CN1191785C - Magnetic resonance imaging apparatus - Google Patents
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- CN1191785C CN1191785C CN 99110629 CN99110629A CN1191785C CN 1191785 C CN1191785 C CN 1191785C CN 99110629 CN99110629 CN 99110629 CN 99110629 A CN99110629 A CN 99110629A CN 1191785 C CN1191785 C CN 1191785C
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Abstract
In order to provide a magnetic resonance imaging method and apparatus which avoids artifacts due to the motion of a subject when the imaging is conducted with the interval between time phases reduced, a two-dimensional Fourier space is divided into a plurality of regions A, A' - D, D' symmetrically with respect to the frequency axis kx, and data acquisitions for the peripheral regions B and B', C and C', D and D' are sequentially conducted with the data acquisition for the central regions A and A' interposed each time. At this time, the data acquisition is conducted alternately for each TR in a pair of symmetric regions, thereby minimizing the time difference between symmetric data.
Description
The present invention relates to a kind of magnetic resonance imaging method and device, more particularly, the present invention relates to utilize a pulse train to obtain data, and according to the magnetic resonance imaging method and the device of the data reconstruction image that is obtained, this pulse train produce a magnetic resonance signal at each TR (repetition time).
In magnetic resonance imaging, utilize driving pulse to excite spin in the acceptor at each TR, obtain the magnetic resonance signal that shows as gtadient echo or spin echo form that produced by excitation to fill bidimensional Fourier space.Make magnetic resonance signal have different phase codes for each view, and obtain the echo data of the different a plurality of views on the spatial phase shaft of bidimensional Fourier position.Echo data with all views of being obtained carries out the inverse transformation of bidimensional Fourier with reconstruct one images then.
When obtaining echo data, carry out a program, this program comprise the steps: that bidimensional Fourier spatial division become to comprise phase shaft initial point (is zero in this phase code amount) and near initial point the less one section interval of phase code amount absolute value middle section and in a bigger neighboring area of middle section both sides phase code amount absolute value; Carry out data acquisition, fill a neighboring area, middle section and another neighboring area successively so that utilize viewdata, carry out data acquisition then, fill middle section and a neighboring area successively so that utilize viewdata, then carry out data acquisition, so that utilize viewdata to fill middle section and another neighboring area; Carry out data acquisition repeatedly, thereby reduce the interval between the data acquisition of middle section with respect to the interval between the data acquisition of each neighboring area.
When carrying out this data acquisition, use by data to constitute one group of data and carry out image reconstruction as the data that gather the neighboring area of middle section both sides as the middle section collection.The data of employed here two side peripheral areas are its acquisition time cycle and the most approaching data of middle section data acquisition time cycle.This make corresponding to middle section continuously more new data can reconstruct a plurality of successive images.
The state (time phase) of each reconstructed image indication acceptor in about time cycle of gathering the middle section data.Because utilize above-mentioned data acquisition program to reduce the interval of middle section data acquisition, the image of reconstruct at length indicates the time phase of acceptor continuously.
But, according to data acquisition program, owing to be to carry out these regional data acquisitions successively, so the data acquisition time cycle one of in the neighboring area of middle section both sides is different with another neighboring area according to the view number order.Because but these neighboring areas are endowed the phase code amount with same absolute contrary sign, so as long as time phase that is different from another neighboring area time phase of a neighboring area, the any symmetry all can destroy data that moves of acceptor then, therefore, may cause in reconstructed image, occurring interference images.
An object of the present invention is to provide a kind of magnetic resonance imaging method and device, they can avoid when imaging the interference images that produces that moves owing to acceptor, and have reduced the interval between time phase.
According to a first aspect of the invention, provide a kind of magnetic resonance imaging method, this method may further comprise the steps: a bidimensional Fourier spatial division is become with respect to a frequency axis symmetric a plurality of zones corresponding with DC component; Be mutually symmetrical and carry out alternately gathering of magnetic resonance signal for a pair of repeatedly with the most approaching middle section of the frequency axis in said a plurality of zones, with for many except that a pair of middle section that is mutually symmetrical pair of selected in the neighboring area is carried out alternately gathering of magnetic resonance signal, when each the repetition according to from a pair of right to the selected neighboring area of another right order conversion; Use by in once repeating for said middle section to the magnetic resonance signal gathered and with this repetition in one group of magnetic resonance signal constituting of many corresponding magnetic resonance signals of the most approaching corresponding time point collection of the right data acquisition time point of middle section image of reconstruct continuously to the neighboring area.
