CN103845055B - Cardiac magnetic resonance imaging method and system - Google Patents
Cardiac magnetic resonance imaging method and system Download PDFInfo
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- CN103845055B CN103845055B CN201210511669.8A CN201210511669A CN103845055B CN 103845055 B CN103845055 B CN 103845055B CN 201210511669 A CN201210511669 A CN 201210511669A CN 103845055 B CN103845055 B CN 103845055B
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Abstract
The invention provides a cardiac magnetic resonance imaging method, which comprises the following steps of applying first selected-layer 180-degree radio-frequency pulses to an imaging layer in a diastolic period of a first cardiac cycle according to a first electrocardiogram trigger signal; applying first non-selected-layer 180-degree radio-frequency pulses to an area including the imaging layer in a systaltic period of a second cardiac cycle according to a second electrocardiogram trigger signal, wherein the area comprises a heart tissue and blood; after relaxation time T for a magnetization vector of the blood, exciting the imaging layer and acquiring image data. The application of the selected-layer 180-degree radio-frequency pulses and the excitation of the imaging layer are positioned at adjacent time phases of the cardiac cycle, so the problem that a selected-layer 180-degree radio-frequency pulse applying layer and a sequence exciting layer are inconsistent is solved. The invention also provides a cardiac magnetic resonance imaging system.
Description
[technical field]
The present invention relates to magnetic resonance imaging arts, especially relate to a kind of cardiac magnetic resonance imaging method and system.
[background technology]
At present in nuclear magnetic resonance process, adopt black blood technology to avoid or eliminate the artifact that blood flow signal produces.So-called black blood, refers to the blood flowing into imaging aspect, because proton in blood is without Mxy, and the no signal when sequence excites and present black.Conventional black blood technology comprises the empty technology of spin echo stream and inversion recovery (Single inversion recovery), double-inversion recovers (double inversion recovery) technology etc., what wherein commonly use in the magnetic resonance imaging of heart is double-inversion recovery technology, this technology can ensure under the effect suppressing blood flow preferably, keep myocardial signal, artifact is less.
Double-inversion recovery technology in use, can be used non-choosing layer 180 degree of radio-frequency pulse of binding together and select layer 180 degree of radio-frequency pulse, and in heart scanning process, adopt the black blood module of double-inversion recovery technology, its implementation process is as follows:
1, after receiving electrocardio triggering signal, applying non-choosing layer 180 degree of radio-frequency pulse to comprising the region needing imaging aspect, making the magnetization vector in whole region turn over turnback;
2, and then in a short period of time, apply to select layer 180 degree of radio-frequency pulse to needs imaging aspect, make the magnetization vector of imaging aspect turn over turnback;
3, the magnetization vector of blood relax towards close to zero time, be excited into picture aspect;
4, acquisition of image data while.
When the signal not comprising the blood that selected layer 180 degree of radio-frequency pulses excited relaxes towards very little or even zero, be excited into picture aspect, because blood is flowing, flowing into the blood signal of imaging aspect also very little is even zero, so the blood signal in the view data obtained is very little, namely serve the effect of black blood.The tissue such as cardiac muscle, blood vessel wall, pericardium has signal to be Lycoperdon polymorphum Vitt in various degree or white, and like this, blood signal and tissue signal form good contrast, can show the anatomical structure of heart better.
Above-mentioned double-inversion echo technique, whole process completes within a cardiac cycle, and paradoxical expansion applies non-choosing layer 180 degree of radio-frequency pulse, applies to select layer 180 degree of radio-frequency pulse between heart isovolumic contraction period to phase of maximum ejection.Heart isovolumic contraction period up to phase of maximum ejection time, intracardiac pressure raises fast, cardiac muscle rapid desufflation, by blood pump to trunk, the accelerated motion gradually that heart in this process is, and to be excited into as aspect be carry out in the mid-diastolic of heart, the cardiac shape in two stages has very large difference, therefore the imaging aspect selecting layer 180 degree of radio-frequency pulse to be applied to and the imaging aspect excited likely cause the two inconsistent because of the difference of cardiac shape, have occurred the inaccurate situation of choosing layer.
