WO2016170863A1

WO2016170863A1 - Magnetic resonance imaging device and magnetic resonance imaging method

Info

Publication number: WO2016170863A1
Application number: PCT/JP2016/057310
Authority: WO
Inventors: 延之吉澤; 板垣　博幸
Original assignee: 株式会社日立製作所
Priority date: 2015-04-22
Filing date: 2016-03-09
Publication date: 2016-10-27
Also published as: JPWO2016170863A1; JP6378426B2

Abstract

Through the present invention, BSI data are acquired during open time (in which an RF pulse or gradient magnetic field is not applied) of an ASL image acquisition sequence, in order to acquire a hemodynamic image of blood flowing in and a hemodynamic image of blood flowing out of the same region, or other information of the region, in a short time and without positional misalignment. At this time, BSI data acquired in open time at the time of acquisition of a control image in an ASL image acquisition sequence are disposed in a region of lower spatial frequency in k space than BSI data acquired in open time at the time of acquisition of a label image, and, in open time when each image is acquired, the BSI data are disposed in the region of low spatial frequency in k space to the degree that the data are acquired at a timing at which the effect of a pre-pulse is small.

Description

Magnetic resonance imaging apparatus and magnetic resonance imaging method

The present invention relates to a Magnetic Resonance Imaging (hereinafter referred to as MRI) technique, and particularly to a technique for depicting hemodynamics.

An MRI apparatus is a measurement apparatus that obtains an image of a subject using a nuclear magnetic resonance (NMR) phenomenon, and irradiates a subject with a high-frequency magnetic field (hereinafter referred to as RF) pulse, and in response, Measure NMR signals generated by the nuclear spins that make up the tissue. Based on the measured NMR signal, the form and function of the subject's head, abdomen, limbs, etc. are imaged two-dimensionally or three-dimensionally. At the time of imaging, the NMR signal is given different phase encoding and slice encoding by the gradient magnetic field, and frequency encoding is given to the NMR signal, which is measured as time series data. The measured NMR signal is reconstructed into an image by two-dimensional or three-dimensional Fourier transform.

In an MRI apparatus, there is imaging that displays hemodynamics based on the difference between an image labeled with a blood proton (label image) and an image not labeled (control image) (see, for example, Patent Document 1 and Patent Document 2). By these methods, a perfusion image can be obtained without contrast. This perfusion image is generally called an ArterialerSpin Labeling Perfusion (ASL Perfusion; ASL) image. Note that a blood vessel image can be obtained by photographing at the timing before the labeled / controlled blood proton reaches the perfusion region by the method disclosed in Patent Document 1 or Patent Document 2.

On the other hand, there is a technique for rendering veins using absolute value images and phase images. Among them, there is a method of drawing a vein by creating a phase mask from a phase image and applying the phase mask to the absolute value image (see, for example, Patent Document 3 and Non-Patent Document 1). Various methods for creating a phase mask have been proposed. This vein rendering method is called Susceptibility / Weighted / Imaging (SWI) or Blood / Sensitivity / Imaging (BSI).

Also, as in Non-Patent Document 2, there is a technique for obtaining a quantitative susceptibility map (QSM) from an absolute value image and a phase image. In addition, there is a technique for determining brain oxygen uptake rate (OEF) from QSM.

US Patent No. 5846197 U.S. Pat. US Pat. No. 6,658,280

Based on the ASL image and BSI / QSM / OEF (hereinafter referred to as BSI) images, the hemodynamics of blood (arteries) flowing into the same site and the blood (venouss) flowing out, or other Information. Usually, both images are generated from data acquired separately. In this case, in the comparison, misalignment between images due to separate acquisition of ASL data and BSI data becomes a problem. In addition, since the shooting is performed separately, the shooting time becomes longer.

The present invention has been made in view of the above circumstances, and acquires a hemodynamic image of blood flowing into the same part and a hemodynamic image of blood flowing out or other information of the part in a short time without misalignment. It aims at providing the technology to do.

∙ Acquire BSI data in the idle time of the ASL image acquisition sequence (time to apply no RF pulse or gradient magnetic field). At this time, the BSI data acquired in the free time at the time of acquiring the control image of the ASL image acquisition sequence is arranged in the low spatial frequency region of k space from the BSI data acquired in the free time at the time of acquiring the label image. Moreover, in the idle time at the time of each image acquisition, the data acquired at the timing with less influence of the pre-pulse is arranged in the low spatial frequency region of the k space.

According to the present invention, the hemodynamic image of blood flowing into the same part and the hemodynamic image of blood flowing out or other information on the part can be acquired in a short time without positional deviation.

Configuration diagram of the MRI apparatus of the first embodiment (a) Sequence diagram of a general ASL sequence (b) is an explanatory diagram for explaining the free time of an ASL sequence (a) and (b) are explanatory diagrams for explaining the PLD. (a) is a sequence diagram of a data acquisition sequence example in the ASL sequence of the first embodiment, (b) is a sequence diagram of a BSI sequence example of the first embodiment Functional block diagram of the overall control unit of the first embodiment Explanatory drawing for demonstrating the imaging condition reception screen example of 1st embodiment (a) is an explanatory diagram for explaining the BSI sequence adjustment method of the first embodiment, (b) is an explanatory diagram for explaining a specific data acquisition order Explanatory diagram for explaining an example of combination of ASL and BSI shooting methods Explanatory drawing for demonstrating the example of an imaging condition reception screen of 2nd embodiment Functional block diagram of the overall control unit of the third embodiment Functional block diagram of the overall control unit of a modification of the third embodiment

<< First Embodiment >>
Hereinafter, a first embodiment of the present invention will be described. Hereinafter, in all the drawings for explaining the embodiments of the present invention, those having the same function are denoted by the same reference numerals unless otherwise specified, and repeated explanation thereof is omitted.

[Configuration of MRI system]
FIG. 1 is a configuration diagram of the MRI apparatus 100 of the present embodiment. The MRI apparatus 100 obtains a tomographic image of the subject 101 using the NMR phenomenon. As shown in the figure, the MRI apparatus 100 of the present embodiment includes a static magnetic field generating magnet 102 that generates a static magnetic field around a subject 101, a gradient magnetic field coil 103 that generates a gradient magnetic field in the space, and this region Transmitting RF coil (transmitting coil) 104 that irradiates a high-frequency magnetic field, RF probe (receiving coil) 105 that detects an MR signal generated by the subject 101, signal detection unit 106, signal processing unit 107, and overall control Unit 108, gradient magnetic field power source 109, RF transmission unit 110, subject 101, bed 112 for moving subject 101 in and out of static magnetic field generating magnet 102, display / operation unit 113, Is provided.

The static magnetic field generating magnet 102 generates a uniform static magnetic field in the direction perpendicular to the body axis of the subject 101 in the vertical magnetic field method and in the body axis direction in the horizontal magnetic field method. Permanent magnet type, normal conducting type or superconducting type static magnetic field generating source arranged around the.

