JP2016154619A - Magnetic resonance imaging apparatus - Google Patents

Abstract

PROBLEM TO BE SOLVED: To provide an MRI (Magnetic Resonance Imaging) apparatus which can detect movement of a site such as the diaphragm with high accuracy.SOLUTION: An MRI apparatus 100 comprises a setting part 26a and a control part 10. The setting part 26a sets a first application region to which an excitation pulse for detecting a respiratory time phase is applied and a second application region to which refocusing pulse is applied, in such a way that a volume of a region to which both of the excitation pulse and the refocusing pulse are applied becomes a prescribed volume value. A control part 10 executes first imaging to detect the respiratory time phase on the basis of first imaging data obtained from the region and second imaging to collect second imaging data within a range including an object on the basis of the respiratory time phase obtained by the first imaging while applying the excitation pulse and the refocusing pulse to the first application region and the second application region respectively.SELECTED DRAWING: Figure 1

Description

  Embodiments described herein relate generally to a magnetic resonance imaging apparatus.

  Magnetic Resonance Imaging (MRI) magnetically excites a subject's nuclear spin placed in a static magnetic field with a Larmor frequency RF (Radio Frequency) pulse. This is an imaging method for reconstructing an image from a generated NMR (Nuclear Magnetic Resonance) signal.

  In magnetic resonance imaging, there is an imaging method in which the heart is imaged following the movement of the diaphragm corresponding to respiratory motion. In this case, the motion detection pulse application region for detecting the motion of the diaphragm is set in the diaphragm, and the magnetic resonance signal is collected from the motion detection pulse application region immediately before the magnetic resonance signal is collected from the imaging region of the heart. . The magnetic resonance signals collected from the motion detection pulse application region are used to correct the heart imaging region or to determine the timing of heart imaging.

JP 2011-147561 A

  The problem to be solved by the present invention is to provide a magnetic resonance imaging apparatus that can accurately detect the movement of a region such as the diaphragm.

  In the magnetic resonance imaging apparatus of the embodiment, the setting unit is configured so that the volume of a region to which both the excitation pulse for detecting the respiratory time phase and the refocusing pulse are applied has a predetermined volume value. A first application region to be applied and a second application region to which the refocus pulse is applied are set. The controller detects the respiratory time phase based on the first imaging data obtained from the region while applying the excitation pulse and the refocus pulse to the first application region and the second application region, respectively. One imaging and a second imaging for collecting second imaging data in a range including the target are executed based on the respiratory time phase obtained by the first imaging.

FIG. 1 is a functional block diagram showing the configuration of the MRI apparatus according to the first embodiment. FIG. 2 is a view for explaining imaging of the heart in the first embodiment. FIG. 3 is a flowchart illustrating an imaging process procedure according to the first embodiment. FIG. 4 is a diagram for explaining the maximum FOV volume data in the first embodiment. FIG. 5 is a flowchart showing the processing in step S104 in the first embodiment. FIG. 6A is a diagram illustrating an example of a temporarily specified heart region. FIG. 6B is a diagram illustrating an example of a finally identified heart region. FIG. 6C is a diagram illustrating an example of a finally identified heart region. FIG. 7 is a diagram for explaining an example of a probe application region in the first embodiment. FIG. 8 is a diagram for explaining an example of a method for calculating the direction of the application region in the first embodiment. FIG. 9A is a diagram for explaining an example of a method for calculating the direction of the application region in the first embodiment. FIG. 9B is a diagram for explaining an example of a method for calculating the direction of the application region in the first embodiment. FIG. 10 is a diagram for explaining an example of a method for calculating the slice thickness A in the first embodiment. FIG. 11 is a diagram for explaining an example of a method for setting the collection range of multi-slice data according to the first embodiment. FIG. 12 is a flowchart showing the process in step S104 in the second embodiment. FIG. 13 is a flowchart showing the processing in step S104 in the third embodiment. FIG. 14 is a flowchart showing the processing in step S104 in the fourth embodiment. FIG. 15 is a diagram illustrating an example of a display example according to the fourth embodiment.

  Hereinafter, a magnetic resonance imaging apparatus according to an embodiment (hereinafter, appropriately referred to as an “MRI (Magnetic Resonance Imaging) apparatus”) will be described with reference to the drawings. Note that the embodiments are not limited to the following embodiments. The contents described in each embodiment can be applied in the same manner to other embodiments in principle.

(First embodiment)
FIG. 1 is a functional block diagram showing the configuration of the MRI apparatus 100 according to the first embodiment. As shown in FIG. 1, the MRI apparatus 100 includes a static magnetic field magnet 1, a gradient magnetic field coil 2, a gradient magnetic field power supply 3, a bed 4, a bed control unit 5, a transmission coil 6, a transmission unit 7, A reception coil 8, a reception unit 9, a sequence control unit 10, and a computer 20 are provided. Note that the MRI apparatus 100 does not include the subject P (for example, the human body) shown in the dotted frame in FIG. Moreover, the structure shown in FIG. 1 is only an example. For example, the sequence control unit 10 and each unit in the computer 20 may be configured to be appropriately integrated or separated.

  The static magnetic field magnet 1 is a magnet formed in a hollow cylindrical shape (including a magnet whose cross section perpendicular to the axis of the cylinder is elliptical), and generates a static magnetic field in an internal space. The static magnetic field magnet 1 is, for example, a permanent magnet. The static magnetic field magnet 1 may be a superconducting magnet. When the static magnetic field magnet 1 is a superconducting magnet, the MRI apparatus 100 includes a static magnetic field power source (not shown), and the static magnetic field power source supplies a current to the static magnetic field magnet 1. At this time, the static magnetic field magnet 1 is excited by receiving a current supplied from a static magnetic field power source. The static magnetic field power supply may be provided separately from the MRI apparatus 100.

  The gradient magnetic field coil 2 is a coil formed in a hollow cylindrical shape (including a coil whose cross section perpendicular to the axis of the cylinder is elliptical), and is disposed inside the static magnetic field magnet 1. The gradient coil 2 is formed by combining three coils corresponding to the X, Y, and Z axes orthogonal to each other, and these three coils individually supply current from the gradient magnetic field power supply 3. In response, a gradient magnetic field is generated in which the magnetic field strength varies along the X, Y, and Z axes. The gradient magnetic fields of the X, Y, and Z axes generated by the gradient magnetic field coil 2 are, for example, a slice gradient magnetic field Gs, a phase encode gradient magnetic field Ge, and a read gradient magnetic field Gr. The gradient magnetic field power supply 3 supplies a current to the gradient magnetic field coil 2.

