CN102215749B - Magnetic resonance imaging device and magnetic resonance imaging method - Google Patents
Magnetic resonance imaging device and magnetic resonance imaging method Download PDFInfo
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- G01R33/44—Arrangements or instruments for measuring magnetic variables involving magnetic resonance using nuclear magnetic resonance [NMR]
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- G01R33/567—Image enhancement or correction, e.g. subtraction or averaging techniques, e.g. improvement of signal-to-noise ratio and resolution gated by physiological signals, i.e. synchronization of acquired MR data with periodical motion of an object of interest, e.g. monitoring or triggering system for cardiac or respiratory gating
- G01R33/5673—Gating or triggering based on a physiological signal other than an MR signal, e.g. ECG gating or motion monitoring using optical systems for monitoring the motion of a fiducial marker
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- G01R—MEASURING ELECTRIC VARIABLES; MEASURING MAGNETIC VARIABLES
- G01R33/00—Arrangements or instruments for measuring magnetic variables
- G01R33/20—Arrangements or instruments for measuring magnetic variables involving magnetic resonance
- G01R33/44—Arrangements or instruments for measuring magnetic variables involving magnetic resonance using nuclear magnetic resonance [NMR]
- G01R33/48—NMR imaging systems
- G01R33/54—Signal processing systems, e.g. using pulse sequences ; Generation or control of pulse sequences; Operator console
- G01R33/56—Image enhancement or correction, e.g. subtraction or averaging techniques, e.g. improvement of signal-to-noise ratio and resolution
- G01R33/565—Correction of image distortions, e.g. due to magnetic field inhomogeneities
- G01R33/56509—Correction of image distortions, e.g. due to magnetic field inhomogeneities due to motion, displacement or flow, e.g. gradient moment nulling
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Abstract
An image having a high imaging efficiency and few body movement artifacts can be acquired by detecting a measurement period for each cycle on the basis of body movement information for a plurality of cycles which was detected from a subject that makes cyclic body movements, and by controlling the number of echo signals to be measured according to the duration of the detected measurement period.
Description
Technical field
The present invention relates to measure nuclear magnetic resonance, NMR (hereinafter referred to as " the NMR ") signal of hydrogen in examinee's body, phosphorus etc. and the Density Distribution of nuclear, distribution of relaxation times etc. are carried out the breathing synchro measure of NMR (Nuclear Magnetic Resonance)-imaging (hereinafter referred to as " the MRI ") device of image conversion.
Background technology
The MRI device is the NMR signal (echo-signal) that the nuclear spin of the tissue of measurement formation examinee, particularly human body produces, and with the form of its head, abdominal part, extremity etc., the device that function is carried out two dimension or 3-D viewization.In shooting, for echo-signal, pay the out of phase coding line frequency coding of going forward side by side by leaning magnetic field, be used as time series data and measure.Measured echo-signal is reconstructed into image by two dimension or three dimensional fourier transform.
If use above-mentioned MRI device to come the examinee is made a video recording, then under the situation that generation examinee's body moves in shooting, meeting produces because of the moving pseudo-shadow (artifact) that causes of this body in image, thereby becomes the obstruction of diagnosis.Breathing moving is as moving a kind of of examinee's body, in order to get rid of the pseudo-shadow of breathing due to moving, has adopted various maneuvers.For example, have and breathe the maneuver make a video recording synchronously.This maneuver is used the detection of the displaced position that is used for the moving detecting sensor of body that monitoring breathes and navigator echo (navigator echo) the stomach wall face due to breathing mutually when breathing etc., and uses when the breathing of regulation mutually that the displaced position resultant echo signal of regulation comes reconstructed image.This breathe shooting synchronously sometimes also with electrocardiographic wave synchronously and be used for carrying out.
Using the breathing shooting synchronously of the moving detecting sensor of body that is used for the monitoring breathing, the operator will be from visually judging respiratory waveform, and set to play from the triggering signal that drives according to breathing and breathe the time delay till stable and breathe the stable time that is in.Then, set according to this, device is carried out the pulse train of (the receiving the ま Ru) time portion that descends in the breathing stabilization time that sets.
In addition, as the strategy of subduing of the respiration artefacts of sneaking into image, for example method of record in patent documentation 1 is arranged.Applying so that the measured echo-signal on opportunity that the acceleration that the stomach wall due to breathing is moved becomes minimum is disposed at the low frequency region in k space of this method control phase coding.The time efficiency of this method is identical with the common shooting that does not have such phase code control, but compares with common shooting, and pseudo-shadow will tail off.
Patent documentation 1:JP spy opens the 2008-148918 communique
Using the breathing shooting synchronously of the moving detecting sensor of body that is used for the monitoring breathing, as mentioned above, owing in the breathing stabilization time that sets, carry out the pulse train of part fall time, will inevitably make breathing the pulse train number of times that repeats in stabilization time and measured echo-signal number not rely on the breathing cycle and keep constant.Therefore, in examinee's breathing at interval under the irregular situation, have that camera time is long to cause inefficent probability.Its reason is, if want to obtain the moving less image of pseudo-shadow of body, then in irregular breathings stabilization time, must make time of implementation of pulse train of respiration consistent stabilization time with the minimum breathing, for this reason, the echo-signal number that can measure in the time at respiration can reduce.And then, in any case shorten the pulse train time of implementation of respiration because irregular breathing, the opportunity of disordered breathing measured echo-signal one enter into the low frequency region in k space, it is obvious that pseudo-shadow just becomes.
In addition, in the method that patent documentation 1 is put down in writing, measured echo-signal has the probability of the low frequency region that enters the k space under the breathing labile state, thereby the degree that motion artifacts is subdued will depend on breathing state.And then under examinee's the situation that is irregular respiration, the detection of phase will become difficult when carrying out identical breathing synchronously with electrocardiographic wave, the image quality instability be arranged and the too many probability consuming time that causes making a video recording.That is to say that camera time will depend on the cycle of electrocardiographic wave and breathe degree of stability.
