JP2701201B2 - Magnetic resonance diagnostic equipment - Google Patents

Description

DETAILED DESCRIPTION OF THE INVENTION

[0001]

TECHNICAL FIELD [0001] The present invention relates to ¹ H to other nuclides,
For example, by the occurrence of the polarization transfer to ¹³ C, M spin of ¹³ C
The present invention relates to a magnetic resonance diagnostic apparatus for observing an R signal with high sensitivity.

[0002]

2. Description of the Related Art A magnetic resonance diagnostic apparatus is a device that can non-invasively image the distribution of water in a living body by detecting ¹ H of water molecules, and is widely used clinically. It is a diagnostic device. However, current morphological information can only be obtained from water molecule images.

On the other hand, for example, by detecting metabolites ¹ H, ¹³ C or ³¹ P, metabolic information in a living body can be obtained, and therefore, a multi-nucleus NMR (Nuclear Magnification) can be obtained.
eticResonance). Among them, ¹³ C-NMR has recently attracted attention.
This, ¹³ C in order natural abundance of 1.1% of low ¹³ C
It is possible to track the state of metabolism after labeling,
^This is because metabolic information different from ¹ H and ³¹ P can be obtained.

However, this ¹³ C-NMR has a problem that the sensitivity of detecting ¹³ C is low, and a method for improving S / N such as decoupling and polarization transfer has been developed in an analytical NMR apparatus. . As the latter polarization transfer method, GAMorris et al., Journal of the American Chemical
INEPT (I) presented at Society vol.101, p.760 (1979)
nsensitive Nuclei Enhanced by Polarozation Transfe
r), DMDoddrell, etc. are Journal of Magnetic Resonanc
evol.48, p.323 (1982) DEPT (Distortio
nless Enhancement by Polarization Transfer).

As shown in the pulse sequence of INEPT shown in FIG. 10, by applying three ¹ H pulses and two ¹³ C pulses, the sensitivity of ¹³ C can be improved and the S / N can be improved. It is. The ¹ H pulse is
An extremely short-time high-frequency magnetic field that selectively excites only ¹ H is defined, and a ¹³ C pulse is defined as an extremely short-time high-frequency magnetic field that selectively excites only ¹³ C. Also, three of the ¹ H pulse each, according to their application order, first of the ¹ H pulse, a second of the ¹ H pulse, the third ¹
This is called an H pulse. In addition, each of the two ¹³ C pulses is converted into a first ¹³ C pulse, a second
^{Called 13} C pulse.

In this INEPT pulse sequence,
Not having received the polarization of ¹ H, (referred to ¹³ C from signal) MR signal from ¹³ C by two ¹³ C pulse is also observed at the same time. In order to remove the ^13C- derived signal, a method called a phase cycle has been developed. The phase cycle method is a method of alternately inverting the phase of the third ¹ H pulse to + y and -y as shown in FIG.
In accordance with the phase inversion of the third ¹ H pulse, the phase of the MR signal (polarization movement signal) due to the polarization movement is also inverted. In contrast, the phase of the ¹³ C-derived signal is not inverted. Therefore, only the polarization transfer signal can be observed by taking the difference between the MR signals obtained by performing the phase cycle. Similar results can be obtained by applying the first and second ¹³ C pulses to the phase cycle method. Note that this phase cycle method uses the DEP shown in FIG.
It is also applicable to T.

When the high-frequency magnetic field distribution of the probe is almost uniform as in an analytical NMR apparatus, such a phase cycle method is useful for observing only a polarization transfer signal. However, when the above-described polarization transfer method is applied to a living body to perform in vivo observation, the above-described phase cycle method is insufficient. In other words, in the case of observation in vivo, due to the non-uniform distribution of the high-frequency magnetic field of the probe and the non-uniform distribution derived from the living body,
The observed MR signal contains other signal components in addition to the polarization transfer signal and the ¹³ C-derived signal. Therefore, there is a problem that the S / N is deteriorated.

[0008]

SUMMARY OF THE INVENTION An object of the present invention is to provide a magnetic field resonance diagnostic apparatus capable of observing only an MR signal due to polarization transfer even when a high-frequency magnetic field distribution is not uniform.

