NUCLEAR MAGNETIC RESONANCE DIAGNOSTIC APPARATUS

Abstract: In an NMR diagnostic apparatus, it is desirable to obtain a scanogram of an imaginarily cross-sectionally sliced portion (S) of a patient (P), which has a high spatial resolution. The specific nucleus of the patient (P) is first excited by receiving the 90° pulse (H₁) under the influence of the first linear gradient field (G₂). The spin of the excited sliced portion (S) of the patient (P) is secondly warped by the linear gradient field (G z ), the field strength of which is determined by the given equation (3). Under the influence of the warping linear gradient field (G z ), another linear gradient field (G xy ) is superimposed thereto. Finally NMR signals are derived from the excited sliced portion (S) and thus are processed by Fourier transformation so as to obtain the scannogram.

Description: The present invention relates to a nuclear magnetic resonance diagnostic apparatus (referred to as an "NMR" hereinafter) for imaging as a two-dimensional projection image (referred to as a "scanogram" hereinafter) a specific nucleus spin density distribution present in an object to be examined, e.g., a patient (referred to as a "patient"), in two directions by using the NMR phenomenon. To obtain a scanogram by means of a conventional diagnostic apparatus utilizing the NMR phenomenon, one-dimensional projection data (referred to as a "PD" hereinafter) has been used. As is known, the "scanogram" is utilized to determine which portion of an object such as a diseased portion the NMR images are taken for, before a plurality of the formal NMR images are taken for diagnostic purpose. To obtain the PD, a uniform static magnetic field H₀ is applied to the patient along the z-axis, and a linear gradient magnetic field (referred to as a "linear gradient field") G z generated by a pair of gradient magnetic field generating coils 1A and 1B is superimposed to the static field H₀ along the z-axis, as shown in Fig. 1. A specific nucleus with regard to the static field H₀ resonates at an angular frequency ω₀ given by the following formula: ω₀ = γH₀ (1) where γ is a gyromagnetic ratio and is inherently determined by individual specific nucleus. A rotating magnetic field, or an RF pulse H₁ having so an angular frequency ω₀ as to resonate only the specific nucleus is applied via a pair of transmitter coils 2A and 2B to the shown x-y plane of the patient P defined by the above-mentioned linear gradient field G z , so that the NMR phenomenon occurs only in a cross-sectionally sliced portion S (referred to a "sliced portion") of the patient, which is taken for tomographic images. This sliced portion is regard as a flat portion, but it has a thickness indeed. The NMR phenomenon is observed by an NMR signal, e.g., a free induction decay signal (referred to as a "FID signal") through a pair of receiver coils or probe head coils 3A and 3B. This FID signal is subjected to Fourier transformation, thereby obtaining a single spectrum with respect to a rotating frequency of the specific nucleus spin. To obtain a projection image in a predetermined direction in the x-y plane of the sliced portion S, the sliced portion S is excited to cause the NMR phenomenon. Thereafter, a magnetic field G xy having a linear gradient along the X'-axis is superimposed to the static field H₀. This X'-axis is obtained by rotating the x-axis toward the y-axis through a given angle ϑ. Equivalent field lines E in the sliced portion S of the patient P then become straight, and the rotating frequency of the specific nucleus spin on the equivalent field line E is expressed by the above equation (1). For illustrative convenience, it is assumed that signals D₁ to D n similar to the FID signal are produced from the equivalent field lines E₁ to E n , respectively. The amplitudes of the signals D₁ to D n are proportional to the nucleus spin densities on the equivalent field lines E₁ to E n respectively extending through the sliced portions. In practice, however, the obtained FID signal is a sum of those signals D₁ to D n or is a composite FID signal. When the composite FID signal is processed by Fourier transformation, a PD (one-dimensional projection image) is obtained by a projection of the sliced portion S along the x'-axis. When successive PDs are obtained by continuously changing and projecting the sliced portion, a scanogram SG is obtained as shown in Fig. 3. To realize a satisfactory spatial resolution of the scanogram SG in the longitudinal direction of the patient P, many projections must be performed under the conditions that the slice thickness must be very thin and any space between the adjacent sliced portions must be eliminated. However, in general, a shift of the sliced portion is performed by mechanically moving the patient P in the longitudinal direction Z. As a result, a mechanism of a patient moving device (not shown) becomes complex. Furthermore, as the level of the FID signal is proportional to the quantity of excited magnetization. The thinner, the slice thickness becomes, the smaller, the FID signal becomes. As a result, a signal to noise ratio (referred to as an "S/N" ratio hereinafter) is significantly lowered. To improve the S/N ratio, the same sliced portion must be repeatedly examined from the same projection direction. As a result, projection time is prolonged, though a PD for only one sliced portion is obtained. Prior art document PHYSICS IN MEDICINE AND BIOLOGY, Volume 25, May 