receives the spin-echoed signal of lumbar spine.The signal that receives is input to computing machine 24 through receiver part 20 and A-D converter part 22.Computing machine 24 deposits the input signal of receiving coil part 106 in storer, with this as measurement data.Therefore, the spin-echo data that will be used for piece image is collected storer from receiving coil part 106.
In a predetermined circulation, repeat aforesaid operations for example 256 times.For each repetition, change phase encoding gradient magnetic field Gp, all can obtain different phase encodings at every turn.This represents with a plurality of dotted lines in the waveform of Fig. 6 (3).
Computing machine 24 is finished image reconstruction according to the spin-echo data of collecting that is used for all images in storer, produce the image of lumbar spine.Show the image that produces like this on display part 32, this is a visible image.
Under the condition that does not depart from design of the present invention and scope, can constitute many embodiment that differs greatly of the present invention.Should be appreciated that, the specific embodiment that the invention is not restricted in instructions, describe, the present invention only is limited by the accompanying claims.
Claims (5)
1, a kind of RF coil comprises:
When 3 orthogonal directions were expressed as x direction, y direction, z direction respectively, first electric channel extended in the x direction;
Second electric channel is parallel to first electric channel in the x-y plane;
The 3rd electric channel is parallel to first electric channel in the x-z plane;
The 4th electric channel is parallel to the 3rd electric channel in being parallel to a plane on x-y plane, and is parallel to second electric channel in being parallel to a plane on x-z plane;
The 5th electric channel first to fourth electric channel that is connected in series, so that first and second electric channel carries the corresponding electric current of equidirectional, the 3rd and the 4th electric channel carries the corresponding electric current with the equidirectional of the current opposite in direction of first and second electric channel;
The 6th electric channel extends along the y direction in the x-y plane;
The 7th electric channel is parallel to the 6th electric channel in the x-y plane;
The 8th electric channel is parallel to the 6th electric channel in the y-z plane;
The 9th electric channel is parallel to the 8th electric channel in being parallel to a plane on x-y plane, and is parallel to the 7th electric channel in being parallel to a plane on y-z plane; With,
The tenth electric channel the 6th electric channel to the nine electric channels that are connected in series, so that the 6th and the 7th electric channel carries the corresponding electric current of equidirectional, the 8th and the 9th electric channel carries the corresponding electric current with the equidirectional of the current opposite in direction of the 6th and the 7th electric channel;
Wherein the 5th electric channel and the tenth electric channel are at z direction non-overlapping copies mutually.
2, the RF coil of claim 1, it is characterized in that: one of the 5th and the tenth electric channel is arranged in another inside of the 5th and the tenth electric channel on x-y plane, and in the 5th and the tenth electric channel another is arranged in the inside of one of the 5th and the tenth electric channel on the plane that is parallel to the x-y plane.
3, a kind of RF coil comprises:
When 3 orthogonal directions were expressed as x direction, y direction, z direction respectively, first electric channel extended in the x direction;
Second electric channel is parallel to first electric channel in the x-y plane;
The 5th electric channel first and second electric channels that are connected in series are so that first and second electric channel carries the corresponding electric current of equidirectional;
The 6th electric channel extends along the y direction in the x-y plane;
The 7th electric channel is parallel to the 6th electric channel in the x-y plane;
The tenth electric channel be connected in series the 6th electric channel and the 7th electric channel are so that the 6th and the 7th electric channel carries the corresponding electric current of equidirectional;
Wherein the 5th electric channel and the tenth electric channel are at z direction non-overlapping copies mutually.