In order to add the accuracy of general election layer, prior art adopts the mode increasing thickness to solve the problems referred to above, but the blood flow volume being in non-excited state can be increased while increasing thickness, can strengthen blood signal like this, weaken black blood effect.Meanwhile, when aspect is thinner, increases the way of thickness and imaging aspect not necessarily can be made selecting layer by layer within face, can myocardial signal be weakened like this.
[summary of the invention]
The invention provides a kind of cardiac magnetic resonance imaging method and system, the method and system can solve double-inversion recovery technology in cardiac magnetic resonance imaging and select the inaccurate problem of layer.
A kind of cardiac magnetic resonance imaging method, comprises the steps:
S10) according to the first electrocardio triggering signal, at the diastole of first cardiac cycle, apply first and select layer 180 degree of radio-frequency pulse to imaging aspect, make the magnetization vector of described imaging aspect turn over turnback;
S20) according to the second electrocardio triggering signal, at the paradoxical expansion of second cardiac cycle, apply the first non-choosing layer 180 degree of radio-frequency pulse to the region comprising described imaging aspect, make the magnetization vector in described region turn over turnback, described region comprises heart tissue and blood;
S30) magnetization vector of described blood is after relaxation time t, excite described imaging aspect and acquisition of image data, described relaxation time t refers to that the magnetization vector of described blood relaxes towards the interval of threshold range, and described blood does not comprise the blood excited by described choosing layer 180 degree of radio-frequency pulse.
Optionally, described threshold range is 0 ~ X, and wherein X refers to 10% of the magnetization vector absolute value of described blood.
Optionally, the late diastole of first cardiac cycle after scanning starts, applies first and selects layer 180 degree of radio-frequency pulse to imaging aspect.
Optionally, after scanning starts, the diastole of first cardiac cycle, excites described imaging aspect but non-image data, applies described first and select layer 180 degree of radio-frequency pulse to described imaging aspect after exciting described imaging aspect.
Optionally, when n is more than or equal to 2, at the diastole of the n-th cardiac cycle, described in excite described imaging aspect and also comprise the steps: after acquisition of image data
S40) applying n-th selects layer 180 degree of radio-frequency pulse to described imaging aspect;
S50) according to the (n+1)th electrocardio triggering signal, at the paradoxical expansion of (n+1)th cardiac cycle, apply the n-th non-choosing layer 180 degree of radio-frequency pulse to the region comprising described imaging aspect, described region comprises heart tissue and blood;
S30) magnetization vector of described blood is after relaxation time t, excites described imaging aspect and acquisition of image data.
Optionally, described view data comprises the view data of imaging layer covering weave and again flows into the view data of blood of imaging aspect.
Optionally, described cardiac magnetic resonance imaging method is applied to gtadient echo man family sequence or spin echo man family sequence.
Optionally, all also comprise before step S10, step S20 and step S50
S60) the R ripple in electrocardio ripple is received,
S70) according to described R ripple, described electrocardio triggering signal is produced.
The present invention also provides a kind of cardiac magnetic resonance imaging system, and described system comprises:
Select layer radio-frequency pulse unit, for according to the first electrocardio triggering signal, at the diastole of first cardiac cycle, apply first and select layer 180 degree of radio-frequency pulse to imaging aspect, make the magnetization vector of described imaging aspect turn over turnback;
Non-choosing layer radio-frequency pulse unit, for the paradoxical expansion at second cardiac cycle, apply the first non-choosing layer 180 degree of radio-frequency pulse to the region comprising described imaging aspect, make the magnetization vector in described region turn over turnback, described region comprises heart tissue and blood;
Excite collecting unit, for the magnetization vector of described blood after relaxation time t, excite described imaging aspect and acquisition of image data, described relaxation time t refers to that the magnetization vector of described blood relaxes towards the interval of threshold range, and described blood does not comprise the blood excited by described choosing layer 180 degree of radio-frequency pulse.
