JP5289292B2 - Magnetic resonance imaging device - Google Patents

Description

  The present invention relates to a magnetic resonance imaging apparatus having an MR angiography (MRA) function.

  Magnetic resonance imaging is a technique in which the nuclear spin of a subject placed in a static magnetic field is excited with a high-frequency signal of Larmor frequency, and an image is obtained from a FID (free induction decay) signal or echo signal generated by this excitation. It is.

  One category of magnetic resonance imaging is MR angiography that images blood dynamics. Further, as one form of MR angiography, there is a method in which a signal is dropped by locally labeling a spin with an inversion pulse (high frequency inversion pulse).

  For example, the location (label area) to be pre-saturated by the inversion pulse is set together with the time interval from the inversion pulse to the excitation pulse of the main scan, and the movement trajectory of the portion where the signal changes (lower signal) due to the influence of pre-saturation There is a flow imaging method (bolus tracking method, Edelman, et.al., Radiology, Vol. 171, 551-556, 1989) for observing movement of blood and the like by observing the image on the image.

  FIG. 9 shows a pulse sequence according to this method, and FIG. 10 shows a conventional label area setting screen. First, the inversion pulse 1 is applied. At this time, the slice selective gradient magnetic field 2 is applied and the position of the label region is supported so that the region (label region) assumed to be the inflow source to the region of interest ROI is selectively inverted and excited. The offset frequency 3 is added to the inversion pulse 1. The label area can be set in an arbitrary direction by applying the label area in a direction indicated by a dotted line in FIG. These setting methods are shown in Matt Bernstein et.al., JMRI, Vol. 4, 105-108, 1994, etc.

  After the waiting time (inversion time) TI [s] from the inversion pulse 1, the imaging section is excited by the excitation pulse 4. After applying the phase encoding gradient magnetic field 5, the echo signal 6 is collected after the echo time TE. By repeating this series of operations for the number of encoding steps necessary for image reconstruction, one shooting is completed.

  If the echo time TE is sufficiently shorter than the inversion time TI, when the blood flow moves in a certain direction at an average velocity v [m / s], the blood flow presaturated in the label region 7 is approximately v ×. Captured at the position moved by TI [m]. Thereby, it is possible to observe the movement of the photographing target during photographing.

  When this method is used for diagnosis, the setting of the location of the label area and the setting of the inversion time TI are the most important imaging parameters, but there is a problem that it is not intuitive for the operator and is difficult to use.

  For example, when it is desired to observe the dynamics of blood flow in the vicinity of the region of interest ROI, the presaturated blood flow reaches the region of interest ROI just as it reaches the region of interest ROI when the excitation pulse 4 is applied. On the other hand, it is necessary to set a label area at a position upstream by an appropriate distance. This distance is determined depending on the blood flow velocity v and the inversion time TI. For this reason, in order to collect a target image, it is necessary to repeatedly shoot while changing the reversal time TI or moving the label area, which is very inconvenient. In particular, the range that can be set as the inversion time TI is limited due to circumstances such as the T1 value of the subject to be photographed, and the setting may be difficult.

An object of the present invention, a magnetic resonance imaging apparatus, when displaying the photographed image data is to be able to provide a diagnosis support information.

The present invention labels an imaging object including a moving body in a label area in an imaging area by applying a specific high-frequency pulse during application of a gradient magnetic field under a predetermined pulse sequence,
After the waiting time from the specific high-frequency pulse, the moving object is labeled to generate an image of the imaging target by performing imaging for collecting signals from the imaging area, and the pulse sequence is slice selection wherein said specific radio-frequency pulses for labeling imaging object applied with use gradient, the the generated captured target image, and displaying by superimposing a mark indicating the label area.

According to the present invention, in a magnetic resonance imaging apparatus, when displaying the photographed image data, it is possible to provide a diagnosis support information.

  Embodiments of a magnetic resonance imaging apparatus (MRI apparatus) according to the present invention will be described below with reference to the drawings. Characteristically, this MRI apparatus is a non-contrast MR angiography (MRA) that acquires, for example, an image representing the dynamics of blood flow as a moving object (moving body) in a subject without using a contrast agent. It has a function to execute. For the pulse sequence for performing this non-contrast MRA, a harmonic inversion (inversion) pulse of selective excitation is used.