Summary of the invention
, the objective of the invention is for this reason, in the shooting of using MR imaging apparatus, even there is irregular body moving, also can obtain shooting efficient height, the moving few image of pseudo-shadow of body.
To achieve these goals, MR imaging apparatus of the present invention and MR imaging method, based on the moving information of bodies detected from have the moving examinee of cycle gonosome, a plurality of cycles, detect during the measurement in each cycle, and come the echo-signal number of control survey according to the time width during the detected measurement.
Specifically, MR imaging apparatus of the present invention possesses: body moves test section, and it detects the examinee's who freely breathes the moving information of periodic body; Measure control part, it according to the moving information of body, measures the echo-signal of the phase code of regulation based on the pulse train of regulation from the examinee; Arithmetic processing section, it uses echo-signal to come reconstruct examinee's image; And display part, its displayed map picture, wherein, arithmetic processing section detects during the measurement in each cycle based on the moving information of the body in a plurality of cycles, measures the echo-signal number that the time width of control part during according to detected measurement comes control survey.
In addition, MR imaging method of the present invention possesses: the moving step that detects of body, and the periodic body that detects the examinee who freely breathes moves information; Detect the step during the measurement in each cycle based on the moving information of the body in a plurality of cycles; And measuring process, based on the pulse train of regulation, according to the moving information of body, from the echo-signal that the examinee measures the phase code of regulation, in measuring process, according to the time width during the detected measurement, come the echo-signal number of control survey.
According to MR imaging apparatus of the present invention and MR imaging method, the measurement when can not rely on the moving degree of stability ground of body and carrying out moving with one under mutually.Consequently, even there is irregular body moving, also can obtain shooting efficient height, the moving few image of pseudo-shadow of body.
Description of drawings
Fig. 1 is the block diagram that the integral body of an embodiment of the MRI device that the present invention relates to of expression constitutes.
Fig. 2 is an example of the respiratory waveform of explanation under the regular respiratory situation and the breathing that the present invention relates to figure of first embodiment of shooting synchronously.
Fig. 3 is an example of the respiratory waveform of explanation under the irregular respiration situation and the breathing that the present invention relates to figure of first embodiment of shooting synchronously.
Fig. 4 is the flow chart of the handling process that relates to of expression first embodiment of the present invention.
Fig. 5 is an example of the respiratory waveform of explanation under the irregular respiration situation and the breathing that the present invention relates to figure of second embodiment of shooting synchronously.
Fig. 6 is that expression is resolved respiratory waveform and the figure of an example of the block diagram that obtains.
Fig. 7 is the figure that is illustrated on the respiratory waveform example of setting the GUI that is used for selecting the threshold value during smooth.
Fig. 8 is the figure that expression shows the demonstration example of carrying out situation of the synchronous shooting of breathing that the present invention relates to.
Fig. 9 is an example of the respiratory waveform of explanation under the irregular respiration situation and the breathing that the present invention relates to figure of the 3rd embodiment of shooting synchronously.
(symbol description)
1 examinee, 2 magnetostatic field generating units, 3 leaning magnetic field generating units, 4 measure control part, 5 sending parts, 6 acceptance divisions, 7 signal processing parts, 8 central processoies (CPU), 9 gradient magnetic field coils, 10 leaning magnetic field power supplys, 11 high frequency generators, 12 manipulators, 13 high frequency amplifiers, 14a high frequency coil (transmission coil), 14b high frequency coil (receiving coil), 15 signal amplifiers, 16 quadrature phase detector devices, the 17A/D changer, 18 disks, 19 CDs, 20 display, 21ROM (read only memory), 22RAM (random access memory), 23 trace balls or mouse, 24 keyboards, 51 gantry (gantry), 52 workbench, 53 baskets, 54 blood processor
The specific embodiment
Below, according to accompanying drawing, be elaborated at the preferred implementation of MRI device of the present invention.In addition, at the whole figure that are used for explanation working of an invention mode, have the part mark prosign of identical function, and omit the explanation of its repetition.
At first, the whole summary of an example of the MRI device that explanation the present invention relates to based on Fig. 1.Fig. 1 is the block diagram that the integral body of an embodiment of the MRI device that the present invention relates to of expression constitutes.This MRI device is to utilize the NMR phenomenon to obtain the device of examinee's faultage image, and as shown in Figure 1, the MRI device possesses magnetostatic field generating unit 2, leaning magnetic field generating unit 3, sending part 5, acceptance division 6, arithmetic processing section 7 and measurement control part 4 and constitutes.
Magnetostatic field generating unit 2, if vertical magnetic field mode, then on the direction of the space around the examinee 1 and its axon quadrature, if horizontal magnetic field mode, then in its axon direction uniform magnetostatic field is produced, the source takes place in the magnetostatic field of dispose the permanent magnet mode around examinee 1, often leading mode or superconduction mode.
Leaning magnetic field generating unit 3 is made of the gradient magnetic field coil 9 of reeling on coordinate system (rest frame) X, the Y of MRI device, Z three direction of principal axis and the leaning magnetic field power supply 10 that drives each gradient magnetic field coil.By drive the leaning magnetic field power supply 10 of each coil according to the order from measurement control part 4 described later, X, Y, Z three axial leaning magnetic field Gx, Gy, Gz are applied in examinee 1 horizontal transverse field space.During shooting, apply slice direction leaning magnetic field pulse (Gs) in the direction with section (slice) face (shooting cross section) quadrature, setting is for examinee 1 section, applying phase-encoding direction leaning magnetic field pulse (Gp) and frequency coding direction leaning magnetic field pulse (Gf) with this sliced surfaces quadrature and orthogonal remaining both direction, and the positional information of all directions of in echo-signal, encoding.
