JP6391920B2 - Magnetic resonance imaging system - Google Patents

Description

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

  The MRI apparatus magnetically excites a nuclear spin of a subject placed in a static magnetic field with a radio frequency (RF) signal of Larmor frequency, and generates nuclear magnetic resonance (NMR) generated by this excitation. This is an image diagnostic apparatus that reconstructs an image from a resonance signal.

  In imaging using an MRI apparatus, a fat suppression method that suppresses an NMR signal (fat signal) from fat is known. As one of fat suppression methods, a method of suppressing a fat signal by applying a fat suppression pulse as an RF prepulse is known.

  Fat suppression pulses include CHESS (chemical shift selective) pulse, SPIR (SPectrally selective Inversion Recovery) pulse, SPAIR (SPectral Attenuated Inversion Recovery) pulse, and other frequency selective fat suppression pulses, and STIR (short inversion time inversion recovery) pulses. Are slice selective fat suppression pulses.

  The frequency selective fat saturation pulse uses the fact that the resonance frequency of the fat signal is shifted by chemical shift from the resonance frequency of the NMR signal from water (water signal), and thus the NMR signal corresponding to the resonance frequency of the fat signal. It is a region non-selective fat saturation pulse that suppresses frequency selective.

  The CHESS pulse is a frequency-selective fat suppression pulse in which an inversion time (TI), which is a period between the application timing of the fat suppression pulse and the application timing of the RF excitation pulse, can be regarded as zero. The SPIR pulse is a frequency selective fat suppression pulse with a flip angle (FA) set to 150 degrees to 180 degrees, and the SPAIR pulse is a frequency selection with an FA set to 180 degrees to 260 degrees. Fat suppression pulse. The SPAIR pulse is an adiabatic pulse that is not easily affected by the inhomogeneity of the RF magnetic field (B1).

  On the other hand, the slice selective fat saturation pulse is a region selective fat saturation pulse that spatially suppresses an NMR signal by selecting a specific slice. When applying a slice selective fat suppression pulse, the NMR signal for imaging is collected at the timing when the fat signal is suppressed using the difference in the longitudinal relaxation time (T1) between the fat region and the water region. TI is set to an appropriate value. The STIR pulse is also an adiabatic pulse.

  Furthermore, a technique for improving the fat suppression effect by combining a plurality of fat suppression pulses is also known.

JP 2008-264499 A

  An object of this invention is to provide the magnetic resonance imaging apparatus which can suppress a fat signal more favorably.

A magnetic resonance imaging apparatus according to an embodiment of the present invention includes an imaging condition setting unit, an imaging system, and an imaging parameter storage unit. The imaging condition setting unit is configured such that at least one of the inversion time between the application timing of the fat suppression pulse and the application timing of the high-frequency excitation pulse and the flip angle of the fat suppression pulse is appropriate according to both the repetition time and the echo time. Imaging conditions including application of the fat suppression pulse are set so as to be at least one of time and an appropriate angle. The imaging system performs magnetic resonance imaging of the subject according to the imaging conditions. The imaging parameter storage unit includes first time information in which a plurality of repetition times are associated with a plurality of first time data, and first angle information in which the plurality of repetition times are associated with a plurality of first angle data. A second time information that associates a plurality of echo times with a plurality of second time data, and a second information that associates the plurality of echo times with a plurality of second angle data. Save at least one of the angle information. The imaging condition setting unit refers to at least one of the first time information and the first angle information, and at least one of the second time information and the second angle information, and performs the magnetic resonance At least one of first time data and first angle data corresponding to the repetition time for imaging, and at least one of second time data and second angle data corresponding to the echo time for magnetic resonance imaging. By obtaining one, at least one of the appropriate time and the appropriate angle is obtained.