  The bed 4 includes a top plate 4a on which the subject P is placed. Under the control of the bed control unit 5, the bed 4a is placed in the cavity of the gradient coil 2 (with the subject P placed thereon). Insert it into the imaging port. Usually, the bed 4 is installed such that the longitudinal direction is parallel to the central axis of the static magnetic field magnet 1. The couch controller 5 drives the couch 4 under the control of the computer 20 to move the couchtop 4a in the longitudinal direction and the vertical direction.

  The transmission coil 6 is arranged inside the gradient magnetic field coil 2 and receives a supply of RF pulses from the transmission unit 7 to generate a high-frequency magnetic field. The transmission unit 7 supplies the transmission coil 6 with an RF pulse corresponding to the Larmor frequency determined by the type of target atom and the magnetic field strength.

  The receiving coil 8 is disposed inside the gradient magnetic field coil 2 and receives a magnetic resonance signal (hereinafter referred to as “MR signal” as appropriate) emitted from the subject P due to the influence of the high-frequency magnetic field. When receiving the MR signal, the receiving coil 8 outputs the received MR signal to the receiving unit 9.

  The transmission coil 6 and the reception coil 8 described above are merely examples. What is necessary is just to comprise by combining one or more among the coil provided only with the transmission function, the coil provided only with the reception function, or the coil provided with the transmission / reception function.

  The receiving unit 9 detects the MR signal output from the receiving coil 8 and generates MR data based on the detected MR signal. Specifically, the receiving unit 9 generates MR data by digitally converting the MR signal output from the receiving coil 8. In addition, the reception unit 9 transmits the generated MR data to the sequence control unit 10. The receiving unit 9 may be provided on the gantry device side including the static magnetic field magnet 1 and the gradient magnetic field coil 2.

  The sequence control unit 10 images the subject P by driving the gradient magnetic field power source 3, the transmission unit 7, and the reception unit 9 based on the sequence information transmitted from the computer 20. Here, the sequence information is information defining a procedure for performing imaging. The sequence information includes the strength of the current supplied from the gradient magnetic field power supply 3 to the gradient magnetic field coil 2 and the timing of supplying the current, the strength of the RF pulse supplied from the transmitter 7 to the transmission coil 6 and the timing of applying the RF pulse, and reception. The timing at which the unit 9 detects the MR signal is defined. For example, the sequence control unit 10 is an integrated circuit such as an application specific integrated circuit (ASIC) or a field programmable gate array (FPGA), or an electronic circuit such as a central processing unit (CPU) or a micro processing unit (MPU).

  When the sequence control unit 10 receives the MR data from the reception unit 9 as a result of driving the gradient magnetic field power source 3, the transmission unit 7 and the reception unit 9 and imaging the subject P, the received MR data is sent to the computer 20. Forward.

  The computer 20 performs overall control of the MRI apparatus 100, image generation, and the like. The computer 20 includes an interface unit 21, an image generation unit 22, a storage unit 23, an input unit 24, a display unit 25, and a control unit 26.

  The interface unit 21 transmits sequence information to the sequence control unit 10 and receives MR data from the sequence control unit 10. Further, when receiving the MR data, the interface unit 21 stores the received MR data in the storage unit 23. The MR data stored in the storage unit 23 is arranged in the k space by the control unit 26. As a result, the storage unit 23 stores k-space data.

  The image generation unit 22 reads the k-space data from the storage unit 23 and generates an image by performing reconstruction processing such as Fourier transform on the read k-space data.

  The storage unit 23 stores MR data received by the interface unit 21, k-space data arranged in k-space by the control unit 26, image data generated by the image generation unit 22, and the like. The storage unit 23 stores probe imaging conditions 23a. The probe imaging condition 23a will be described later. The storage unit 23 is, for example, a RAM (Random Access Memory), a semiconductor memory element such as a flash memory, a hard disk, an optical disk, or the like.

  The input unit 24 receives various instructions and information input from the operator. The input unit 24 is, for example, a pointing device such as a mouse or a trackball, or an input device such as a keyboard. The display unit 25 displays various GUIs (Graphical User Interface), images generated by the image generation unit 22, and the like under the control of the control unit 26. The display unit 25 is a display device such as a liquid crystal display.

  The control unit 26 performs overall control of the MRI apparatus 100 and controls imaging, image generation, image display, and the like. For example, the control unit 26 receives input of imaging conditions on the GUI, generates sequence information according to the received imaging conditions, and transmits the generated sequence information to the sequence control unit 10. The control unit 26 includes an imaging condition setting unit 26a. For example, the control unit 26 is an integrated circuit such as an ASIC or FPGA, or an electronic circuit such as a CPU or MPU.

  Subsequently, FIG. 2 is a diagram for explaining imaging of the heart in the first embodiment. In the first embodiment, an imaging method for imaging the heart following the movement of the diaphragm corresponding to the respiratory motion is applied. In this imaging method, there are a method for detecting the movement of the diaphragm and correcting the heart imaging region itself (hereinafter referred to as “body motion correction method”), and a method for determining the imaging timing while the heart imaging region is fixed. (Hereinafter referred to as “body motion trigger method”).

  2A is a diagram illustrating a timing chart when the body motion correction method is applied, and FIG. 2B is a diagram illustrating a timing chart when the body motion trigger method is applied. First, points common to FIG. 2A and FIG. 2B will be described. The waveform shown in FIG. 2 shows the position of the diaphragm that moves up and down as the subject P breathes. Of the breathing phases that repeat inhaling and exhaling, the position of the diaphragm is lowered when inhaling and the position of the diaphragm is raised when exhaling. 2A and 2B, the application area of the motion detection pulse for detecting the movement of the diaphragm is set in the diaphragm, and each echo and each segment from the imaging area of the heart. Immediately before the MR data is collected, the MR data is collected from the motion detection pulse application region. In FIG. 2, a box described as “main scan” corresponds to the collection of MR data from the imaging region of the heart, and a plurality of “trace scan” boxes arranged immediately before “main scan” are motion detection pulses. This corresponds to the collection of MR data from the application region.