According to a second aspect of the invention, provide a kind of Magnatic Resonance Imaging (MRI) apparatus, this device comprises: the area limiting device is used for a bidimensional Fourier spatial division is become with respect to a frequency axis symmetric a plurality of zones corresponding with DC component; The acquisition of magnetic resonance signals device, be used for repeatedly being mutually symmetrical and carrying out alternately gathering of magnetic resonance signal with the most approaching middle section of the frequency axis in said a plurality of zones for a pair of, with for many except that a pair of middle section that is mutually symmetrical pair of selected in the neighboring area is carried out alternately gathering of magnetic resonance signal, when each the repetition according to from a pair of right to the selected neighboring area of another right order conversion; With the image reconstruction device, be used for using by once repeat for said middle section to the magnetic resonance signal gathered and with this repetition in one group of magnetic resonance signal constituting of many corresponding magnetic resonance signals of the most approaching corresponding time point collection of the right data acquisition time point of middle section image of reconstruct continuously to the neighboring area.
According to a third aspect of the invention we, provide as the described magnetic resonance device of second aspect, wherein said acquisition of magnetic resonance signals device is said middle section to said many to neighboring area collecting magnetic resonance signal alternately on the symmetric position with respect to frequency axis.
According to the present invention, for each zone of in bidimensional Fourier space, being mutually symmetrical to collecting magnetic resonance signal alternately, thereby reduce time difference between each regional centering viewdata.And, carry out data acquisition in regular turn, so that be the interval between the data acquisition of middle section and the weak point of comparing for the corresponding interval between the data acquisition of neighboring area.
According to a forth aspect of the invention, provide as arbitrary described Magnatic Resonance Imaging (MRI) apparatus in the second aspect and the third aspect, wherein the acquisition of magnetic resonance signals device is gathered carrying out replacing of magnetic resonance signal for middle section repeatedly, to gather all right magnetic resonance signals of middle section, then for many alternately collections of carrying out magnetic resonance signal, to gather all right magnetic resonance signals of selected neighboring area to selecting in the neighboring area.
According to a fifth aspect of the invention, provide as arbitrary described Magnatic Resonance Imaging (MRI) apparatus in the second aspect and the third aspect, wherein said acquisition of magnetic resonance signals device repeatedly for middle section to many in the neighboring area selected one carry out alternately gathering of magnetic resonance signal, with gather middle section to selected all right magnetic resonance signals of neighboring area.
Therefore, the invention provides a kind of magnetic resonance imaging method and device, they have avoided moving the interference images of generation owing to acceptor when imaging, and have reduced the interval between time phase.
Can be well understood to of the present invention other purpose and advantage with reference to accompanying drawing for the description of the preferred embodiments of the present invention by following.
Fig. 1 is the block diagram of a kind of device of formation according to the present invention.
Fig. 2 is the sequential chart of the employed illustrated example pulse sequence of this device imaging.
Fig. 3 is the sketch map of this device of expression for the spatial exemplary division of bidimensional Fourier.
Fig. 4 is the sketch map of the spatial data acquisition of bidimensional Fourier for this device of expression.
Fig. 5 is the sketch map of the spatial data acquisition of bidimensional Fourier for this device of expression.
Fig. 6 is the sketch map of the spatial data acquisition of bidimensional Fourier for this device of expression.
Fig. 7 carries out the sequential chart of data acquisition for this device.
Fig. 8 carries out another sequential chart of data acquisition for this device.
Fig. 9 carries out the sketch map of image reconstruction for this device of expression.
Figure 10 is the sketch map of the spatial data acquisition of bidimensional Fourier for this device of expression.
Figure 11 carries out the sequential chart of data acquisition for this device.
Figure 12 carries out another sequential chart of data acquisition for this device.
Figure 13 carries out the sketch map of image reconstruction for this device of expression.