4, a kind of MR imaging method comprises the steps:
When 3 orthogonal directions in the space of placing a research object are expressed as x direction, y direction, z direction respectively, produce a static magnetic field in the z direction;
In this space, produce gradient magnetic; In this space, produce a high frequency magnetic field;
Measurement comes from the magnetic resonance signal in this space; With
Produce an image according to the magnetic resonance signal that measures;
The step of generation high frequency magnetic field is wherein finished by using a RF coil, and said RF coil comprises:
First electric channel extends in the x direction;
Second electric channel is parallel to first electric channel in the x-y plane;
The 3rd electric channel is parallel to first electric channel in the x-z plane;
The 4th electric channel is parallel to the 3rd electric channel in being parallel to a plane on x-y plane, and is parallel to second electric channel in being parallel to a plane on x-z plane;
The 5th electric channel first to fourth electric channel that is connected in series, so that first and second electric channel carries the corresponding electric current of equidirectional, the 3rd and the 4th electric channel carries the corresponding electric current with the equidirectional of the current opposite in direction of first and second electric channel;
The 6th electric channel extends along the y direction in the x-y plane;
The 7th electric channel is parallel to the 6th electric channel in the x-y plane;
The 8th electric channel is parallel to the 6th electric channel in the y-z plane;
The 9th electric channel is parallel to the 8th electric channel in being parallel to a plane on x-y plane, and is parallel to the 7th electric channel in being parallel to a plane on y-z plane; With,
The tenth electric channel the 6th electric channel to the nine electric channels that are connected in series, so that the 6th and the 7th electric channel carries the corresponding electric current of equidirectional, the 8th and the 9th electric channel carries the corresponding electric current with the equidirectional of the current opposite in direction of the 6th and the 7th electric channel;
Wherein the 5th electric channel and the tenth electric channel are at z direction non-overlapping copies mutually.
5, a kind of MR imaging apparatus comprises; When 3 orthogonal directions in the space of placing a research object are expressed as x direction, y direction, z direction respectively, be used for producing the static magnetic field generation device of a static magnetic field in the z direction;
Be used in this space, producing the gradient magnetic generation device of gradient magnetic;
Be used in this space, producing the high frequency magnetic field generation device of a high frequency magnetic field;
Be used to measure the measurement mechanism of the magnetic resonance signal that comes from this space; With
Produce the image forming appts of an image according to the magnetic resonance signal that measures by measurement mechanism;
High frequency magnetic field generation device wherein comprises a RF coil, and said RF coil comprises:
First electric channel extends in the x direction;
Second electric channel is parallel to first electric channel in the x-y plane;
The 3rd electric channel is parallel to first electric channel in the x-z plane;
The 4th electric channel is parallel to the 3rd electric channel in being parallel to a plane on x-y plane, and is parallel to second electric channel in being parallel to a plane on x-z plane;
The 5th electric channel first to fourth electric channel that is connected in series, so that first and second electric channel carries the corresponding electric current of equidirectional, the 3rd and the 4th electric channel carries the corresponding electric current with the equidirectional of the current opposite in direction of first and second electric channel;
The 6th electric channel extends along the y direction in the x-y plane;
The 7th electric channel is parallel to the 6th electric channel in the x-y plane;
The 8th electric channel is parallel to the 6th electric channel in the y-z plane;
The 9th electric channel is parallel to the 8th electric channel in being parallel to a plane on x-y plane, and is parallel to the 7th electric channel in being parallel to a plane on y-z plane; With,
The tenth electric channel the 6th electric channel to the nine electric channels that are connected in series, so that the 6th and the 7th electric channel carries the corresponding electric current of equidirectional, the 8th and the 9th electric channel carries the corresponding electric current with the equidirectional of the current opposite in direction of the 6th and the 7th electric channel;