Sending part 5 is in order to excite the NMR phenomenon in the nuclear spin of the atom of the biological tissue that constitutes examinee 1, to examinee's 1 irradiation high frequency magnetic field pulse (hereinafter referred to as " RF pulse "), sending part 5 is made of high frequency coil (transmission coil) 14a of high frequency generator 11, manipulator 12, high frequency amplifier 13 and transmitting terminal.High-frequency impulse from high frequency generator 11 outputs, based on the opportunity from the instruction of measuring control part 4, carry out Modulation and Amplitude Modulation by manipulator 12, and after being amplified by high frequency amplifier 13 through this amplitude-modulated high-frequency impulse, be provided to the high frequency coil 14a that is configured near examinee 1, thereby the RF pulse irradiation is arrived examinee 1.
Measure the pulse train that control part 4 is based on certain regulation and control leaning magnetic field generating unit 3, sending part 5 and acceptance division 6, and the repeated control unit is carried out in the measurement of the applying of RF pulse and leaning magnetic field pulse, echo-signal.Measure control part 4 and under the control of CPU8, work, the required echo data of reconstruct of examinee 1 faultage image is collected required various command be sent to leaning magnetic field generating unit 3, sending part 5 and acceptance division 6, and they are controlled.
In addition, the MRI device that the present invention relates to possesses: the body dynamic sensor, and it is installed on the examinee place or is disposed near it, and is moving for detection of examinee's body; With the moving detecting unit 26 of body, it is transfused to the signal from the body dynamic sensor, and detects examinee's the moving information of body.Then, be input to CPU8 by the moving information of the moving detecting unit 26 detected bodies of body via measuring control part 4.
For example, as the example of detection based on the moving detecting sensor of body of the shift in position of the stomach wall face of breathing, at abdominal part the hollow corrugated tube that stretches according to the stomach wall face is installed, can be used the baroceptor of the air pressure that detects this hollow bellows interior.Because flexible corresponding with corrugated tube, bellows interior air pressure can produce change, therefore can detect the changing position of stomach wall face indirectly by this air pressure.Perhaps, also can be ultrasonic sensor, it uses ultrasonic irradiation stomach wall face, detects the changing position of stomach wall face according to the required time of the detection of echo.
In addition, in Fig. 1, the high frequency coil 14a of transmitting terminal and gradient magnetic field coil 9, if in the magnetostatic field space of the magnetostatic field generating unit 2 that examinee 1 is inserted into, be the vertical magnetic field mode, then be configured with examinee 1 with standing facing each other, if the horizontal magnetic field mode then is configured according to the mode around examinee 1.In addition, the high frequency coil 14b of receiving terminal according to examinee face-off or around mode arrange.
The shooting object nuclear species of present MRI device is examinee's main composition material what face that workbench popularizes, i.e. hydrogen nuclei (proton).By the information relevant with the spatial distribution in relaxation time of the spatial distribution of proton density, excited state is carried out image conversion, come form or the function of human body head, abdominal part, extremity etc. are carried out two dimension or three-dimensional camera shooting.
(first embodiment)
Next, first embodiment about MRI device of the present invention and MRI method describes.Present embodiment is come between the moving stable phase of detection bodies based on the moving information of the body in a plurality of cycles, and comes the echo-signal number of control survey according to the time width between each stable phase.Below, moving with the breathing of moving as body is example, explains present embodiment, but the present invention and present embodiment are not to be defined in to breathe to move.At first, the summary of present embodiment is described, secondly, explains the handling process of present embodiment.
The summary of present embodiment is as follows.
When carrying out present embodiment, the operator is stated from the examinee on the workbench in advance, the moving detecting sensor of body is installed on the examinee, and makes movable workbench make examinee's desirable shooting position be positioned at magnetic field center.During this is prepared in advance during ensuing measurement of neutralization in, the examinee do not held one's breath and keep freely breathing.Be that the present invention and present embodiment do not require the examinee to hold one's breath by force.
Signal from the moving detecting sensor of body is imported into the moving detecting unit 26 of body.If the desirable shooting of examinee position is disposed at magnetic field center, then CPU8 through the respiratory waveform of a plurality of cycle monitorings from the examinee of moving detecting unit 26 inputs of body, and carries out the parsing of the respiratory waveform in a plurality of cycles before implementing this measurement.Then, between the breathing stable phase that CPU8 determines among the respiratory waveform detect, namely during respiratory waveform smooth (just, during the measurement of echo-signal).
Fig. 2 and Fig. 3 represent from an example of the examinee's of moving detecting unit 26 inputs of body respiratory waveform.Fig. 2 is the examinee's of expression regular respiratory a example of respiratory waveform 200, and Fig. 3 is the examinee's of expression irregular respiration a example of respiratory waveform 300.They all represent to be accompanied by examinee's periodic breathing, and the stomach wall face is dipping and heaving periodically in vertical direction.Fig. 2 and respiratory waveform shown in Figure 3, the longitudinal axis is represented the displaced position of the vertical direction of stomach wall face, the transverse axis express time.The state that corresponding because the air-breathing and abdominal distension of the upside of the longitudinal axis, stomach wall face rise, the corresponding state that abdominal retraction, stomach wall face descend owing to exhale of the downside of the longitudinal axis.In addition, between the little breathing stable phase of the change in location of stomach wall face be smooth during, through a plurality of cycles, interval is roughly identical in Fig. 2 of regular respiratory, 201a, 201b be smooth during.On the other hand, in Fig. 3 of irregular respiration 301a, 301b, 301c be smooth during, interval difference among a plurality of cycles.In addition, these smooth during between during be that the stomach wall face is rapidly during the non-flat forms of displacement.