[0009]

According to the present invention, at least three ¹ H pulses as a high-frequency magnetic field for selectively exciting ¹ H spins are applied in order to selectively excite spins of other nuclides. By executing a pulse sequence of sequentially applying at least two other nuclide pulses as a magnetic field, a polarization transfer from the ¹ H to the other nuclide occurs, and an MR signal is observed from the spin of the other nuclide, In the magnetic resonance diagnostic apparatus for obtaining the spectrum of the other nuclide based on the MR signal, the MR signal may include a first component due to the polarization transfer, and an incompleteness of a flip angle between the ¹ H pulse and the spin of the other nuclide. And a third component directly derived from the spins of the other nuclide derived from the spins of the other two nuclides, and the first component is extracted. So as to remove the second component and the third component, at least one of the ¹ H pulse of the phase in the three of the ¹ H pulse is inverted in the repetition of the pulse sequence, the two other The phase of at least one other nuclide pulse in the nuclide pulse is inverted during the repetition of the pulse sequence, a plurality of MR signals observed by the repetition of the pulse sequence are added / subtracted, and the other nuclide is added based on the result of the addition / subtraction. Is obtained.

[0010]

Embodiments of the present invention will be described below with reference to the drawings. Note that ¹ H and other nuclides are used as examples of the rich spin and the diluted spin. Other nuclides are described here as ¹³ C, but of course,
¹⁵ N, etc.

FIG. 1 is a block diagram showing the configuration of a magnetic resonance diagnostic apparatus according to one embodiment of the present invention. In FIG. 1, a uniform static magnetic field and a linear gradient magnetic field distribution in x, y, and z3 directions orthogonal to each other are provided to a subject (not shown) by a static magnetic field magnet 1 and gradient coils 2 and shim coils 3 provided inside the magnet. Is applied. Gradient coil 2
Are driven by a gradient coil power supply 5 to generate a gradient magnetic field independently in each of x, y, and z directions. The shim coil 3 is driven by a shim coil power supply 6 and generates a magnetic field for improving magnetic field uniformity. The probe 4 provided inside the gradient coil 2 applies a high-frequency magnetic field to the subject by receiving a high-frequency signal from the transmission units 7 and 8, and receives a magnetic field resonance signal (MR signal) from the subject. . The probe 4 may be used for both transmission and reception, or may be provided separately for transmission and reception. After the MR signal received by the probe 4 is detected by the receiving unit 9, the MR signal is transferred to the data collecting unit 11, where it is subjected to A / D conversion, and then sent to the computer system 12 for data processing. The transmitting units 7 and 8, the receiving unit 9 and the probe 4 are ¹ H
It is possible to transmit and receive at both resonance frequencies with ¹³ C.

The above-described gradient coil power supply 5, shim coil power supply 6, reception unit 9, and data collection unit 11 are all controlled by a sequence control unit 10 and controlled by a sequence control unit 120 computer system 12. The computer system 12 is controlled by a command from the console 13. The MR signal input from the data acquisition unit 11 to the computer system 12 is appropriately added and subtracted, Fourier transform is performed, and the ¹³ C spectrum is reconstructed based on the result. This spectrum is sent to the image display 14 and displayed.

FIG. 2 is a diagram showing a pulse sequence of INEPT with an incomplete flip angle. According to the present embodiment, this pulse sequence is improved to an effective phase cycle method that enables observation (detection) of only a magnetization component (polarization transfer component) due to only polarization transfer in observation in vivo. In the following description, a ¹ H pulse is defined as a pulsed high-frequency magnetic field that selectively excites only ¹ H for an extremely short time, and a ¹³ C pulse is
It is defined as a pulsed high-frequency magnetic field that selectively excites only ¹³ C for an extremely short time. Also, three of the ¹ H pulse each, according to their application order, first of the ¹ H pulse, a second of the ¹ H pulse, referred to as a third of the ¹ H pulse. Also, two ¹³ C pulse each, according to their application order, referred to as the first ¹³ C pulse, the second ¹³ C pulse.

In the calculation, the flip angles of the ^first to third ¹ H pulses are set to 90 °, 180 °, and 90 °, respectively, and the flip angles of the first and second ¹³ C pulses are calculated. Is set to 180 °, 90 °, but in v
Due to the inhomogeneity of the high-frequency magnetic field in ivo, it actually works as imperfection. The incomplete flip angles of each of the ^first to third ¹ H pulses are represented as b1, b2, and b3, and the incomplete flip angles of each of the first and second ¹³ C pulses are represented as b4, b5. It shall be.