Introduce embodiments of the invention in further detail referring now to accompanying drawing.Fig. 1 is the block diagram as a kind of Magnatic Resonance Imaging (MRI) apparatus of one embodiment of the present of invention.An embodiment of the device that the structure representative of this device constitutes according to the present invention, and an embodiment of method of the present invention is represented in the operation of this device.
(structure)
Introduce the structure of Magnatic Resonance Imaging (MRI) apparatus now.As shown in Figure 1, this device comprises that is a tubular magnetostatic field generation part 2 substantially, and being used within it, the portion space produces uniform magnetostatic field (main field).Be provided with one and basic be tubular main coil part 6 for tubular gradient coil part 4 and one are basic in magnetostatic field generation part 2, these two coiler parts have a common central shaft.Acceptor 8 is placed by supporting arrangement (not shown) carrying that of being formed in the main coil 6 is basic to be tubular space.
Utilize main coil part 6 to pick up the magnetic resonance signal that spins and produce by being excited.Said main coil part 6 links to each other with a receptor part 14 that is used to receive the signal that is picked up by main coil part 6.
Be sent to a computer 18 from the digital signal of said analog-digital converter part 16 outputs, said computer 18 is stored in received signal in the memorizer (not shown).Thereby in memorizer, constitute a data space.This data space constitutes a bidimensional Fourier space.Computer 18 carries out the inverse transformation of bidimensional Fourier for the data in the said bidimensional Fourier space.
(operation)
Introduce the operation of this device now.Imaging is to carry out under the control of control section 20.Introduce imaging procedures with the gtadient echo technology as special case of magnetic resonance imaging below.The gtadient echo technology is used the pulse train as the exemplary expression of Fig. 2.
Fig. 2 is the schematically showing of pulse train of the magnetic resonance signal (gtadient echo signal) that is used to obtain a view.This pulse train repeated in the cycle of 1TR, for example, 256 times, to gather the gtadient echo signal of 256 views.
The collection of the enforcement of pulse train and gtadient echo signal is by control section 20 controls.Obviously, this imaging technique is not limited to the gtadient echo technology, can also adopt for example spin echo technique of other technology.
Shown in Fig. 2 (6), this pulse train (a)-(c) is divided into three phases along time shaft.At first, utilize as realizing the RF excitation at 90 ° of pulse P90 shown in (1) in the stage (a).Said RF excitation is to utilize the main coil part 6 by transmitter portion 12 excitations to realize.
Meanwhile, as shown in (2), apply a slice gradient magnetic field Gs.Said slice gradient magnetic field Gs utilizes the gradient coil part 4 by 10 excitations of gradient driver unit to apply.Thereby excite the spin (selective exitation) in the predetermined section in the acceptor 8.
Then, shown in (3) in the stage (b), apply a phase encoding gradient magnetic field Gp.Phase encoding gradient magnetic field Gp utilizes the gradient coil part 4 by 10 excitations of gradient driver unit to realize.Thereby phase code is carried out in spin.
Utilize as phase code in the stage slice gradient magnetic field Gs shown in (2) phasing (rephase) is carried out in spin again.In addition, read gradient magnetic Gr for one that applies shown in (4), spin is separated phase (dephase).The said gradient magnetic Gr that reads utilizes the gradient coil part 4 by 10 excitations of gradient driver unit to apply.
Then, apply and shown in (4) in the stage (c), read gradient magnetic Gr, thereby produce the gtadient echo signal MR of the acceptor 8 as shown in (5).
Gtadient echo signal MR is received by main coil part 6.The signal that is received is sent to computer 18 by receptor part 14 and analog-digital converter part 16.Computer 18 is kept at the signal that is sent in the memorizer as measurement data.So in the bidimensional Fourier space of memorizer, collect the gtadient echo data of a view.
In the cycle of 1TR, repeat aforesaid operations, for example 256 times.When each repetitive operation, change phase encoding gradient magnetic field Gp between repeatedly repeating, to form different phase codes.With dashed lines is represented this situation in Fig. 2 (3).
Referring now to Fig. 3,, the figure shows the bidimensional Fourier space that in memorizer, forms, also be referred to as the conceptual diagram in " k-space " sometimes.As shown in Figure 3, said bidimensional Fourier space has mutually orthogonal two coordinate axes kx and ky.The kx axle is represented frequency axis, and the ky axle is represented phase shaft.Bidimensional Fourier space changes along two axles from+100% to-100%.