In the present embodiment, according to the length during smooth, change the number of the echo-signal of measuring, and control is applied to the phase code of the echo-signal of measurement.Consequently, compared to existing technology, the required echo-signal of measurement image reconstruct more efficiently in time.Namely, in existing breathing shooting synchronously, because the echo-signal number that will measure in the breathing cycle once is made as constant (for example four), therefore, be under examinee's the situation of irregular respiration like that at Fig. 3, primary smooth during 301a in the measurement of the echo-signal of some time residue too much, cause secondary smooth during 301b deficiency of time in the measurement of the echo-signal of identical some.Yet present embodiment makes the number difference of the echo-signal of measurement according to the length during smooth.Preferred measure most probable number MPN purpose echo-signal during using whole during smooth.Therefore, the required echo-signal of measurement image reconstruct service time efficiently.
(determining method during respiratory waveform smooth)
Next, determining method during respiratory waveform smooth is described.At first, as first determining method, the method for the block diagram of the number of times distribution of using the value of representing respiratory waveform is described.
CPU8 uses respiratory waveform as shown in Figure 2, and the number of times of creating the value of expression respiratory waveform distributes namely at the block diagram of the position frequency of the stomach wall face of the direction vertical with the stomach wall face (hereinafter referred to as the z direction).Fig. 6 represents an example of block diagram.The transverse axis of block diagram shown in Figure 6 is to follow the displacement of z direction of the stomach wall face position of breathing, from its minimum to coming quantization means with the interval of regulation the peak.That is to say that 0 (zero) is corresponding with the extreme lower position of the stomach wall face position of z direction, 144 is corresponding with the extreme higher position of the stomach wall face position of z direction, and middle value is corresponding with the centre position of stomach wall face respectively.The longitudinal axis of block diagram is illustrated in the occurrence frequency of each position of the stomach wall face of z direction in the one-period of breathing.Generally in the breathing cycle, because of during the low state in the stomach wall face position of expiration z direction than because of long during the high state in the stomach wall face position of air-breathing z direction, therefore in block diagram, the low stomach wall face position one square one-tenth high frequency in left side.
Behind the block diagram that the number of times of creating the value of representing respiratory waveform as described above distributes, CPU8 is according to the block diagram of creating, scope at the respiratory waveform corresponding with the expiration state is the lower scope of value of respiratory waveform, detects the value 601 of the maximum respiratory waveform of number of times.Then, CPU8 is on the left and right sides of the block diagram centered by 601 is two-way, selects to have the scope of value of respiratory waveform of stipulated number as breathing steady statue, and select this breathing steady statue during during the measurement as echo-signal.After, be called this period smooth during.Specifically, to be from 601 right sides on the bigger direction of the value of respiratory waveform, not only have the number of times of regulation but also the value of the respiratory waveform corresponding with the number of times that is positioned at Rack β and determine to be upper limit threshold 602, to be from 601 left sides on the less direction of the value of respiratory waveform, not only have the number of times of regulation but also the value of the respiratory waveform corresponding with the number of times that is positioned at Rack α and determine to be lower threshold 603, and during the scope of the value of the respiratory waveform that is clipped in the middle is made as respiratory waveform smooth.In addition, α can be made as play the respiratory waveform minima from 601 till, and then β is made as 0, thus will from the respiratory waveform minima play be made as respiratory waveform smooth till 601 during.
It more than is the explanation of first determining method during respiratory waveform smooth.
Next, describe about second determining method during respiratory waveform smooth.Second determining method is the method for operator during direct selection on the respiratory waveform is smooth.Fig. 7 represents to select GUI (Graphical User Interface: example graphic user interface) during respiratory waveform smooth for the operator.On the respiratory waveform 700 that is shown on the display 20, expression be used for is selected the horizontal stripe 702 overlapping demonstrations of horizontal stripe (bar) 701 and expression lower threshold of the upper limit threshold of the scope during smooth.The operator uses trace ball or mouse 23 to adjust the position of the above-below direction of setting these horizontal stripes 701 and 702, distinguishes capping threshold value and lower threshold thus.CPU8 select the value of respiratory waveform be clipped in these upper limit thresholds of setting and the value between the lower threshold during be used as smooth during.In addition, lower threshold 302 can be made as the respiratory waveform minima, will be during be made as respiratory waveform smooth till the respiratory waveform minima plays upper limit threshold 701.
It more than is the explanation of second determining method during respiratory waveform smooth.
In addition, can carry out in conjunction with deciding for detection of the threshold value during smooth above-mentioned two kinds of methods.For example, the threshold value that determines with first method can be adjusted with second method again.In this case, for example, each threshold value that will determine with first method shows as the initial position of the bound threshold value horizontal stripe 701,702 in second method.
(this measurement)
Next, the breathing synchro measure about the examinee that freely breathes describes.Based on the imaging conditions of being set by the operator, measure control part 4 and repeat pulse train with the repetition time of setting as one of imaging conditions (TR).Preferably make this pulse train repeat to be not only during smooth, and during non-flat forms, also continue.Particularly under steady statue, measure echo-signal SSFP (Steady State Free Precision: type pulse train steady state free precession), in order to keep steady statue, need continue the repetition pulse sequence with the short repetition time (TR), therefore preferably during smooth, also continue pulse train with the identical repetition time (TR) in addition.
Carrying out under the state of pulse train, CPU8 is from the moving detecting unit 26 of body input respiratory waveforms continuously, based on each threshold value of setting or select in a manner mentioned above, detects time started point and concluding time point during respiratory waveform smooth at any time.Time started during smooth point is that respiratory waveform transfers the time point in the scope to outside the threshold range of bound, and the concluding time point during smooth is that respiratory waveform transfers extraneous time point in the threshold range of bound.