Ignoring spin evolution due to chemical shifts, the M collected by the INEPT pulse sequence
The R signal E is represented by A to G as shown in the following equation (1).
Can be expanded to seven components. The ¹ H spin is I, ¹³
The C spin is shown as S, and the state of each spin is I0
, I +, I-, S0, S +, S-.

E = A + B + C + D + E + F + G (1) where A = i / 2 ^1/2 (I0 S + + I0 S−) COS (b2) sin (b1) si
n (b3) sin (b5) B = i / 2 ^1/2 (IO S + + IO S +) COS (b4) sin (b1) si
n (b3) sin (b5) C = i (IOS + + IOS-) COS (b5) sin (b1) sin (b3) sin
(b4) D = i (IO S + + IO S-) COS (b1) sin (b2) sin (b3) sin
(b5) E = (− I 0 S ++ I 0 S−) COS (b3) sin (b4) F = i / 2 (−S + −S−) cos (b5) sin (b4) G = i / 2 ^{1 / 2} (-S + -S-) cos (b4) sin (b5) A and B are polarization transfer components to be observed. C and D are components (incomplete flip angle components) resulting from incomplete flip angle due to inhomogeneity of the high-frequency magnetic field. EG
¹³ but first regardless of the polarization transfer, the second ¹³ C pulse
It is a component originally generated from C ( ^13C- derived component).
The incomplete flip angle component and the ¹³ C-derived component are components to be removed by the phase cycle method according to the present invention.

According to the present invention, A and B are removed by removing the components C to G.
2. Specifically, the pulse sequence of FIG. 2 is repeatedly executed while applying a phase cycle, and only the polarization transfer components of A and B are obtained by adding and subtracting a plurality of observed MR signals. It is possible to detect (extract).

In the IMPET sequence, a spectrum free from the influence of the chemical shift can be obtained by re-imaging the expansion due to the chemical shift with the second ¹ H pulse. As shown in FIG. 12, the first pulse sequence (FIG. 1) in which all the pulses are applied with the + phase of each axis.
2 (a)) and the MR signal acquired by the second pulse sequence (FIG. 12 (b)) in which only the phase of the third ¹ H pulse is inverted and applied. According to the conventional phase cycle method, ¹³ C-derived components EG can be removed. However, the incomplete components C and D of the flip cannot be removed. This principle will be described below.

What is important here is that in each of the above A to G, the sin term contributes to the inversion of the polarity of the MR signal by the inversion of the pulse phase. In FIG. 3, in each of the components A to G, a pulse for inverting the polarity of the MR signal by phase inversion, that is, a pulse in which the flip angle occurs as a sin term is indicated by a mark ○. Here, considering the conventional phase cycle method of inverting the phase of the third ¹ H pulse,
With the first pulse sequence, all components A to G are collected with the positive polarity. Further, by the second pulse sequence in which the phase of the third ¹ H pulse is inverted with respect to the first pulse sequence, each of the components A to D is collected with a positive polarity, and each of the components E to G is collected with a polarity. Inverted-collected as polarity. That is, the MR signals E1 and E2 collected in the first and second pulse sequences are respectively given by the following equation (2).

E1 = + A + B + C + D + E + F + GE2 = -A-B-C-D + E + F + G (2) The difference between the two signals is given by equation (3).

E 1 −E 2 = 2 · A + 2 · B + 2 · C + 2 · D (3) Therefore, it will be understood that each of the components E to G, that is, the components derived from ¹³ C are removed. It will also be appreciated that the C and D flip angle imperfections cannot be removed.

Next, the phase cycle method of the present embodiment will be described. In order to remove the flip angle incomplete component and the ¹³ C-derived component and extract only the polarization transfer component, at least ^one of the ^first to third ¹ H pulses is understood as will be understood from the following description. At least two pulses, one pulse and at least one of the first and second ¹³ C pulses, need to be selected for phase cycling;
In addition, it is necessary to repeatedly execute the pulse sequence at least four times. Although there are a plurality of pulse combinations and pulse sequence repetition times which are subject to a phase cycle for removing the flip angle incomplete component and the ¹³ C-derived component and extracting only the polarization transfer component, here Two cases will be described as representative examples. (First Case) In the first case, as a pulse to be subjected to phase inversion (phase cycle), a ^first 1H pulse (a Philip angle b1) and a first ^13C pulse (a Philip angle b4) are used. Will be described as an example. The pulse sequence as shown in FIG. 2 is repeatedly executed four times. FIG. 4 (a) to (d)
7 shows the first to fourth pulse sequences. However, the order of these pulse sequences is out of order. The phase of the receiving system 9 is indicated by r. + R means that the MR signal received by the receiving system 9 is output as it is as a + phase, which is equivalent to a computer system 1 described later.
2 can be replaced with addition processing in signal processing. "-R" means that the MR signal received by the receiving system 9 is output after being inverted to -phase, which can be replaced by a subtraction process in signal processing in the computer system 12 described later.