1 is a configuration diagram of a magnetic resonance imaging apparatus according to an embodiment of the present invention. The functional block diagram of the computer shown in FIG. The figure which shows an example of the pulse sequence accompanying application of the SPIR pulse or the SPAIR pulse set in the imaging condition setting part shown in FIG. The figure which shows an example of LUT preserve | saved at the imaging parameter preservation | save part shown in FIG. The flowchart which shows the flow of the imaging scan by the magnetic resonance imaging apparatus shown in FIG.

  A magnetic resonance imaging apparatus according to an embodiment of the present invention will be described with reference to the accompanying drawings.

  FIG. 1 is a configuration diagram of a magnetic resonance imaging apparatus according to an embodiment of the present invention.

  The magnetic resonance imaging apparatus 20 includes a cylindrical static magnetic field magnet 21 that forms a static magnetic field, a shim coil 22, a gradient magnetic field coil 23, and an RF coil 24 provided inside the static magnetic field magnet 21.

  In addition, the magnetic resonance imaging apparatus 20 includes a control system 25. The control system 25 includes a static magnetic field power supply 26, a gradient magnetic field power supply 27, a shim coil power supply 28, a transmitter 29, a receiver 30, a sequence controller 31, and a computer 32. The gradient magnetic field power source 27 of the control system 25 includes an X-axis gradient magnetic field power source 27x, a Y-axis gradient magnetic field power source 27y, and a Z-axis gradient magnetic field power source 27z. In addition, the computer 32 includes an input device 33, a display device 34, an arithmetic device 35, and a storage device 36.

  The static magnetic field magnet 21 is connected to a static magnetic field power supply 26 and has a function of forming a static magnetic field in the imaging region by a current supplied from the static magnetic field power supply 26. In many cases, the static magnetic field magnet 21 is composed of a superconducting coil, and is connected to the static magnetic field power supply 26 at the time of excitation and supplied with current. It is common. In some cases, the static magnetic field magnet 21 is composed of a permanent magnet and the static magnetic field power supply 26 is not provided.

  A cylindrical shim coil 22 is coaxially provided inside the static magnetic field magnet 21. The shim coil 22 is connected to the shim coil power supply 28, and is configured such that a current is supplied from the shim coil power supply 28 to the shim coil 22 to make the static magnetic field uniform.

  The gradient magnetic field coil 23 includes an X-axis gradient magnetic field coil 23 x, a Y-axis gradient magnetic field coil 23 y, and a Z-axis gradient magnetic field coil 23 z, and is formed in a cylindrical shape inside the static magnetic field magnet 21. A bed 37 is provided inside the gradient magnetic field coil 23 as an imaging region, and the subject P is set on the bed 37. The RF coil 24 includes a whole body coil (WBC) for transmitting and receiving an RF signal built in the gantry, a bed 37 and a local coil for receiving an RF signal provided near the subject P.

  The gradient magnetic field coil 23 is connected to a gradient magnetic field power supply 27. The X-axis gradient magnetic field coil 23x, the Y-axis gradient magnetic field coil 23y, and the Z-axis gradient magnetic field coil 23z of the gradient magnetic field coil 23 are respectively an X-axis gradient magnetic field power supply 27x, a Y-axis gradient magnetic field power supply 27y, and a Z-axis gradient magnetic field coil 27z. It is connected to the magnetic field power supply 27z.

  The X-axis gradient magnetic field power source 27x, the Y-axis gradient magnetic field power source 27y, and the Z-axis gradient magnetic field power source 27z are supplied with currents supplied to the X-axis gradient magnetic field coil 23x, the Y-axis gradient magnetic field coil 23y, and the Z-axis gradient magnetic field coil 23z, respectively. In the imaging region, a gradient magnetic field Gx in the X-axis direction, a gradient magnetic field Gy in the Y-axis direction, and a gradient magnetic field Gz in the Z-axis direction can be formed, respectively.