1980, W. EDELSTEIN et al. "Spin warp NMR imaging and application to human whole-body imaging" pages 751-756, discloses a spin warp NMR imaging apparatus for whole body imaging in which a magnet produces a static field, and a 90° pulse is simultaneously applied with a gradient magnetic field to a body under investigation: A narrow band RF pulse is applied to the body along with the application of a magnetic field gradient. In this apparatus, phase-encoding is performed in the direction vertical along the static field and not in the longitudinal direction of the patient. It is a primary object of the present invention to provide a diagnostic apparatus by utilizing the nuclear magnetic resonance phenomenon, wherein, no relative mechanical transportation between the object to be examined and the NMR diagnostic apparatus is required to obtain a scanogram of an object to be examined. It is a secondary object of the present invention to provide the NMR diagnostic apparatus in which only a short projection time is required to obtain the scanogram image having a high spatial resolution. These objects may be accomplished by providing a diagnostic apparatus utilizing nuclear magnetic resonance techniques as defined in anyone of claims 1 to 3. The present invention may be best understood with reference to the accompanying drawings in which: Fig. 1 is a schematical diagram of a fundamental construction of an NMR diagnostic apparatus; Fig. 2 schematically shows a fundamental diagram for explaining how to obtain projection data by means of the NMR phenomenon; Fig. 3 schematically shows a fundamental diagram for explaining how to obtain a scanogram by utilizing a one-dimensional projection image; Fig. 4 illustrates a basic configuration for explaining an embodiment of the present invention; Figs. 5A to 5C are schematic diagrams for explaining the moment of magnetization; Fig. 6 is a first operation waveform diagram used in a preferred embodiment of the apparatus according to the invention; Fig. 7 is a second operation waveform diagram used in another preferred embodiment of the apparatus according to the invention; and Fig. 8 schematically shows a block diagram of the NMR diagnostic apparatus according to the invention. When the spin density distribution of a specific nucleus present in a patient P is given as f(x,y,z), and an RF field (generated by a 90° pulse H1) is applied through transmitter coils 2A and 2B, the motion of the net magnetization M in a region V excited by the 90° pulse, for which a scanogram is taken is expressed by the following equation if the relaxation times are negligible. It should be noted that the net magnetization M of a sample e.g., the sliced portion results from summing the individual magnetization vectors (referred to as "net magnetization M" hereinafter). M(x,y,z,t) = f(x,y,z) exp(jωt) (2) where M is a complex number representing the net magnetization, and f(x,y,z) which is generally expressed as a vector but is herein represented by a complex number for the sake of simplicity, is a real number representing the nuclear spin density, j is the imaginary unit (= √ -1 ), ω is the angular frequency of the rotating magnetization which is obtained by equation (1) above, and t is the time which is represented by a real number. A gradient field G z (t) is applied to the patient P along the z-axis of the steady field, so as to satisfy equation (3): where γ is the gyromagnetic ratio of the specific nucleus, ℓ is the typical length of the patient P in the longitudinal direction thereof corresponding to the length of the transmitter coils 2A and 2B arranged in the longitudinal direction thereof (see Fig. 4), ξ is any constant indicating an angle (radian) excluding zero, and n is a variable. When G z (t) is given as a sinusoidal curve gzsin(π/τz)t for n = 1, equation (3) can be satisfied by changing the coefficient gz. Individual magnetizations m shown in Fig. 5A tend to incline along the same direction in response to the 90° pulse, as shown in Fig. 5B (the rotating field rotates at the angular frequency given by equation (2)). However, when a positive gradient field G z is applied along the z-axis of the steady field H₀, the magnetic strength at point Z E becomes greater than that at point Z S , so that the angular frequency of the rotating field is increased. It should be noted that the point Z S indicates the starting point along the z-axis and the point Z E indicates the ending point along the z-axis. However, since the gradient field G z is applied only for time τz (referred to Figs. 6 and 7), when the application of the gradient field G z is interrupted, the magnetization "m" at the points Z S and Z E rotate at the same angular frequency (referred to Fig. 5B). However, each magnetization "m" has a phase difference indicated by an angle  as follows:  = ξ(Z/ℓ) (4) where ξ and ℓ denote the same factors as in equation (3). When the gradient field G z is applied along the z-axis for the given time τz, the magnetic field is warped, as shown in Fig. 5C. In this case, the motion of the individual magnetisation "m" is given as follows: M(x,y,z,t) = C·f(x,y,z) exp{j + (ωt + n)} (5) where M, f, j, ω and t denote the same factors as in equation (2), n denotes the same factor as in equation (3), and C is a constant of proportionality. By using the angle , the signal obtained along the z-axis (i.e., along the longitudinal direction of the patient P) can be separated to obtain the scanogram (two-dimensional projection