Multiple-echo, multiple-view NMR angiography

• US 4,796,635 A
• Filed: 02/11/1987
• Issued: 01/10/1989
• Est. Priority Date: 02/11/1987
• Status: Expired due to Fees

• Current Assignee: General Electric Company
• Original Assignee: General Electric Company
• Inventors: Dumoulin, Charles L.
• Primary Examiner(s): SMITH, RUTH S
• Application Number:
  US07/013,592
• Time in Patent Office: 699 Days
• Field of Search: 128/653, 324/306, 324/307, 324/309
• US Class Current: 600/413
• CPC Class Codes: G01R 33/563 of moving material, e.g. flow contrast angiography

Abstract

Several sequences of radio-frequency and magnetic field gradients are presented for obtaining from a sample multiple response echo signals from which to obtain a plurality of independent angiograms, which can be combined or separately analyzed to provide more information than an individual angiogram, but in substantially the same amount of time as a single angiogram. For example, a series of angiograms, each with a different projection axis, can be obtained in the time required to obtain a single angiogram using a single echo method. If the view angle of each echo is the same, then the acquired angiograms can be added to enhance the signal-to-noise ratio. Anothe pulse sequence simultaneously obtains two or more angiograms, each sensitive to one of two orthogonal flow components of the overall blood flow, the angiograms are then added to give an angiogram which is sensitive to total flow in all directions. Multiple velocity ranges are accommodated in a fourth sequence form.

Claims

1. A method for acquiring a plurality of nuclear magnetic resonance (NMR) angiographic images of flowing material in at least a selected portion of a sample, comprising the steps of:

(a) immersing the sample in a main static magnetic field;

(b) nutating, in an initial part of each of a first sequence and a second sequence of a sequential pair of imaging sequences for each of a multiplicity S of regions of said selected sample portion, the spins of all nuclei of a selected species;

(c) applying a pair of alternating-polarity flow-encoding signal pulses in a first magnetic field gradient impressed upon the sample in a first direction selected to establish one axis of each of the NMR angiographic projection images, to cause a resulting NMR response echo signal from the spin of a moving nucleus to differ from the NMR response echo signal resulting from the spin of a substantially stationary nucleus;

each of the flow-encoding pulses in the first sequence of each pair having a polarity flow-encoding pulse in the second sequence of each pair;

(d) acquiring, responsive to a readout magnetic field gradient impressed upon the sample in a second direction, substantially orthogonal to the first direction, and varied to be different in each j-th one, where 1≦

j≦

N, of a plurality N of response data acquisition time intervals of a sequence, with the second direction being the same in each like-numbered j-th acquisition interval of both sequences of all sequence pairs, a set of data from the NMR response echo signal evoked, from the same sample portion, in each different one of the plurality N of acquisition time intervals of each of the first and sequences;

generating a dephasing pulse in the readout gradient prior to each of the N acquisition time intervals in each sequence;

generating a rephasing pulse in the readout gradient after each of the first (N-1) acquisition time intervals in each sequence; and

providing each rephasing pulse with substantially the same amplitude as the associated dephasing pulse;

(e) subtracting, for each different j-th one of the N different acquisition time intervals, the data acquired in the j-th acquisition interval of one sequence from the data acquired in the like-numbered j-th acquisition interval of the other sequence of each sequence pair, to generate a j-th one of N different-pair difference sets from which response data obtained from stationary nuclei has been substantially removed; and

(f) generating N different angiographic images, with the j-th image being generated from all of the j-th pair difference sets and with each j-th image lying in a plane having a preselected relationship with respect to the first direction and the different second direction for that j-th image.

2. The method of claim 1, wherein step (d) further comprises the step of timing the rephasing pulse after the end of one readout acquisition time interval to be substantially coincident with the dephasing pulse prior to the next readout acquisition time interval.

3. The method of claim 2, wherein step (d) further comprises the step of applying a projection-dephasing gradient signal in a third direction, substantially orthogonal to both the first and second directions, to enhance suppression and limit the dynamic range of the response signals evoked from the nuclei with substantially stationary spins.

4. The method of claim 3, further including the steps of:

providing the projection-dephasing gradient signal as a dephasing pulse, substantially coincident with the dephasing pulse of the readout gradient, followed by an associated dephasing pulse, with a substantially the same amplitude as, but of opposite polarity to, the associated rephasing pulse of the projection-dephasing gradient and temporally positioned substantially coincident with the dephasing pulse of the readout gradient.

5. The method of claim 1, wherein step (d) further comprises the step of applying a projection-dephasing gradient signal in a third direction, substantially orthogonal to both the first and second directions, to enhance suppression, and limit the dynamic range, of the response signals evoked from the nuclei with substantially stationary spins.

6. The method of claim 5, further including the steps of:

providing the projection-dephasing gradient signal as a dephasing pulse, substantially coincident with the dephasing pulse of the readout gradient, and a rephasing pulse, with substantially the same amplitude as, but of opposite polarity to, the associated dephasing pulse of the projection-dephasing gradient and substantially coincident with the dephasing pulse of the readout gradient.

7. The method of claim 1, wherein step (d) includes the steps of:

providing a phase-encoding pulse in a magnetic field gradient in a direction orthogonal to the readout gradient direction; and

assigning, in each pair of sequences, one of the multiplicity S of different values thereto.

8. The method of claim 3, wherein the first direction is the direction of the main static field, and the N different second directions all are in a plane orthogonal thereto.

9. The method of claim 8, wherein the first direction is the Z axis of a Cartesian coordinate system, with each j-th one of the N second directions being in the X-Y plane and at an angle θ

, with respect to the coordinate system Y axis; and

step (d) includes the steps of;

generating in the main static magnetic field a magnetic field gradient G_x in a direction parallel to the X-axis of the coordinate system;

generating in the main static magnetic field a magnetic field gradient G_y in a direction parallel to the Y-axis of the coordinate system; and

setting, during at least a readout portion of each acquisition interval of step (d), the gradient amplitudes G_x =G_x,max cos(θ

_j) and G_y =G_y,max sin(θ

_j), where G_x,max and G_y,max are the respective gradient amplitudes for θ

=0° and

θ

=90°

, respectively.

10. The method of claim 9, wherein step (d) further includes the steps of:

generating a dephasing pulse in each of the G_x and G_y gradients prior to each of the N acquisition time intervals in each sequence; and

scaling the amplitude of each dephasing pulse to be a fixed multiple of, but of opposite polarity to, the readout portion amplitude of the same gradient.

11. The method of claim 10, wherein step (d) includes the steps of:

providing a phase-encoding pulse in the magnetic field gradient G_Z in the Z axis direction; and

assigning, in each pair of sequences, one of the multiplicity S of different values to the phase-encoding pulse.

12. The method of claim 1, wherein step (a) includes the step of limiting the nutating action to a predetermined volume of the sample portion.

13. The method of claim 1, wherein the sample is a portion of a living entity having a cardiac cycle, and further including the step of gating the commencement of each sequence with respect to a designated point in the cardiac cycle of the entity.