Then, CPU8 is if detect time started point during smooth, then to the beginning of the measurement of measuring control part 4 indication echo-signals or restart.Then, measure the indication that control part 4 begins or restarts according to the measurement from CPU8, begin or restart the measurement of echo-signal by the pulse train based on predefined imaging conditions.In the measurement of echo-signal, CPU8 then interrupts the measurement of measuring control part 4 indication echo-signals if detect concluding time point during smooth.Then, measure control part 4 according to the indication of interrupting from the measurement of CPU8, interrupt the measurement of echo-signal.CPU8 is till the measurement of the required echo-signal of image reconstruction finishes, all respectively according to the detecting each time of the time started during smooth point and concluding time point, carry out such to measure control part 4 send echo-signal measurement beginning or restart and interrupt to indicate.If the measurement of the echo-signal that image reconstruction is required finishes, then CPU8 measures control part according to the indication that the measurement from CPU8 finishes to measuring the end of control part 4 indication measurements, finishes the execution of pulse train.
On the other hand, measure control part 4 and during each is smooth, carry out the measurement of echo-signal based on same pulse train.At this moment, measure control part 4 comes the echo-signal of control survey according to separately length during smooth number.Specifically, measure control part 4 and measure more echo-signal long during smooth, measure less echo-signal short during smooth.Preferably make and measure control part 4 no matter the length during smooth, during each is smooth, use the echo-signal of measuring most probable number MPN during its separately whole.Consequently, according to separately length during smooth, the number of measured echo-signal is with difference.
In addition, measuring control part 4 makes the phase code difference of pulse train carry out the measurement of echo-signal during each is smooth.Specifically, in the measurement of the echo-signal during each is smooth, measure the phase code that control part 4 pre-storages have been measured, in the measurement of the echo-signal during the next one is smooth, the echo-signal that applies to measure unmeasured phase code of control phase coding.For example, during smooth, finish and the measurement of echo-signal when interrupting, measure the phase code that applies when control part 4 is pre-stored in the measurement of last echo-signal, the time point that measurement during the next one is smooth restarts is measured control part 4 and is begun the measurement of echo-signal again from the next phase code of the last phase code of storing.That is to say, then last time the echo-signal during smooth measurement carry out the measurement of this echo-signal during smooth.Like this, measure each phase code during smooth of control part 4 controls apply so that: the phase code that the echo-signal of measuring during each is smooth is applied does not repeat, and the echo-signal of the required all phase codes of measurement image reconstruct.
Fig. 2 is illustrated in an example of the measurement of each of examinee of regular respiratory echo-signal during smooth.Ordinate is represented the opportunity that applies of the excitation pulse in the pulse train.Also be same in following Fig. 3,5,9.Will be during smooth during the non-flat forms before the 201a measured echo-signal 202a discarded.201a measures seven echo-signal 203a of phase code 1～7 during smooth, and discarded during next smooth measured echo-signal 202b between the 201b.In addition and since during smooth 201b be with before this smooth during 201a identical during width, so the measured phase code of 201b is 8～14 during smooth, thereby becomes seven identical echo-signal 203b.After this identical.Like this, under the situation of regular respiratory, echo-signal number measured during each is smooth is roughly the same, and control put on each echo-signal phase code so that its during each is smooth between continuously.
On the other hand, Fig. 3 is illustrated in an example of the measurement of each of examinee of irregular respiration echo-signal during smooth.Will be during smooth during the non-flat forms before the 301a measured echo-signal 302a discarded.301a measures five echo-signal 303a of phase code 1～5 during smooth, and discarded during next smooth measured echo-signal 302b till the 301b.In addition, because shorter during 301a compares during 301b and before this smooth during smooth, therefore the phase code of measuring only forms 6,7 two echo-signal 303b.Equally and since during smooth 301b play next smooth during between till the 301c during longer, therefore measured, discarded echo-signal 302c becomes many betwixt.Then, show the four echo-signal 303c that during the next one is smooth 301c measures phase code 8～11.And will be during smooth during next non-flat forms of 301c measured echo-signal 302d discarded.Like this, under the situation of irregular respiration, will control echo-signal number measured during each is smooth according to width during smooth.That is, if short during smooth, the echo-signal number is tailed off, if long during smooth, then also make the echo-signal number become many.Then, identical with the situation of regular respiratory, control put on each echo-signal phase code so that its during each is smooth between continuously.
Under any situation among the irregular breathing of the breathing of the rule of Fig. 2 and Fig. 3, measure control part 4 if finish the measurement of the required all echo-signals of image reconstruction, free respiration measurement is finished.
As two above-mentioned examples, measuring control part 4 is the discarded of rule or the irregular measurement that irrespectively repeats the echo-signal during smooth and the echo-signal during the non-flat forms with breathing.At this moment, not only come the number of the echo-signal of control survey according to separately length during smooth, and the control phase coding apply so that put on phase code in the echo-signal of measuring during each is smooth continuously.Like this, with breathing be rule or irregular irrelevant, can carry out the high shooting of time efficiency.In addition, owing to during non-flat forms, also carry out pulse train continuously, so the intensity long-term stability of echo-signal, image quality will improve.
In addition, above-mentioned explanation continue the example of the measurement of echo-signal although understand respiratory waveform during non-flat forms, but respiratory waveform can not continue the measurement of pulse train and echo-signal yet and interrupts during non-flat forms yet.
It more than is the explanation of the summary of present embodiment.
(measurement is carried out situation and is shown)
Next, describe about the demonstration of carrying out situation of measuring.During the examinee's who continues freely to breathe breathing synchro measure, can with measurement carry out situation to the operator, preferably also show to the examinee understandablely.As displaying contents, for example, can be that the phase code measured is with respect to the ratio of full phase code, the predictive value of measuring/unmeasured phase code number, making a video recording remaining time etc.By at least one the value among them is presented in display 20 grades, can show the situation of carrying out of breathing synchro measure to the operator understandablely.
