Magnetic resonance imaging method and system capable of measuring short "T2" signal components

Abstract: To keep the echo time (T E ) short as well as to minimize T₂-loss in the echo signal components, a novel spin echo method and system are realized. The magnetic resonance (MR) imaging method comprises the steps of: applying a slice-selecting gradient field (G S1 ) to a biological body (20) under medical examination located in a static field; applying a spin excitation pulse (90° pulse) to the biological body (20) while the slice-selecting gradient field (G S1 ) is being applied thereto; applying a refocusing pulse (180° pulse) to the biological body (20) after the application of the slice-selecting gradient field (G S1 ); applying to the biological body (20), a rephasing gradient field (G S2 ) having the same polarity of that of the slice-selecting gradient field (G S1 ) just after the application of the refocusing pulse (180° pulse); and acquiring a spin echo signal induced in a slice (VOI) of the biological body (20) excited by the spin excitation pulse (90° pulse) to obtain MR information of the excited slice (VOI). Furthermore, a magnetic resonance imaging system (100) comprises: first gradient field applying unit (3) for applying a slice-selecting gradient field (G S1 ) to a biological body (20) under medical examination located in a static field; first pulse applying unit (4) for applying a spin excitation pulse (90° pulse) to the biological body (20) while the slice-selecting gradient field (G S1 ) is being applied thereto; second pulse applying unit (4) for applying a refocusing pulse (180° pulse) to the biological body (20) after the application of the slice-selecting gradient field (G S1 ); second gradient field applying unit (3) for applying to the biological body (20), a rephasing gradient field (G S2 ) having the same polarity of that of the slice-selecting gradient field (G S1 ) just after the application of the refocusing pulse (180° pulse); and receiver unit (9:1) for receiving a spin echo signal induced in a slice (VOI) of the biological body (20) excited by the spin excitation pulse (90° pulse) to process MR information of the excited slice (VOI).

Description: The present invention generally relates to a magnetic resonance imaging method and a magnetic resonance imaging system for producing a spectroscopic image and an MR (magnetic resonance) image of a biological body under medical examination, such as a brain of a patient. More specifically, the present invention is directed to a specific spin echo method and a system using this specific spin echo method capable of acquiring short "T 2 " signal components contained in an MR signal. In the conventional MR spectroscopic imaging (referred to as an "MRSI"), there are provided typical two pulse sequences, namely the FID (free induction decay) method with utilizing the selective excitation, and the spin echo method. In accordance with the spectroscopic imaging by employing the known FID pulse sequence, one of the gradient fields along the orthogonal 3-axis directions is used as the slicing gradient field, whereas the remaining two fields as used as the phase-encoding gradient fields. Under such a gradient field relationship, the slicing gradient field is applied to a biological body under medical examination with an application of a selective 90° pulse, and then is ramped down and finally reaches a zero level. Furthermore, when the phase-encoding gradient fields are applied as the same as when the slicing gradient field for the rephasing purpose is applied, and the application of the phase-encoding gradient fields is accomplished, the FID signal is acquired. In this FID method, a time period from the center of the selective excitation 90° pulse until the acquisition of the FID signal, namely the delay time is prolonged, during which the above-described applications of the various gradient fields are carried out. Accordingly, the resultant spectrum contains a baseline distortion. Furthermore, there is another problem in this FID method that the longer the delay time becomes, the more of the FID signals of the short T 2 -relaxation time are lost, or attenuated. Also, in case of the spectroscopic imaging with use of the pulse sequence by the spin echo method, the following pulse sequence operation is carried out. That is, after a selective excitation 90° pulse has been applied to a biological body under medical examination and half of the echo time "T E " (namely, 1/2 T E = τ) has elapsed, a non-selective 180° pulse is applied thereto, and thereafter spin echo signals from the biological body are acquired after another half of echo time "T E " has elapsed. Although the relationship among the orthogonal 3-axis gradient fields of the spectroscopic imaging by this spin echo method is similar