Optionally, described threshold range is 0 ~ X, and wherein X refers to 10% of the magnetization vector absolute value of described blood.
Optionally, select layer radio-frequency pulse unit, also for the late diastole of first cardiac cycle after scanning starts, apply first and select layer 180 degree of radio-frequency pulse to imaging aspect.
Optionally, non-choosing layer radio-frequency pulse unit, also for the diastole of first cardiac cycle after scanning starts, excite described imaging aspect but non-image data, apply described first after exciting described imaging aspect and select layer 180 degree of radio-frequency pulse to described imaging aspect.
Optionally, when n is more than or equal to 2, described radio-frequency pulse unit a, also for the diastole at the n-th cardiac cycle, described in excite described imaging aspect and simultaneously after acquisition of image data, apply n-th and select layer 180 degree of radio-frequency pulse to described imaging aspect;
Described non-choosing layer radio-frequency pulse unit, also for according to the (n+1)th electrocardio triggering signal, at the paradoxical expansion of (n+1)th cardiac cycle, apply the n-th non-choosing layer 180 degree of radio-frequency pulse to the region comprising described imaging aspect, described region comprises heart tissue and blood;
Describedly excite collecting unit, also for the magnetization vector of described blood after relaxation time t, excite described imaging aspect and acquisition of image data.
Optionally, described view data comprises the view data of imaging layer covering weave and again flows into the view data of blood of imaging aspect.
Optionally, described cardiac magnetic resonance imaging system adopts gtadient echo man's family sequence or fast spin echo man family sequence.
Optionally, described system also comprises: receiving element, for receiving the R ripple in electrocardio ripple,
Electrocardio trigger element, for according to described R ripple, produces described electrocardio triggering signal.
The present invention contrasts prior art following beneficial effect:
1) apply to select layer 180 degree of radio-frequency pulse at the relaxing period of a cardiac cycle, the relaxing period of next cardiac cycle is excited into picture aspect, although select layer 180 degree of radio-frequency pulse excite with imaging aspect excite not at same cardiac cycle, but be in next-door neighbour's phase of cardiac cycle relaxing period, the form of heart is roughly the same, therefore can solve in prior art the problem selecting layer 180 degree of radio-frequency pulse to excite aspect and sequence to excite aspect inconsistent.Avoiding the situation in order to select layer accurately to increase the layer block thickness selecting layer 180 degree of radio-frequency pulse to excite in prior art simultaneously, decreasing the blood flow volume selecting layer 180 degree of radio-frequency pulse impact, weakening remaining blood flow signal largely.
2) time point due to the 180 degree of radio-frequency pulse effect of non-choosing layer is consistent with the design of existing scheme, therefore produces the blood signal relaxation time t of black blood effect without the need to making any change because of the enforcement of this programme.Simultaneously because the imaging aspect relaxation of selecting layer 180 degree of radio-frequency pulse to excite is to time of original state much smaller than relaxation time t, so do not affect for imaging layer covering weave signal.
[accompanying drawing explanation]
Fig. 1 is prior art heart cycles and Electrocardiographic corresponding relation figure
Fig. 2 is the sequential chart of prior art cardiac MR imaging method;
Fig. 3 is the schematic flow sheet of cardiac MR imaging method of the present invention;
Fig. 4 is the sequential chart of cardiac MR imaging method of the present invention;
Fig. 5 is the schematic flow sheet of another embodiment of the present invention cardiac magnetic resonance imaging method;
Fig. 6 is the structural representation of cardiac magnetic resonance imaging system of the present invention.
[detailed description of the invention]
For enabling above-mentioned purpose of the present invention, feature and advantage more become apparent, and are described in detail the specific embodiment of the present invention below in conjunction with drawings and Examples.