Fig. 8 shows the example that situation shows of carrying out of breathing synchro measure.Fig. 8 (a) is with respect to full phase code number (801), and the phase code number (802) measured between sandwich the example that shows about "/" comes.Fig. 8 (b) show measurement elapsed time (804) in reality, and the full Measuring Time (803) predicted according to full phase code number between sandwich the example that shows about "/" comes.Fig. 8 (c) is the example that shows the ratio of the phase code number measured corresponding with full phase code number with progress bar, and the horizontal stripe that shows the corresponding different colours of the ratio of the phase code number of using and having measured comes full-filling gradually and full phase code to count the example of corresponding whole horizontal stripe.
(handling process)
Next, the handling process of present embodiment is described.The handling process of present embodiment constitutes by preparing handling process and these two flow processs of this measurement handling process in advance.Fig. 4 is the flow chart of representing two handling processes of present embodiment respectively.The below processing of each step of explanation.
Preparing in advance in the handling process before this measurement, at first, the operator is stated from the examinee on the workbench, and the moving detecting sensor of body is installed on the examinee, thereby and movable workbench is disposed under the state of magnetic field center at the desirable shooting position with the examinee, carry out following each step.
In step 401, CPU8 monitors at regular intervals from moving detecting unit 26 examinees' input, that freely breathe of body respiratory waveform.
In step 402, CPU8 resolves respiratory waveform and decides for detection of the threshold value during respiratory waveform smooth.Even the decision during smooth can be above-mentioned first method with the method for block diagram and second method is the method directly selected of operator any in the two.Perhaps, the threshold value that determines with first method can be adjusted with second method again.
If aforesaidly prepare end in advance, then transfer to the handling process 403～410 of this measurement of following explanation.
In step 403, based on the imaging conditions of being set by the operator, measure control part 4 and repeat pulse train with the repetition time (TR), and the measurement of beginning echo-signal.
In step 404, CPU8 obtains from the value of the examinee's of moving detecting unit 26 inputs of body respiratory waveform, the i.e. displaced position of stomach wall face.
In step 405, CPU8 is based on each threshold value that determines in step 402, the value of judging respiratory waveform belong to smooth during or belong to during the non-flat forms.Transfer to step 406 being judged to be under the situation about belonging to during smooth, under situation about being judged to be during belonging to non-flat forms, transfer to step 408.
In step 406, because measured echo-signal is measured during smooth, therefore, CPU8 is disposed at the k locus corresponding with the phase code that puts on this echo-signal in order to adopt this echo-signal in image reconstruction with echo data.In addition, as mentioned above, CPU8 can also show according to the situation of carrying out that the phase code number of having measured upgrades measurement.
In step 407, measure control part 4 and make phase code enter next step.
In step 408, because measured echo-signal is measured during non-flat forms, therefore, CPU8 discards this echo-signal and is not used in image reconstruction.
In step 410, CPU8 judges the echo-signal of whether having measured full phase code, if measured the echo-signal of full phase code, then finishes this measurement handling process, if do not measure the echo-signal of full phase code, then returns step 404.
It more than is the explanation of the handling process of present embodiment.
In addition, in description of the present embodiment, though be that example is illustrated with the respiratory waveform, for using other the measurement of bio information such as ecg wave form or pulse wave, can use the present invention too.
As described above described, MRI device and MRI method according to present embodiment, with breathing be rule or irregular irrelevant, only use the echo-signal of during respiratory waveform smooth, measuring to come reconstructed image, therefore, even irregular respiration also can suppress based on the pseudo-shadow of this irregular breathing and obtains images with high image quality.In addition, come the number of the echo-signal of control survey according to the length during respiratory waveform smooth, and stride under a plurality of situations during smooth in measurement, applying so that put on the phase code of the echo-signal of measuring during each is smooth of control phase coding do not repeat.Consequently, needn't require the examinee to hold one's breath by force and can under freely breathing, make a video recording, and with breathing be rule or irregular irrelevant, shooting efficient is uprised, therefore the prolongation of camera time is minimized.
(second embodiment)
Next, second embodiment about MRI device of the present invention and MRI method describes.Present embodiment is that breathing synchro measure of the present invention is applied in many sections (multi-slice) shooting.Be that with the difference of above-mentioned first embodiment as many sections shootings, the measurement of the echo-signal during smooth is implemented in the measurement of echo-signal of preferentially carrying out the same phase code of each section.That is to say, in a repetition time (TR), make the identical echo-signal of measuring from each section of phase code.Below based on Fig. 5 difference with the first above-mentioned embodiment only is described, and omit explanation at identical point.Fig. 5 shows an example of many section shootings of carrying out three.
Explanation is omitted in preparing in advance because of identical with above-mentioned first embodiment before this measurement.
In this measurement, respiratory waveform be in smooth during the time, measure control part 4 and measure the echo-signal of each section in a repetition time (TR) with same phase code.For example, as shown in Figure 5,501a during smooth measures control part 4 and repeats many section sequences three times, and (TR) cuts into slices to measure the echo-signal of phase code 1 by each in the repetition time first time, and measures the echo-signal of phase code 1-1～phase code 3-1.At this, first digit representative section number, second digit represents the phase code number.At the repetition time second time (TR), measure control part 4 and measure the echo-signal of next phase code 2 by each section, and measure the echo-signal of phase code 1-2～phase code 3-2.In repetition time (TR) for the third time, measure control part 4 and measure the echo-signal of next phase code 3 by each section, and measure the echo-signal of phase code 1-3～phase code 3-3.
During the next one is smooth among the 501b, measures control part 4 and measure echo-signal next step, phase code 4 of the last phase code of measuring of 501a during smooth by each section, and measure the echo-signal of phase code 1-4～phase code 3-4.In addition, during each is smooth between, only otherwise the identical section number of repeated measure and the echo-signal of phase code get final product, so can make slice number sign indicating number and phase code discontinuous.
Below, similarly, measure control part 4 and during follow-up each is smooth, change phase code ground and come to repeat the measurement of the echo-signal of same phase code with the repetition time (TR) by each section, and till the measurement of the echo-signal of the full phase code of cutting into slices by each finishes, repeat the measurement of the echo-signal during smooth.