  The RF coil 24 is connected to at least one of the transmitter 29 and the receiver 30. The transmission RF coil 24 has a function of receiving an RF signal from the transmitter 29 and transmitting it to the subject P, and the reception RF coil 24 is accompanied by excitation of the nuclear spin inside the subject P by the RF signal. It has a function of receiving the NMR signal generated in this way and giving it to the receiver 30.

  On the other hand, the sequence controller 31 of the control system 25 is connected to the gradient magnetic field power supply 27, the transmitter 29 and the receiver 30. The sequence controller 31 is control information necessary for driving the gradient magnetic field power supply 27, the transmitter 29, and the receiver 30, for example, operation control information such as the intensity, application time, and application timing of the pulse current to be applied to the gradient magnetic field power supply 27. And the gradient magnetic field power supply 27, the transmitter 29 and the receiver 30 are driven according to the stored predetermined sequence to drive the X-axis gradient magnetic field Gx, the Y-axis gradient magnetic field Gy, and the Z-axis gradient magnetic field. It has the function of generating Gz and RF signals.

  The sequence controller 31 is configured to receive raw data, which is complex data obtained by detection of an NMR signal and A / D (analog to digital) conversion in the receiver 30, and supply the received raw data to the computer 32. The

  For this reason, the transmitter 29 is provided with a function of applying an RF signal to the RF coil 24 based on the control information received from the sequence controller 31, while the receiver 30 detects the NMR signal received from the RF coil 24. Then, by executing necessary signal processing and A / D conversion, a function of generating raw data that is digitized complex data and a function of supplying the generated raw data to the sequence controller 31 are provided.

  Further, the computer 32 is provided with various functions by executing the program stored in the storage device 36 of the computer 32 by the arithmetic unit 35. However, a specific circuit having various functions may be provided in the magnetic resonance imaging apparatus 20 instead of at least a part of the program.

  FIG. 2 is a functional block diagram of the computer 32 shown in FIG.

  The computing device 35 of the computer 32 functions as the imaging condition setting unit 40 and the data processing unit 41 by executing a program stored in the storage device 36. The imaging condition setting unit 40 includes an imaging sequence setting unit 40A, a fat suppression pulse setting unit 40B, and a TI / FA determination unit 40C. The storage device 36 functions as an imaging parameter storage unit 42, a k-space data storage unit 43, and an image data storage unit 44.

  The imaging condition setting unit 40 has a function of setting imaging conditions including a pulse sequence based on instruction information from the input device 33 and outputting the set imaging conditions to the sequence controller 31. In particular, the imaging condition setting unit 40 has a function of setting imaging conditions by the fat suppression method.

  The imaging sequence setting unit 40A of the imaging condition setting unit 40 has a function of setting an imaging sequence for collecting NMR signals (imaging data) for generating MR image data. Examples of the imaging sequence used for the fat suppression method include a pulse sequence such as a fast spin echo (FSE) sequence.

  The fat suppression pulse setting unit 40B has a function of setting a fat suppression pulse to be applied. Examples of fat suppression pulses include CHESS pulses, SPIR pulses, SPAIR pulses, and STIR pulses. The CHESS pulse is a frequency selective fat saturation pulse that can be regarded as having a TI of zero. The SPIR pulse is a frequency selective fat suppression pulse having a FA of 150 to 180 degrees. The SPAIR pulse is a frequency selective fat suppression pulse with a FA of 180 to 260 degrees. The STIR pulse is a region selective fat suppression pulse.

  The TI / FA determination unit 40C has a function of determining FA and TI of the fat suppression pulse to appropriate values. The optimum values of FA and TI of fat suppression pulses vary depending on TE as well as TR. Therefore, in order to improve the fat suppression effect, it is important to determine the FA and TI of the fat suppression pulse according to both TR and TE.

  Therefore, the TI / FA determination unit 40C is configured to set at least one of the TI and FA of the fat suppression pulse to at least one of an appropriate time and an appropriate angle according to both TR and TE. That is, the TI / FA determination unit 40C sets at least one of TI and FA of the region-selective fat saturation pulse or the frequency-selective fat saturation pulse at an appropriate time and an appropriate angle according to both TR and TE. be able to.