The gradient magnetic field coil 103 is composed of gradient magnetic field coils wound in the three-axis directions of X, Y, and Z that are the real space coordinate system (stationary coordinate system) of the MRI apparatus 100. Each gradient coil is connected to a gradient magnetic field power source 109 that drives the gradient coil, and generates a gradient magnetic field according to a current (signal) supplied via the gradient magnetic field power source 109. Specifically, the gradient magnetic field power supply 109 of each gradient coil is driven in accordance with a command from the overall control unit 108 described later, and supplies current to each gradient coil. Thereby, gradient magnetic fields Gx, Gy, and Gz are generated in the three axial directions of X, Y, and Z.

When imaging a two-dimensional slice plane, a slice gradient magnetic field pulse (Gs) is applied in a direction orthogonal to the slice plane (imaging cross section) to set a slice plane for the subject 101, orthogonal to the slice plane and orthogonal to each other. The phase encoding gradient magnetic field pulse (Gp) and the frequency encoding (lead-out) gradient magnetic field pulse (Gf) are applied in the remaining two directions, and position information in each direction is encoded in the echo signal.

The transmission coil 104 is a coil that irradiates the subject 101 with a high-frequency magnetic field (RF) pulse, is connected to the RF transmission unit 110, and applies an RF pulse to the subject 101 in accordance with the high-frequency pulse current supplied from the RF transmission unit 110. Irradiate. As a result, an NMR phenomenon is induced in the nuclear spins of the atoms constituting the biological tissue of the subject 101. Specifically, the RF transmission unit 110 is driven in accordance with a command from the overall control unit 108 to be described later, the high frequency pulse is amplitude-modulated and amplified, and then the transmission RF coil 104 disposed in the vicinity of the subject 101 is disposed. , The subject 101 is irradiated with an RF pulse.

The receiving coil 105 is a coil that receives an NMR signal (echo signal) emitted by the NMR phenomenon of the nuclear spin constituting the living tissue of the subject 101, and is connected to the signal detection unit 106. The echo signal received by the reception coil 105 is sent to the signal detection unit 106.

The signal detection unit 106 performs processing for detecting an echo signal received by the reception coil 105. Specifically, an echo signal of the response of the subject 101 induced by the RF pulse irradiated from the RF coil 104 is received by the reception RF coil 105 disposed in the vicinity of the subject 101, and an overall control unit described later In accordance with a command from 108, the signal detection unit 106 amplifies the received echo signal, divides the signal into two orthogonal signals by quadrature detection, and samples a predetermined number (for example, 128, 256, 512, etc.). Each sampling signal is A / D converted to a digital quantity and sent to a signal processing unit 107 described later. Therefore, the echo signal is obtained as time-series digital data (hereinafter referred to as echo data) composed of a predetermined number of sampling data.

The signal processing unit 107 performs various processes on the echo data, and sends the processed echo data to the overall control unit 108.

The overall control unit 108 controls various data processing and display and storage of processing results, and has a CPU and a memory. Further, a storage device 115 such as an optical disk or a magnetic disk is provided.

Specifically, echo data collection is performed by controlling each unit, and when echo data is input, it is stored in an area corresponding to the k space of the memory based on the encoding information applied to the echo data. . A group of echo data stored in an area corresponding to the k space of the memory is also referred to as k space data. Then, the overall control unit 108 performs processing such as signal processing and image reconstruction by Fourier transform on the k-space data, and the resulting image of the subject 101 is displayed on the display / operation unit 113 described later. It is displayed and recorded in the storage device 115.

Note that the overall control unit 108 may be constructed on an information processing apparatus independent of the MRI apparatus 100.

The display / operation unit 113 includes a display unit that displays an image of the reconstructed subject 101, a trackball or a mouse that inputs various control information of the MRI apparatus 100 and control information of processing performed by the overall control unit 108, and And an operation unit such as a keyboard. The operation unit is disposed in the vicinity of the display unit, and the operator controls various processes of the MRI apparatus 100 interactively through the operation unit while looking at the display unit.

Each function of the overall control unit 108 of the present embodiment includes a CPU, a memory, and a storage device, and is realized by the CPU loading a program stored in the storage device in advance into the memory and executing it. All or some of the functions may be realized by hardware such as ASIC (Application Specific Integrated Circuit) and FPGA (field.-programmable gate array). In addition, various data used for processing of each function and various data generated during the processing are stored in the storage device 115.

In FIG. 1, the transmission coil 104 and the gradient magnetic field coil 103 are opposed to the subject 101 in the static magnetic field space of the static magnetic field generating magnet 102 into which the subject 101 is inserted, in the case of the vertical magnetic field method, If the horizontal magnetic field method is used, the object 101 is installed so as to surround it. The receiving coil 105 is installed so as to face or surround the subject 101.

Generally, the imaging target of the MRI apparatus 100 is the main constituent substance of the subject, proton. The MRI system 100 can visualize the shape or function of the human head, abdomen, extremities, etc. in two or three dimensions by imaging the spatial distribution of proton density and the relaxation phenomenon of excited protons. Take a picture.

The imaging method using the MRI apparatus 100 will be described. Different phase encodings are given depending on the gradient magnetic field, and echo signals obtained by the respective phase encodings are detected. As the number of phase encodings, values such as 128, 256, and 512 are usually selected per image. Each echo signal is usually obtained as a time-series signal composed of 128, 256, 512, and 1024 sampling data.

The MRI apparatus 100 creates a single MR image by performing Fourier transform (hereinafter referred to as FT) on these data, performs various analyzes, and presents the results to the user. The analysis performed by the MRI apparatus 100 includes, for example, temperature measurement of a subject. In some cases, pre-pulses having various effects are applied prior to the imaging.

In the present embodiment, in this MRI apparatus 100, a first pulse sequence for acquiring data for generating an inflow kinetic image that is a dynamic image of blood flowing into a predetermined site, and a pre- And a second pulse sequence for acquiring data for generating the defined information. At this time, the second pulse sequence is executed in a free time within the repetition time of the first pulse sequence. Then, the execution of the second pulse sequence is controlled so that the data acquired in the second pulse sequence minimizes the influence of the first pulse sequence.

Hereinafter, in the present embodiment, the imaging sequence for acquiring BSI data as the second pulse sequence is used as the first pulse sequence by using an imaging sequence by ASL Perfusion that acquires ASL data (hereinafter, ASL sequence). A case where a sequence (BSI sequence) is used will be described as an example. That is, in the present embodiment, the BSI sequence is executed during the free time of the ASL sequence for acquiring ASL data. When the imaging conditions for each pulse sequence are set, the BSI sequence parameters executed in each idle time are adjusted using the imaging conditions.

First, the outline of ASL sequence and BSI sequence will be explained.