In addition, also repeat many section sequences though measure control part 4 during non-flat forms, the phase code of this moment gets final product arbitrarily, does not perhaps apply also passable.Thus, the signal intensity of echo-signal will be stablized, and image quality will improve.In addition, during non-flat forms be smooth during before the 501a, smooth during 501a and next smooth during between the 501b and during smooth after the 501b measured each echo-signal of cutting into slices will not be used in image reconstruction and go out of use.
As described above described, according to MRI device and the MRI method of this form of implementation, in many section shootings, also can access the effect same with the first above-mentioned embodiment.Namely, with breathing be rule or irregular irrelevant, only use the echo-signal of during respiratory waveform smooth, measuring to carry out image reconstruction by each section, therefore can suppress based on the pseudo-shadow of breathing, and images with high image quality is obtained by each section in the time efficiency highland.
(the 3rd embodiment)
Next, the 3rd embodiment about MRI device of the present invention and MRI method describes.Present embodiment is applied to three-dimensional camera shooting with breathing synchro measure of the present invention.Three-dimensional camera shooting replaces making the slice position difference in many section shootings, is to excite a large amount of (volume) back to apply the section coding independently with phase code on slice direction, thereby to the positional information of echo-signal coding slice direction.With the difference of above-mentioned each embodiment be, as three-dimensional camera shooting, applying so that the measurement of the echo-signal between during each is smooth does not repeat with phase code according to the section coding of each coding of control that is to say that the section coding carries out with at least one the different mode in the phase code.Below only illustrate and the difference of each above-mentioned embodiment based on Fig. 9, omit explanation at identical point.Fig. 9 is the cut into slices example of three-dimensional camera shooting of coded number 4 of expression.
Preparing in advance identical with the first above-mentioned embodiment and omit explanation before Yin Ben measures.
In this measurement, in the time of during respiratory waveform is smooth, measure control part 4 and measure the section coding of regulation and the echo-signal of phase code with the repetition time (TR) once, and change in section coding and the phase code at least one in repeatedly at least and measure echo-signal each.Fig. 9 shows and will phase code be fixed and change the unit that section coding comes the measurement of repetition echo-signal, comes the example of repetition by changing phase code.That is, measure control part 4 with repetition time during (TR) repetition pulse sequence, make the circulation (loop) of section coding be altered to the inboard, and change the circulation of phase code in the arranged outside of this circulation, control applying of two codings.In addition, on the contrary, section coding fix and is changed the unit that phase code is come the measurement of repetition echo-signal, also can cutting into slices encodes repeat by changing.
And, measure control part 4 during each is smooth, control applying of each coding according to the section coding with at least one different mode of phase code.Fig. 9 shows and measures each coding of control part 4 controls so that the measuring sequence of section coding and phase code continuous example during each is smooth.In addition, owing to the coding that needs only at least one during each is smooth is different just passable, therefore discontinuous also passable.
Specifically, in three-dimensional camera shooting shown in Figure 9, measure control part 4 901a during smooth and repeat three-dimensional pulse train, and phase code is fixed as 1, as the initial circulation that changes the section coding, measure four echo-signals of coding 1-1～4-1.At this, first numeral section coding, the second numeral phase code.Next, phase code is become 2, repeat to change the circulation of section coding, and measure four echo-signals of coding 2-1～2-4.Below similarly, measure control part 4 smooth according to this during 901a during width, measure till the echo-signal of coding 3-3, thereby measure 11 echo-signals (903a) of coding 1-1～3-3 altogether.
901b during the next one is smooth measures the Next coding 4-3 of the last coding 3-3 that control part 4 applies from 901a during before smooth, begins the measurement of echo-signal.Next, phase code is become 4 repeat to change the circulation of section coding, and measure four echo-signals of coding 1-4～4-4.Next, phase code is become 5 repeat to change the circulation of section coding, and measure two echo-signals of coding 1-5～2-5.That is to say, measure control part 4 smooth according to this during 901b during width, the echo-signal till measuring from coding 4-3 to 2-5, thus measure seven echo-signals (903b) of coding 1-1～3-3 altogether.Later also is same during smooth.
In addition, also repeat three-dimensional pulse train though measure control part 4 during non-flat forms, section coding and the phase code of this moment get final product arbitrarily, perhaps do not apply also passable.Thus, the signal intensity of echo-signal will be stablized, and image quality will improve.In addition, during non-flat forms be smooth during before the 901a, smooth during 901a and next smooth during between the 901b and during smooth after the 901b measured each echo-signal of cutting into slices will not be used in image reconstruction and go out of use.
As described above described, according to MRI device and the MRI method of present embodiment, in three-dimensional camera shooting, also can obtain the effect same with above-mentioned first embodiment.That is, with breathing be rule or irregular irrelevant, only use the echo-signal of during respiratory waveform smooth, measuring to come reconstructed image, therefore can suppress based on the pseudo-shadow of breathing, the 3-D view of high image quality is obtained on the time efficiency highland.
It more than is the explanation of each embodiment of MRI device of the present invention and MRI method.But MRI device of the present invention and MRI method are not limited to the disclosed content of explanation of the respective embodiments described above, and can obtain other modes on the basis of purport of the present invention.
For example, in each above-mentioned embodiment, during the measurement as echo-signal, although understand example during the moving waveform of selective body smooth, but the invention is not restricted to smooth during, also can the moving waveform of selective body desirable during.Also having in addition under the moving situation during stable of body, also can select between such stable phase.For example, can be during the suction condition of breathing disorder of internal organs.As long as setting threshold with can select desirable during.