In the first pulse sequence, all pulses are applied with a + phase (+ X or + Y), and the receiving system 9 is set to a + phase. Therefore, the MR signal E1 collected in the first pulse sequence is
It is given by equation (4). E1 = + (+ A + B + C + D + E + F + G) (4) Next, in the second pulse sequence, the first ¹ H pulse is applied after being inverted to the -phase (-X). The phases of the other pulses are the same as in the first pulse. The receiving system 9 is set to the negative phase. Therefore, the MR signal E1 acquired in the second pulse sequence is given by the equation (5). E2 =-(-A-B-C + D + E + F + G) (5) Then, in the third pulse sequence, the first ¹³ C
The pulse is applied inverted to -phase (-X). The phases of the other pulses are the same as in the first pulse. The receiving system 9 is set to the positive phase. Therefore, the MR signal E3 collected in the third pulse sequence is given by the equation (6). E3 = + (+ A + BC + DE-F + G) (6) Finally, in the fourth pulse sequence, the ^first 1H
The pulse is applied inverted to -phase (-X) and the first
The ¹³ C pulse is also inverted and applied to -phase (-X).
The phases of the other pulses are the same as in the first pulse. Receiving system 9
Is set to the negative phase. Therefore, the MR signal E4 collected in the fourth pulse sequence is (7)
Given by the formula. E4 =-(-AB + C + DEF + G) (7) The MR signals of E1 to E4 are added by the computer system 12. As the MR signal E obtained by this addition,
It is given by equation (8).

E = 4 · A + 4 · B (8) As described above, only the polarization transfer components A and B can be extracted. (Second case) In the second case, as a pulse to be subjected to phase inversion (phase cycle), a ^{first 1} H pulse (a Philip angle b1) and a second ¹³ C pulse (a Philip angle b5) Will be described as an example. The pulse sequence as shown in FIG. 2 is repeatedly executed four times. FIG. 5 (a) to (d)
7 shows the first to fourth pulse sequences. However, the order of these pulse sequences is out of order.

In the first pulse sequence, all pulses are applied with a + phase (+ X or + Y), and the receiving system 9 is set to a + phase. Therefore, the MR signal E1 collected in the first pulse sequence is
It is given by equation (9). E1 = + (+ A + B + C + D + E + F + G) (9) Next, in the second pulse sequence, the second ¹³ C pulse is inverted to the negative phase (-X) and applied. The phases of the other pulses are the same as in the first pulse. The receiving system 9 is set to the negative phase. Therefore, the MR signal E1 collected in the second pulse sequence is given by the following equation (10). E2 =-(-AB + CD + E + FG) (10) Then, in the third pulse sequence, the first ^13C
The pulse is applied inverted to -phase (-X). The phases of the other pulses are the same as in the first pulse. The receiving system 9 is set to the negative phase. Therefore, the MR signal E3 collected in the third pulse sequence is given by the equation (11). E3 =-(-ABC-D + E + F + G) (11) Finally, in the fourth pulse sequence, the ^first 1H
The pulse is applied inverted to -phase (-X) and the first
The ¹³ C pulse is also inverted and applied to -phase (-X).
The phases of the other pulses are the same as in the first pulse. Receiving system 9
Is set to + phase. Therefore, the MR signal E4 acquired in the fourth pulse sequence is (1
It is given by equation 2). E4 = + (+ A + BCD + E + FG) (12) The MR signals of E1 to E4 are added by the computer system 12. As the MR signal E obtained by this addition,
It is given by equation (13).