  Here, as an example, a case will be described in which the TI of the SPIR pulse or the SPAIR pulse is set to an appropriate time according to TR and TE. The same applies to the case where the FA of the CHESS pulse is set to an appropriate angle corresponding to TR and TE, and the case where the application condition of the STIR pulse is set. For example, when FA is set to an appropriate angle, TI may be replaced with FA and an appropriate angle may be obtained.

  FIG. 3 is a diagram showing an example of a pulse sequence involving application of SPIR pulse or SPAIR pulse set in the imaging condition setting unit 40 shown in FIG.

  In FIG. 3, the horizontal axis represents time, RF represents an RF pulse, and ECHO represents an NMR echo signal. As shown in FIG. 3, an RF excitation pulse (FLIP) is applied after TI from the application timing of the fat suppression pulse (FAT-SAT), and an RF refocusing pulse (REFOCUS) is repeatedly applied following the RF excitation pulse (FLIP). It is possible to set imaging conditions for repeating the fat suppression sequence with TR. When data collection is performed using such a fat suppression sequence, NMR echo signals corresponding to the center of the k space are collected after TE from the application timing of the RF excitation pulse (FLIP).

  An appropriate TI value corresponding to TR and TE can be determined using a function or a look-up table (LUT) for calculating an appropriate TI value using TR and TE as parameters. Accordingly, the imaging parameter storage unit 42 stores information such as a function or LUT for obtaining a TI value corresponding to TR and TE. Information such as functions or LUTs stored in the imaging parameter storage unit 42 can be acquired in advance by simulation or actual measurement. The TI / FA determination unit 40C is configured to obtain an appropriate TI value according to TR and TE with reference to information such as a function or LUT stored in the imaging parameter storage unit 42.

  FIG. 4 is a diagram illustrating an example of the LUT stored in the imaging parameter storage unit 42 illustrated in FIG.

  As illustrated in FIG. 4, the imaging parameter storage unit 42 includes a first time table in which a plurality of TRs and a plurality of first time data TI_TR are associated with each other, a plurality of TEs, and a plurality of second time data TI_TE. And a second time table associated with the LUT can be stored as an LUT. That is, the first time data TI_TR for obtaining the first time data TI_TR as a component of TI that changes depending on TR as shown in FIG. 4 (A) without using one table for obtaining TI using TR and TE as parameters. 1 and a second time table for obtaining second time data TI_TE as a TI component that changes depending on TE as shown in FIG. 4B are stored in the imaging parameter storage unit 42. be able to.

TI can be expressed as the sum of first time data TI_TR that changes depending on TR and second time data TI_TE that changes depending on TE, as shown in Equation (1).
TI = TI_TR + TI_TE (1)

  When TR and TE that affect the optimal value of TI of fat suppression pulses are compared, TR is more dominant. Therefore, Equation (1) corrects the TI (TI_TR) obtained based on the MR imaging TR regardless of the MR imaging TE with the correction value (TI_TE) corresponding to the MR imaging TE. It can also be said that this is an expression for obtaining an appropriate time as a TI value for MR imaging.

The first time data TI_TR corresponding to the MR imaging TR and the second time data TI_TE corresponding to the MR imaging TE are stored in the first time table and the second time table, respectively. It can be obtained by an interpolation process based on the data value. That is, when calculating the first time data TI_TR by linear interpolation, the first time data TI_TR can be calculated by the equation (2).
TI_TR (TR) = TI_TR [n] + (TR-TR [n]) / (TR [n + 1] -TR [n]) * (TI_TR [n + 1] -TI_TR [n]) (2)
However, in Equation (2), TR [i] and TI_TR [i] are the data values of TR and TI_TR identified by index i in the first time table, and n is smaller than TR for MR imaging, The index of the data value TR [i] closest to the TR for MR imaging.