Wherein the 5th electric channel and the tenth electric channel are at z direction non-overlapping copies mutually.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN 00102385 CN1201165C (en) | 2000-02-21 | 2000-02-21 | RF coil and magnetic resonance imaging method and equipment |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN 00102385 CN1201165C (en) | 2000-02-21 | 2000-02-21 | RF coil and magnetic resonance imaging method and equipment |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| CN1310343A true CN1310343A (en) | 2001-08-29 |
| CN1201165C CN1201165C (en) | 2005-05-11 |
Family
ID=4576373
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CN 00102385 Expired - Fee Related CN1201165C (en) | 2000-02-21 | 2000-02-21 | RF coil and magnetic resonance imaging method and equipment |
Country Status (1)
| Country | Link |
|---|---|
| CN (1) | CN1201165C (en) |
Cited By (4)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN100416294C (en) * | 2002-06-21 | 2008-09-03 | 皇家飞利浦电子股份有限公司 | Magnetic resonance imaging apparatus and method |
| CN103364747A (en) * | 2012-04-05 | 2013-10-23 | 西门子公司 | Method and control apparatus for controlling magnetic resonance systems |
| CN106526512A (en) * | 2016-11-30 | 2017-03-22 | 重庆三峡学院 | Radio frequency coil capable of being used for head nuclear magnetic resonance imaging |
| CN104155622B (en) * | 2014-08-26 | 2017-10-03 | 国家电网公司 | A kind of planar radio frequency coils for nuclear magnetic resonance |
-
2000
- 2000-02-21 CN CN 00102385 patent/CN1201165C/en not_active Expired - Fee Related
Cited By (6)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN100416294C (en) * | 2002-06-21 | 2008-09-03 | 皇家飞利浦电子股份有限公司 | Magnetic resonance imaging apparatus and method |
| CN103364747A (en) * | 2012-04-05 | 2013-10-23 | 西门子公司 | Method and control apparatus for controlling magnetic resonance systems |
| CN103364747B (en) * | 2012-04-05 | 2016-11-23 | 西门子公司 | For controlling method and control equipment, the magnetic resonance system of magnetic resonance system and controlling sequence determination device |
| US10416258B2 (en) | 2012-04-05 | 2019-09-17 | Siemens Aktiengesellschaft | Controlling magnetic resonance systems |
| CN104155622B (en) * | 2014-08-26 | 2017-10-03 | 国家电网公司 | A kind of planar radio frequency coils for nuclear magnetic resonance |
| CN106526512A (en) * | 2016-11-30 | 2017-03-22 | 重庆三峡学院 | Radio frequency coil capable of being used for head nuclear magnetic resonance imaging |
Also Published As
| Publication number | Publication date |
|---|---|
| CN1201165C (en) | 2005-05-11 |
Similar Documents
| Publication | Publication Date | Title |
|---|---|---|
| CN102772210B (en) | Diffusion weighted MR imaging | |
| US6326789B1 (en) | Receive coil and magnetic resonance imaging method and apparatus | |
| JP4283580B2 (en) | Method for optimizing k-space trajectory of magnetic resonance tomography apparatus | |
| CN102933141B (en) | Rf coil unit and mri apparatus | |
| CN1301524A (en) | Magnetic resonance signal receiver and magnetic resonance imaging device | |
| CN103076582B (en) | The method and magnetic resonance device of the MR data in collection three-D volumes fragment | |
| CN1201165C (en) | RF coil and magnetic resonance imaging method and equipment | |
| EP1122550A1 (en) | RF coil array with reduced intercoil coupling | |
| CN1201166C (en) | Receiving coil and magnetic resonance imaging method and equipoment | |
| US6297636B1 (en) | RF coil, RF magnetic field generating apparatus and magnetic resonance imaging method and apparatus | |
| JP3034851B1 (en) | RF coil and magnetic resonance imaging method and apparatus | |
| CN1245047A (en) | Section K-space method for 3-D magnetic resonance imaging | |
| CN1278422A (en) | Method for mfg. gradient coil, gradient coil unit, gradient coil nuclear magnetic resonance imaging apparatus | |
| CN1355425A (en) | Magnetic resonance imaging method, three-D imaging method and magnetic resonance imaging system | |
| CN1192245C (en) | MR imaging method and apparatus | |
| KR100678872B1 (en) | Magnetic resonance imaging method and apparatus | |
| CN1196439C (en) | FR coil and magnetic resonance image system | |
| JPH1057340A (en) | Mr signal receiving method, apparatus and rf coil | |
| KR100610931B1 (en) | Rf coil and magnetic resonance imaging method and apparatus | |
| JP4542357B2 (en) | RF coil and MRI apparatus | |
| JP4699739B2 (en) | MRI equipment | |
| JP4030676B2 (en) | Magnetic resonance imaging device | |
| CN1531903A (en) | RF coil device and magnetic resonant imaging device | |
| JP4002805B2 (en) | Coil assembly, magnetic field forming apparatus, and magnetic resonance imaging apparatus | |
| WO2013023186A1 (en) | System and method for the establishment of magnetic field patterns in a coil set with voltage-driven current shunts |
Legal Events
| Date | Code | Title | Description |
|---|---|---|---|
| C06 | Publication | ||
| PB01 | Publication | ||
| C10 | Entry into substantive examination | ||
| SE01 | Entry into force of request for substantive examination | ||
| C14 | Grant of patent or utility model | ||
| GR01 | Patent grant | ||
| C17 | Cessation of patent right | ||
| CF01 | Termination of patent right due to non-payment of annual fee |
Granted publication date: 20050511 |