to that of the FID method, the spin echo signals are acquired just after 1/2 T E has elapsed since the non-selective excitation 180° pulse had been applied. In other words, the MR signal (spin echo signal) acquisition of the spin echo method starts earlier than the MR signal (FID signal) acquisition of the FID method. Moreover, in case of this spin echo method, since the dephasing phenomenon of the spin which happens to occur after the selective excitation 90° pulse due to the disturbance in uniformity of magnetic fields, can be rephased by the non-selective 180° pulse to acquire the spin echo signals, there is another merit that no baseline distortion is contained in the spin echo signal. However, when the spectroscopic imaging is performed by utilizing the pulse sequence of the conventional spin echo method, since the selective excitation slicing gradient field is first applied to the biological body, and thereafter the dephased spins caused by this slicing gradient field are compensated by applying the non-selective excitation 180° pulse, the overall echo time "T E " cannot be considerably shortened. Even if the application time duration of the selective excitation slicing gradient field would be shortened as much as possible, the overall echo time "T E " could be more or less shortened. As a consequence, since the total echo time "T E " is still long, the spin echo signals having short "T 2 " (spin-to-spin (relaxation) time would be lost, leading to low S/N ratios. For example, generally speaking, T 2 of water is approximately 100 milliseconds, whereas T 2 of γ-ATP is about 10 to 15 milliseconds, which could not be acquired at a practically acceptable signal level, or satisfying S/N ratio in the conventional spectroscopic imaging with employment of the pulse sequence of the conventional spin echo method. US-A-4 740 748 discloses a method of magnetic resonance imaging wherein nuclear spins are excited in an image area in a selected plane of an object by superimposing a sliceselection gradient along an axis and a 90° radio frequency pulse. Thereafter, an encoding pulse sequence is applied which is followed by a refocussing of the nuclear spins by a 180° radio frequency pulse. A rephasing of the nuclear spins may be achieved by either reversing the encoding gradient field between the 90° and 180° pulses, or by applying a rephasing gradient field after the 180° pulse. A.A. Maudsley et al.: "Spin Echo 31 P Spectroscopic Imaging in the Human Brain"; Magn. Res. Med. 14, pages 415 to 422 (1990), discloses a magnetic resonance imaging method wherein a spin excitation pulse is first applied to a biological body whereafter either only phase-encoding gradients without any refocussing pulse (180° pulse) are applied to the body, or a first half of the phase-encoding gradients is applied followed by a refocussing 180° pulse whereafter the second half of the phase-encoding gradients is applied. No slice-selecting gradient field is employed. The present invention has been made in an attempt to solve the above-described problems, and therefore, has an object to provide both of a novel MR imaging method and a novel MR imaging system capable of considerably shortening an echo time "T E " by employing an improved spin echo pulse sequence. Another object of the present invention is to provide a novel spectroscopic imaging method and also a novel spectroscopic imaging system capable of acquiring a spin echo signal having a very short "T 2 " (spin-to-spin relaxation) time at a practically acceptable S/N ratio without any baseline distortion. To achieve the above-described objects, a magnetic resonance imaging method, according to the present invention, comprises the steps as mentioned in claim 1. Furthermore, according to another aspect of the present invention, a magnetic resonance imaging system (100) comprises the features mentioned in claim 7. For a better understanding of the present inventive method as well as system, reference is made of the following description in conjunction with the accompanying drawings, in which: Fig. 1 is a conceptional diagram for an overall arrangement of an MR imaging system 100 according to a first preferred embodiment of the present invention; Fig. 2 is a schematic block diagram of the concrete circuit arrangement of this MR imaging system 100; Figs. 3A to 3D are timing charts for explaining a pulse sequence of a first specific spin echo method employed in the MR imaging system 100 used for spectroscopy imaging; Fig. 4 is an illustration for a volume of interest "VOI" and a region outside this VOI; Figs. 5A to 5D schematically illustrate transition of spin vectors in the specific spin echo method; Figs. 6A and 6B schematically represent attenuations of spin vectors according to both of the conventional and inventive spin echo