[ASL sequence]
FIG. 2 (a) shows an RF pulse application timing chart as an example of the ASL sequence 300. FIG. As shown in the figure, in the first pulse sequence (ASL sequence 300), after applying a labeling pulse (label RF pulse) 311 as a pre-pulse, a predetermined time (waiting time PLD (post labeling delay)) 313 is set. Data collection (ASL data acquisition) 312, labeling sequence 310, executed after (preferably immediately after) labeling sequence 310, a predetermined time (PLD) after applying control pulse (control RF pulse) 321 as a pre-pulse 323 to collect data (ASL data acquisition) 322, and a control sequence 320.

In the ASL sequence 300, the labeling sequence 310 and the control sequence 320 are alternately executed at each repetition time interval TR.

The labeling pulse 311 is a pulse for labeling blood protons (reversed with respect to the direction of the static magnetic field), and the control pulse 321 does not substantially label the blood protons, and the MT effect is applied to the labeling pulse 311 application state. This is a pulse for aligning.

As shown in FIGS. 3A and 3B, the labeling pulse 311 is applied to the labeling pulse application region 610. When the blood labeled by the labeling pulse 311 reaches the perfusion region, data at the slice position 620 is acquired.

The waiting times PLD313 and 323 are times until the labeled / controlled blood protons flow into the imaging slice, and are generally input by the user for imaging. However, as shown in FIGS. 3 (a) and 3 (b), the

PLDs

313 and 323 vary depending on the distance Dis between the labeling pulse application region 610 and the slice position 620 or the blood flow velocity of the subject 101. . Therefore, the PLD may be determined by the system in consideration of such information. Note that the PLD 313 and the PLD 323 have the same length.

FIG. 4 (a) shows a typical pulse sequence 340 used as a sequence (data acquisition sequence) executed during the period of

ASL data acquisition

312 and 322. As the data acquisition sequence 340, for example, as shown in FIG. 4 (a), an EPI pulse sequence is used in addition to an SE pulse sequence. In this figure, RF, Gs, Gp, and Gf indicate application axes of the RF pulse, slice selection gradient magnetic field pulse, phase encode gradient magnetic field pulse, and frequency encode gradient magnetic field pulse, respectively. This pulse sequence 340 is executed for the number of slices determined by the imaging conditions.

2A illustrates a pulse sequence in the case of acquiring data by 2D multi-slice, but of course, a pulse sequence capable of acquiring data by 3D may be used as the data acquisition sequence.

Note that the ASL perfusion image is obtained by the difference between the label image obtained from the labeling sequence 310 and the control image obtained from the control sequence 320.

[BSI sequence]
For the BSI sequence 400 for acquiring BSI data, for example, a 3D Gradient Echo EPI sequence shown in FIG. 4B is used. Here, as an example, a 3D RF spoiled SSFP (RF-Spoiled Steady State Free Precession) sequence is shown. The case where the number of echo trains is 5 is illustrated. Also in this figure, RF, Gs, Gp, and Gf indicate application axes of the RF pulse, slice selection gradient magnetic field pulse, phase encode gradient magnetic field pulse, and frequency encode gradient magnetic field pulse, respectively.

[Shooting Sequence of this Embodiment]
As shown in FIG. 2 (b), the ASL sequence 300 includes a plurality of (in this case, four) idle times (331, 332, 333, 334) in terms of time. The idle time 331 is the idle time in the labeling sequence 310, the time from the application of the labeling pulse 311 to the ASL data acquisition 312, and the idle time 332 is the idle time in the labeling sequence 310, which is the ASL data acquisition 312. This is the time from the end to the application of the control pulse 321. The

idle times

333 and 334 are idle times in the control sequence 320. The time from the application of the control pulse 321 to the ASL data acquisition 322 and the application of the labeling pulse 311 from the end of the ASL data acquisition 322, respectively. It is time until.

In this embodiment, the BSI sequence is executed in at least one of the four free times (331, 332, 333, 334) to acquire BSI data. This realizes simultaneous measurement of ASL and BSI.

At this time, in this embodiment, the BSI data acquired in the free time in the control sequence 320 is arranged in the low spatial frequency region of the k space from the BSI data acquired in the free time in the labeling sequence 310. Further, in the control sequence 320 and the labeling sequence 310, the BSI data acquired at a timing with less influence of the pre-pulse is arranged in the low spatial frequency region of the k space.

In order to realize this, the overall control unit 108 of the present embodiment includes an imaging condition reception unit 210, a sequence adjustment unit 220, a measurement unit 230, an image reconstruction unit 240, a display image, as shown in FIG. And a generation unit 250. Details of each part will be described below.

[Shooting condition reception unit 210]
The shooting condition reception unit 210 receives various shooting parameter settings from the user as shooting conditions. Accepted parameters are, for example, field of view FOV, repetition time TR, effective echo time TE, slice number Slice #, time interval between echo signals IET (Inter Echo Time), number of echo signals measured with one excitation ETL (echo train length), frequency encoding step number Freq #, phase encoding step number Phase #, and the like. In the present embodiment, the ASL sequence 300 and the BSI sequence 400 are accepted.

Hereinafter, among the imaging parameters, the imaging parameters for the ASL sequence 300 for acquiring the data for ASL (hereinafter referred to as ASL _Data ) are shown with the subscript _ASL , for example, TR _ASL or ETL _ASL . However, ASL Perfusion-specific parameters such as PLD are excluded. In addition, imaging parameters for the BSI sequence 400 for acquiring BSI data (hereinafter referred to as BSI _Data ) are shown with a subscript _BSI such as TR _BSI and ETL _BSI .

The imaging condition reception unit 210 of the present embodiment displays the imaging parameter reception screen on the display device of the display / operation unit 113 and receives settings via the display / operation unit 113. Note that a plurality of types of shooting parameter sets (preset parameters) may be stored in the storage device 115 in advance, the preset parameters selected by the user may be displayed, and the displayed preset parameters may be adjusted by the user.

The shooting condition reception screen 500 is shown in FIG. As shown in the figure, the shooting condition reception screen 500 of the present embodiment receives the shooting conditions of the ASL sequence 300, receives the shooting conditions of the ASL shooting condition display field 510 for displaying the received conditions, and the shooting conditions of the BSI sequence 400, And a BSI imaging condition display field 520 for displaying the accepted conditions.

In the shooting condition reception screen 500, it is desirable that the same shooting condition items are displayed side by side (corresponding to each other) in the ASL shooting condition display field 510 and the BSI shooting condition display field 520. There are photographing conditions that should be equal or multiples in both sequences. By displaying them side by side, it becomes easier to compare and compare the imaging conditions set for both sequences.