  FIG. 1 shows a schematic configuration of the MRI apparatus according to the present embodiment. This MRI apparatus includes a bed unit on which a patient P as a subject is placed, a static magnetic field generating unit for generating a static magnetic field, a gradient magnetic field generating unit for adding position information to the static magnetic field, and transmission and reception for transmitting and receiving high-frequency signals. A control unit that controls the entire system and image reconstruction, and an electrocardiogram measurement unit that measures an ECG signal as a signal representing the cardiac time phase of the subject P.

The static magnetic field generation unit includes, for example, a superconducting magnet 101 and a static magnetic field power supply 102 that supplies current to the magnet 101, and an axial direction of a cylindrical opening (diagnostic space) into which the subject P is loosely inserted. (Z-axis direction) to generate a static magnetic field _{H 0.} A shim coil 114 is provided in the magnet portion. A current for homogenizing the static magnetic field is supplied from the shim coil power supply 115 to the shim coil 114 under the control of the host computer 106. The couch portion can removably insert the top plate on which the subject P is placed into the opening of the magnet 101.

  The gradient magnetic field generation unit includes a gradient magnetic field coil unit 103 incorporated in the magnet 101. The gradient coil unit 103 includes three sets (types) of x, y, and z coils 103x, 103y, and 103z for generating gradient magnetic fields in the X, Y, and Z axis directions orthogonal to each other. The gradient magnetic field unit also includes a gradient magnetic field power supply 4 that supplies current to the x, y, and z coils 103x, 103y, and 103z. The gradient magnetic field power supply 4 supplies a pulse current for generating a gradient magnetic field to the x, y, z coils 103x, 103y, and 103z under the control of a sequencer 5 described later.

By controlling the pulse current supplied from the gradient magnetic field power source 104 to the x, y, z coils 103x, 103y, 103z, the gradient magnetic fields in the three axes X, Y, and Z, which are physical axes, are synthesized and orthogonal to each other. The logical axis directions of the slice direction gradient magnetic field Gs, the phase encode direction gradient magnetic field Ge, and the readout direction (frequency encode direction) gradient magnetic field Gr can be arbitrarily set and changed. Slice direction, phase encoding direction, and gradient magnetic fields in the readout direction are superimposed on the static magnetic field H _0.

  The transmission / reception unit includes an RF coil 107 disposed in the vicinity of the subject P in the imaging space in the magnet 101, and a transmitter 108T and a receiver 108R connected to the coil 107. The transmitter 108T and the receiver 108R operate under the control of the sequencer 105. The transmitter 108T supplies the RF coil 107 with an RF current pulse having a Larmor frequency for causing nuclear magnetic resonance (NMR). The receiver 108R takes in an echo signal (high frequency signal) received by the RF coil 107, and performs various signal processing such as preamplification, intermediate frequency conversion, phase detection, low frequency amplification, filtering, etc. A digital amount of echo data (original data) corresponding to the echo signal is generated by / D conversion.

  The control / arithmetic unit includes a sequencer (also called a sequence controller) 105, a host computer 106, an arithmetic unit 110, a storage unit 111, a display unit 112, an input unit 113, an audio generator 116, and an MRA expert system 120. Among these, the host computer 106 has a function of instructing the pulse sequence information to the sequencer 105 according to the stored software procedure and overseeing the operation of the entire apparatus.

  The host computer 106 performs an imaging scan based on the pulse sequence following a preparatory operation such as a positioning scan. This imaging scan is a scan that collects a set of echo data necessary for image reconstruction, and is set to a two-dimensional scan here. The imaging scan is performed using an ECG gate method based on an ECG signal. This ECG gate method may not be used in some cases.

  This pulse sequence is a three-dimensional (3D) scan or a two-dimensional (2D) scan. The pulse trains include SE (spin echo) method, FSE (fast SE) method, FASE (fast asymmetric SE) method (that is, imaging method combining the fast SE method with the half Fourier method), EPI (echo planar imaging). ) Method, etc. are used.

  The sequencer 105 includes a CPU and a memory, stores pulse sequence information sent from the host computer 106, controls operations of the gradient magnetic field power source 104, the transmitter 108T, and the receiver 108R according to this information, The echo data output from the receiver 108 </ b> R is once input and transferred to the arithmetic unit 1010. Here, the pulse sequence information is all information necessary for operating the gradient magnetic field power source 104, the transmitter 108T, and the receiver 108R in accordance with a series of pulse sequences, for example, x, y, z coils 103x, 103y. , 103z includes information on the intensity, application time, application timing, etc.