Bidimensional Fourier space is along the axle of phase shaft direction with respect to ky=0, and perhaps frequency axis kx is divided into 8 zones symmetrically, promptly regional A, A ', B, B ', C, C ', D and D '.Every group of zone A and A ', B and B ', C and C ', D and D ' constitute a pair of zone that is mutually symmetrical.
Zone group A and A ' are right with the most approaching zone of frequency axis kx, and these two zones are called as " middle section " hereinafter.Zone A and A ' represent an example of middle section according to the present invention.Other area B and B ', C and C ', D and D ' be arranged in regular turn regional A and A ' around, they represent an example of neighboring area according to the present invention.
Preferably, bidimensional Fourier space is divided into regional A, A '-D, D ' equably, makes to have impartial interval hereinafter the time phase of a plurality of reconstructed images of detailed description.But, when allowing to have unequal interval time phase, divide with regard to not needing that equalization is carried out in bidimensional Fourier space.In addition, the quantity of division is not limited to 8, and can be to be equal to or greater than any even number of 6.This division is finished by computer 18.
As illustrational hereinafter, computer 18 carries out data acquisition according to certain order for the bidimensional Fourier space of so dividing.Some examples of data acquisition track in Fig. 4-6, have been represented to carry out for bidimensional Fourier space.
At first, gather viewdata (hereafter is " data ") along track shown in Figure 4.At first have+data of 100% phase code amount along track 1 collection.Track 1 belongs to neighboring area D.Then, gather data along track 2 with-100% phase code amount.Track 2 belongs to neighboring area D '.
But track 1 and 2 is arranged in the position that bidimensional Fourier space phase code measurer has the same absolute contrary sign.For the time difference between track 1 and 2 data of gathering is 1TR.The time difference of 1TR is the minima by time difference between the data of apparatus of the present invention collection.For example, 1TR equals 20 milliseconds.In other words, collection has for example data of 20 milliseconds of time differences on the position that is mutually symmetrical along phase shaft direction in the bidimensional Fourier space.Can think positively that these data have essentially identical time phase.
Then, gather the data of phase code amount with the little step of ratio+100% along the track 3 that belongs to neighboring area D.Then, gather the data that have than the phase code amount of one 100% a little step along the track 4 that belongs to neighboring area D '.But track 3 and 4 is arranged in the position that bidimensional Fourier space phase code measurer has the same absolute contrary sign.Time difference between track 3 and 4 data of gathering is 1TR.
Afterwards, replace image data according to same way as in the symmetric position of neighboring area D and D '.So the time difference in neighboring area D and D ' between the data of symmetric position collection is respectively 1TR.
When finishing at track m during for the data acquisition of neighboring area D and D ', beginning is for the data acquisition of middle section A and A '.In other words, gathers in middle section A along a track m+1 who belongs to middle section A and to have the data of maximum positive phase encoding amount, an edge track m+2 belonging to middle section A ' gathers in middle section A ' and has the data of maximum minus phase encoding amount then.
Then, in middle section A, gather the data that have than the phase code amount of the little step of maximum positive phase encoding amount along a track m+3 who belongs to middle section A, in middle section A ', gather the data that have than the phase code amount of the little step of maximum minus phase encoding amount along a track m+4 who belongs to middle section A ' then.Afterwards, according to same way as symmetric position image data continuously in middle section A and A ', till reaching the track n-1 and n adjacent with the ky=0 axle.Equally, the time difference between the data of symmetric position collection is respectively 1TR in middle section A and A '.
Then, along track image data shown in Figure 5.In other words, gathers in the C of neighboring area along the track 1 ' that belongs to neighboring area C and to have the data of maximum positive phase encoding amount, the edge track 2 ' that belongs to neighboring area C ' is gathered in the C ' of neighboring area and is had the data of maximum minus phase encoding amount then.
But track 1 ' and 2 ' is arranged in the position that bidimensional Fourier space phase code measurer has the same absolute contrary sign.Time difference between track 1 ' and the 2 ' data of gathering is 1TR.