[Sequence adjustment section]
The measurement unit 230 described later basically performs measurement according to the imaging conditions received by the imaging condition reception unit 210. However, in the present embodiment, as described above, in the execution of the BSI sequence 400, the influence of the labeling pulse 311 of the ASL sequence 300 is suppressed as much as possible. In this way, the sequence adjustment unit 220 in this embodiment suppresses the influence of the labeling pulse 311 of the ASL sequence 300 in this way, the BSI sequence 400 (second pulse sequence) in each idle time (331, 332, 333, 334). ) Encoding amount and execution timing are adjusted.

The sequence adjustment unit 220 according to the present embodiment determines the number of BSI data to be acquired in each free time (331, 332, 333, 334) and the k-space arrangement position based on the shooting conditions set by the user.

That is, the sequence adjustment unit 220 of the present embodiment calculates the number of shots and the encoding amount of the BSI sequence 400 to be executed in each free time (331, 332, 333, 334) based on the shooting conditions. Then, the BSI sequence 400 is adjusted so that the data is measured with the calculated number of shots and the calculated encoding amount in each of the idle times (331, 332, 333, 334).

Here, the encoding amount to be determined is the phase encoding amount for 2D imaging, and the phase encoding amount and slice encoding amount for 3D imaging.

As described above, in the present embodiment, BSI data BSI _Data acquired in BSI sequence 400, the data BSI _Data for BSI to get

free time

333 and 334 in the control sequence 320, idle time in the labeling sequence 310 to get to 331 and 332 disposed in the low spatial frequency region of the k-space from the data BSI _data for BSI. In the control sequence 320 and the labeling sequence 310, the BSI data BSI _Data acquired at a timing with less influence of the pre-pulse is arranged in the low spatial frequency region of the k space.

The length of the idle time (331, 332, 333 and 334), respectively, represent the ASL _Lab1, ASL _Lab2, ASL _Cont1, ASL _{Cont 2,} when a period of

ASL data acquisition

312 and 322 representing the ASL _Acq, between them Have the following relations (1) and (2).

_{_{ASL Lab1 = ASL Cont1 = PLD ···}} (1)
ASL _Lab2 = ASL _Cont2 = TR _ASL -PLD-ASL _Acq・・・ (2)
TR _ASL is the repetition time of the ASL sequence 300. The ASL data acquisition period ASL _Acq is uniquely determined internally depending on the shooting conditions set by the user.

First, the sequence adjustment unit 220 first calculates the number of shots that can be executed in each free time (331, 332, 333, 334).

The number of shots that can be executed in each idle time, the length _{_{_{ASL Lab1, ASL Lab2, ASL Cont1}}} , ASL Cont2 of each idle time, respectively, divided by the repetition time TR _BSI of BSI sequence 400, determined. Here, assuming that the number of shots that can be executed in the

free times

331 and 333 is SHOT # ₁ , and the number of shots that can be executed in the

free times

332 and 334 is SHOT # ₂ , respectively, the following equations (3) and (4) It can be calculated by

SHOT # ₁ = ASL _Lab1 / TR _BSI = PLD / TR _BSI (3)
SHOT # ₂ = ASL _Lab2 / TR _BSI = (TR _ASL -PLD-ASL _Acq ) / TR _BSI (4)
Note that the number of data BSI _Data acquired in each free time (331, 332, 333, 334) can be calculated by the following equations (5) and (6). The number of data acquired in the

free times

331 and 333 is DATA # ₁ , the number of data acquired in the

free times

332 and 334 is DATA # _2, and the number of echo trains is ETL _BSI .

DATA # ₁ = SHOT # ₁ × ETL _BSI (5)
DATA # ₂ = SHOT # ₂ × ETL _BSI (6)
Next, the sequence adjustment unit 220 determines the k-space arrangement of the data BSI _Data acquired at each free time (331, 332, 333, 334). That is, the encoding amount of the data BSI _Data acquired in each free time (331, 332, 333, 334) is determined.

Since the data acquired in the

free times

331 and 332 are easily affected by labeled blood protons, it is desirable to use data in the high frequency region. On the other hand, the data acquired in the

free times

333 and 334 is not affected by the labeled blood protons, and is preferably data in a low spatial frequency region.

Also, the

idle times

331 and 333 immediately after the labeling pulse 311 and the control pulse 321 are not easily affected by the prepulse because the blood affected by the prepulse has not yet flowed into the imaging slice. Therefore, in the same labeling sequence 310 and control sequence 320, it is desirable that data having a shorter period from pre-pulse application to data acquisition be arranged in a low spatial frequency region.

Accordingly, BSI _data in the lower spatial frequency region is acquired in the order of the

idle times

333, 334, 331, and 332.

The sequence adjustment unit 220 calculates each free time (331, 332) so that it is arranged in the k space in the above order based on the number of shots that can be acquired in each free time (331, 332, 333, 334) calculated in advance. 333, 334), the encoding amount of the BSI sequence 400 to be executed is determined.

A specific example will be described with reference to FIGS. 7 (a) and 7 (b). Here, the parameters of the shooting conditions entered by the user are as follows: TR _ASL = 4000 ms, PLD = 1500 ms, ASL data acquisition period ASL _Acq = 300 ms, TR _BSI = 50 ms, echo train number ETL _BSI = 5, phase encoding step number Phase # _BSI = 384, number of slices Slice # _BSI = 40, parallel imaging double speed RAPID _BSI = 2.0.

The formula (1), the equation _{(2), ASL Lab1 = ASL} Cont1 = 1500ms, ASL Lab2 = because it is ASL _Cont2 = 2200ms, the number of shots that can be executed in the free time 331 and 333 (ASL _Lab1 and ASL _Cont1) SHOT # ₁ and SHOT # ₂ are calculated by the following equations (7) and (8) from the above equations (3) and (4), respectively.

SHOT # ₁ = 1500/50 = 30 (7)
SHOT # ₂ = 2200/50 = 44 (8)
For example, when using a 3D RF spoiled SSFP (RF-Spoiled Steady State Free Precession) sequence for the BSI sequence 400, data can be filled in the ky direction for ETL _BSI = 5 lines per shot from the above shooting conditions. . Therefore, the shot number SHOT # required to fill the kx-ky space is expressed by the following equation (9) using the total phase encoding step number Phase # _BSI and RAPID _BSI .

SHOT # = Phase # _BSI / (RAPID _BSI × ETL _BSI ) = 38.4 (9)
Since the required number of shots is 38, the sequence adjustment unit 220 determines the phase encoding amount at the time of acquiring each data of each shot so as to acquire ky = −18 to 19 by TE _BSI . It should be noted that the data for 0.4 shots that cannot be divided are desirably zero-padded, but the present invention is not limited to this.

In the kz direction, since Slice # _BSI = 40, the slice encoding amount at the time of each data acquisition is determined so that kz = −19 to 20 is acquired.

Therefore, the sequence adjustment unit 220 of the present embodiment, for example, as shown in Table 710 of FIG.7 (b), for the kz direction and the ky direction, from the free time 333 (ASL _Cont1 ), Centric (centric) The phase encoding amount and slice encoding amount of the BSI sequence 400 to be executed in each free time (331, 332, 333, 334) are determined so that BSI _data in the low spatial frequency region is acquired.