  The arithmetic unit 110 inputs echo data (original data or raw data) output from the receiver 108R through the sequencer 105, and arranges the echo data in a Fourier space (also referred to as k space or frequency space) in its internal memory. Then, the echo data is subjected to two-dimensional or three-dimensional Fourier transform for each group to reconstruct the image data in real space. Further, the arithmetic unit can perform a data synthesizing process, a difference arithmetic process, and the like as necessary.

  In this synthesis process, two-dimensional image data of a plurality of frames are added for each corresponding pixel, and maximum value projection (MIP) or minimum for selecting the maximum value or minimum value in the line-of-sight direction for three-dimensional data Value (MIP) projection processing and the like are included. As another example of the synthesis process, the axes of a plurality of frames may be matched in the Fourier space and synthesized into one frame of echo data as it is. The addition processing includes simple addition processing, addition averaging processing, weighted addition processing, and the like.

  The storage unit 111 can store not only the reconstructed image data but also the image data that has been subjected to the above-described combining process and difference process. The display 112 displays an image. In addition, information regarding imaging conditions, pulse sequences, image synthesis, and difference calculation desired by the operator can be input to the host computer 106 via the input unit 113.

  Furthermore, the electrocardiogram measurement unit attaches to the body surface of the subject and detects an ECG signal as an electrical signal, and performs various processes including digitization on the sensor signal to perform the host computer 106 and the sequencer. ECG unit 118 that outputs to 105. The measurement signal from the electrocardiogram measurement unit is used by the sequencer 105 when performing an imaging scan. Thereby, the synchronization timing by the ECG gate method (electrocardiogram synchronization method) can be set appropriately, and the ECG gate method imaging scan based on this synchronization timing can be performed to collect data.

  The MRA expert system 120 has a function for supporting the setting of the position of the label area and the waiting time (inversion time) TI from the inversion pulse to the excitation pulse. As this support function, a reference image acquired in advance for positioning of an imaging section and positioning of a label area, a mark representing the label area, and a blood flow labeled with an inversion pulse are obtained from the label area with an inversion time TI. Then, it is displayed on the display 112 together with an index indicating the position at which the excitation pulse application time is reached. In this embodiment, two types of support modes are facilitated. The operator can selectively use the first and second types of support modes.

  In the first support mode, a certain inversion time TI is assumed, and a plurality of arrival positions corresponding to various blood flow velocities v are presented under the assumed inversion time TI, while the second support mode is Assuming a certain blood flow velocity v, a plurality of arrival positions corresponding to various inversion times TI are presented under the assumed blood flow velocity v.

  FIG. 2A shows an example of a label area setting support screen in the first support mode. The reference image 9 is an image acquired with a relatively low resolution specification using a spin echo or an echo planar method before the main scan. In the label area setting scene, the MRA expert system 120 displays a rectangular mark 10 representing the label area on the reference image 9 through the inversion time TI assumed from the label area. A plurality of line marks 11 that represent a plurality of assumed positions reached under v by dotted lines, the corresponding assumed flow velocity V, and the assumed inversion time TI are displayed. In FIG. 2, three line marks 11 are displayed together with corresponding sticky notes with flow rates of 10 cm / s, 20 cm / s, and 30 cm / s, respectively. The relationship between the line mark 11 and the corresponding flow velocity can be arbitrarily set, and the operator may set a numerical value, or may be set as a default value according to the examination site.

  Each line mark 11 has a corresponding flow velocity v, and an image scale conversion distance obtained by multiplying the assumed inversion time TI by a distance from the end (or center) of the label area mark 10. Therefore, it is arranged in parallel with the major axis of the label area mark 10.

  The operator can confirm the region of interest ROI in the reference image 9, refer to the line mark 11 for the position of the ROI, and set the label region at a suitable position for the region of interest ROI with the mark 10, Further, the inversion time TI can be set to a suitable time by changing the assumed inversion time TI while the label area is fixed. Specifically, the operator operates a pointer such as a mouse of the input device 113 to move the mark 10 in the label area on the reference image 9, and changes its shape as necessary. Further, the operator changes the estimated inversion time TI by tapping the keyboard of the input device 113, for example.

  When the mark 10 in the label area is moved, the MRA expert system 120 recalculates the position of the line mark 11 on the reference image 9 and redisplays the line mark 11 at that position. Accordingly, the display position of the line mark 11 moves following the movement of the mark 10 in the label area.