methods; Figs. 7A to 7C are timing charts for explaining a pulse sequence of a second specific spin echo method employed in the MR imaging system 100 used for spectroscopy imaging; Fig. 8 schematically illustrates a waveform chart for explaining signal levels of echo signals acquired by the second specific spin echo method of Fig. 7; Fig. 9 represents chemical shift data of 31 P acquired by utilizing the second specific spin echo method of Fig. 7; and Figs. 10A to 10D are timing charts for explaining a pulse sequence of a third specific spin echo method employed in the MR imaging system 100 used for MR imaging. Fig. 1 schematically represents an overall arrangement of an MR (magnetic resonance) imaging system 100 with employment of a first specific spin echo method according to a first preferred embodiment of the present invention. As shown in Fig. 1, the first MR imaging system 100 mainly comprises a computer unit 1, a sequence controller 2, a power source 3 for generating gradient fields, an RF pulse transmitter 4, an echo pulse receiver 9 and a display unit 10. Under control of this computer unit 1, the sequence controller 2 executes a predetermined sequence operation of various circuit arrangements. A biological body 20 under medical examination such as a patient is located within a static field generated by a main magnet unit 5. Both of a selective excitation 90° pulse and a non-selective excitation 180° pulse are applied from the transmitter 4 as an RF pulse via a transmitter coil 6 to the biological body 20 under control of the sequencer 2 (will be discussed in detail). Also, gradient fields in the orthogonal 3-axis directions (namely, X-axis, Y-axis and Z-axis) are applied from the power source 3 for generating gradient fields via a gradient coil 7 to the biological body 20 under control of the sequence controller 2. An MR signal (spin echo signal) induced in the biological body 20, for instance, a brain of a patient is received by a receiver coil 8 and thereafter detected by the detector 9. Then, the detected spin echo signal is supplied to the computer unit 1 so as to acquire chemical shift information in case of spectroscopic imaging. Accordingly, a spectroscopic image is displayed on the display unit 10 based on this acquired chemical shift information. Furthermore, in case of MR imaging, an MR image is reconstructed from the detected spin echo signal in the computer unit 1 and displayed on the display unit 10. INTERNAL ARRANGEMENT OF MR IMAGING SYSTEM In Fig. 2, there is shown an internal arrangement of the above-described MR imaging system 100 of Fig. 1. As represented in Fig. 2, and RF pulse amplifier 14 is connected between the RF pulse transmitter 4 and the transmitter coil 6 so as to amplify the RF pulses. A preamplifier 19 is connected between the receiver 9 and the receiver coil 8 in order to amplify the MR signals (spin echo signals) received from the receiver coil 8. Both of these RF pulse transmitter 4 and receiver 9 are controlled by the sequence controller 2 under control of the computer unit 1. The above-described gradient field coil 7 is constructed of three orthogonal-field coils Gx-coil 7X, Gy-coil 7Y and Gz-coil 7Z, and similarly the power source 3 for generating gradient fields is arranged by three gradient-field transmitters 3X, 3Y, 3Z and three gradient-field amplifiers 13X, 13Y and 13Z. These gradient-field transmitters 3X, 3Y and 3Z are controlled by the sequence controller 2 under control of the computer unit 1. FIRST SPECIFIC SPIN ECHO METHOD As previously explained, the MR imaging system 100 according to the first preferred embodiment of the present invention utilizes a first specific spin echo method. A pulse sequence of this specific spin echo method is represented in Figs. 3A to 3D. Under control of the sequence controller 2 shown in Figs. 1 and 2, the pulse sequence of the first specific spin echo method is executed as follows: When a selective excitation 90° pulse of Fig. 3A is applied to the biological body 20 (see Fig. 1), a slicing gradient field "G S1 " is applied thereto (see Fig. 3B) from the gradient field generating power source 3 under such a condition that a static field is being applied to this biological body 20. Then, when this slicing gradient field "G S1 " is ramped down and thereafter reaches a zero level of the field strength at a time "t G ", a non-selective excitation 180° pulse is applied to the biological body 20 so as to refocus the spins (will be described in detail). Since the non-selective excitation 180° pulse is applied immediately after the application of the selective excitation 90° pulse has been applied and the strength of the slicing gradient field "G S1 " becomes zero, an entire echo time "T E " can be cosiderably shortened as compared with the conventional echo time. That is, this