E = 4 · A + 4 · B (13) As described above, only the polarization transfer components A and B can be extracted. As described above, by the above-described phase cycle, MR
By observing the signals and adding the MR signals, only the polarization transfer components A and B can be extracted. The number of repetitions of the pulse and the pulse sequence to be subjected to the phase cycle is not limited to the above, and the flip angle imperfect component and the component derived from ¹³ C can be removed and only the polarization transfer component can be extracted. Can be arbitrarily changed.

This phase cycle is also applicable to a so-called modified INEPT pulse sequence. FIG.
FIG. 9 is a diagram showing a modified INEPT pulse sequence.
If the time interval between the first ¹³ C pulse and the second ¹³ C pulse is ４ · J (where J is a coupling time constant), the modified INEPT pulse sequence includes the second ¹ H pulse and the first ¹³ C pulse. ¹³ C
It is not necessary to apply the pulse and the pulse simultaneously.

FIG. 7 shows a pulse sequence in which the modified INEPT of FIG. 6 is applied to localization. The phase cycle can be applied to this pulse sequence. The principles of the phase cycle of the present invention can also be applied to INEPT with added decoupling pulses. FIG. 8 shows a pulse sequence of INEPT to which a decoupling pulse is added.
This pulse sequence indicates a sequence for the CH ₂ system. In this pulse sequence, a third ¹³ C pulse is added to FIG. 2 as a high frequency magnetic field. In order to apply a phase cycle in which the flip angle imperfect component and the ¹³ C-derived component can be removed by the INEPT to which the decoupling pulse is added and only the polarization transfer component can be extracted, at least the target pulse of the phase cycle must be It is necessary to select three pulses and repeat the pulse sequence at least eight times. (First Case) In a first case, a first ¹ H pulse, a first ¹³ C pulse, and a third ¹³ C pulse are selected as target pulses of a phase cycle. The phase of the target pulse in each of the first to eighth pulse sequences is shown below. However, pulses other than the target pulse are uniformly applied to + in the entire pulse sequence.

First time; (+ b6, + b4, + b1, + r) Second time; (+ b6, + b4, + b1, -r) Third time; (+ b6, -b4, + b1, + r) Fourth time; (+ b6, -b4, (-B1, -r) 5th; (-b6, + b4, + b1, -r) 6th; (-b6, + b4, -b1, -r) 7th; (-b6, -b4, + b1, + r) 8 Second time: (−b6, −b4, −b1, −r) (Second case) In the second case, the first ¹ H pulse, the second ¹³ C pulse, and the third ¹³ C pulse are phase-shifted. Selected as the target pulse for the cycle. The phase of the target pulse in each of the first to eighth pulse sequences is shown below. However, pulses other than the target pulse are uniformly applied to + in the entire pulse sequence.

First time; (+ b6, + b5, + b1, -r) Second time; (+ b6, + b5, -b1, -r) Third time: (+ b6, -b5, + b1, -r) Fourth time; (+ b6, -r) (b5, -b1, + r) 5th; (-b6, + b5, + b1, + r) 6th; (-b6, + b5, -b1, -r) 7th; (-b6, -b5, + b1, -r) Eighth: (−b6, −b4, −b1, + r) Thus, the INEPT with the decoupling pulse applied
By performing the phase cycle in the first or second case, only the polarization transfer component can be extracted.
Of course, other cases may be used as long as only the polarization transfer component can be extracted. It should be noted that FIG.
In this case, only the polarization transfer component can be extracted by executing the phase cycle similarly to the case of FIG. The present invention can be implemented in various modifications without being limited to the above-described embodiment.

[0031]

According to the present invention, at least three ¹ H pulses as a high-frequency magnetic field for selectively exciting ¹ H spins are sequentially applied, and at least three high-frequency magnetic fields for selectively exciting spins of other nuclides are applied. By executing a pulse sequence of sequentially applying two other nuclide pulses, a polarization transfer from the ¹ H to the other nuclide occurs,
In the magnetic resonance diagnostic apparatus for observing an MR signal from the spin of the other nuclide and obtaining a spectrum of the other nuclide based on the MR signal, the MR signal includes a first component due to the polarization transfer and the ¹ H pulse. And the second component due to the incompleteness of the flip angle of the other nuclide spin;
A third component derived directly from the spins of the other nuclide and derived directly from the spins of the other nuclide, extracting the first component and removing the second component and the third component. In addition, at least one of the three ¹ H pulses
The phase of the ¹ H pulse is inverted during the repetition of the pulse sequence, and the phase of at least one other nuclide pulse of the two other nuclide pulses is inverted during the repetition of the pulse sequence. It is characterized in that a plurality of MR signals observed by repetition are added and subtracted, and the spectrum of the other nuclide is obtained based on the result of the addition and subtraction.