  When the assumed inversion time TI is changed, the MRA expert system 120 recalculates the position of the line mark 11 on the reference image 9 according to the changed inversion time TI, and redisplays the line mark 11 at the position. (See FIG. 2 (b)).

  Further, the operator can rotate the mark 10 in the label area. FIG. 3 shows the mark 13 in the rotated label area. The MRA expert system 120 tilts the line mark 11 following the rotation of the mark 13 in the label area so as to maintain parallelism with the major axis of the mark 13 in the label area. Since the object to be imaged may move in any direction from the label area, the line mark 14 is displayed as a dotted line on both the upper and lower sides in parallel with the major axis of the mark 13 in the label area.

  Further, the operator can change the shape of the mark 10 in the label area to a circle. FIG. 4 shows the mark 19 in the label area changed to a circle. The MRA expert system 120 changes the mark 20 representing the arrival position of the label blood flow to a circle so as to draw a concentric circle with the mark 13 in the label area. The distance from the center or edge of the mark 13 in the label area to each mark 20 is set to a distance corresponding to TI × v, as in the case of the rectangle. Regarding the method of inversion excitation of such a non-rectangular region, PABottomley, et.al., J. of Appl. Phys. Vol 62, 4284, 1987 or CJ Hardy, et.al., J. of Magn Reso., Vol 77, 233-250, 1988.

  Next, the second support mode will be described. In the first support mode described above, a plurality of arrival positions corresponding to various blood flow velocities v are presented under the assumption of the inversion time TI. Assuming a blood flow velocity v, a plurality of arrival positions corresponding to various inversion times TI are presented.

  FIG. 5A shows an example of a label area setting support screen in the second support mode. By the MRA expert system 120, a rectangular mark 15 representing a label area is displayed on the reference image 9 with a plurality of assumed positions where blood flows out of the label area at an assumed flow velocity and arrives through various inversion times TI. A plurality of line marks 16 represented by dotted lines, the corresponding inversion times TI, and the assumed flow velocity V are displayed.

  In FIG. 5A, three line marks 16 are displayed together with corresponding inversion times TI 200 ms, 400 ms, and 600 ms, respectively. The relationship between the line mark 16 and the corresponding inversion time TI can be arbitrarily set, and the operator may set a numerical value, or may be set as a default value according to the examination site. Good.

  Each line mark 16 is a position where a distance corresponding to a distance obtained by multiplying the corresponding inversion time TI by the assumed flow velocity v is separated from the end (or center) of the label area mark 15 by the scale of the image. The label area mark 15 is arranged in parallel with the major axis.

  When the operator operates a pointer such as a mouse of the input device 113 to move the label area mark 15 on the reference image, the MRA expert system 120 follows the movement of the label area mark 15 in accordance with the movement of the label area mark 15. The position of the upper line mark 16 is recalculated, and the line mark 16 is displayed again at that position. Accordingly, the display position of the line mark 16 moves following the movement of the mark 15 in the label area. When the assumed flow velocity v is changed by the operator, the MRA expert system 120 recalculates the position of the line mark 18 on the reference image according to the changed assumed flow velocity v, and sets the line mark 18 at the position. It is displayed again (see FIG. 5B). Further, as in the first support mode, the mark 15 in the label area can be rotated, and the line mark 16 is inclined so as to maintain parallel to the major axis of the mark 15 in the label area. The In addition, when the shape of the mark 15 in the label area is changed to a circle, the mark 16 representing the arrival position of the label blood flow is changed to a circle so as to draw a concentric circle with the mark 15 in the label area.

  As described above, in the present embodiment, the arrival positions at various flow velocities v assuming the inversion time TI are displayed as indexes for setting the position of the label area or adjusting the inversion time TI, and conversely, Assuming the flow velocity v, each arrival position at various inversion times TI is displayed as an index for setting the position of the label area, so that a label area is set at a suitable position, or a suitable inversion time. TI can be set.

  The MRA expert system 120 updates the standard pulse sequence and supplies the data to the sequencer 105 in accordance with the position of the label area and the inversion time TI set as described above. The sequencer 105 executes the pulse sequence by controlling the gradient magnetic field power source 104, the transmitter 108T, and the receiver 108R according to the supplied pulse sequence data.