image). In the same manner as described with the conventional method, when the gradient field G xy is applied to the steady field H₀ along the x'-axis which forms the angle ϑ with respect to the x-axis (see Fig. 2), the FID signal is obtained as follows: where K is the constant of proportionality. According to equations (1) and (4), ω(x') = γG xy x' and (Z) = (ξ/ℓ)Z are given, and equation (6) can be rewritten as follows: A scanogram Sg(x',Z) can be given as follows: Equation (6') can be rewritten in accordance with equation (7) as follows: The scanogram Sg(x',Z) can be obtained by two-dimensional Fourier-transform of F(t,n) (equation (8)) by: The FID signal is collected such that the value of ξ in equation (3) is amplified to have a value sufficiently indicating a change of Fd(t,n) along the nth direction where n is an integer (-N,..., -2, -1, 0, 1, 2,..., N). The field application method will be summarized with reference to Fig. 6. The linear gradient field G z is applied along the z-axis in the first step in such a manner that a specific nucleus in a sliced portion of the patient P is excited by a 90° pulse having a predetermined frequency component. In the second step, the linear gradient field G z satisfying equation (3) is applied to the sliced portion. That is, this linear gradient field has such a feature that the strength of magnetization changes in accordance with the value obtained by equation (3), as indicated by the dotted line. At the same time, a negative composite gradient field G xy is also applied to generate the NMR signal after time τs of the third step has passed from end of the second step. Although this field is not directly associated with the principle of the present invention, it must be used in practice. The individual magnetization m in the sliced portion excited by the gradient field G z applied during the time period τ Z represents "the warp phenomenon". The excitation of the magnetization in the first step may be alternatively performed by applying a 90° impulse, as shown in Fig. 7. When the NMR or FID signals are collected, therefore, the entire sliced portions for which a scanogram is taken can be excited by the magnetic fields, so that a good S/N ratio can be achieved. Accordingly if the signal collection conditions are not changed in case of the present embodiments, it is not necessary to introduce any measure to improve the S/N ratio, with the result that the total projection time can be shortened as compared to that of the conventional method. Furthermore, the phase data of the magnetization is used to separate images obtained in the longitudinal direction of the patient P, so that the patient need not be moved with respect to the diagnostic apparatus, thereby obtaining a scanogram which covers a wide area of the patient. Fig. 8 shows a circuit configuration of an apparatus for practicing the NMR measuring method described above. A transmitter unit 10 will first be described. The transmitter unit 10 includes an oscillator (not shown) to generate an RF pulse H1 having a carrier wave with a center frequency of 4.258 MHz (corresponding to a magnetic field of 0.1T (1,000 gauss) for a hydrogen nucleus). The RF pulse is amplitude-modulated by a SINC function to obtain the RF pulse H1. This RF pulse H1 is applied to a tuner 12. The tuner 12 selects the RF pulse (90° pulse) having a specific frequency so as to tune the pulse width which is tuned to a specific nucleus of the patient P, and applies through the probe head coils 3A and 3B the 90° pulse to the given sliced portion to be exited of the patient P. On the other hand, the static field H₀ generated by a magnet 30 is applied to the patient P in a predetermined direction, as previously explained. Under such conditions, the gradient field G z and the composite gradient field G xy are applied through the coil pairs 1A, 1B and 2A, 2B respectively at predetermined field strength and application timings. The application timings can be controlled by a central control unit 14. The detection, collection and processing of the NMR signals from the patient P will now be described. After an application of the composite gradient fields G xy , NMR signals are obtained by the excited sliced portions S of the patient P through the receiver coils 3A and 3B. The signals are amplified by a pre-amplifier 16 through the tuner 12, and amplified signals are then detected by a detector 18. Output signals from the detector 18 are again amplified by an amplifier 20 to a predetermined level. Only the signal components of these amplified signals within a required band are filtered by a low-pass filter (LPF) 22. The filtered signal components are converted by an A/D converter 24 into digital signals. These digital signals are supplied to an arithmetic logic unit 26 which performs Fourier transformation and various types of operations as indicated by the equations previously described, thereby obtaining a scanogram. The scanogram is then monitored on a display device 28. According to the present invention, there is provided a diagnostic apparatus by utilizing the nuclear magnetic resonance phenomenon, wherein the spin density distribution of the specific nucleus in the patient can be imaged as a scanogram having a sufficient spatial resolution with respect to the longitudinal direction of the patient without performing a relative mechanical transportation of the patient with respect to the diagnostic apparatus in requiring a short projection time.