  An example of the body motion correction method will be described with reference to FIG. The body motion correction method is a method for detecting the movement of the diaphragm and correcting the imaging region itself of the heart. For example, in the body movement correction method, as shown in FIG. 2A, a trace scan that is performed immediately before the main scan is maintained with the TR (Repetition Time), which is the interval between the main scan and the main scan being substantially constant. The number of repetitions of is also constant. In other words, in the body motion correction method, the trace scan is performed a certain number of times while keeping the TR substantially constant, and then the main scan is switched. The position of the diaphragm detected in the last trace scan is within the threshold range (upper limit). MR data collected in the main scan is used for image generation (“Correct” in FIG. 2). On the other hand, if the position of the diaphragm is outside the threshold range, MR data is collected in the main scan, but is not used for image generation (“Correct & Reject” in FIG. 2).

  In this body motion correction method, the amount of movement of the heart is estimated in real time based on the position of the diaphragm detected in real time, and the position of the imaging region of the main scan is corrected in real time based on the estimated amount of movement of the heart. The

  An example of the body movement trigger method will be described with reference to FIG. The body motion trigger method is a method of detecting the movement of the diaphragm and determining the imaging timing while the imaging region of the heart is fixed. For example, in the body motion trigger method, as shown in FIG. 2 (B), TR for a certain period is secured, but TR itself is not kept constant. Also, the number of repetitions of the trace scan performed immediately before the main scan is not constant. That is, in the body movement trigger method, after the trace scan is performed an arbitrary number of times, when the position of the diaphragm detected by the trace scan falls within the threshold range (within the range between the upper limit value and the lower limit value), Switch to the main scan. Even if the diaphragm position detected by the trace scan falls within the threshold range, if the TR for a certain period is not secured, the main scan is not switched.

  In this body motion trigger method, since the respiratory time phase of the main scan is substantially constant, unlike the body motion correction method, the position of the imaging region of the main scan is not corrected in principle.

  In both cases of the body motion correction method and the body motion trigger method, the main scan may be performed in synchronization with an electrocardiogram signal (ECG (Electrocardiogram)). That is, in this case, only MR data collected at a timing that satisfies a desired respiratory time phase and cardiac phase at the same time are used for image generation. In addition, the range of the threshold value indicated by the upper limit value and the lower limit value is adjusted as appropriate according to the relationship with the desired image quality. FIG. 2 shows an example in which the main scan is performed during the period when the person exhales. However, the embodiment is not limited thereto, and the main scan may be performed during the period when the person inhales.

  FIG. 3 is a flowchart illustrating an imaging process procedure according to the first embodiment. As shown in FIG. 3, in the first embodiment, the imaging condition setting unit 26a first receives an imaging plan setting from the operator (step S101). For example, the imaging condition setting unit 26a holds in advance information on a pulse sequence in which initial values of imaging parameters such as TR and TE (Echo Time) are set. In addition, the information of the pulse sequence is managed by a set of a plurality of pulse sequence groups including a preparation scan and an imaging scan for each imaging region and imaging purpose, for example. The imaging condition setting unit 26a presents a set of pulse sequence groups to the operator via the GUI, and accepts selections and changes as appropriate from the operator, thereby determining a pulse sequence group and imaging parameters to be performed in the target examination. .

  Subsequently, based on the imaging plan received by the imaging condition setting unit 26a, the sequence control unit 10 starts execution of a preparation scan (step S102). Here, the preparation scan (also referred to as “preparation imaging”) is a scan performed prior to an imaging scan (also referred to as “main imaging”) that collects images used for diagnosis. A scan for collecting a sensitivity map, a scan for shimming, and the like are included.

  Subsequently, the sequence control unit 10 executes a maximum FOV (Field Of View) volume data collection scan (maximum FOV scan) (step S103).

  In the first embodiment, since “1D Motion Probe” is used as a technique for detecting respiratory motion, the motion detection pulse is referred to as a “probe”.

  Here, the volume data of the maximum FOV is the three-dimensional MR data collected with the maximum FOV that can be set as the MRI apparatus 100 around the center of the magnetic field (for example, a range in which the uniformity of the static magnetic field strength can be ensured). That is. Since the volume data is used for deriving the probe position and multi-slice data collection range, it is necessary to collect the volume data in a range including landmarks used for deriving each position. For example, in the first embodiment, the volume data is collected in a range including the apex of the liver and the heart.

  FIG. 4 is a diagram for explaining the maximum FOV volume data in the first embodiment. For example, as shown in FIG. 4, the sequence control unit 10 sets the head-foot direction as the readout direction, sets the left-right direction as the phase encoding direction, sets the dorsoventral direction as the slice encoding direction, and sets the MRI apparatus 100. 3D MR data is collected with the maximum FOV that can be set as Note that the resolution in the head and foot direction can be increased by setting the head and foot direction as the readout direction. Further, the position of the diaphragm and the position of the heart are most effective when the image feature on the coronal sectional image is automatically detected or when the detection result is confirmed. In addition, in the head-and-foot direction, which is the two directions on the coronal cross-sectional image, and in the left-right direction, the effect of folding out of the imaging region is less in the left-right direction. For the above reasons, it is desirable to collect volume data in a combination of the encoding directions described above.

  Returning to FIG. 3, subsequently, the imaging condition setting unit 26a derives the probe position and the collection range of the multi-slice data using the maximum FOV volume data collected in step S103 (step S104).

  FIG. 5 is a flowchart showing the processing in step S104 in the first embodiment. As illustrated in FIG. 5, the imaging condition setting unit 26a detects, for example, the position of the apex of the liver and the heart region using the model image (step S201). Then, the imaging condition setting unit 26a causes the storage unit 23 to store information indicating the detected position of the apex of the liver and information indicating the heart region. The model image is an image (MR image) obtained by imaging a subject (for example, a standard single patient) with the MRI apparatus 100 in advance. The embodiment is not limited to this, and an average image of images obtained by imaging a plurality of patients may be used as the model image, for example. The model image may be an image subjected to image processing.

  A technique for detecting the position of the apex of the liver and the heart region from the maximum FOV volume data using the model image will be described. First, on the model image, the position of the apex of the liver and the region of the heart are known. For example, a group of voxels constituting a three-dimensional heart region is known as the heart region. Therefore, the imaging condition setting unit 26a performs image processing for deforming the maximum FOV volume data rigidly or non-rigidly so as to match the model image, and the position of the apex of the liver on the maximum FOV volume data after deformation, And, the region of the heart is specified. For example, the imaging condition setting unit 26a identifies each voxel in the deformed maximum FOV volume data corresponding to each voxel constituting the heart region in the model image, and identifies the identified voxel group as the heart region. .