Set forth a lot of detail in the following description so that fully understand the present invention, but the present invention can also adopt other to be different from mode described here to implement, therefore the present invention is not by the restriction of following public specific embodiment.
In cardiac magnetic resonance imaging, in order to remove the artifact that blood flow produces, the normal black blood technology adopting double-inversion to recover at present.As shown in Figure 2, double-inversion recovery technology completes the process of a data acquisition usually in a cardiac cycle, a cardiac cycle comprises paradoxical expansion and diastole (as shown in Figure 1), first apply to select layer 180 degree of radio-frequency pulse to imaging aspect at paradoxical expansion, at relaxing period, imaging aspect is excited, different from the cardiac shape of relaxing period owing to being in systole, so cause selecting the imaging aspect of layer 180 degree of radio-frequency pulses applying inconsistent with the imaging aspect excited, therefore the formation method that a kind of cardiac magnetic resonance is provided is necessary, to solve the problem.
As shown in Figure 3, a kind of method of cardiac magnetic resonance imaging, comprises the steps:
Perform step S10, according to the first electrocardio triggering signal, at the diastole of first cardiac cycle, apply first and select layer 180 degree of radio-frequency pulse to imaging aspect, make the magnetization vector of described imaging aspect turn over turnback.
Described choosing layer 180 degree of radio-frequency pulse refer to the radio-frequency pulse simultaneously applied with slice selective gradient, and the magnetization vector of specific aspect can be turn to contrary direction by it.
As shown in Figure 1, paradoxical expansion comprises Atrial systole, isovolumic contraction period, phase of maximum ejection, penetrates at a slow speed the blood phase.In practical operation, it is the period judging residing for heart according to electrocardio ripple, electrocardio ripple generally represents with PQRST ripple, wherein P wave table shows that heart enters Atrial systole, Q wave table shows that heart is about to enter isovolumic contraction period, S wave table shows that heart is in isovolumic contraction period, and to T wave table, S ripple shows that heart is by the stage of systole to relaxing period transition, R wave table shows that heart enters isovolumic contraction period by Atrial systole.QRS ripple is as triggered mark, when the R ripple received, namely produces described electrocardio triggering signal.Certainly, as shown in Figures 2 and 4, R ripple and electrocardio trigger the delay between (VSM Trigger) is because Trigger has late effect.
As shown in Figure 1, diastole comprises isovolumic relaxation phase, phase of rapid filling, reduced filling period and diastasis, preferably, in the present embodiment, in the diastasis of first cardiac cycle, applies to select layer 180 degree of radio-frequency pulse to imaging aspect.Or at the diastole of first cardiac cycle, excite described imaging aspect but non-image data, apply described first after exciting described imaging aspect and select layer 180 degree of radio-frequency pulse to described imaging aspect.
Perform step S20, according to the second electrocardio triggering signal, at the paradoxical expansion of second cardiac cycle, apply the first non-choosing layer 180 degree of radio-frequency pulse to the region comprising described imaging aspect, make the magnetization vector in described region turn over turnback, described region comprises heart tissue and blood.
Described non-choosing layer 180 degree of radio-frequency pulse, refer to the radio-frequency pulse not applying slice selective gradient, it can perfect aspect excite, and ensures that all magnetization vectors in magnet bore all turn to contrary direction.
Perform step S30, the magnetization vector of described blood, after relaxation time t, excites described imaging aspect and acquisition of image data.
Described relaxation time t refers to that the magnetization vector of described blood relaxes towards the interval of threshold range, and described blood does not comprise the blood excited by described choosing layer 180 degree of radio-frequency pulse.Preferably, described threshold range is 0 ~ X, and wherein X is 10% of the magnetization vector absolute value of described blood.
Because relaxation time t is generally the half being less than cardiac cycle, and the interval of diastole is longer than Syst interval, therefore when blood signal starts after relaxation time t at systole, heart must be in relaxing period.