Similarly, when the second time data TI_TE is calculated by linear interpolation, the second time data TI_TE can be calculated by Expression (3).
TI_TE (TE) = TI_TE [m] + (TE-TE [m]) / (TE [m + 1] -TE [m]) * (TI_TE [m + 1] -TI_TE [m]) (3)
However, in Equation (3), TE [j] and TI_TE [j] are data values of TE and TI_TE identified by the index j in the second time table, and m is smaller than the MR imaging TE, The index of the data value TE [j] closest to the TE for MR imaging.

Therefore, if the TR for MR imaging is 1800 [ms] and the TE for MR imaging is 500 [ms], the data values of the first time table shown in FIG. 4A and FIG. Equation (2), Equation (3) and Equation (1) using the data values of the second time table shown in Fig. It becomes.
TI_TR (1800) = 150+ (1800-1500) / (2000-1500) * (170-150) = 162 (4-1)
TI_TE (500) = 0+ (500-300) / (600-300) * (60-0) = 40 (4-2)
TI = 162 + 40 = 202 [ms] (4-3)

  In the first time table shown in FIG. 4 (A) and the second time table shown in FIG. 4 (B), two sets of data values are displayed. Of course, three or more sets of data values are recorded. You can also If the number of combinations of data values is increased, the accuracy of the interpolation process can be improved. Further, when there are three or more data values, nonlinear interpolation may be performed using an arbitrary function.

In addition, the function is not limited to the table shown in FIG. For example, when the first time data TI_TR and the second time data TI_TE change linearly with respect to TR and TE, respectively, the TI for MR imaging is expressed by the equation (5) using the coefficients a, b, and c. Can be obtained.
TI = aTR + bTE + c (5)

  In this case, the coefficients a, b, c themselves may be measured instead of the data values in the table. Similarly, an equation for calculating the TI for MR imaging can be prepared using an arbitrary function such as a nonlinear function.

  However, as shown in FIG. 4, if the TI for MR imaging is calculated based on the table for each TR and TE, there will be one parameter for the data value to be measured in advance. For this reason, it is easy to acquire information for obtaining the TI value corresponding to the TR and TE for MR imaging, which should be stored in the imaging parameter storage unit 42.

  As described above, the FA of the fat suppression pulse can also be set to an appropriate value according to TR and TE. Therefore, the imaging condition setting unit 40 performs imaging including application of the fat suppression pulse with at least one of TI and FA of the fat suppression pulse as at least one of an appropriate time and an appropriate angle according to both TR and TE. A function for setting conditions is provided.

  Therefore, the imaging parameter storage unit 42 includes first time information in which a plurality of TRs and a plurality of first time data are associated with each other, and a plurality of TRs and a plurality of first angle data in association with each other. At least one of the angle information can be stored. In addition, at least one of the second time information that associates the plurality of TEs with the plurality of second time data and the second angle information that associates the plurality of TEs with the plurality of second angle data is stored. be able to.

  Then, the imaging condition setting unit 40 refers to at least one of the first time information and the first angle information and at least one of the second time information and the second angle information, and performs TR for MR imaging. By acquiring at least one of first time data and first angle data corresponding to, and at least one of second time data and second angle data corresponding to TE for MR imaging, an appropriate time And at least one of the appropriate angles. Further, at least one of first time data and first angle data corresponding to TR for MR imaging, and at least one of second time data and second angle data corresponding to TE for MR imaging are: It can be acquired by interpolation processing based on a plurality of data values measured in advance stored in the imaging parameter storage unit 42.

  The data processing unit 41 acquires the NMR signals collected by the imaging scan under the imaging conditions set in the imaging condition setting unit 40 from the sequence controller 31 and stores the k space in the k space formed in the k space data storage unit 43. A function of arranging as data, a function of reconstructing image data by acquiring k-space data from the k-space data storage unit 43 and performing an image reconstruction process including Fourier transform (FT), obtained by reconstruction A function of writing the received image data in the image data storage unit 44, and a function of performing necessary image processing on the image data captured from the image data storage unit 44 and causing the display device 34 to display the image data.