In Table 710 shown in FIG. 7B, the kz direction indicates the slice encoding step, and the kz direction indicates the center phase encoding step of the five lines. That is, first, the free time _{333 (ASL Cont1), ky =} (76,38,0, -38, -76) 5 with lines, kz = - a (14-15) slices acquired centric, After that, in the free time 334 (ASL _Cont2 ), after acquiring the remaining slices centric for 5 lines of ky = (76, 38, 0, -38, -76), ky = (75, 39, 1, Repeat the acquisition of each slice centricly for 5 lines (-37, -75).

[Measurement section]
The measurement unit 230 according to the present embodiment applies a high-frequency magnetic field pulse to a desired region of the subject 101, applies a gradient magnetic field pulse to the region, and the subject in accordance with preset imaging conditions and a pulse sequence. The nuclear magnetic resonance signal generated from the region is measured. In the present embodiment, control is performed so as to execute the first pulse sequence (ASL sequence 300) and the second pulse sequence (BSI sequence 400).

In the present embodiment, as described above, the measurement unit 230 converts the second pulse sequence (BSI sequence 400) into free time (331, 332, 333) within the repetition time of the first pulse sequence (ASL sequence 300). , 334). The BSI sequence 400 that is the second pulse sequence is executed according to the adjustment result by the sequence adjustment unit 220.

[Image reconstruction unit]
The image reconstruction unit 240 reconstructs an image from data acquired by the first pulse sequence (ASL sequence 300) and data acquired by the second pulse sequence (BSI sequence 400), respectively, according to the imaging conditions.

In this embodiment, a label image is generated from the data acquired in the labeling sequence 310 of the ASL sequence 300, and a control image is generated from the data acquired in the control sequence 320.

Also, a phase image and an absolute value image are generated from the data acquired by the BSI sequence 400.

[Display image generator]
The display image generation unit 250 generates a display image to be displayed on the display device of the display / operation unit 113 from the reconstructed image by a predetermined method.

In this embodiment, the difference between the label image and the control image is taken to generate an ASL image. In addition to the display image, various types of information are also calculated. For example, using a phase image and an absolute value image generated from data acquired by the BSI sequence 400, a vein image drawn by SWI (Susceptibility Weighted Imaging) or BSI (Blood Sensitivity Imaging), a quantitative magnetic susceptibility map (QSM) (Quantitative Susceptibility Mapping)) and information including at least one of brain oxygen uptake rate (OEF (Oxygen Extraction Fraction)) is generated.

This embodiment is characterized in that two different images are obtained in one scan and are compared. Therefore, the display image generation unit 250 of the present embodiment generates a display image so that both can be easily compared.

Here, Fig. 8 shows an example of the label / control RF pulse method, 2D / 3D (dimension), and data acquisition sequence of

ASL sequence

300, and 2D / 3D (dimension) and data acquisition sequence of BSI sequence 400. Are shown respectively.

As shown in this figure, in the ASL sequence 300, PASL, pCASL, etc. are used as the label / control method, 2D / 3D, and any of the data acquisition sequences is SE-EPI, SSFP-EPI, FSE, VRFA-FSE. Etc. can be used.

In the BSI sequence 400, the dimension is limited to 3D, but as a data acquisition sequence, RF spoiled SSFP (RF-SpoiledoilSteady State Free Precession), SSFP-EPI, or the like can be used.

In ASL sequence 300, label / control RF pulse system, 2D / 3D, and data acquisition sequence can be selected. In the BSI sequence 400, a data acquisition sequence can be selected. These selections allow simultaneous measurement in various combinations. It is desirable to select a combination suitable for clinical use.

For example, if the first pulse sequence (ASL sequence 300) is a 2D multi-slice measurement sequence and the second pulse sequence (BSI sequence 400) is a 3D measurement sequence, display image generation The unit 250 performs MPR (Multi-Planar Reconstruction) processing on the three-dimensional image data reconstructed from the data obtained by the second pulse sequence, and reconstructs the data obtained by the first pulse sequence. You may comprise so that the image of a slice position may be produced | generated as a display image.

In this case, in order to display the 3D image obtained by the BSI sequence 400 in accordance with the 2D image obtained by the ASL sequence 300, the display image generation unit 250 according to the present embodiment displays the imaging conditions (slice position and (Slice thickness) is referred to, MPR is automatically performed internally, and a BSI image is generated and displayed.

This makes it possible to display an ASL image and a BSI image with the same slice and slice thickness. Therefore, it is expected that evaluation is facilitated by displaying images side by side in visual evaluation.

If the 2D / 3D and data acquisition sequence selected for the ASL sequence 300 and the data acquisition sequence selected for the BSI sequence 400 are both 3D SSFP-EPI, they are obtained by the control sequence 320 of the ASL sequence 300. The data can also be used as data for creating BSI data.

As described above, according to the MRI apparatus 100 of the present embodiment, the application of a high-frequency magnetic field pulse to a desired region of a subject, the application of a gradient magnetic field pulse to the region, according to preset imaging conditions and a pulse sequence, And a measurement unit 230 that measures a nuclear magnetic resonance signal generated from the region of the subject, and the pulse sequence generates data for generating an inflow dynamic image that is a dynamic image of blood flowing into a predetermined site. A first pulse sequence to be acquired (ASL sequence 300), and a second pulse sequence to acquire data for generating predetermined information other than the inflow dynamic image of the part (BSI sequence 400), and The second pulse sequence (BSI sequence 400) is executed in a free time within the repetition time of the first pulse sequence (ASL sequence 300).

The first pulse sequence (ASL sequence 300) includes a labeling sequence 310 that collects data at a predetermined time after applying a labeling pulse 311 as a prepulse, and the prepulse that is executed after the labeling sequence 310. And a control sequence 320 that collects data at a predetermined time after applying the control pulse 321. The labeling sequence 310 and the control sequence 320 are alternately executed.

As described above, according to the present embodiment, the BSI sequence 400 is executed during the idle time of the ASL sequence 300 to acquire BSI data. Therefore, a hemodynamic image of blood (arteries) flowing into the brain, a hemodynamic image of blood (venouss) flowing out of the brain, a quantitative susceptibility map of the brain, and a brain oxygen uptake rate are taken once. Can be obtained at Since both data are acquired substantially simultaneously, the positional deviation between the images is less than that of the conventional method acquired separately, and the photographing time can be shortened. In addition, the clinical value is expected to identify the shape of the brain tumor.