[Brief description of the drawings]

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

FIG. 2 is a diagram showing a pulse sequence of an INEPT with an incomplete flip angle.

FIG. 3 is a diagram showing a pulse that occurs as a sin term in the pulse sequence of FIG. 2;

FIG. 4 is a diagram showing first to fourth pulse sequences to which the phase cycle of the present invention is applied.

FIG. 5 is a diagram showing another pulse sequence from the first time to the fourth time to which the phase cycle of the present invention is applied.

FIG. 6 shows a modified INE to which the phase cycle of the present invention can be applied.
The figure which shows the pulse sequence of PT.

FIG. 7 is a diagram showing a pulse sequence in which the pulse sequence of FIG. 6 is applied to local excitation.

FIG. 8 is a diagram showing a decoupling INEPT pulse sequence to which the phase cycle of the present invention can be applied.

FIG. 9 is a diagram showing a modification of the decoupling INEPT pulse sequence of FIG. 8;

FIG. 10 is a diagram showing an INEPT pulse sequence.

FIG. 11 is a diagram showing a DEPT pulse sequence.

FIG. 12 shows a INEPT to which a conventional phase cycle method is applied.
The figure which shows a pulse sequence.

[Explanation of symbols]

1 ... static field magnet, 2 ... gradient coils, 3 ... shim, 4 ... probe ^{(1 H, 13 C),} 5 ... gradient coil power supply, 6 ... shim coil power supply, 7 ... ¹ H transmission unit, 8 ... ¹³ C transmission unit , 9 ... ¹³ C receiving unit, 10 ... sequence control unit, 11 ... data collection unit, 12 ... computer system, 13 ... console, 14 ... image display.

Claims (3)

(57) [Claims] At least three ¹ H pulses as a high-frequency magnetic field for selectively exciting ¹ H spins are sequentially applied, and at least two other nuclides as a high-frequency magnetic field for selectively exciting spins of other nuclides. By executing a pulse sequence of sequentially applying pulses, the ¹ H
A magnetic resonance diagnostic apparatus for generating a polarization transfer from the other nuclide to the other nuclide, observing an MR signal from the spin of the other nuclide, and obtaining a spectrum of the other nuclide based on the MR signal. A first component due to movement, a second component due to the incompleteness of the flip angle of the ¹ H pulse and the spin of the other nuclide, and a direct component from the spin of the other nuclide derived from the two other nuclide spins. The first component is extracted, and the three components are removed so as to remove the second component and the third component.
¹ H least one of the ¹ H pulse phase within a pulse is inverted in the repetition of the pulse sequence, the two other nuclides pulses of at least one other nuclides pulse phases in the repetition of the pulse sequence A magnetic resonance diagnostic apparatus comprising: adding and subtracting a plurality of MR signals that are inverted in a pulse sequence and observed by repetition of the pulse sequence, and obtaining a spectrum of the other nuclide based on a result of the addition and subtraction. Wherein the first pulse sequence to be applied in the three of the ¹ H pulse and the two all other nuclides pulse + phase, the three of the ¹ H pulse of the first of the ¹ H pulse by the - phase A second pulse sequence to invert and apply, a third pulse sequence to invert only the first other nuclide pulse of the two other nuclide pulses to -phase and apply, the first ¹ H pulse and the first 2. The magnetic resonance diagnostic apparatus according to claim 1, wherein a fourth pulse sequence in which only the other nuclide pulse is inverted to the negative phase and applied is executed. 3. A ^first pulse sequence in which all of the three ¹ H pulses and the two other nuclide pulses are applied in a positive phase, and only the last other nuclide pulse of the two other nuclide pulses is in a negative phase. a second pulse sequence for inverting and applying, said three of the ¹ H pulse of the first of the ¹ H pulse only - and third pulse sequence to be applied in inverted phases,
2. The magnetic resonance diagnostic apparatus according to claim 1, wherein a fourth pulse sequence in which only the first ¹ H pulse and the last other nuclide pulse are applied in a negative phase is applied.