  Accordingly, the components including the static magnetic field magnet 21, the gradient magnetic field coil 23, the RF coil 24, and the like, the control system 25, and the data processing unit 41 of the computer 32 cooperate with each other, so An imaging system for performing MR imaging is formed. However, various types of systems are known as the detailed configuration of the imaging system.

  Next, the operation and action of the magnetic resonance imaging apparatus 20 will be described.

  FIG. 5 is a flowchart showing the flow of an imaging scan by the magnetic resonance imaging apparatus 20 shown in FIG.

  First, the subject P is set on the bed 37 in advance, and a static magnetic field is formed in the imaging region of the static magnetic field magnet 21 (superconducting magnet) excited by the static magnetic field power supply 26. Further, a current is supplied from the shim coil power supply 28 to the shim coil 22, and the static magnetic field formed in the imaging region is made uniform.

  On the other hand, in step S1, the imaging condition setting unit 40 sets an imaging protocol including the type and number of fat suppression pulses, the type of imaging sequence, and the like.

  In step S2, the imaging condition setting unit 40 sets imaging parameters of an imaging protocol including TR and TE.

  Next, in step S3, the TI / FA determination unit 40C sets the FA and TI values of the fat suppression pulse to appropriate times and angles according to TR and TE. Specifically, the TI / FA determination unit 40C refers to information illustrated in FIG. 4 stored in the imaging parameter storage unit 42, and calculates FA and TI according to TR and TE.

  Further, other imaging conditions necessary for MR imaging are set in the imaging condition setting unit 40. When the setting of imaging conditions is completed, MR imaging of the subject P can be started. In step S4, MR imaging of the subject P is executed.

  Specifically, an imaging scan start instruction is given from the input device 33 to the imaging condition setting unit 40. For this reason, imaging conditions including a pulse sequence are output from the imaging condition setting unit 40 to the sequence controller 31. Then, the sequence controller 31 drives the gradient magnetic field power source 27, the transmitter 29, and the receiver 30 according to the imaging conditions to form a gradient magnetic field in the imaging region where the subject P is set, and the RF coil 24 outputs an RF signal. Is generated.

  Therefore, an NMR signal generated by nuclear magnetic resonance inside the subject P is received by the RF coil 24 and given to the receiver 30. The receiver 30 receives the NMR signal from the RF coil 24, performs necessary signal processing, and then performs A / D conversion to generate raw data that is an NMR signal of digital data. The receiver 30 gives the generated raw data to the sequence controller 31. The sequence controller 31 provides the raw data to the data processing unit 41, and the data processing unit 41 arranges the raw data as k-space data in the k-space formed in the k-space data storage unit 43.

  Subsequently, the data processing unit 41 retrieves k-space data from the k-space data storage unit 43 and performs image reconstruction processing to reconstruct the image data. Further, the data processing unit 41 performs necessary image processing on the image data and causes the display device 34 to display the image data. Thereby, the display device 34 displays an MR image in which the signal value of the fat component is well suppressed by applying the fat suppression pulse with FA and TI appropriately set according to TR and TE.

  In the magnetic resonance imaging apparatus 20 as described above, at least one of FA and TI of the fat suppression pulse is set to an appropriate value according to TR and TE.

  For this reason, according to the magnetic resonance imaging apparatus 20, even if the optimum values of the FA and TI of the fat saturation pulse change depending on TR and TE, the FA and TI are set to an appropriate angle and TR following the TR and TE. Can be set to time. As a result, the fat suppression effect can be improved. That is, a good fat suppression image can be obtained without depending on imaging parameters such as TR and TE.

  For example, when imaging is performed with a single shot FSE sequence, if the TE is long, the null point at which the longitudinal magnetization of fat becomes zero is shifted by a non-negligible amount, but deterioration of the fat suppression effect can be avoided.