Claims: An apparatus for examining an object (P) by nuclear magnetic resonance comprising: magnetic means (30) for applying to the object (P) a static magnetic field (H₀); first coil means (1A; 1B) which is arranged along a longitudinal axis (z) of the object (P) and is energized so as to apply to the object (P) a first gradient magnetic field (G z ), the field direction of the first gradient magnetic field (G z ) being parallel to that of the static magnetic field (H₀) and the field strength thereof changing linearly in an opposite manner along the longitudinal axis (z); probe head coil means (3A; 3B) for applying selective RF pulses (H₁) to the object (P) so as to excite nuclear spins in a measurable volumic region of the object (P), and for detecting nuclear magnetic resonance signals derived from said measurable volumic region of the object (P); second coil means (2A; 2B) for applying a second gradient magnetic field (G xy )to the object (P) so as to define a projection angle of the nuclear magnetic resonance signals, the field direction of the second gradient magnetic field (G xy ) being parallel to the static magnetic field (H₀) and the strength of the second gradient magnetic field (G xy ) being gradient at a right angle with respect to the first gradient magnetic field (G z ) and changing linearly in an opposite manner along an axis (x') perpendicular to the longitudinal axis (z); a central control unit (14) for controlling application timings of the non-selective RF pulses (H₁), the first gradient magnetic field (G xy ) of the object (P) under the static magnetic field (H₀) and the strength of the first gradient magnetic field (G z ), so as to repeat a predetermined sequence while changing the strength of the first gradient magnetic field (G z ) for phase-encoding, the predetermined sequence including a first period for which the selective RF pulses (H₁) for exciting a nuclear magnetic resonance, and the first gradient magnetic field (G z ) for determining an imaging region are applied of the object (P), a second period for which the first gradient magnetic field (G z ) is applied to the object (P) for phase-encoding and a third period for which the second gradient magnetic field (G xy ) is applied of the object (P) for reading out the nuclear magnetic resonance signals; and an arithmetic logic unit (26) which receives the nuclear magnetic resonance signals obtained from said measurable volumic region of the object (P) through the probe head means (3A; 3B) during application periods of the second gradient magnetic field (G xy ) while repeating the predetermined sequence and executes the arithmetic logic operation on duration times and phase information of the nuclear magnetic resonance signals by use of two-dimensional Fourier transformation so as to obtain a two-dimensional projection image of the measurable volumic region of the object (P) with respect to the predetermined direction. An apparatus for examining an object (P) by nuclear magnetic resonance comprising: magnetic means (30) for applying to the object (P) a static magnetic field (H₀); first coil means (1A; 1B) which is arranged along a longitudinal axis (z) of the object (P) and is energized so as to apply to the object (P) a first gradient magnetic field (G z ), the field direction of the first gradient magnetic field (G z ) being parallel to that of the static magnetic field (H₀) and the field strength thereof changing linearly in an opposite manner along the longitudinal axis (z); probe head coil means (3A; 3B) for applying non-selective RF pulses (H₁) to the object (P) so as to excite nuclear spins in a measurable volumic region of the object (P), and for detecting nuclear magnetic resonance signals derived from said measurable volumic region of the object (P); second coil means (2A; 2B) for applying a second gradient magnetic field (G xy ) of the object (P) so as to define a projection angle of the nuclear magnetic resonance signals, the field direction of the second gradient magnetic field (G xy ) being parallel to the static magnetic field (H₀) and the strength of the second gradient magnetic field (G xy ) being gradient at a right angle with respect to the first gradient magnetic field (G z ) and changing linearly in an opposite manner along an axis (x') perpendicular to the longitudinal axis (z); a central control unit (14) for controlling application timings of the non-selective RF pulses (H₁), the first gradient magnetic field (G xy ) of the object (P) under the static magnetic field (H₀) and the strength of the first gradient magnetic field (G z ), so as to repeat a predetermined sequence while changing the strength of the first gradient magnetic field (G z ) for phase-encoding, the predetermined sequence including a first period for which only non-selective RF pulses (H₁) are applied to the object (P) for exciting a nuclear