Claims (14)
1. MR imaging apparatus possesses:
Body moves test section, and it detects the examinee's who freely breathes the moving information of periodic body;
Measure control part, it according to the moving information of described body, measures the echo-signal of the phase code of regulation based on the pulse train of regulation from described examinee;
Arithmetic processing section, it uses described echo-signal to come the described examinee's of reconstruct image; With
Display part, it shows described image,
Described MR imaging apparatus is characterised in that,
Described arithmetic processing section, detect the measurement in each cycle based on the moving information of the described body in a plurality of cycles during,
Described measurement control part comes the echo-signal number of control survey according to width during during the detected described measurement,
Described body moves the test section detection waveform, and this waveform is represented the temporal displacement of described examinee's desirable position,
Described arithmetic processing section is created block diagram at the value of waveform based on the described waveform in described a plurality of cycles, and is detected based on this block diagram during the measurement in described each cycle.
2. MR imaging apparatus as claimed in claim 1 is characterized in that,
Described measurement control part during according to described measurement during width, make the echo-signal of measurement count difference.
3. MR imaging apparatus as claimed in claim 1 is characterized in that,
Described measurement control part makes at the first echo-signal number of measuring during measuring than many at the second echo-signal number of measuring during measuring, wherein, described second during measuring during width during measuring than described first during the width weak point.
4. MR imaging apparatus as claimed in claim 1 is characterized in that,
Described measurement control part makes in the phase code of the echo-signal of measuring during first measurement different with the phase code of the echo-signal of measuring during second measurement.
5. MR imaging apparatus as claimed in claim 1 is characterized in that,
Described measurement control part control phase coding makes: in the phase code of first echo-signal of measuring during measuring, with continuous in the phase code of second echo-signal of measuring during measuring.
6. MR imaging apparatus as claimed in claim 1 is characterized in that,
Described measurement control part is during the described measurement and the pulse train that puts rules into practice continuously during the non-measurement in addition, and the echo-signal that will measure during described non-measurement is not used in the reconstruct of described image and discards.
7. MR imaging apparatus as claimed in claim 1 is characterized in that,
The pulse train that described measurement control part only puts rules into practice during described measurement is measured described echo-signal.
8. MR imaging apparatus as claimed in claim 1 is characterized in that,
Described arithmetic processing section, based on described block diagram decide for detection of during the described measurement, at the threshold value of the value of described waveform, and during detecting the measurement in described each cycle based on the threshold value at the value of this waveform.
9. MR imaging apparatus as claimed in claim 8 is characterized in that,
Be clipped at during between the threshold value of the value of described waveform, compare with other waveform fields, substantially smooth during.
10. MR imaging apparatus as claimed in claim 1 is characterized in that,
Described body moves the test section detection waveform, and this waveform is represented the temporal change of described examinee's desirable position,
Described display part is overlapping display threshold configuration part on this waveform, this threshold setting portion accept for detection of during the described measurement, at the setting of the threshold value of the value of described waveform,
Described MR imaging apparatus possesses input part, and this input part is accepted the operation of described threshold setting portion,
Described arithmetic processing section is based on during carrying out measurement that preset threshold detects described each cycle via described threshold setting portion.
11. MR imaging apparatus as claimed in claim 1 is characterized in that,
Described display part shows information, the phase code number that this information representation is measured and measure elapsed time at least one among the two.
12. MR imaging apparatus as claimed in claim 1 is characterized in that,
Between the repetition time of described pulse train, be many sections pulse train of measuring echo-signal from a plurality of sections,
Described measurement control part during each is measured, changes the measurement of echo-signal that phase code ground comes the same phase code of each section of repetition.
13. MR imaging apparatus as claimed in claim 1 is characterized in that,
Described pulse train is the pulse train of carrying out three-dimensional camera shooting,
Described measurement control part control section coding and phase code applying so that: during each was measured, this section was encoded different with in the phase code at least one.
14. a MR imaging method possesses:
The moving step that detects of body, the periodic body that detects the examinee who freely breathes moves information;
Detect step during the measurement, detect the measurement in each cycle based on the moving information of the described body in a plurality of cycles during; With
Measuring process based on the pulse train of regulation, according to the moving information of described body, is measured the echo-signal of the phase code of regulation from described examinee,
Described MR imaging method is characterised in that,
In described measuring process, according to width during during the detected measurement, come the echo-signal number of control survey,
Detection waveform in the moving detection of described body step, this waveform is represented the temporal displacement of described examinee's desirable position,
During described measurement, detect in the step based on the described waveform in described a plurality of cycles and create block diagram at the value of waveform, and detect based on this block diagram during the measurement in described each cycle.
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| DE102009055960B4 (en) * | 2009-11-27 | 2021-01-14 | Siemens Healthcare Gmbh | Method for the acquisition of measurement data from a breathing examination subject using magnetic resonance technology and the associated computer program |
| JP5623149B2 (en) * | 2010-06-18 | 2014-11-12 | 株式会社日立メディコ | Magnetic resonance imaging apparatus and imaging method thereof |
| EP2515138A1 (en) | 2011-04-19 | 2012-10-24 | Koninklijke Philips Electronics N.V. | Motion triggered MR imaging using APT/CEST |
| US10247804B2 (en) | 2014-02-13 | 2019-04-02 | Koninklijke Philips N.V. | Method of time-efficient 4D magnetic resonance imaging |
| DE102016205718A1 (en) * | 2016-04-06 | 2017-10-12 | Siemens Healthcare Gmbh | Method for displaying medical image data |
| JP7020930B2 (en) * | 2018-01-24 | 2022-02-16 | 富士フイルムヘルスケア株式会社 | Magnetic resonance imaging device, magnetic resonance imaging system and parameter estimation method |
| CN109001660B (en) * | 2018-06-12 | 2020-07-28 | 上海联影医疗科技有限公司 | Film imaging method and magnetic resonance imaging system |
| CN114795182B (en) * | 2022-06-24 | 2022-09-02 | 山东奥新医疗科技有限公司 | Magnetic resonance imaging artifact eliminating method and related components |
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