  Although specific embodiments have been described above, the described embodiments are merely examples, and do not limit the scope of the invention. The novel methods and apparatus described herein can be implemented in a variety of other ways. Various omissions, substitutions, and changes can be made in the method and apparatus described herein without departing from the spirit of the invention. The appended claims and their equivalents include such various forms and modifications as are encompassed by the scope and spirit of the invention.

20 Magnetic Resonance Imaging Device 21 Magnet for Static Magnetic Field 22 Shim Coil 23 Gradient Magnetic Field Coil 24 RF Coil 25 Control System 26 Static Magnetic Field Power Supply 27 Gradient Magnetic Field Power Supply 28 Shim Coil Power Supply 29 Transmitter 30 Receiver 31 Sequence Controller 32 Computer 33 Input Device 34 Display Device 35 computing device 36 storage device 37 bed 40 imaging condition setting unit 40A imaging sequence setting unit 40B fat suppression pulse setting unit 40C TI / FA determination unit 41 data processing unit 42 imaging parameter storage unit 43 k-space data storage unit 44 image data storage unit P subject

Claims (7)

At least one of the inversion time between the application timing of the fat saturation pulse and the application timing of the high frequency excitation pulse and the flip angle of the fat suppression pulse has an appropriate time and an appropriate angle according to both the repetition time and the echo time. As at least one, an imaging condition setting unit set to an imaging condition including application of the fat suppression pulse;
An imaging system for performing magnetic resonance imaging of a subject according to the imaging conditions;
Storing at least one of first time information in which a plurality of repetition times are associated with a plurality of first time data, and first angle information in which the plurality of repetition times are associated with a plurality of first angle data; And at least one of second time information that associates a plurality of echo times with a plurality of second time data, and second angle information that associates the plurality of echo times with a plurality of second angle data. An imaging parameter storage unit to be stored;
With
The imaging condition setting unit refers to at least one of the first time information and the first angle information, and at least one of the second time information and the second angle information, and performs the magnetic resonance At least one of first time data and first angle data corresponding to the repetition time for imaging, and at least one of second time data and second angle data corresponding to the echo time for magnetic resonance imaging. A magnetic resonance imaging apparatus configured to obtain at least one of the appropriate time and the appropriate angle by acquiring one. The imaging condition setting unit includes at least one of the first time data and the first angle data corresponding to the repetition time for the magnetic resonance imaging, and the echo time corresponding to the magnetic resonance imaging. and at least one of second time data and the second angle data, a magnetic resonance imaging apparatus configured according to claim 1 to obtain by interpolation processing based on the pre-acquired plurality of data values. The imaging condition setting unit sets at least one of an inversion time and a flip angle obtained based on the repetition time for the magnetic resonance imaging independently of the echo time for the magnetic resonance imaging for the magnetic resonance imaging. magnetic resonance imaging apparatus of the appropriate time and the appropriate angle of at least one of them ask configured claim 1 or 2, wherein by correcting the correction value corresponding to the echo time. The imaging condition setting unit, one of the claims 1 to 3 configured to set at least one of the appropriate time and the appropriate angle of at least one of the inversion time and the flip angle of the frequency-selective fat saturation pulse 2. A magnetic resonance imaging apparatus according to claim 1. The magnetic resonance imaging apparatus according to claim 4, wherein the imaging condition setting unit is configured to set an inversion time of an SPIR pulse or a SPAIR pulse to the appropriate time. The magnetic resonance imaging apparatus according to claim 4 , wherein the imaging condition setting unit is configured to set a flip angle of a CHESS pulse to the appropriate angle. The imaging condition setting unit, any inversion time region selective fat saturation pulse and flip angle of at least one of claims 1 to 3 configured to set at least one of the appropriate time and the appropriate angle 2. A magnetic resonance imaging apparatus according to claim 1.

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