Then, in the C of neighboring area, gather the data that have than the phase code amount of the little step of maximum positive phase encoding amount along the track 3 ' that belongs to neighboring area C.Then, in the C ' of neighboring area, gather the data that have than the phase code amount of the little step of maximum minus phase encoding amount along the track 4 that belongs to neighboring area C '.But track 3 ' and 4 ' is arranged in the position that bidimensional Fourier space phase code measurer has the maximum value contrary sign.Time difference between track 3 ' and the 4 ' data of gathering is 1TR.
Afterwards, replace image data according to the symmetric position of the same manner in neighboring area C and C '.So the time difference between the data of the symmetric position collection in neighboring area C and C ' is respectively 1TR.
When finishing the data acquisition of the track m ' in neighboring area C and C ', the data acquisition of beginning middle section A and A '.The data acquisition of middle section A and A ' is carried out according to aforementioned the same manner.So the time difference in middle section A and A ' between the data of symmetric position collection is respectively 1TR.But the data of gathering for middle section A and A ' this moment and front are that the data of middle section A and A ' collection are separated and are kept in the memorizer.
Then, edge track image data as shown in Figure 6.In other words, gather the data that have maximum positive phase encoding amount among the B of neighboring area, gather the data that have maximum minus phase encoding amount among the B ' of neighboring area along the track 2y that belongs to neighboring area B ' then along the track 1y that belongs to neighboring area B.
But track 1y and 2y are arranged in the position that bidimensional Fourier space phase code measurer has the same absolute contrary sign.Time difference between the data of track 1y and 2y collection is 1TR.
Then, gather the data that have among the B of neighboring area than the phase code amount of the little step of maximum positive phase encoding amount along the track 3y that belongs to neighboring area B.Then, gather the data that have among the B ' of neighboring area than the phase code amount of the little step of maximum minus phase encoding amount along the track 4 ' that belongs to neighboring area B '.But track 3y and 4y are arranged in the position that bidimensional Fourier space phase code measurer has the same absolute contrary sign.Time difference between the data of gathering in track 3y and 4y is 1TR.
Afterwards, replace image data according to the same manner symmetric position in neighboring area B and B '.So the time difference in neighboring area B and B ' between the data of symmetric position collection is respectively 1TR.
When track my finishes the data acquisition of neighboring area B and B ', the data acquisition of beginning middle section A and A '.The same manner carries out the data acquisition of middle section A and A ' as described above.So the time difference in middle section A and A ' between the data of symmetric position collection is respectively 1TR.But the middle section A of middle section A that gather this moment and the data of A ' and collection in the past and the data of A ' are separated and are kept in the memorizer.
Then, program is returned data acquisition as shown in Figure 4, afterwards, carries out data acquisition as shown in Figure 5 and Figure 6; And carry out whole procedure repeatedly.The data that repeated acquisition is obtained are kept at corresponding zone in the memorizer.
Fig. 7 represents above-mentioned data acquisition according to chronological order, and wherein vertical axis is represented the phase code amount, the trunnion axis express time.As shown in Figure 7, for t0-t1 hocket data acquisition of neighboring area D and D ' of each TR in the period, for t1-t2 hocket data acquisition of middle section A and A ' of each TR in the period, for t2-t3 hocket data acquisition of neighboring area C and C ' of each TR in the period, for t3-t4 in the period each TR carry out the data acquisition of middle section A and A ', for t4-t5 in the period each TR carry out the data acquisition of neighboring area B and B ', for t5-t6 in the period each TR carry out the data acquisition of middle section A and A '; And repeat whole procedure.
In other words, carry out the data acquisition of a plurality of neighboring area B and B ', C and C ' and D and D ' continuously, insert the data acquisition of middle section A and A ' at every turn in the centre.Therefore, reduced the time difference of data acquisition time between the cycle of middle section A and A '.In addition, in every pair of zone, be 1TR along the time difference between the data of phase shaft direction symmetric position collection.
Although be according to the phase code amount is carried out from the mode that maximum progressively changes to minima for each regional data acquisition as mentioned above, but obviously can carry out data acquisition like this, make the phase code amount progressively change to maximum, as the exemplary expression of Fig. 8 from minima.
The data of neighboring area C and C ' and D and D ' are exactly respectively in the data of during back and formerly period gathering adjacent with period Ti.The data acquisition period of neighboring area B and B ' is not adjacent with period Ti, but the most approaching with it.The data of neighboring area B and B ' can be used before the period Ti or after the period Ti, because they are identical with respect to the time difference of period Ti.