entire echo time "T E " of the first specific spin echo method is defined by ("τ" + "τ") as shown in Fig. 3A. Since such a shorter echo time "T E " is realized, various spins having very short "T 2 " times can be detected at practically acceptable signal levels. In other words, although such spins having very short "T 2 " times could not be acquired in the conventional MR imaging system, they can be sufficiently acquired in the MR imaging system 100 according to the present invention by utilizing the first specific spin echo pulse sequence. Also, according to the first specific spin echo method, another slicing gradient field "G S2 " having the same polarity as that of the first-mentioned slicing gradient field "G S1 " is applied to the biological body 20 just after the above-described non-selective excitation 180° pulse is applied, namely at a time "t c " shown in Fig. 3B. As a result, the spins are rephased and the slicing gradient field "G S1 " applied during the selective excitation can be compensated by applying the slicing gradient field "G S2 ". In addition, if either a first encoding gradient field "G E1 ", or a second encoding gradient field "G E2 ", otherwise both of these first and second encoding gradient fields "G E1 " and "G E2 " are applied to the biological body 20 at the same time when the slicing gradient field "G S2 " for the compensation purpose is applied thereto, 3-D (dimensional) spectroscopy and 3-D CS (chemical shift) imaging may be performed during a data acquisition time period (see Figs. 3A, 3C and 3D). DATA ACQUISITION FOR CHEMICAL SHIFT IMAGING Referring now to Figs. 4 and 5, transition of spin vectors located within a volume of interest "VOI" and outside this "VOI" will be explained. The spin vector behavior according to the first specific spin echo method is performed as follows: When the selective excitation 90° pulse of Fig. 3A is applied to the spin of the biological body 20 (Fig. 5A 1 ), the phase shift caused by the slicing gradient field "G S1 " is produced in the condition of the spin as shown in Fig. 5A 2 . Moreover, this spin condition of Fig. 5A 2 is changed into another spin condition of Fig. 5A 3 due to dephasing by the effects of field inhomogeneity within 1/2 T E (= τ). When the spin condition is brought into such a condition as shown in Fig. 5A 3 , the non-selective excitation 180° pulse is applied to reverse the polarity of the spin as represented in Fig. 5B. Subsequently, when the next (compensating) slicing gradient field G S2 is applied (see Fig. 3B), the spin condition of Fig. 5B is changed into another spin condition of Fig. 5C, namely the spins are rephased. Thereafter, the spin is refocused to induce the echo signals during the data acquisition period (see Figs. 3B and 5D). Generally speaking, as a result of the spin behaviour, the net vector value of the spin caused by the spin precession is reduced in accordance with the "T 2 " relaxation time. Accordingly, as previously explained, since the total echo time "T E " of the present invention is considerably shorter than that of the conventional spin echo method, reduction of the net spin vector value is not so large, as compared with that of the conventional spin echo method. This advantage of the present invention will now be visually explained with reference to Figs. 6A and 6B. As illustrated in Fig. 6A, with regard to a spin having a constant relaxation time "T 2 ", for instance, when τ 1 = 2 msec (i.e., echo time T E = 2τ 1 = 4 msec), a strength of an echo signal acquired by the first specific spin echo method of the present invention is attenuated from one point "A" to another point "B" on the Y axis during a time period of "τ 1 " (2 msec) in accordance with the relaxation time "T 2 ". To the contrary, as shown in Fig. 6B, when τ = 4 msec (i.e., echo time T E = 2τ 2 = 8 msec), a strength of an echo signal acquired by the conventional spin echo method is further attenuated from one point "A" via the previous point "B" to another point "C" during a time period of τ 2 (4 msec). As a consequence, the signal to noise (S/N) ratio according to the present invention can be considerably improved, as compared with that of the conventional spin echo method. For instance, in case of ATP (Adenosin Triphosphate) whose relaxation time "T 2 " is equal to 15 msec, signal strengths of echo signals acquired by the inventive method and the conventional method, respectively, are considerably different from each other as follows: Assuming now that the echo time "T E " of the present invention is selected to be 4 msec, and "T E " of the conventional method is selected to be 8 msec, the signal strength "SS" is given by the following equation (1) : SS = Ae -2τ/T2 Then, in case of "T E " = 4 msec (present invention), SS 1 = Ae -4msec/15msec = 0.77 In case of "T E " = 8 