  Thereafter, the imaging condition setting unit 26a performs image processing for reversely transforming the maximum FOV volume data into the original maximum FOV volume data, and finally specifies the position of the vertex of the liver on the maximum FOV volume data after the reverse deformation. At the same time, the heart region is provisionally specified. For example, the imaging condition setting unit 26a tentatively specifies the heart region by specifying the voxel group constituting the heart region in the maximum FOV volume data after reverse deformation. FIG. 6A is a diagram illustrating an example of a temporarily specified heart region. For example, as shown in FIG. 6A, the imaging condition setting unit 26a provisionally defines a three-dimensional region H1 of the heart by specifying a voxel group constituting the region of the heart in the maximum FOV volume data after inverse deformation. To be specific. Here, since the shape of the region H1 is complicated, it may be complicated to handle the region H1 as a heart region and perform various subsequent processes on the region H1. 6B and 6C are diagrams illustrating an example of the finally identified heart region. Therefore, the imaging condition setting unit 26a finally specifies a rectangular parallelepiped H2 circumscribing the region H1, as shown in FIG. 6B. Since the shape of the rectangular parallelepiped H2 is not complicated, it is not complicated to treat the region H2 as a heart region and perform various subsequent processes on the region H2. Note that the imaging condition setting unit 26a may finally specify an ellipsoid H3 circumscribing the region H1, as illustrated in FIG. 6C. Similarly, since the shape of the ellipsoid H3 is not complicated, it is not complicated to treat the region H3 as a heart region and perform various subsequent processes on the region H3. The position of the apex of the liver and the region of the heart are detected by specifying the final location of the apex of the liver and the final region of the heart region by the method as described above. Here, since the region H2 or the like whose shape is not complicated is detected as the heart region, various subsequent processes performed on the detected heart region can be easily performed. Note that the embodiment is not limited to this, and the imaging condition setting unit 26a may perform image processing for rigid body deformation or non-rigid body deformation on the model image so as to match the maximum FOV volume data. .

  The imaging condition setting unit 26a may detect the heart region by other methods. For example, on the model image, the position of the heart (for example, the upper end position and the lower end position of the heart, the mitral valve that is a feature point of the heart, the apex, the center of the left ventricle, etc.) is known. Therefore, for example, the imaging condition setting unit 26a performs image processing for rigidly deforming or non-rigidly deforming the maximum FOV volume data so as to match the model image, and the position of the heart on the maximum FOV volume data after the deformation. Identify. Thereafter, the imaging condition setting unit 26a performs image processing for reversely transforming the maximum FOV volume data into the original maximum FOV volume data, and specifies the position of the heart on the maximum FOV volume data after the reverse deformation. Then, the imaging condition setting unit 26a detects the heart region by estimating the heart region from the specified heart position.

  Note that the imaging condition setting unit 26a may further detect positions of large blood vessels, spinal cords, and the like by the same method.

  Then, the imaging condition setting unit 26a acquires the probe imaging condition 23a stored in the storage unit 23 (Step S202). The probe imaging condition 23a includes a “predetermined volume value” described later. The probe imaging condition 23a includes a slice thickness of an application region P1, which will be described later, a slice thickness of an application region P2, which will be described later, and an application, which will be described later, when the volume of a region R3 described later has a “predetermined volume”. Imaging conditions relating to various application regions R1 and R3 including the direction of the region R1, the direction of the application region R2, which will be described later, and the length in the readout direction of the application region P1 and the application region P2 are included.

  Here, the predetermined volume value will be described. FIG. 7 is a diagram for explaining an example of a probe application region in the first embodiment. In the first embodiment, as an application method of a probe, a case where a two-surface crossing method in which an excitation pulse of a SE (Spin Echo) method and a refocusing pulse are crossed to excite a square columnar region is used as an example. Will be described. The excitation pulse is also referred to as a flip pulse or a 90 ° pulse. The refocus pulse is also referred to as a flop pulse or a 180 ° pulse. FIG. 7 shows a rectangular parallelepiped application region R1 to which an excitation pulse is applied and a rectangular parallelepiped application region R2 to which a refocus pulse is applied.

  Further, FIG. 7 shows a quadrangular columnar region R3 where the application region R1 and the application region R2 intersect. That is, the region R3 is a region where both the excitation pulse and the refocus pulse are applied. As a result of applying the excitation pulse and the refocus pulse, the MR data obtained from the region R3 is subjected to a one-dimensional Fourier transform, and the edge between the lung field and the liver is detected, thereby detecting the position of the apex of the diaphragm. Is done. That is, in the above trace scan, for example, an application region R1 to which an excitation pulse is applied and an application region R2 to which a refocus pulse is applied while applying an excitation pulse and a refocus pulse for detecting a respiratory time phase. The respiratory time phase is detected based on the MR data obtained from the region R3 where and intersect. In the above-described imaging scan, MR data in a range including the heart is collected using the detected respiratory phase. Note that the trace scan corresponds to, for example, the first imaging, and the imaging scan corresponds to, for example, the second imaging.

  Here, the larger the volume of the region R3, the better the SNR (signal-to-noise ratio) of the MR data obtained from the region R3, but there is a tendency for the edges to become blurred. On the other hand, the smaller the volume of the region R3, the sharper the edge obtained, but the SNR of the MR data obtained from the region R3 tends to deteriorate. Note that the edge detection is more likely to succeed as the SNR becomes better or the obtained edge becomes more sensitive. Therefore, it is difficult to increase the edge detection accuracy simply by increasing or decreasing the volume of the region R3.

  The above-mentioned “predetermined volume value” means, for example, an edge obtained as a result of an experiment in which the operator changes the volume of the region R3 to various values and measures the edge sensitivity and SNR in each volume. This is the volume value of the region R3 when the edge detection accuracy determined by the sharpness and SNR exceeds a predetermined reference.

  Returning to the description of FIG. 5, the imaging condition setting unit 26a calculates the directions of the two application regions (step S203). 8 and 9A to 9B are diagrams for explaining an example of a method for calculating the direction of the application region in the first embodiment. For example, as shown in the example of FIG. 8, when the position P1 of the liver apex and the heart region H2 are detected in step S201, the imaging condition setting unit 26a does not include the heart region H2. Thus, the orientations of the application region R1 and the application region R2 when the application region R1 and the application region R2 are set so that the position P1 of the liver apex is included at the center of the region R3 are calculated. Here, the sizes of the application region R1 and the application region R2 whose directions are calculated are sizes based on the imaging conditions included in the probe imaging condition 23a acquired in step S202.