Further, the MRI apparatus 100 of the present embodiment further includes a sequence adjustment unit 220 that adjusts the second pulse sequence (BSI sequence 400), and the first pulse sequence (ASL sequence 300) includes a plurality of idle times. (331, 332, 333, 334), and the sequence adjustment unit 220 performs the second pulse sequence (BSI) to be executed in each of the idle times (331, 332, 333, 334) based on the imaging conditions. The number of shots and the encoding amount of the sequence 400) are calculated, and the second pulse sequence (BSI sequence 400) is adjusted according to the calculation result, and the encoding amount is set to the

free times

333 and 334 in the control sequence 320. Data to be acquired is calculated so as to be arranged in a low spatial frequency region of k-space from data acquired in the

free times

331 and 332 in the labeling sequence 310. Further, the encoding amount is further calculated so that data acquired at a timing with less influence of the pre-pulse is arranged in a low spatial frequency region of k-space.

Therefore, the data acquired by the BSI sequence 400 is not easily affected by the pre-pulse (labeling pulse 311). Therefore, a high-quality BSI image can be obtained even when it is acquired in the free time.

Note that there are individual differences in the time it takes for the labeled blood to reach the reflux region. For this reason, in actual clinical practice, it is common to photograph with multiple PLDs. According to the present embodiment, in accordance with the set PLD, the sequence adjustment unit 220 changes the PLD in order to determine the number of shots and the encoding amount of the BSI sequence 400 executed in each idle time. However, the optimum BSI sequence 400 can be easily determined. Accordingly, it is possible to flexibly cope with changes in the photographing conditions.

<< Second Embodiment >>
A second embodiment of the present invention will be described. In the first embodiment, for the BSI sequence 400 that is executed during the free time of the ASL sequence 300, the encoding amount is determined so that the data acquired during the free time with little influence of the labeling pulse 311 is arranged in the low spatial frequency region. Adjust the sequence. In the present embodiment, when the ASL sequence 300 is a 2D imaging sequence, the data acquisition order of the imaging slice is also adjusted.

The MRI apparatus of the present embodiment has basically the same configuration as the MRI apparatus 100 of the first embodiment. However, as described above, since the acquisition order of the imaging slices of the ASL sequence 300 is also adjusted, the processing of the imaging condition reception unit 210 and the sequence adjustment unit 220 is different. Hereinafter, the present embodiment will be described focusing on the configuration different from the first embodiment.

Since blood follows a route called vein (BSI) from the artery through the perfusion region (ASL Perfusion), the BSI data acquired in the free time 332 may be affected by the acquisition of ASL data. Therefore, in this embodiment, in the image (BSI image) generated from the data acquired by the BSI sequence 400 to the user, which is more important is the image on the parietal side (Head side) or the image on the brain base side (Foot side). And automatically change the ASL imaging slice ordering accordingly.

That is, in the present embodiment, the first pulse sequence (ASL sequence 300) is a sequence for two-dimensional multi-slice measurement, and the second pulse sequence (BSI sequence 400) is a sequence for three-dimensional measurement. In the second pulse sequence, the imaging condition includes information (BSI image priority) for specifying a priority side with respect to the slice direction of the first pulse sequence, and the sequence adjustment unit 220 includes the first pulse sequence. The excitation frequency is further calculated, and at this time, the excitation frequency is calculated so as to be acquired first from the slice on the priority side.

For this reason, the imaging condition reception unit 210 of the present embodiment further receives the priority of the BSI image in addition to the imaging conditions received in the first embodiment. As shown in FIG. 9, in addition to the area for receiving each shooting condition, the BSI shooting condition display field 520 displays a shooting condition receiving screen 500a further including an area for specifying priority (priority specifying area) 521, Accept via this screen.

Also, the sequence adjustment unit 220 of this embodiment determines the encoding amount of the BSI sequence 400, as in the first embodiment. Further, according to the priority received by the imaging condition reception unit 210, the imaging slice acquisition order of the ASL sequence 300 is also determined.

Specifically, the sequence adjustment unit 220 determines to acquire the imaging slice acquisition order from the higher priority. That is, as illustrated in FIG. 9, when the user selects that the data on the parietal side (Head side) is more important, in the ASL sequence 300, the imaging slice ordering (ASL Slice order) is changed to the Head direction. To Foot direction (HF). On the other hand, if the user selects the Foot side, the ordering is F-H.

Note that the imaging slice ordering in the ASL sequence 300 calculated by the sequence adjustment unit 220 may be displayed on the imaging condition reception screen 500a.
In this case, the ASL shooting condition display field 510 of the shooting condition reception screen 500a includes a slice order display field 511 as shown in FIG.

The sequence adjustment unit 220 displays the adjustment result in the slice order display field 511. That is, as shown in this figure, the display of “ASL slice order” 511 changes in conjunction with “BSI priority dir” 521.

As described above, the MRI apparatus 100 of the present embodiment includes the measurement unit 230 as in the first embodiment, and the second pulse sequence (BSI sequence 400) is changed to the first pulse sequence (ASL sequence). Execute in the free time within the repetition time of 300).

Further, it further includes a sequence adjustment unit 220, and the data acquired in the

free times

333 and 334 in the control sequence 320 of the ASL sequence 300 is lower in the k space than the data acquired in the

free times

331 and 332 in the labeling sequence 310. The encoding amount of the BSI sequence 400 is calculated so that the data that is arranged in the spatial frequency domain and acquired at a timing with less influence of the pre-pulse is arranged in the low spatial frequency domain of the k space.

Furthermore, in the MRI apparatus 100 of the present embodiment, the first pulse sequence (ASL sequence 300) is a two-dimensional multi-slice measurement sequence, and the second pulse sequence (BSI sequence 400) is a three-dimensional A sequence for measurement, and the imaging condition includes information specifying a priority side in the second pulse sequence with respect to the slice direction of the first pulse sequence (ASL sequence 300), and the sequence adjustment unit 220 further calculates an excitation frequency of the first pulse sequence (ASL sequence 300), and the excitation frequency is calculated so as to be acquired first from the priority slice.

Thereby, according to this embodiment, the same effect as the first embodiment can be obtained. Furthermore, the time interval from the ASL top slice (Slice # 1) to the free time 332 can be extended. For this reason, the influence of the labeling pulse 311 in the ASL sequence 300 can be minimized.

<< Third Embodiment >>
A third embodiment of the present invention will be described. In the present embodiment, the shooting conditions input by the user are also adjusted.

The MRI apparatus of the present embodiment has basically the same configuration as the MRI apparatus 100 of the first embodiment. However, as shown in FIG. 10, the overall control unit 108 of the present embodiment also adjusts shooting conditions, and therefore includes a shooting condition adjustment unit 260 in addition to the configuration of the first embodiment. Hereinafter, the present embodiment will be described focusing on the configuration different from the first embodiment.

The imaging condition adjustment unit 260 of the present embodiment adjusts the imaging conditions received by the imaging condition reception unit 210. This imaging condition adjustment unit 260 adjusts a predetermined imaging condition among the imaging conditions of the second pulse sequence (BSI sequence 400) according to the imaging conditions of the first pulse sequence (ASL sequence 300). The predetermined imaging conditions (adjustment imaging conditions) to be adjusted are the field of view (FOV), each encoding direction, the time interval between echo signals, the number of echo signals measured with one excitation, and the parallel imaging Contains at least one of the double speed numbers.