The image that uses these data reconstructions be basically acceptor 8 in period Ti, i.e. the image of the state of period Ti is because the data of middle section A and A ' are gathered in period Ti.
Utilize the data of the middle section A that in period Ti+1, gathers and A ' then and carry out another image reconstruction, shown in Fig. 9 (3) at neighboring area B that gathers with the immediate corresponding period of period Ti+1 and the data of B ', C and C ', D and D '.Obtain to belong to substantially the image of period Ti+1 thus.
Then, utilize at the data of middle section A that period Ti+2 gathers and A ' and the neighboring area B that in corresponding period, gathers and the data of B ', C and C ', D and D ' and carry out image reconstruction again, shown in Fig. 9 (4) near period Ti+2.Obtain to belong to substantially the image of period Ti+2 thus.
Afterwards, utilize the data of the middle section A that gathers in a certain period and A ' and the neighboring area B that gathers in corresponding period of the most approaching a certain period and the data of B ', C and C ', D and D ' to carry out image reconstruction in the same way, thereby generate image time phase of each data acquisition period of middle section A and A '.
Because data acquisition is by carrying out for the data acquisition of middle section A and A ' each the insertion when gathering the data of a plurality of neighboring areas, so reduced time difference between time phase of collection middle section A and A '.Therefore, a plurality of images of continuous reconstruct are with the state that indicates acceptor 8 time phase of minute interval.
In addition, owing to be respectively 1TR for each zone to the time difference between the data of each position of being mutually symmetrical along phase shaft, acceptor 8 any moves for data and produces influence along phase shaft direction equalization.Therefore, in bidimensional Fourier space, keep the symmetry of data, thereby avoided in reconstructed image, occurring interference images.
So apparatus of the present invention of operation can be effectively applied to various uses, obtain when being included in bend elbow or knee elbow joint or knee joint interior tissue image, the contrast agent in the injected into blood vessel is carried out dynamic imagery or to the imaging of puncture needle situation of movement in the diagnosis such as biopsy.
Though the above-mentioned data acquisition for middle section A and A ' and neighboring area B and B ', C and C ', D and D ' is carried out according to regional order, but also can be according to gathering a pair of neighboring area data, and the mode of inserting the data acquisition of a pair of middle section be carried out data acquisition.In other words, as the exemplary expression of Figure 10, data acquisition is carried out according to order, at first the track in neighboring area D and D ' 1 and 2; Then, the track in middle section A and A ' 3 and 4 '; Then, the track 5 and 6 of track 1 and 2 inboards in neighboring area D and D '; Afterwards, the track 3 in middle section A and A ' and the track 7 and 8 of 4 inboards, or the like.In neighboring area D and D ' and middle section A and A ' for each track to such data acquisition that hockets.Data acquisition to neighboring area B and B ' and C and C ' is carried out in the same way.
Figure 11 is according to the above-mentioned operation of temporal representation.As shown in the figure, carry out for the data acquisition of neighboring area D and D ' with for the data acquisition of middle section A and A ' at period t0-t0 with interlace mode, carry out for neighboring area C and C ' with for the data acquisition of middle section A and A ' at period t2-t4 with interlace mode, carry out data acquisition at period t4-t6 for neighboring area B and B ' and middle section A and A ' with interlace mode.Repeat whole procedure afterwards.Obviously, can carry out data acquisition from a point to a point as shown in figure 12 away from frequency axis near frequency axis.
By such data acquisition, obtain as Figure 13 (1) according to the data shown in the time sequencing.As shown in the figure, when carrying out the data acquisition of middle section A and A ' continuously, sequentially carry out the data acquisition of neighboring area B and B ', C and C ' and D and D '.Carry out image reconstruction according to the mode shown in for example Figure 13 (2)-(4) according to the data of so obtaining.