  An example of a method for calculating the direction of the application region in the first embodiment will be described in more detail. For example, a case will be described in which a region (for example, a two-dimensional region) on the axial cross section of the heart region H2 is a region as shown in the example of FIG. 9A. In this case, as shown in the example of FIG. 9A, the imaging condition setting unit 26a is configured so that the region H2 is not included in the axial cross section when viewed from the head and foot direction, and the center of the region R3 The directions of the application region R1 and the application region R2 when the application region R1 and the application region R2 are set to intersect are calculated so as to include the vertex position P1.

  For example, the case where the region on the axial cross section of the heart region H3 is a region as shown in the example of FIG. 9B will be described. In this case, as shown in the example of FIG. 9B, the imaging condition setting unit 26a is configured so that the region H3 is not included in the axial cross section when viewed from the head and foot direction, and the center of the region R3 The directions of the application region R1 and the application region R2 when the application region R1 and the application region R2 are set to intersect are calculated so as to include the vertex position P1.

  When MR data is collected from the application region of the probe immediately before the MR data is collected from the heart region, if the application region overlaps the heart region, the relationship between the recovery of longitudinal magnetization and the heart Artifacts may occur in this image. Therefore, the orientations of the application region R1 and the application region R2 are calculated so that the heart region is not included.

  Further, “α” in the example of FIG. 8 indicates an angle formed by the direction of the application region R1 and the direction of the application region R2. “L” indicates the length of the region R3 in the reading direction (head-and-foot direction). Note that the length in the readout direction of the region R3 is equal to the length in the readout direction of the application region R1 and the length in the readout direction of the application region R2. “A” indicates the thickness (slice thickness) of the application region R1 and the application region R2 in the slice direction.

  If the position of the large blood vessel or the spinal cord is further detected in step S201, the imaging condition setting unit 26a further includes the spinal cord so that the position of the large blood vessel is not included in step S203. As described above, the orientations of the application region R1 and the application region R2 when the application region R1 and the application region R2 are set may be calculated.

  Returning to the description of FIG. 5, the imaging condition setting unit 26a calculates the slice thickness A when the volume of the region R3 becomes the “predetermined volume value” (step S204). An example of a method for calculating the slice thickness A will be described. FIG. 10 is a diagram for explaining an example of a method for calculating the slice thickness A in the first embodiment. FIG. 10 shows an example when the application region R1, the application region R2, and the region R3 are viewed from the reading direction.

The rhombus area S of the region R3 shown in the example of FIG. 10 can be expressed by the following formula (1).
S = A ² / sin α (1)
“/” Is an operator indicating division.

The imaging condition setting unit 26a calculates a slice thickness A that satisfies the following expression (2), thereby calculating the slice thickness A when the volume of the region R3 is a “predetermined volume value”.
V = S × L
= A ² / sin α × L (2)
“×” is an operator indicating multiplication. In Expression (2), “V” is a “predetermined volume value” included in the probe imaging condition 23a acquired in step S202. In Expression (2), “L” is the length in the reading direction of the application region P1 and the application region P2 included in the probe imaging condition 23a acquired in step S202 (the length in the reading direction of the region R3). . In the expressions (1) and (2), “α” is an angle formed by the direction of the application region R1 calculated in step S203 and the direction of the application region R2.

  That is, the imaging condition setting unit 26a calculates the slice thickness A from Equation (2) using “V”, “α”, and “L” whose values are known.

  The imaging condition setting unit 26a then calculates the orientations of the application region R1 and the application region R2 and the slice thickness A, and the length in the readout direction of the application region P1 and the application region P2 included in the probe imaging condition 23a acquired in step S202. Are set in the probe imaging condition 23a (step S205).

  In step S205, the imaging condition setting unit 26a may display the set imaging conditions on a GUI (Graphical User Interface) displayed on the display unit 25 to allow the operator to confirm. Furthermore, the imaging condition setting unit 26a may accept correction of the displayed imaging conditions by the operator. When the displayed imaging condition is corrected, the imaging condition setting unit 26a sets the corrected imaging condition as the probe imaging condition 23a.

  Then, the imaging condition setting unit 26a sets a multi-slice data collection range based on the upper end position and the lower end position of the heart specified from the maximum FOV volume data (step S206). FIG. 11 is a diagram for explaining an example of a method for setting the collection range of multi-slice data according to the first embodiment. For example, as shown in the example of FIG. 11, the imaging condition setting unit 26a offsets the L1 in the head direction from the upper end position of the heart and the offset in the foot direction from the lower end position of the heart. A range determined by the position where L2 is taken is set.

  Returning to FIG. 3, the sequence control unit 10 executes a scan for positioning the basic cross-sectional image of the heart (step S105).

  In step S105, the sequence control unit 10 collects multi-slice data according to the collection range set in step S206. In the first embodiment, the sequence control unit 10 collects multi-slice data while synchronizing with an electrocardiogram signal. That is, the sequence controller 10 applies an excitation pulse using an electrocardiogram signal as a trigger signal, and performs an operation of collecting MR data for one slice for a plurality of slices. In this case, it is desirable that the sequence control unit 10 finishes collecting MR data for one slice within one heartbeat cycle (for example, 1RR). Further, the sequence control unit 10 desirably collects each slice with the same delay time from the trigger signal (for example, R wave).

  Next, the image generation unit 22 generates volume data by reconstructing a plurality of axial images along the body axis direction of the subject P from the multi-slice data. For example, the volume data is a group of 20 axial images. The image generation unit 22 performs isotropic processing on the volume data (interpolation processing performed so that each of the three directions x, y, and z is equidistant), and then provides it to the subsequent processing. May be. Alternatively, the image generation unit 22 may provide volume data that is not subjected to isotropic processing for subsequent processing.

  Subsequently, the imaging condition setting unit 26a detects cross-sectional positions of a plurality of types of basic cross-sectional images from the volume data, and generates and displays a plurality of types of basic cross-sectional images from the volume data according to the detected positions. . The cross-sectional position of the basic cross-sectional image is a spatial position of the basic cross-sectional image in the three-dimensional image space, and is represented by a parameter that can uniquely identify the basic cross-sectional image from the volume data. For example, the parameter is represented by a central coordinate point (for example, the center of the left ventricle) of the basic cross-sectional image and two vectors (for example, a short axis and a long axis) on the basic cross-sectional image. In addition, the plurality of types of basic cross-sectional images generated here are generated as positioning images of images collected in the subsequent imaging scan.