Described view data comprises the organize image data of imaging aspect and again flows into the Blood Image data of imaging aspect.The magnetization vector of described blood is because relaxation is to very little or zero, when carrying out exciting collection, the blood of faint magnetization vector flow into imaging aspect again, and it is exactly the part of black that the blood signal in therefore imaging aspect shows in the picture, namely serves the effect of black blood.
Described cardiac magnetic resonance imaging method is applied to gtadient echo man family sequence or spin echo man family sequence.About being excited into picture aspect, adopt different sequences, its process excited is different, but one of ordinary skill in the art should know not homotactic excitation process, and this is no longer going to repeat them.
Said process is process (the employing the technical program of first time image data acquiring, at initial cardiac cycle, do not carry out exciting collection, or carry out exciting but not image data), in actual operation, as shown in Figure 4, except first time excites, to gather imaging be apply to select layer 180 degree of radio-frequency pulse in relaxing period latter stage of preceding cardiac cycle or carry out sequence in mid-diastolic to excite but not except image data, ensuingly to excite in gatherer process at every turn, layer 180 degree of radio-frequency pulse are selected to be all that and then the last time excites the after-applied of collection, as shown in Figure 5, detailed process is as follows:
Namely when n is more than or equal to 2, at the diastole of the n-th cardiac cycle, described in excite described imaging aspect and and then also comprise the steps: after acquisition of image data simultaneously
Perform step S40, apply n-th and select layer 180 degree of radio-frequency pulse to described imaging aspect.
Perform step S50, according to the (n+1)th electrocardio triggering signal, at the paradoxical expansion of (n+1)th cardiac cycle, apply the n-th non-choosing layer 180 degree of radio-frequency pulse to the region comprising described imaging aspect, described region comprises heart tissue and blood.
Re-execute step S30, the magnetization vector of described blood, after relaxation time t, excites described imaging aspect and acquisition of image data.
Below for the 3rd cardiac cycle (namely during n=2), the process exciting image data is described:
Perform step S40, at the diastole of second cardiac cycle, described in excite described imaging aspect and simultaneously and then apply the second choosing layer 180 degree of radio-frequency pulse to described imaging aspect after acquisition of image data.
Perform step S50, according to the 3rd electrocardio triggering signal, at the paradoxical expansion of the 3rd cardiac cycle, apply the 2nd non-choosing layer 180 degree of radio-frequency pulse to the region comprising described imaging aspect, described region comprises heart tissue and blood.
Re-execute step S30, the magnetization vector of described blood, after relaxation time t, excites described imaging aspect and acquisition of image data.
As shown in Fig. 3 and Fig. 5, all also comprise before step S10, step S20 and step S50:
Step S60) receive R ripple in electrocardio ripple.
Step S70) according to described R ripple, produce described electrocardio triggering signal.
The technical program, at the relaxing period of previous cardiac cycle imaging aspect is applied with and selects layer 180 degree of radio-frequency pulse, the relaxing period of a rear cardiac cycle carries out exciting of imaging aspect, although select layer 180 degree of radio-frequency pulse excite with imaging aspect excite not at same cardiac cycle, but be in next-door neighbour's phase of cardiac cycle relaxing period, the form of heart is roughly the same, therefore solves in prior art the problem that imaging aspect that the imaging aspect of selecting layer 180 degree of radio-frequency pulse to apply and sequence excite is inconsistent.
As shown in Figure 6, present invention also offers a kind of cardiac magnetic resonance imaging system, comprising: select layer radio-frequency pulse unit 100, non-choosing layer radio-frequency pulse unit 200 and excite collecting unit 300, wherein
Select layer radio-frequency pulse unit 100, for according to the first electrocardio triggering signal, at the diastole of first cardiac cycle, apply first and select layer 180 degree of radio-frequency pulse to imaging aspect, make the magnetization vector of described imaging aspect turn over turnback; Described choosing layer 180 degree of radio-frequency pulse refer to the radio-frequency pulse simultaneously applied with slice selective gradient, and the magnetization vector of specific aspect can be turn to contrary direction by it.QRS ripple is as triggered mark, when the R ripple received, namely produces described electrocardio triggering signal.