msec (conventional method), SS 2 = Ae -8msec/15msec = 0.59 where symbol "A" is an amplitude of an echo signal and selected to be "1" in this calculation. As apparent from the above-described equations (2) and (3), assuming now that the noise levels are equal to each other in both of the spin echo methods, the S/N ratio achieved by the first spin echo method of the present invention can be increased by approximately 30% with regard to ATP having T E = 15 msec. Furthermore, since the echo signals are acquired by way of the first spin echo method, no correction is required for the baseline distortion. SECOND SPECIFIC SPIN ECHO METHOD Referring now to Figs. 7 and 9, a second specific spin echo method according to the present invention will be described. Figs. 7A to 7C represent a pulse sequence of this second specific spin echo method. This second specific spin echo method is constructed by three sets of pulse sequences. That is, Fig. 7A represents a first pulse sequence which is identical to the pulse sequence of the first specific spin echo method (see Fig. 3). Fig. 7B indicates a second pulse sequence and Fig. 7C denotes a third pulse sequence. A series of this second specific spin echo method will now be explained, which is similar to the known CPMG (Carr-Purcell-Meiboom-Gill) method except for the application timing of the rephasing gradient field "Gs". First of all, the first pulse sequence (one 180° - pulse application) shown in Fig. 7A is carried out with respect to the biological body 20 in the MR imaging system 100 (see Fig. 1). Since the operation of this first pulse sequence is the same as that of the first specific spin echo method, no further explanation is made in the following description. After a preselected time period has elapsed, the second pulse sequence (two 180° -pulses application) shown in Fig. 7B is carried out with respect to the same biological body 20. As seen from Fig. 7B, after a first non-selective excitation 180° pulse has been applied to the biological body 20 and the rephasing compensation gradient field G S2 is applied thereto, a second non-selective excitation 180° pulse is applied thereto with having a time interval of 2τ. Subsequently, after the first and second encoding gradient fields "G E1 " and "G E2 " have been applied, the spin echo signals are acquired within the second echo data acquisition period "ACQ 2 ". Similarly, after a predetermined time period has passed from the second echo data acquisition ACQ 2 , the third pulse sequence (three 180° -pulses application) shown in Fig. 7C is performed with respect to the same biological body 20. As seen from Fig. 7C, three non-selective excitation 180° pulses are sequentially applied to the biological body 20 with a time interval of "2τ". After applying the third 180° pulse and the encoding gradient fields "G E1 ", "G E2 " have been applied, the third echo data acquisition period "ACQ 3 " is commenced. As previously explained, according to the second specific spin echo method, the echo times T E1 to T E3 are successively prolonged. The signal strength of the echo signal acquired under the longer echo time, e.g., T E3 is attenuated, or lower, as compared with the signal strength of the echo signal acquired under the shorter echo time, e.g., T E1 , as represented in Fig. 8. As a consequence, taking account of the above-described signal strength relationship with the echo time T E , T 2 values of the respective signal components derived from the biological body 20 can be precisely calculated. Therefore, there is such an advantage that although such shorter T 2 values could not be detected by utilizing the long echo time of the conventional spin echo method, these shorter T 2 values can be sufficiently detected by employing the second specific spin echo method. For instance, when a chemical shift of phosphorus ( 31 P) contained in a brain of the biological body 20 is measured, the second spin echo method is performed in the MR imaging system 100 shown in Fig. 1. Then, as represented in Fig. 9, various components of phosphorus ( 31 P) having various short "T 2 " times, e.g., γ-ATP, α-ATP and β-ATP can be measured as the chemical shift information (echo pulses) in the computer unit 1 of Fig. 1. It should be noted that since such a pulse sequence of the second specific spin echo method can be easily produced from the pulse sequencer 2 by utilizing the known computer program, no further explanation thereof is made in the specification. Also, the number of 180° pulses may be arbitrarily varied in accordance with the inventive idea of the second specific spin echo method. MR IMAGING In the above-described first and second preferred embodiments, the first and second specific spin echo methods have been employed so as to perform spectroscopic imaging. The present invention is