magnetic resonance, a second period for which the first gradient magnetic field (G z ) is applied of the object (P) for phase-encoding and a third period for which the second gradient magnetic field (G xy ) is applied of the object (P) for reading out the nuclear magnetic resonance signals; and an arithmetic logic unit (26) which receives the nuclear magnetic resonance signals obtained from said measurable volumic region of the object (P) through the probe head means (3A; 3B) during application periods of the second gradient magnetic field (G xy ) while repeating the predetermined sequence and executes the arithmetic logic operation on duration times and phase information of the nuclear magnetic resonance signals by use of two-dimensional Fourier transformation so as to obtain a two-dimensional projection image of the measurable volumic region of the object (P) with respect to the predetermined direction. An apparatus for examining an object (P) by nuclear magnetic resonance comprising: magnetic means (30) for applying to the object (P) a static magnetic field (H₀); first coil means (1A; 1B) which is arranged along a longitudinal axis (z) of the object (P) and is energized so as to apply to the object (P) a first gradient magnetic field (G z ), the field direction of the first gradient magnetic field (G z ) being parallel to that of the static magnetic field (H₀) and the field strength thereof changing linearly in an opposite manner along the longitudinal axis (z); probe head coil means (3A; 3B) for applying RF pulses (H₁) to the object (P) so as to excite nuclear spins in a measurable volumic region of the object (P), and for detecting nuclear magnetic resonance signals derived from said measurable volumic region of the object (P); second coil means (2A; 2B) for applying a second gradient magnetic field (G xy ) of the object (P) so as to define a projection angle of the nuclear magnetic resonance signals, the field direction of the second gradient magnetic field (G xy ) being parallel to the static magnetic field (H₀) and the strength of the second gradient magnetic field (G xy ) being gradient at a right angle with respect to the first gradient magnetic field (G z ) and changing linearly in an opposite manner along an axis (x') perpendicular to the longitudinal axis (z); a central control unit (14) for controlling application timings of the non-selective RF pulses (H₁), the first gradient magnetic field (G xy ) of the object (P) under the static magnetic field (H₀) and the strength of the first gradient magnetic field (G z ), so as to repeat a predetermined sequence while changing the strength of the first gradient magnetic field (G z ) for phase-encoding, the predetermined sequence including a first period for which RF pulses (H₁) are applied to the object (P) for exciting a nuclear magnetic resonance, a second period for which the first gradient magnetic field (G z ) is applied of the object (P) for phase-encoding and a third period for which the second gradient magnetic field (G xy ) is applied of the object (P) for reading out the nuclear magnetic resonance signals; and an arithmetic logic unit (26) which receives the nuclear magnetic resonance signals obtained from said measurable volumic region of the object (P) through the probe head means (3A; 3B) during application periods of the second gradient magnetic field (G xy ) while repeating the predetermined sequence and executes the arithmetic logic operation on duration times and phase information of the nuclear magnetic resonance signals by use of two-dimensional Fourier transformation so as to obtain a two-dimensional projection image of the measurable volumic region of the object (P) with respect to the predetermined direction. An apparatus for examining an object (P) by nuclear magnetic resonance as claimed in anyone of claims 1 to 3, characterized in that it further comprises: a tuner (12) which is coupled to the probe head coil means (3A; 3B) so as to apply the RF pulses (H₁) to the object (P) and receive the nuclear magnetic resonance signals; an amplifier (16) which is coupled via the tuner (12) to the probe head coil means (3A; 3B) and amplifies the nuclear magnetic resonance signals; a detector (18) which is connected to the amplifier (16) so as to detect the amplifier nuclear magnetic resonance signals; an analogue/digital converter (24) which is connected to the detector (18) so as to convert the detected nuclear magnetic resonance signals to be processed in the arithmetic logic unit (26); and a display device (28) which is connected to the arithmetic logic unit (26) so as to visually display the two-dimensional projection image of the cross-sectionally sliced portion (S) of the object (P).

Inventors: TAKASE, HIDETOMO
Applicants: KABUSHIKI KAISHA TOSHIBA
Application year: 1983
Main classification: G01R33
IPC codes: G01R33, A61B5, A61B10