In another embodiment, described choosing layer radio-frequency pulse unit 100, also for the late diastole at first cardiac cycle, applies first and selects layer 180 degree of radio-frequency pulse to imaging aspect; Or described choosing layer radio-frequency pulse unit 100, also for the diastole at first cardiac cycle, excites described imaging aspect but non-image data, apply described first after exciting described imaging aspect and select layer 180 degree of radio-frequency pulse to described imaging aspect.
Non-choosing layer radio-frequency pulse unit 200, for the paradoxical expansion at second cardiac cycle, apply the first non-choosing layer 180 degree of radio-frequency pulse to the region comprising described imaging aspect, make the magnetization vector in described region turn over turnback, described region comprises heart tissue and blood; Described non-choosing layer 180 degree of radio-frequency pulse, refer to the radio-frequency pulse not applying slice selective gradient, it can perfect aspect excite, and ensures that all magnetization vectors in magnet bore all turn to contrary direction.
In the magnetic resonance hardware of reality, the 180 degree of radio-frequency pulses selecting layer radio-frequency pulse unit 100 to apply and the non-180 degree of radio-frequency pulses selecting layer unit to apply are produced by same group or several groups of radio-frequency coils, only select layer 180 degree of radio-frequency pulse also to need to apply the slice selective gradient pulse of gradient coil generation simultaneously.
Excite collecting unit 300, for the magnetization vector of described blood after relaxation time t, excite described imaging aspect and acquisition of image data, described view data comprises the view data of imaging layer covering weave and again flows into the Blood Image data of imaging aspect.
Described relaxation time t refers to that the magnetization vector of described blood relaxes towards the interval of threshold range, described blood does not comprise the blood excited by described choosing layer 180 degree of radio-frequency pulse, preferably, described threshold range is 0 ~ X, and wherein X refers to 10% of the magnetization vector absolute value of described blood.
The above-mentioned process being cardiac magnetic resonance system and carrying out first time image data acquiring, in actual scanning process, as shown in Figure 4, except first time excites, to gather imaging be apply to select layer 180 degree of radio-frequency pulse at the relaxing period end of preceding cardiac cycle or start sequence in mid-diastolic to excite but not except image data, ensuingly to excite in gatherer process at every turn, select layer 180 degree of radio-frequency pulse to be all and then lastly excite the after-applied of collection.
Namely when n is more than or equal to 2, described choosing layer radio-frequency pulse unit 100, also for the diastole at the n-th cardiac cycle, described in excite described imaging aspect and simultaneously after acquisition of image data, apply n-th and select layer 180 degree of radio-frequency pulse to described imaging aspect.
Described non-choosing layer radio-frequency pulse unit 200, also for according to the (n+1)th electrocardio triggering signal, at the paradoxical expansion of (n+1)th cardiac cycle, apply the n-th non-choosing layer 180 degree of radio-frequency pulse to the region comprising described imaging aspect, described region comprises heart tissue and blood.
Describedly excite collecting unit 300, also for the magnetization vector of described blood after relaxation time t, excite described imaging aspect and acquisition of image data.
Described cardiac magnetic resonance imaging system adopts gtadient echo man's family sequence or fast spin echo man family sequence.
As shown in Figure 6, described cardiac magnetic resonance imaging system also comprises:
Receiving element 400, for receiving the R ripple in electrocardio ripple.
Electrocardio trigger element 500, for according to described R ripple, produces described electrocardio triggering signal.