not limited to this spectroscopic imaging, but may be applied to MR imaging. A method to acquire an MR image according to a third specific spin echo method of the present invention will now be summarized with reference to a timing chart of Fig. 10. As seen from Figs. 10A and 10B, the RF pulses (90° and 180° pulses) and the slicing gradient field G S (G S1 and G S2 ) are applied to the biological body 20 in a similar manner to that of the first specific spin echo method (see Figs. 1A and 1B). In accordance with the third specific spin echo method, when the phase encoding gradient field G E is applied, a reading gradient field G R is also applied as shown in Figs. 10C and 10D at the same timing. Such a pulse sequence of the application of both gradient fields G E and G R is repeatedly performed to obtain MR image data. It should be noted that since all of the echo signals cannot be acquired in accordance with the third specific spin echo method, the following specific process is executed. That is, after the non-selective excitation 180° pulse has been applied to the biological body 20, the reading gradient field G R is ramped down in a negative direction (i.e., "-G R ") and thereafter intersects with a baseline, and furthermore is ramped up toward a positive direction (i.e., "+G R ") during a time period "T R " from the end of the 180° pulse to the end of the encoding gradient field G E . As a result, a half or more echo pulses among the entire echo pulse can be successively acquired so that desirable MR images can be obtained in accordance with the third specific spin echo method of the present invention.

Claims: A magnetic resonance (MR) imaging method comprising the steps of: applying a spin excitation RF pulse to a biological body (20) under medical examination being located in a static magnetic field to excite a volume of interest therein; applying a refocusing RF pulse to said biological body; applying a phase encoding magnetic field gradient to said biological body; acquiring a spin echo signal induced in said volume of interest to obtain MR information of said volume of interest; characterized in that : said spin excitation RF pulse is applied together with a slice-selecting magnetic field gradient; said refocusing RF pulse is applied immediately after the application of said slice-selecting magnetic field gradient and before any application of said phase encoding magnetic field gradient; after the application of said refocusing RF pulse, a rephasing magnetic field gradient is applied to said biological body along the same axis as said slice-selecting magnetic field gradient and with the same polarity as said slice-selecting magnetic field gradient. An MR imaging method as claimed in claim 1, wherein said refocusing pulse applying step includes the step of: applying said refocusing pulse (180° pulse) immediately after the application of said slice-selecting gradient field (G S1 ). An MR imaging method as claimed in claim 1, wherein said refocusing pulse applying step includes the steps of: applying a first refocusing pulse as said refocusing pulse immediately after the application of said slice-selecting gradient field (G S1 ); and additionally applying a series of refocusing pulses to the biological body (20) at the substantially same first time interval (2τ) after the application of the first refocusing pulse; and also said rephasing gradient field applying step includes the step of: applying said encoding gradient field (G E1 , G E2 ) immediately after the application of said series of refocusing pulses (180° pulse) has been completed. An MR imaging method as claimed in claim 3, wherein said first time interval (2τ) between the successive refocusing pulses (180° pulse) is two times longer than a second time interval (τ) between said spin excitation pulse (90° pulse) and said first refocusing pulse (180° pulse). An MR imaging method as claimed in claim 3 or 4, wherein when said rephasing gradient field (G S2 ) has been applied to the biological body (20), chemical shift information about said excited slice (VOI) is acquired by processing said spin echo signal induced in said slice (VOI) of the biological body (20) excited by said spin excitation pulse (90° pulse). An MR imaging method as claimed in any of claims 1 to 5, further comprising the steps of: applying a phase-encoding gradient field (G E ) to said biological body (20); and applying a signal-reading gradient field (G R ) to said biological body (20) at the substantially same time when said phase-encoding gradient field (G E ) is applied in such a manner that the polarity of said signal-reading gradient field (-G R ) has, at first, a negative value, whereafter said signal-reading gradient field (-G R ) is changed so that it thereafter intersects with a baseline and then is directed toward