In other words, utilize the middle section A that gathers at period Tj and A ' data and respectively before period Tj, afterwards and the image of the data reconstruction period Tj of the neighboring area B that gathers of eclipsed with it period (shown in Figure 13 (2)) and B ', C and C ', D and D '; Middle section A that utilization is gathered at period Tj+1 and the data of A ' and respectively before period Tj+1, afterwards and the image of the data reconstruction period Tj+1 of the neighboring area B that gathers of eclipsed with it period (shown in Figure 13 (3)) and B ', C and C ', D and D '; Middle section A that utilization is gathered at period Tj+2 and the data of A ' and respectively before period Tj+2, afterwards and the image of the data reconstruction period Tj+2 of the neighboring area B that gathers of eclipsed with it period (shown in Figure 13 (4)) and B ', C and C ', D and D '.Carry out image reconstruction afterwards in the same way.Preferably, so be successive the time phase of a plurality of images of reconstruct.
Though above description is to make with reference to the Magnatic Resonance Imaging (MRI) apparatus in application level magnetic field, obviously this device can be used so-called vertical magnetic field, wherein the body shaft quadrature of the direction of static magnetic field and acceptor.
In addition, though above description is to make at the example according to the data of a view of 1TR interval collection, obviously the present invention is not limited thereto, but can be applied to gather according to the interval of 1TR the data conditions of a plurality of views.And the present invention can be applied to EPI (echo wave plane imaging) technology.Under the prerequisite that does not break away from design of the present invention and scope, can constitute the different embodiment that the more plants of the present invention.Should be appreciated that the present invention is not limited to the specific embodiment described in the description, and be limited by the accompanying claims.
Claims (4)
1, a kind of Magnatic Resonance Imaging (MRI) apparatus, it comprises:
The area limiting device, be used for bidimensional Fourier spatial division become with respect to the axisymmetric a plurality of zones of DC component correspondent frequency;
The acquisition of magnetic resonance signals device, be used for repeatedly to being mutually symmetrical and carrying out alternately gathering of magnetic resonance signal with the immediate a pair of middle section of the frequency axis in said a plurality of zones, with to except that said middle section to be mutually symmetrical many pair of selected in the neighboring area is carried out alternately gathering of magnetic resonance signal, and when each the repetition according to from a pair of right to the selected neighboring area of another right order conversion; With
The image reconstruction device, be used for utilizing be included in repetitive process for said middle section to the magnetic resonance signal gathered and with this repetitive process in one group of magnetic resonance signal reconstructed image sequentially of the right data acquisition time of middle section many corresponding magnetic resonance signals to the neighboring area of putting that immediate a plurality of corresponding time point gathers.
2, Magnatic Resonance Imaging (MRI) apparatus as claimed in claim 1, it is characterized in that said acquisition of magnetic resonance signals device be middle section with respect to the symmetric a plurality of positions of frequency axis to many to neighboring area collecting magnetic resonance signal alternately.
3, Magnatic Resonance Imaging (MRI) apparatus as claimed in claim 1 or 2, it is characterized in that said acquisition of magnetic resonance signals device repeatedly for middle section to carrying out alternately the gathering of magnetic resonance signal to gather all right magnetic resonance signals of middle section, for many pair of selected in the neighboring area is carried out alternately gathering to gather all right magnetic resonance signals of selected neighboring area of magnetic resonance signal then.
4, Magnatic Resonance Imaging (MRI) apparatus as claimed in claim 3 is characterized in that said acquisition of magnetic resonance signals device is that middle section is to carrying out alternately gathering to gather middle section to all magnetic resonance signals right with selected neighboring area of magnetic resonance signal with many to pair of selected in the neighboring area repeatedly.
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| CN 99110629 CN1191785C (en) | 1998-07-21 | 1999-07-21 | Magnetic resonance imaging apparatus |
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| JP205069/1998 | 1998-07-21 | ||
| JP10205069A JP3051374B2 (en) | 1998-07-21 | 1998-07-21 | Magnetic resonance imaging device |
| JP205069/98 | 1998-07-21 | ||
| CN 99110629 CN1191785C (en) | 1998-07-21 | 1999-07-21 | Magnetic resonance imaging apparatus |
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| JP3878429B2 (en) * | 2001-04-05 | 2007-02-07 | ジーイー・メディカル・システムズ・グローバル・テクノロジー・カンパニー・エルエルシー | MRI equipment |
| JP3814157B2 (en) * | 2001-04-17 | 2006-08-23 | ジーイー・メディカル・システムズ・グローバル・テクノロジー・カンパニー・エルエルシー | MRI equipment |
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