  Next, image data is generated by the arithmetic unit 110 from the MR data collected by the execution of the pulse sequence, and is displayed on the display 112. The MRA expert system 120 has a function of providing diagnosis support information when displaying the image data.

  FIG. 6 shows an example of an image display screen. Reference numeral 24 denotes a generated image, and a mark 21 indicating a label area and a blood flow velocity scale 22 are superimposed on the image 24. Reference numeral 23 denotes a labeled blood flow image. The speed scale 22 is graduated at distances on the image corresponding to distances multiplied by various blood flow velocities v with respect to the inversion time TI of the pulse sequence used for imaging. With this scale 22, the flow path of the labeled blood flow 23 can be estimated.

  Further, the MRA expert system 120 has a function of calculating an average blood flow velocity. FIG. 7 shows a screen at the time of calculating the average blood flow velocity. Reference numeral 25 denotes a label area mark. On the image, the labeled blood flow 30 is displayed together with the blood vessel image 31, for example, as a low signal. The operator operates the pointer 29 to approximately trace the path from the label area to the labeled blood flow 30 as the measurement target according to the blood vessel image 31 with a plurality of straight lines 27 at the joint (vertex) 26. Go. That is, the operator sequentially designates the joint 26 by clicking the mouse while tracing the path where the subject 30 has moved from the lower end of the label area with the pointer 29.

  The MRA expert system 120 calculates the average speed by converting the distance L [m] of the broken line 27 into the actual distance and dividing the distance L by the inversion time TI [m / s]. The value is displayed as 28. As a result, the speed of the object to be photographed can be measured accurately and conveniently, which is convenient for the operator. If necessary, the speed may be corrected by moving the imaging target during the echo time TE [s].

  FIG. 8 shows the pulse sequence provided by the MRA expert system 120. The portion indicated by A is the same as the conventional example shown in FIG. In the part indicated by B, the pre-saturation part including the inversion pulse 1, the slice selection gradient magnetic field pulse 2, the frequency shift pulse 3 for the location of the label area is deleted from the A part, and only the signal generation part 40 Part. Functionally, only the inversion pulse 1 may be deleted. Images of the A part and the B part are alternately taken, and images are reconstructed separately to obtain two sets of image data. By creating a difference image of the obtained image data, it is possible to suppress a signal from a portion where the subject to be imaged (blood flow here) does not move. Thereby, a part with a motion can be drawn more clearly. The speed scale 22 in FIG. 6 is also displayed in the difference image in FIG. Further, the setting for calculating the average speed in FIG. 7 may be performed on the difference image in FIG.

  The pulse sequence of FIG. 8 is after the pre-saturation part (inversion pulse 1, gradient magnetic field pulse for slice selection 2, frequency shift pulse 3 for the location of the label area), and the signal generation part (actual imaging pulse train). By applying the high frequency inversion pulse 1 again before applying the frequency shift pulse 3 for the location of the slice selection gradient magnetic field pulse 2 and the label region before the portion 40), the presaturating region is It may be set in a region other than the inversion excitation region. In other words, in the above method, labeling is realized by lowering the label area relative to other areas, but conversely, the label area is reduced by lowering the area other than the label area. May be extracted.

  The actual imaging portion indicated by 40 in FIG. 8 shows the case of the FE method, but other pulse sequences such as a spin echo method, an echo planar method, a rare (RARE) ) Method (also called fast spin echo method), trueFISP method, etc. are also possible. In addition, since the movement of the imaging target is often related to cardiac time phase and body movement due to breathing, the application of the high-frequency inversion pulse is synchronized with the waveform of ECG synchronization, pulse wave synchronization, respiratory synchronization, etc. May be collected. After triggering the respiratory synchronization waveform, it may be collected in synchronization with the first electrocardiogram waveform.

(Modification)
The present invention is not limited to the above-described embodiments, and various modifications can be made without departing from the scope of the invention at the stage of implementation. Furthermore, the above embodiment includes various stages, and various inventions can be extracted by appropriately combining a plurality of disclosed constituent elements. For example, some constituent requirements may be deleted from all the constituent requirements shown in the embodiment.