Hereinafter, the adjustment of the shooting conditions of the ASL sequence 300 and the BSI sequence 400 will be described in detail.

It is desirable that the encoding directions of the field of view (FOV) and read-out / phase / slice are always aligned (same) in both sequences. Further, it is desirable that the IET of the BSI sequence 400, the double speed number of parallel imaging, and the ETL are adjusted to be an integral multiple of those of the ASL sequence 300.

The shooting condition adjustment unit 260 holds in the storage device 115 the shooting condition calculation rule (shooting condition calculation rule) of the BSI sequence 400 with respect to the shooting condition of the ASL sequence 300 in advance for the above-described adjusted shooting condition. Then, the shooting condition adjustment unit 260 calculates the shooting condition of the BSI sequence 400 according to the shooting condition calculation rule using the shooting condition input as the shooting condition of the ASL sequence 300, and calculates the shooting condition initially set by the user. Replace with what you did.

As described above, the imaging condition calculation rule to be retained is FOV, an instruction to make the encoding direction equal, IET, a double speed of parallel imaging, a parameter that is an integer multiple such as ETL, and the multiple thereof.

For example, the imaging condition adjustment unit 260 may be configured to display the replaced imaging condition in the BSI imaging condition display field 520 of the imaging condition reception screen 500.

Here, the case where the imaging condition adjustment unit 260 is provided and the imaging conditions of the BSI sequence 400 are automatically adjusted according to the imaging conditions of the ASL sequence 300 has been described as an example, but the present invention is not limited to this. For example, the user may input parameters via the shooting condition reception screen 500 and determine whether or not the apparatus is appropriate. In this case, the imaging condition adjustment unit 260 may not be provided.

In this case, for example, as shown in FIG. 11, it further includes a determination unit 270 that determines the suitability of the accepted shooting conditions, and when the received shooting conditions violate a predetermined rule (shooting condition calculation rule), The shooting condition adjustment unit 260 may be configured to perform at least one of a process of notifying a user of a message and a process of automatically setting shooting conditions according to a rule.

That is, when the user inputs a value outside the shooting condition calculation rule as the shooting condition of the BSI sequence 400, the shooting condition adjustment unit 260, for example, displays a message that gives a warning to the display / operation unit 113, or an appropriate Suggestion may be displayed as a value, and the user may be prompted to input again.

Furthermore, the shooting condition calculation rules stored in the storage device 115 may include rules regarding the number of integrations and spatial resolution. The number of integrations and the spatial resolution are desirably different between both sequences. Therefore, for example, as an imaging condition calculation rule, an adjustment value or a change amount is held in advance for these imaging conditions.

In this case, when the user inputs the same shooting condition as the ASL sequence 300 regarding the number of integrations and / or spatial resolution as the shooting condition of the BSI sequence 400, the shooting condition adjustment unit 260 displays a message to the user and re-enters it. Encourage or adjust automatically according to the shooting condition calculation rules.

free times

Further, the MRI apparatus 100 of the present embodiment further includes an imaging condition adjustment unit 260 that adjusts the imaging conditions, and the imaging condition adjustment unit 260 includes, among the imaging conditions of the second pulse sequence (BSI sequence 400), The predetermined imaging conditions are adjusted according to the imaging conditions of the first pulse sequence (ASL sequence 300).

Thus, according to this embodiment, since it has the same configuration as that of the first embodiment, the same effect as that of the first embodiment can be obtained. Furthermore, according to the present embodiment, since the imaging conditions of the ASL sequence 300 and the BSI sequence 400 can be adjusted to the optimum ones, an image optimal for comparison can be obtained by both sequences.

This makes it easy to calculate image distortion if, for example, the imaging sequence for both measurements is an EPI system.

In the above-described embodiment, the configuration is such that the user input is adjusted even when the shooting conditions of the BSI sequence 400 are automatically set. However, the present invention is not limited to this.

The shooting conditions (adjustment shooting conditions) that can be automatically calculated from the shooting conditions of the ASL sequence 300 in accordance with predetermined shooting condition calculation rules may be configured so that the user does not need to input the shooting conditions of the BSI sequence 400. Good.

That is, when configured in this way, for the adjusted shooting conditions, the shooting condition receiving unit 210 displays the shooting conditions of the first pulse sequence (ASL sequence 300) in the first display column (ASL shooting condition display column 510). ), The imaging condition adjustment unit 260 generates the imaging condition of the second pulse sequence (BSI sequence 400) according to the imaging condition of the first pulse sequence, and the imaging condition adjustment unit 260 In one display column, the imaging conditions of the received first pulse sequence are displayed, and in the second display field (BSI imaging condition display field 520), the imaging conditions of the generated second pulse sequence are displayed. indicate.

Specifically, the shooting condition reception unit 210 displays the shooting condition reception screen 500 shown in FIG. 6 in such a manner that only the shooting conditions of the ASL sequence 300 can be input as the adjusted shooting conditions. Only the shooting conditions of the ASL sequence 300 are accepted. At this time, other imaging parameters of the BSI sequence 400 are arbitrarily set by the user.

In addition, when the imaging condition adjustment unit 260 receives the setting of the imaging condition, the imaging condition adjustment unit 260 calculates the imaging condition of the BSI sequence 400 according to a predetermined imaging condition calculation rule. The calculated shooting conditions are displayed in the corresponding shooting condition fields of the BSI shooting condition display field 520 of the shooting condition reception screen 500, respectively.

Predetermined imaging condition calculation rules include, for example, as described above, FOV and readout / phase / slice encoding directions are always aligned (assuming the same), IET of BSI sequence 400, double speed of parallel imaging, ETL Is an integer multiple of those of the ASL sequence 300, and the number of integrations and the spatial resolution are different values.

By configuring in this way, simply by setting the shooting conditions for the ASL sequence 300, the shooting conditions for the BSI sequence 400 can also be set, so that ASL data and BSI data can be obtained simultaneously in a single scan. The optimal shooting conditions can be set easily.

Note that this embodiment may be combined with the second embodiment.