  Subsequently, the imaging condition setting unit 26a accepts the setting of the basic cross-sectional image from the operator on the basic cross-sectional image, and when the setting of all the basic cross-sectional images is completed, the process proceeds to step S106 in FIG. The operator browses the displayed basic cross-sectional image, confirms whether or not an appropriate basic cross-sectional image is set as an image collected by the imaging scan, and adjusts the position of the basic cross-sectional image as necessary. To do. At this time, for example, the imaging condition setting unit 26 a stores information indicating the set or adjusted cross-sectional position of the basic cross-sectional image in the storage unit 23.

  Returning to FIG. 3, when the execution of a series of preparation scans is completed in this manner, the sequence control unit 10 continues to execute the imaging scan (step S106). In the following, a case where data collection is performed in a plurality of segments in an imaging scan will be described as an example.

  Although there is a slight difference between the body motion correction method and the body motion trigger method, in the first embodiment, the sequence control unit 10 combines the imaging conditions set in step S205 immediately before executing the main scan. Based on (the direction of the application region R1 and the application region R2, the slice thickness, and the length in the reading direction of the application region P1 and the application region P2), a trace scan is executed to detect the position of the apex of the diaphragm (step S107). ).

  Here, the combination of the imaging conditions set in step S205 is a condition for performing a trace scan such that the edge detection accuracy exceeds a predetermined reference. Therefore, in step S107, the sequence control unit 10 can detect the position of the apex of the diaphragm with high accuracy. As a result, the movement of the diaphragm can be detected with high accuracy.

  Further, since the operator can save the trouble of setting the imaging conditions when performing the tray scan, the inspection throughput is improved.

  In addition, before the operator performs a trace scan, the scanning conditions are variously changed on a trial basis and the trace scan is performed, and the detection accuracy of the edge is set to a predetermined value without taking the trouble of searching for an optimal imaging condition. Imaging conditions that exceed the standard can be automatically set.

  Then, the sequence control unit 10 determines whether or not the position of the apex of the diaphragm is within the threshold range (step S108). When the position of the apex of the diaphragm is within the threshold range (step S108; Yes), the sequence control unit 10 continues to execute the main scan (step S109). If the position of the apex of the diaphragm is not within the threshold range (step S108; No), the sequence control unit 10 returns to the execution of the trace scan again. Then, the sequence control unit 10 determines whether or not there is a next segment (step S110). If there is a next segment (step S110; Yes), the sequence control unit 10 returns to the execution of the trace scan again. On the other hand, if there is no next segment (step S110; No), the process is terminated.

  The MRI apparatus 100 according to the first embodiment has been described above. According to the MRI apparatus 100, as described above, the movement of the diaphragm can be detected with high accuracy.

  Note that the MRI apparatus 100 according to the first embodiment calculates the slice thickness when the volume of the region R3 becomes a “predetermined volume value” after calculating the orientations of the application region R1 and the application region R2. This is an effective method when the degree of freedom in the direction of the application region R1 and the application region R2 is limited for some reason. For example, if the heart and liver (diaphragm) are close to each other, or if it is empirically known that the excitation pulse should be applied to the spinal fluid flowing through the spinal canal and the signal should be dropped, the direction of the excitation pulse It is effective because it is determined.

(Second Embodiment)
In the first embodiment, as described above, the case where the slice thickness is calculated so that the volume of the region R3 becomes the “predetermined volume value” after setting the directions of the application region R1 and the application region R2 has been described. . However, the MRI apparatus sets the slice thickness of the application region R1 and the application region R2 to the slice thickness indicated by the imaging condition included in the probe imaging condition 23a in advance, and the volume of the region R3 becomes the “predetermined volume value”. As described above, the directions of the application region R1 and the application region R2 may be calculated. Such an embodiment will be described as a second embodiment.

  FIG. 12 is a flowchart showing the process in step S104 in the second embodiment. The MRI apparatus according to the second embodiment is different from the MRI apparatus 100 according to the first embodiment in that the processes of steps S301 to S303 are executed instead of the processes of steps S203 to S205. Therefore, such different points will be described, and the same processing and configuration may be denoted by the same reference numerals and description thereof may be omitted.

  Steps S201, S202, and S206 are the same processes as those in the first embodiment, and a description thereof will be omitted.

  The imaging condition setting unit 26a calculates the direction of the application region R1 (step S301). For example, if the position P1 of the liver apex and the heart region H2 are detected in step S201, the imaging condition setting unit 26a does not include the heart region H2, and the liver is located in the center portion. The direction of the application region R1 when the application region R1 is set so as to include the vertex position P1 is calculated. Here, the size of the application region R1 in which the orientation is calculated is a size based on the imaging condition included in the probe imaging condition 23a acquired in step S202. For example, when the region (for example, a two-dimensional region) on the axial section of the heart region H2 is a region as shown in the example of FIG. 9A, the imaging condition setting unit 26a sets the head-foot direction. , The orientation of the application region R1 when the application region R1 is set so that the region H2 is not included in the axial section and the position P1 of the apex of the liver is included in the central portion is calculated. .

  If the position of the large blood vessel or the spinal cord is further detected in step S201, the imaging condition setting unit 26a further includes the spinal cord so that the position of the large blood vessel is not included in step S301. As described above, the direction of the application region R1 when the application region R1 is set may be calculated.

  Then, the imaging condition setting unit 26a calculates the direction of the application region R2 when the volume of the region R3 becomes the “predetermined volume value” (step S302). Note that the size of the application region R2 for which the orientation is calculated is also a size based on the imaging condition included in the probe imaging condition 23a acquired in step S202. An example of a method for calculating the direction of the application region R2 will be described.

  For example, the imaging condition setting unit 26a calculates the direction α of the application region R2 when the volume of the region R3 is “a predetermined volume value” by calculating the angle α that satisfies the above-described formula (2). .

  In the second embodiment, in Expression (2), “V” is a “predetermined volume value” included in the probe imaging condition 23a acquired in step S202. In Expression (2), “L” is the length in the reading direction of the application region P1 and the application region P2 included in the probe imaging condition 23a acquired in step S202 (the length in the reading direction of the region R3). . In Expression (2), “A” is the slice thickness of the application region P1 and the application region P2 included in the probe imaging condition 23a acquired in step S202.