In sum, the technical program applies to select layer 180 degree of radio-frequency pulse at the relaxing period of previous cardiac cycle, the relaxing period of a rear cardiac cycle is excited into picture aspect, although select layer 180 degree of radio-frequency pulse excite with imaging aspect excite not at same cardiac cycle, but be both in the phase of cardiac cycle next-door neighbour, the form of heart is roughly the same, therefore can solve in prior art the problem selecting layer 180 degree of radio-frequency pulse to excite aspect and sequence to excite aspect inconsistent.Avoiding the situation in order to select layer accurately to increase the layer block thickness selecting layer 180 degree of radio-frequency pulse to excite in prior art simultaneously, decreasing the blood flow volume selecting layer 180 degree of radio-frequency pulse impact, weakening remaining blood flow signal largely.And because the time point of non-choosing layer 180 degree of radio-frequency pulse effect is consistent with the design of existing scheme, therefore the relaxation time t of the blood signal of black blood effect is produced without the need to making any change because of the enforcement of this programme, the imaging aspect relaxation simultaneously selecting layer 180 degree of radio-frequency pulse to excite to time of original state much smaller than relaxation time t, so do not affect for imaging layer covering weave signal.
Although the present invention discloses as above with preferred embodiment; so itself and be not used to limit the present invention, any those skilled in the art, without departing from the spirit and scope of the present invention; when doing a little amendment and perfect, therefore protection scope of the present invention is when being as the criterion of defining with claims.
Claims (16)
1. a cardiac magnetic resonance imaging method, is characterized in that, comprises the steps:
S10) according to the first electrocardio triggering signal, at the diastole of first cardiac cycle, apply first and select layer 180 degree of radio-frequency pulse to imaging aspect, make the magnetization vector of described imaging aspect turn over turnback;
S20) according to the second electrocardio triggering signal, at the paradoxical expansion of second cardiac cycle, apply the first non-choosing layer 180 degree of radio-frequency pulse to the region comprising described imaging aspect, make the magnetization vector in described region turn over turnback, described region comprises heart tissue and blood;
S30) magnetization vector of described blood is after relaxation time t, excite described imaging aspect and acquisition of image data, described relaxation time t refers to that the magnetization vector of described blood relaxes towards the interval of threshold range, and described blood does not comprise the blood excited by described choosing layer 180 degree of radio-frequency pulse.
2. cardiac magnetic resonance imaging method as claimed in claim 1, it is characterized in that, described threshold range is 0 ~ X, and wherein X refers to 10% of the magnetization vector absolute value of described blood.
3. cardiac magnetic resonance imaging method as claimed in claim 1, is characterized in that, starting the late diastole scanning rear first cardiac cycle, applies first and selects layer 180 degree of radio-frequency pulse to imaging aspect.
4. cardiac magnetic resonance imaging method as claimed in claim 1, it is characterized in that, starting the diastole scanning rear first cardiac cycle, excite described imaging aspect but non-image data, apply described first after exciting described imaging aspect and select layer 180 degree of radio-frequency pulse to described imaging aspect.
5. cardiac magnetic resonance imaging method as claimed in claim 1, is characterized in that, when n is more than or equal to 2, at the diastole of the n-th cardiac cycle, described in excite described imaging aspect and also comprise the steps: after acquisition of image data
S40) applying n-th selects layer 180 degree of radio-frequency pulse to described imaging aspect;
S50) according to the (n+1)th electrocardio triggering signal, at the paradoxical expansion of (n+1)th cardiac cycle, apply the n-th non-choosing layer 180 degree of radio-frequency pulse to the region comprising described imaging aspect, described region comprises heart tissue and blood;
S30) magnetization vector of described blood is after relaxation time t, excites described imaging aspect and acquisition of image data.
6. cardiac magnetic resonance imaging method as stated in claim 5, is characterized in that, described view data comprises the view data of imaging layer covering weave and again flows into the view data of blood of imaging aspect.
7. cardiac magnetic resonance imaging method as claimed in claim 5, it is characterized in that, described cardiac magnetic resonance imaging method is applied to gtadient echo man family sequence or spin echo man family sequence.