100 MRI apparatus, 101 subject, 102 static magnetic field generating magnet, 103 gradient magnetic field coil, 104 transmission coil, 105 reception coil, 106 signal detection unit, 107 signal processing unit, 108 overall control unit, 109 gradient magnetic field power supply, 110 RF transmission Unit, 112 bed, 113 display / operation unit, 115 storage device, 210 shooting condition reception unit, 220 sequence adjustment unit, 230 measurement unit, 240 image reconstruction unit, 250 display image generation unit, 260 shooting condition adjustment unit, 300 ASL Sequence, 310 Labeling Sequence, 311 Labeling Pulse, 312 ASL Data Acquisition, 313 PLD, 320 Control Sequence, 321 Control Pulse, 322 ASL Data Acquisition, 323 PLD, 331 Free Time, 332 Free Time, 333 Free Time, 334 Free Time, 340 pulse sequence, 400 BSI sequence, 500 shooting condition reception screen, 500a shooting condition reception screen, 510 ASL shooting condition display field, 5 11 Slice order display field, 520 BSI imaging condition display field, 521 Priority specification area, 610 Labeling pulse application position, 620 Slice position, 710 table

Claims

Application of a high-frequency magnetic field pulse to a desired region of the subject, application of a gradient magnetic field pulse to the region, and a nuclear magnetic resonance signal generated from the region of the subject according to preset imaging conditions and a pulse sequence Equipped with a measuring unit to measure
The pulse sequence is
A first pulse sequence for acquiring data for generating an inflow dynamic image that is a dynamic image of blood flowing into a predetermined site;
A second pulse sequence for obtaining data for generating predetermined information other than the inflow dynamic image of the part, and
2. The magnetic resonance imaging apparatus according to claim 1, wherein the second pulse sequence is executed in a free time within a repetition time of the first pulse sequence.
The magnetic resonance imaging apparatus according to claim 1,
The first pulse sequence is:
After applying a labeling pulse as a pre-pulse, a labeling sequence for collecting data after a predetermined time, and
A control sequence that is executed after the labeling sequence, collects data after a predetermined time after applying a control pulse as the pre-pulse, and
The magnetic resonance imaging apparatus, wherein the labeling sequence and the control sequence are executed alternately.
The magnetic resonance imaging apparatus according to claim 2,
A sequence adjustment unit for adjusting the second pulse sequence;
The first pulse sequence comprises a plurality of idle times,
The sequence adjustment unit calculates the number of shots and the encoding amount of the second pulse sequence to be executed in each idle time based on the imaging condition, and adjusts the second pulse sequence according to the calculation result. ,
The encoding amount is calculated so that data acquired in a free time in the control sequence is arranged in a low spatial frequency region of k space from data acquired in a free time in the labeling sequence. Magnetic resonance imaging device.
The magnetic resonance imaging apparatus according to claim 3,
The sequence adjustment unit further calculates an encoding amount of the second pulse sequence so that data acquired at a timing with less influence of the pre-pulse is arranged in a low spatial frequency region of k-space. Magnetic resonance imaging device.
The magnetic resonance imaging apparatus according to claim 3,
The first pulse sequence is a sequence for two-dimensional multi-slice measurement,
The second pulse sequence is a sequence for three-dimensional measurement,
The imaging condition includes information for specifying a priority side with respect to the slice direction of the first pulse sequence,
The sequence adjustment unit further calculates an excitation frequency of the first pulse sequence,
The magnetic resonance imaging apparatus according to claim 1, wherein the excitation frequency is calculated so as to be acquired first from the priority slice.
The magnetic resonance imaging apparatus according to claim 1,
A shooting condition adjusting unit for adjusting the shooting condition;
The imaging condition adjusting unit adjusts a predetermined imaging condition among the imaging conditions of the second pulse sequence according to the imaging conditions of the first pulse sequence.
The magnetic resonance imaging apparatus according to claim 6,
The predetermined imaging condition includes at least one of an imaging field of view, each encoding direction, a time interval between echo signals, the number of echo signals measured by one excitation, and a parallel imaging multiple speed number. Magnetic resonance imaging device.
The magnetic resonance imaging apparatus according to claim 1,
A shooting condition receiving unit for receiving shooting conditions via the shooting condition receiving screen;
The shooting condition reception screen is
A first display field for displaying imaging conditions of the first pulse sequence;
A second display field for displaying the imaging conditions of the second pulse sequence,
In the first display field and the second display field, display fields having the same imaging conditions are arranged in association with each other.
The magnetic resonance imaging apparatus according to claim 8,
A discriminator for discriminating the suitability of the accepted shooting conditions;
A shooting condition adjustment unit that performs at least one of a process of notifying a user of a message and a process of setting a shooting condition according to the rule when the accepted shooting condition is contrary to a predetermined rule; And a magnetic resonance imaging apparatus.
The magnetic resonance imaging apparatus according to claim 8,
A shooting condition adjustment unit,
The imaging condition receiving unit receives the imaging condition of the first pulse sequence via the first display field,
The imaging condition adjustment unit generates the imaging condition of the second pulse sequence according to the imaging condition of the first pulse sequence, and the received first pulse sequence is displayed in the first display column. The magnetic resonance imaging apparatus is characterized in that the imaging conditions of the generated second pulse sequence are displayed in the second display column.
The magnetic resonance imaging apparatus according to claim 1,
From the data acquired in the first pulse sequence and the data acquired in the second pulse sequence, respectively, an image reconstruction unit for reconstructing an image,
A display image generation unit that generates a display image to be displayed on the display device from the reconstructed shita image, and
The first pulse sequence is a sequence for two-dimensional multi-slice measurement,
The second pulse sequence is a sequence for three-dimensional measurement,
The display image generation unit performs MPR (Multi Planar Reconstruction) processing on the three-dimensional image data reconstructed from the data obtained by the second pulse sequence, and from the data obtained by the first pulse sequence. A magnetic resonance imaging apparatus, wherein an image of each reconstructed slice position is generated as the display image.
The magnetic resonance imaging apparatus according to claim 1,
The magnetic resonance imaging apparatus, wherein the second pulse sequence is one of an RF spoiled SSFP (RF-Spoiled Steady State Free Precession) sequence and an SSFP-EPI sequence.
The magnetic resonance imaging apparatus according to claim 1,
The information generated from the data acquired in the second pulse sequence is a SWI (Susceptibility Weighted Imaging) or BSI (Blood Sensitivity Imaging) generated vein image, a quantitative susceptibility map (QSM (Quantitative Susceptibility Mapping) ) And brain oxygen uptake rate (OEF (Oxygen Extraction Fraction)).
The data for generating information other than the inflow dynamic image of the part is acquired in the idle time of the first pulse sequence for acquiring the data for generating the inflow dynamic image that is a conductor image of blood flowing into the predetermined part. Perform a second pulse sequence,
A magnetic resonance imaging method comprising: reconstructing the inflow dynamic image from data obtained by the first pulse sequence, and generating the information from data obtained by the second pulse sequence.
The magnetic resonance imaging method according to claim 14,
The first pulse sequence is:
A labeling sequence for collecting data after applying a labeling pulse;
A control sequence that executes after the labeling sequence, collects data after applying a control pulse, and
The labeling sequence and the control sequence are executed alternately,
The magnetic resonance imaging method, wherein the second pulse sequence has an encoding amount determined so that data acquired in a free time in the control sequence is arranged in a low spatial frequency region of k-space.