a positive polarity (+G R ). A magnetic resonance (MR) imaging system (100) comprising: first gradient magnetic field applying means ( 3Z ) for applying a slice-selecting gradient magnetic field and a rephasing gradient magnetic field to a biological body (20) under medical examination located in a static magnetic field; second gradient magnetic field applying means (3Y) for applying a phase-encoding magnetic field gradient to said biological body; RF pulse applying means (4) for applying a spin excitation RF pulse and a refocusing RF pulse to said biological body (20); means (9, 1) for receiving a spin echo signal induced in a volume of interest of said biological body 20) excited by said spin excitation RF pulse and refocused by said refocusing RF pulse and for processing said received spin echo signal; characterized in that : said first gradient magnetic field applying means (3Z) and said RF pulse applying means (4) are arranged to apply said slice-selecting gradient magnetic field together with said spin excitation RF pulse; said RF pulse applying means (4) and said second gradient magnetic field applying means (3Y) are arranged to apply said refocusing RF pulse immediately after the application of said slice-selecting magnetic field gradient and before any application of said phase encoding magnetic field gradient; said first gradient magnetic field applying means (3Z) is further arranged to apply said rephasing magnetic field gradient along the same axis as said slice-selecting magnetic field gradient, with the same polarity as said slice-selecting magnetic field gradient, and after the application of said refocusing RF pulse. An MR imaging system (100) as claimed in claim 7, wherein said second pulse applying means (4) applies said refocusing pulse (180° pulse) immediately after the application of said slice-selecting gradient field (G S1 ) under control of a sequence controller (2). An MR imaging system (100) as claimed in claim 7, wherein said second pulse applying means (4) is operated under control of a sequence controller (2) to firstly apply a first refocusing pulse immediately after the application of said slice-selecting gradient field (G S1 ), and subsequently to apply a series of refocusing pulses to the biological body (20) at the substantially same time interval (2τ) after the application of the first refocusing pulse; and said rephasing gradient field applying means (3) applies said encoding gradient field (G E1 , G E2 ) immediately after the application of said series of refocusing pulses (180° pulse) has been completed. An MR imaging system (100) as claimed in claim 9, wherein said first time interval (2τ) between the successive refocusing pulses (180° pulse) is two times longer than a second time interval (τ) between said spin excitation pulse (90° pulse) and said refocusing pulse (180° pulse). An MR imaging system (100) as claimed in claim 9, wherein when said rephasing gradient field (G S2 ) has been applied to the biological body (20) by said rephasing gradient field applying means (3), chemical shift information about said excited slice (VOI) is acquired in said receiving means (9:1) by processing said spin echo signal induced in said slice (VOI) excited by said spin excitation pulse (90° pulse). An MR imaging system (100) as claimed in any of claims 7 to 11, further comprising: second gradient field applying means (3) for applying a phase-encoding gradient field (G E ) to said biological body (20); and third gradient field applying means (3) for applying a signal-reading gradient field (G R ) to said biological body (20) at the substantially same time when said phase-encoding gradient field (G E ) is applied in such a manner that the polarity of said signal-reading gradient field (-G R ) has, at first, a negative value, whereafter said signal-reading gradient field (-G R ) is changed so that it thereafter intersects with a baseline and then is directed toward a positive polarity (+G R ). An MR imaging system (100) as claimed in any of claims 7 to 12, wherein said first and second pulse applying means includes a spin excitation pulse transmitter (4), a spin excitation pulse amplifier (14), and a transmitter coil (6). An MR imaging system (100) as claimed in any of claims 7 to 13, wherein said signal receiving means includes a receiver (9), a preamplifier (19), and a receiver coil (8), and also a computer unit (1). An MR imaging system (100) as claimed in any of claims 7 to 14, wherein said first and second gradient field applying means (3; 4) include at least three transmitters (3X, 3Y, 3Z), three amplifiers (13X, 13Y, 13Z), and three coils (7X, 7Y, 7Z).

Inventors: MIYAZAKI MITSUE, MIYAZAKI, MITSUE
Applicants: TOSHIBA KK, KABUSHIKI KAISHA TOSHIBA
Application year: 1992
Main classification: G01R33
IPC codes: G01R33, A61B5