  That is, the imaging condition setting unit 26a calculates the angle α from Equation (2) using “V”, “A”, and “L” whose values are known. Then, the imaging condition setting unit 26a calculates the direction of the application region R2 when the application region R2 is set in the direction of the angle α with respect to the direction of the direction of the application region R1. At this time, the imaging condition setting unit 26a determines the direction of the application region R2 when the application region R2 is set so that the heart region is not included and the apex position P1 of the liver is included in the central portion. Is calculated. For example, when the region on the axial cross section of the heart region H2 is a region as shown in the example of FIG. 9A, the imaging condition setting unit 26a The direction of the application region R2 is calculated when the application region R2 is set so that the region H2 is not included, and the position P1 of the apex of the liver is included in the central portion.

  The imaging condition setting unit 26a then calculates the orientations of the application region R1 and the application region R2, the slice thicknesses of the application region P1 and the application region P2 included in the probe imaging condition 23a acquired in step S202, and the length in the readout direction. Is set as the probe imaging condition 23a (step S303).

  In step S303, the imaging condition setting unit 26a may display the set imaging conditions on the GUI displayed on the display unit 25 to allow the operator to confirm. Furthermore, the imaging condition setting unit 26a may accept correction of the displayed imaging conditions by the operator. When the displayed imaging condition is corrected, the imaging condition setting unit 26a sets the corrected imaging condition as the probe imaging condition 23a.

  Thereafter, in S107, immediately before executing the main scan, the sequence control unit 10 executes a trace scan based on the imaging conditions set in step S303 to detect the position of the apex of the diaphragm.

  Here, the imaging conditions set in step S303 are conditions for performing a trace scan such that the edge detection accuracy exceeds a predetermined reference. Therefore, in step S107, the sequence control unit 10 can detect the position of the apex of the diaphragm with high accuracy. As a result, the movement of the diaphragm can be detected with high accuracy.

  In addition, after calculating the direction of the application region R1, the case where the direction of the application region R2 is calculated when the volume of the region R3 becomes the “predetermined volume value” has been described. The direction of the application region R1 when the volume of the region R3 becomes a “predetermined volume value” may be calculated.

  The MRI apparatus according to the second embodiment has been described above. According to the MRI apparatus according to the second embodiment, as described above, the movement of the diaphragm can be detected with high accuracy.

  As described above, the MRI apparatus according to the second embodiment uses the slice thicknesses of the application region R1 and the application region R2 as the slice thickness indicated by the imaging conditions included in the probe imaging condition 23a in advance. The directions of the application region R1 and the application region R2 are calculated so that the volume of R3 becomes a “predetermined volume value”. This is an effective method when the degree of freedom of the slice thickness of the application region R1 and the application region R2 is limited for some reason.

(Third embodiment)
In the first embodiment, a case where the slice thickness A is calculated when the volume of the region R3 becomes “a predetermined volume value” will be described. In the second embodiment, the volume of the region R3 is “a predetermined volume value”. However, the embodiment is not limited to this, but the direction of the application region R1 or the application region R2 is calculated. For example, according to the setting by the operator, the process of calculating the slice thickness A when the volume of the region R3 is “predetermined volume value” and the application when the volume of the region R3 is “predetermined volume value” The processing for calculating the direction of the region R1 or the application region R2 can be switched. For example, it is possible to switch to a process that the operator wants to preferentially calculate among these two processes. Such an embodiment will be described as a third embodiment.

  FIG. 13 is a flowchart showing the processing in step S104 in the third embodiment. Compared to the MRI apparatus 100 according to the first embodiment, the MRI apparatus according to the third embodiment executes the process of step 401 after step 202 and performs steps S301 to S303 in the second embodiment. The difference is that this process is also executed. Therefore, such different points will be described, and the same processing and configuration may be denoted by the same reference numerals and description thereof may be omitted.

  In step S401 following step S202, the imaging condition setting unit 26a determines whether or not the value of the switching flag stored in the storage unit 23 is “1”.

  The switching flag will be described. When the operator wants the MRI apparatus to calculate the slice thickness A when the volume of the region R3 is the “predetermined volume value”, the switch flag has a predetermined value, for example, “1” Is set. In addition, when the operator wants the MRI apparatus to calculate the direction of the application region R1 or the application region R2 when the volume of the region R3 is “predetermined volume value”, the switching flag is set by the operator A predetermined value, for example, “0” is set. That is, the operator can set the slice thickness A and the direction of the application region R1 or the application region R2 to be preferentially calculated by setting a predetermined value in the switching flag. That is, it can be said that the value of the switching flag represents the specified content specified by the operator.

  When it is determined that the value of the switching flag is “1” (step S401; Yes), the imaging condition setting unit 26a executes steps S203 to 206 as in the first embodiment.

  On the other hand, when it is determined that the value of the switching flag is not “1”, that is, when it is determined that the value of the switching flag is “0” (step S401; No), the imaging condition setting unit 26a performs the second operation. As in the embodiment, steps S301 to S303 and 206 are executed.

  Therefore, according to the MRI apparatus according to the third embodiment, the operator can set the slice thickness A and the orientation of the application region R1 or the application region R2 to be preferentially calculated.

  Thereafter, in S107, immediately before executing the main scan, the sequence control unit 10 executes a trace scan based on the various conditions set in step S205 or S303 to detect the position of the apex of the diaphragm.

  Here, the various conditions set in step S205 or S303 are conditions for performing a trace scan such that the edge detection accuracy exceeds a predetermined reference. Therefore, in step S107, the sequence control unit 10 can detect the position of the apex of the diaphragm with high accuracy. As a result, the movement of the diaphragm can be detected with high accuracy.

  The MRI apparatus according to the third embodiment has been described above. According to the MRI apparatus according to the third embodiment, as described above, the movement of the diaphragm can be detected with high accuracy.

(Fourth embodiment)
The MRI apparatus according to the embodiment generates a plurality of combinations of imaging conditions of the slice thickness A, the direction of the application region R1, and the direction of the application region R2, and the combination selected by the operator from the generated plurality of combinations Trace scanning may be executed under the imaging conditions indicated by. Such an embodiment will be described as a fourth embodiment. The direction and slice thickness of the application region R1 are examples of parameters related to the application region R1, and the direction and slice thickness of the application region R2 are examples of parameters related to the application region R2.