The block diagram which shows the structure of embodiment of the magnetic resonance imaging by this invention. The figure which shows an example of the label area | region setting screen containing the flow velocity parameter | index by the MRA expert system of FIG. The figure which shows the other example of the label area | region setting screen containing the flow velocity parameter | index by the MRA expert system of FIG. The figure which shows the further another example of the label area | region setting screen containing the flow velocity parameter | index by the MRA expert system of FIG. The figure which shows an example of the label area | region setting screen containing the TI parameter | index by the MRA expert system of FIG. The figure which shows an example of the label area | region mark and flow velocity scale which are displayed with a reconstruction image by the MRA expert system of FIG. The figure which shows an example of the setting screen for the average speed calculation by the MRA expert system of FIG. The figure which shows an example of the pulse sequence for MRA subtraction by the MRA expert system of FIG. The figure which shows an example of the pulse sequence of the general flow imaging method. The figure which shows the conventional label area | region setting screen.

DESCRIPTION OF SYMBOLS 101 ... Magnet 102 ... Static magnetic field power supply 103 ... Gradient magnetic field coil unit 104 ... Gradient magnetic field power supply 105 ... Sequencer 106 ... Host computer 107 ... RF coil 108T ... Transmitter 108R ... Receiver 110 ... Arithmetic unit 111 ... Storage unit 112 ... Display 113 ... Input device 120 ... MRA expert system.

Claims (11)

A mark representing the label area is displayed on the reference image acquired in advance for positioning of the imaging area and positioning of the label area in the imaging area,
Under a predetermined pulse sequence, a specific high-frequency pulse is applied as a pre-pulse during the gradient magnetic field application as a pre-pulse prior to the imaging part for signal acquisition, thereby moving the moving body in the label area that forms part of the imaging area. Generate an image of the imaging object labeled with the moving object by performing the imaging part to collect a signal from the imaging area after waiting time from the specific radio frequency pulse And
The specific high frequency pulse is applied together with a slice selection gradient magnetic field to label the object to be imaged,
On the shooting target image which the generated magnetic resonance imaging apparatus and displaying overlapping the mark representing the label area. 2. The image data according to claim 1, wherein the pulse sequence alternately performs imaging including the specific high-frequency pulse for labeling and imaging not including the specific high-frequency pulse for labeling, and each reconstructed image data. The magnetic resonance imaging apparatus characterized by producing | generating the difference image of. 3. The magnetism according to claim 1, wherein an average speed of the moving body is calculated by a calculation based on a distance of the labeled moving body from the mark in the displayed image to be captured and the waiting time. Resonance imaging device. 4. The magnetic resonance imaging apparatus according to claim 3 , wherein a mark representing the label area and the calculated average speed are superimposed and displayed on the generated image to be photographed . According to claim 1, wherein the imaging target of the image, a magnetic resonance imaging apparatus and displaying overlapping the scale that corresponds to the arrival position of the moving body to the speed of the mark and the moving body. 6. The magnetic scale according to claim 5, wherein the scale is a scale corresponding to a distance obtained by calculating the waiting time of the pulse sequence used for the imaging and the speeds of various moving objects. Resonance imaging device.   2. The pulse sequence according to claim 1, wherein the pulse sequence includes a slice selection signal for reducing a signal in a region other than the label region in addition to the specific high-frequency pulse for labeling an imaging target applied together with a slice selection gradient magnetic field. A magnetic resonance imaging apparatus comprising a high-frequency pulse applied in a state where no gradient magnetic field is applied.   The magnetic resonance imaging apparatus according to claim 1, wherein the specific high-frequency pulse is applied in synchronization with an electrocardiogram.   The magnetic resonance imaging apparatus according to claim 1, wherein the mark representing the label area is rotated according to an operation of an operation unit.   2. The magnetic resonance imaging apparatus according to claim 1, wherein the mark representing the label area is changed in shape according to an operation of an operation unit. A mark representing the label area is displayed on the reference image acquired in advance for positioning of the imaging area and positioning of the label area in the imaging area,
Under a predetermined pulse sequence, a specific high-frequency pulse is applied as a pre-pulse during the gradient magnetic field application as a pre-pulse prior to the imaging part for signal acquisition, thereby moving the moving body in the label area that forms part of the imaging area. Generate an image of the imaging object labeled with the moving object by performing the imaging part to collect a signal from the imaging area after waiting time from the specific radio frequency pulse And
In the pulse sequence, in addition to the specific high-frequency pulse for labeling the imaging target applied together with the slice selection gradient magnetic field, a slice selection gradient magnetic field is applied in order to reduce the signal area other than the label area. Including high frequency pulses applied under non-
On the shooting target image which the generated magnetic resonance imaging apparatus and displaying overlapping the mark representing the label area.

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