8. the cardiac magnetic resonance imaging method as described in claim 1 or 5, is characterized in that, all also comprises before step S10, step S20 and step S50
S60) the R ripple in electrocardio ripple is received,
S70) according to described R ripple, described electrocardio triggering signal is produced.
9. a cardiac magnetic resonance imaging system, is characterised in that, described system comprises:
Select layer radio-frequency pulse unit, for according to the first electrocardio triggering signal, at the diastole of first cardiac cycle, apply first and select layer 180 degree of radio-frequency pulse to imaging aspect, make the magnetization vector of described imaging aspect turn over turnback;
Non-choosing layer radio-frequency pulse unit, for the paradoxical expansion at second cardiac cycle, apply the first non-choosing layer 180 degree of radio-frequency pulse to the region comprising described imaging aspect, make the magnetization vector in described region turn over turnback, described region comprises heart tissue and blood;
Excite collecting unit, for described blood magnetization vector after relaxation time t, excite described imaging aspect and acquisition of image data, described relaxation time t refers to that the magnetization vector of described blood relaxes towards the interval of threshold range, and described blood does not comprise the blood excited by described choosing layer 180 degree of radio-frequency pulse.
10. cardiac magnetic resonance imaging system as claimed in claim 9, it is characterized in that, described threshold range is 0 ~ X, and wherein X refers to 10% of the magnetization vector absolute value of described blood.
11. cardiac magnetic resonance imaging systems as claimed in claim 9, is characterized in that, described choosing layer radio-frequency pulse unit, also for starting the late diastole scanning rear first cardiac cycle, applying first and selecting layer 180 degree of radio-frequency pulse to imaging aspect.
12. cardiac magnetic resonance imaging systems as claimed in claim 9, it is characterized in that, described choosing layer radio-frequency pulse unit, also for starting the diastole scanning rear first cardiac cycle, excite described imaging aspect but non-image data, apply described first after exciting described imaging aspect and select layer 180 degree of radio-frequency pulse to described imaging aspect.
13. cardiac magnetic resonance imaging systems as claimed in claim 9, is characterized in that, when n is more than or equal to 2,
Described choosing layer radio-frequency pulse unit, also for the diastole at the n-th cardiac cycle, described in excite described imaging aspect and simultaneously after acquisition of image data, apply n-th and select layer 180 degree of radio-frequency pulse to described imaging aspect;
Described non-choosing layer radio-frequency pulse unit, also for according to the (n+1)th electrocardio triggering signal, at the paradoxical expansion of (n+1)th cardiac cycle, apply the n-th non-choosing layer 180 degree of radio-frequency pulse to the region comprising described imaging aspect, described region comprises heart tissue and blood;
Describedly excite collecting unit, also for the magnetization vector of described blood after relaxation time t, excite described imaging aspect and acquisition of image data.
14. cardiac magnetic resonance imaging systems as shown in claim 13, is characterized in that, described view data comprises the view data of imaging layer covering weave and again flows into the view data of blood of imaging aspect.
15. cardiac magnetic resonance imaging systems as claimed in claim 13, is characterized in that, described cardiac magnetic resonance imaging system adopts gtadient echo man's family sequence or fast spin echo man family sequence.
16. cardiac magnetic resonance imaging systems as described in claim 9 or 13, it is characterized in that, described system also comprises:
Receiving element, for receiving the R ripple in electrocardio ripple,
Electrocardio trigger element, for according to described R ripple, produces described electrocardio triggering signal.
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| CN110133558B (en) * | 2018-02-09 | 2021-04-30 | 深圳先进技术研究院 | Magnetic resonance dynamic imaging method, device and readable medium |
| CN108765513B (en) * | 2018-06-05 | 2022-06-28 | 上海交通大学 | A method for imaging cardiac blood pool inhibition relaxation parameters |
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