  FIG. 14 is a flowchart showing the processing in step S104 in the fourth embodiment. The MRI apparatus according to the fourth embodiment is different from the MRI apparatus 100 according to the first embodiment in that the processes of steps S501 to S506 are executed instead of the processes of steps S203 to S205. Therefore, such different points will be described, and the same processing and configuration may be denoted by the same reference numerals and description thereof may be omitted.

  Steps S201, S202, and S206 are the same processes as those in the first embodiment, and a description thereof will be omitted.

  The imaging condition setting unit 26a changes only the size of the slice thickness A among the slice thickness A, the direction of the application region R1, and the direction of the application region R2 indicated by the combination of the imaging conditions included in the probe imaging condition 23a. Thus, a plurality of combinations of imaging conditions are generated (step S501). Not limited to this, in step S501, the imaging condition setting unit 26a changes at least one of the slice thickness A, the direction of the application region R1, and the direction of the application region R2 indicated by the combination of the imaging conditions. Thus, a plurality of combinations of imaging conditions may be generated.

  Then, the imaging condition setting unit 26a performs a trace scan under the imaging conditions indicated by each of the plurality of combinations (Step S502).

  Then, the imaging condition setting unit 26a detects the SNR of the MR data obtained from the region R3 obtained by the trace scan and the edge between the lung field and the liver detected by performing one-dimensional Fourier transform on the MR data. Is measured for each combination of imaging conditions (step S503).

  Then, the imaging condition setting unit 26a displays the SNR and the edge strength on the display unit 25 for each combination of imaging conditions (step S504). FIG. 15 is a diagram illustrating an example of a display example according to the fourth embodiment. For example, as illustrated in the example of FIG. 15, the imaging condition setting unit 26a includes the slice thickness A indicated by the combination of imaging conditions included in the probe imaging condition 23a, the direction of the application region R1, and the direction of the application region R2. Only the slice thickness A whose size is changed is displayed on the display unit 25 in association with the SNR and the edge strength. At this time, the imaging condition setting unit 26a displays the slice thickness in a selectable manner. From the display content shown in the example of FIG. 15, the tendency of changes in SNR and edge strength depending on the slice thickness is known.

  Then, the imaging condition setting unit 26a determines whether or not the operator has selected a slice thickness via the input unit 24 (step S505). When it is determined that the slice thickness is not selected (step S505; No), the imaging condition setting unit 26a determines again whether the slice thickness is selected. On the other hand, when it is determined that the slice thickness has been selected (step S505; Yes), the imaging condition setting unit 26a selects a combination of imaging conditions including the selected slice thickness among a plurality of combinations of the generated imaging conditions. The probe imaging condition 23a is set (step S506).

  Thereafter, in S107, immediately before executing the main scan, the sequence control unit 10 executes a trace scan based on the various conditions set in step S506 to detect the position of the apex of the diaphragm.

  Here, when the various conditions set in step S506 are conditions for performing a trace scan such that the edge detection accuracy exceeds a predetermined reference, in step S107, the sequence control unit 10 determines the accuracy. The position of the apex of the diaphragm can be detected well. As a result, the movement of the diaphragm can be detected with high accuracy.

  The MRI apparatus according to the fourth embodiment has been described above. The MRI apparatus according to the fourth embodiment can detect the movement of the diaphragm with high accuracy as described above.

(Other embodiments)
The embodiment is not limited to the above-described first to fourth embodiments.

(Target part)
In the first to fourth embodiments described above, the “heart” is described as an example of the target site, but the embodiment is not limited to this. For example, the present invention can be similarly applied to the inspection of other target parts such as an internal organ that moves by respiratory motion such as “liver”, and various circulatory organs.

  According to the magnetic resonance imaging apparatus of at least one embodiment described above, it is possible to accurately detect the movement of a part such as the diaphragm.

  Although several embodiments of the present invention have been described, these embodiments are presented by way of example and are not intended to limit the scope of the invention. These embodiments can be implemented in various other forms, and various omissions, replacements, and changes can be made without departing from the spirit of the invention. These embodiments and their modifications are included in the scope and gist of the invention, and are also included in the invention described in the claims and the equivalents thereof.

26a Imaging condition setting unit 100 Magnetic resonance imaging apparatus

Claims (6)

A first application region to which the excitation pulse is applied, and the refocus pulse so that a volume of a region to which both the excitation pulse and the refocusing pulse for detecting the respiratory time phase are applied has a predetermined volume value; A setting unit for setting a second application region to which is applied;
First imaging for detecting a respiratory time phase based on first imaging data obtained from the region while applying the excitation pulse and the refocusing pulse to the first application region and the second application region, A control unit that executes second imaging for collecting second imaging data in a range including a target based on the respiratory time phase obtained by the first imaging;
A magnetic resonance imaging apparatus comprising:   The said setting part sets the direction and thickness of a said 1st application area | region, and the direction and thickness of a said 2nd application area | region so that the volume of the said area | region may become a predetermined volume value. Magnetic resonance imaging device.   The setting unit calculates the direction of the first application region and the direction of the second application region, and then calculates the thickness of the first application region and the second value so that the volume of the region becomes a predetermined volume value. The magnetic resonance imaging apparatus according to claim 2, wherein the first application area and the second application area are set by calculating a thickness of the application area.   The setting unit calculates the direction of the first application area and the direction of the second application area so that the volume of the area becomes a predetermined volume value, thereby the first application area and the second application area. The magnetic resonance imaging apparatus according to claim 2, wherein an area is set.   The setting unit calculates a direction of the first application area and a direction of the second application area according to the designation content designated by the operator, and then the volume of the area becomes a predetermined volume value. The thickness of the first application area and the thickness of the second application area are calculated, or the direction of the first application area and the second application area are set so that the volume of the area becomes a predetermined volume value. The magnetic resonance imaging apparatus according to claim 1, wherein the first application region and the second application region are set by calculating a direction of the magnetic field. First application region to which the excitation pulse is applied for imaging for detecting the respiratory phase based on imaging data obtained from the region to which both the excitation pulse and the refocus pulse for detecting the respiratory phase are applied A control unit that executes each of a plurality of combinations of imaging conditions in which at least one of the first parameter relating to the second parameter relating to the second application region to which the refocusing pulse is applied differs
The characteristics of the imaging data obtained by each of the plurality of combinations are displayed on the display unit so that the operator can select any of the plurality of combinations, and the first parameter corresponding to the combination selected by the operator And a setting unit that sets the second parameter as an imaging condition in the imaging,
A magnetic resonance imaging apparatus comprising:

Images