Phase contrast imaging using interleaved projection data

Details Phase contrast imaging using interleaved projection data Phase contrast imaging using interleaved projection data

1999-05-18

2001-02-13

Lateef, Marvin M. (Department: 3737)

Surgery

Diagnostic testing

Detecting nuclear, electromagnetic, or ultrasonic radiation

C324S306000

Reexamination Certificate

active

06188922

ABSTRACT:

BACKGROUND OF THE INVENTION
The field of the invention is nuclear magnetic resonance (“NMR”) imaging methods and systems. More particularly, the invention relates to the acquisition of NMR images indicative of flow, or motion.
When a substance such as human tissue is subjected to a uniform magnetic field (polarizing field B
0
), the individual magnetic moments of the spins in the tissue attempt to align with this polarizing field, but precess about it in random order at their characteristic Larmor frequency. If the substance, or tissue, is subjected to a magnetic field (excitation field B
1
) which is in the x-y plane and which is near the Larmor frequency, the net aligned moment, M
z
, may be rotated, or “tipped”, into the x-y plane to produce a net transverse magnetic moment M
t
. A signal is emitted by the excited spins after the excitation signal B
1
is terminated, this signal may be received and processed to form an image.
When utilizing these signals to produce images, magnetic field gradients (G
x
G
y
and G
z
) are employed. Typically, the region to be imaged is scanned by a sequence of measurement cycles in which these gradients vary according to the particular localization method being used. The resulting set of received NMR signals are digitized and processed to reconstruct the image using one of many well known reconstruction techniques.
The prevailing methods used to acquire NMR signals and reconstruct images use a variant of the well known Fourier transform (FT) imaging technique, which is frequently referred to as “spin-warp” The spin-warp technique is discussed in an article entitled “Spin-Warp NMR Imaging and Applications to Human Whole-Body Imaging” by W. A. Edelstein et al.,
Physics in Medicine and Biology,
Vol. 25, pp. 751-756 (1980). It employs a variable amplitude phase encoding magnetic field gradient pulse prior to the acquisition of NMR spin-echo signals to phase encode spatial information in the direction of this gradient. In a two-dimensional implementation (2DFT), for example, spatial information is encoded in one direction by applying a phase encoding gradient (G
y
) along that direction, and then a spin-echo signal is acquired in the presence of a readout magnetic field gradient (G
x
) in a direction orthogonal to the phase encoding direction. The readout gradient present during the spin-echo acquisition encodes spatial information in the orthogonal direction. In a typical 2DFT pulse sequence, the magnitude of the phase encoding gradient pulse G
y
is incremented (&Dgr;G
y
) in the sequence of views that are acquired during the scan to produce a set of NMR data from which an entire image can be reconstructed.
To increase the rate at which image frames are acquired, image quality may be sacrificed by acquiring fewer phase encoding views, or by using faster pulse sequences that inherently result in lower quality images. With the spin-warp methods, therefore, there is a trade-off between the number of views that are acquired to achieve the desired image resolution and quality, and the rate at which NMR data for a complete image may be acquired.
Diagnostic studies of the human vasculature have many medical applications. X-ray imaging methods such as digital subtraction angiography (“DSA”) have found wide use in the visualization of the cardiovascular system, including the heart and associated blood vessels. Images showing the circulation of blood in the arteries and veins of the kidneys and the carotid arteries and veins of the neck and head have immense diagnostic utility. Unfortunately, however, these x-ray methods subject the patient to potentially harmful ionizing radiation and often require the use of an invasive catheter to inject a contrast agent into the vasculature to be imaged.
Magnetic resonance angiography (MRA) uses nuclear magnetic resonance (NMR) phenomenon to produce images of the human vasculature. Such angiograms provide visualization of the cardiovascular system without subjecting the patient to ionizing radiation. Two basic MRA techniques have been proposed and evaluated. The first class, time-of-flight (TOF) techniques, consists of methods which exploit the differences in signal saturation that exist between flowing blood and stationary tissue. Flowing blood, which is moving through the excited section, is continually refreshed by spins experiencing fewer excitation pulses and is, therefore, less saturated. This effect is magnified by injecting a contrast agent into the patient and timing the acquisition when the contrast bolus flows through the arteries of interest. The result is the desired image contrast between the high-signal blood and the low-signal stationary tissues.
MR methods have also been developed that encode motion into the phase of the acquired signal as disclosed in U.S. Pat. No. Re. 32,701. These form the second class of MRA techniques and are known as phase contrast (PC) methods. Currently, most PC MRA techniques acquire two images, with each image having a different sensitivity to the same velocity component. Angiographic images are then obtained by forming either the phase difference or complex difference between the pair of velocity-encoded images. Phase contrast MRA techniques have been extended so that they are sensitive to velocity components in all three orthogonal directions, but this requires additional data acquisition.
Currently, all known MRA techniques employ a method in which k-space is sampled along Cartesian coordinates. The prevailing method used is the 2DFT or 3DFT fast gradient recalled echo method. While the PC MRA technique does not require the injection of contrast agents into the patient, it is not used in many clinical applications because it usually requires from four to six times as long as the TOF method to acquire the NMR data for a phase contrast MRA image. This is because a separate phase image may be acquired for each axis of motion (x, y and z), and two images (with different velocity encoding) must be acquired for each axis of motion.
SUMMARY OF THE INVENTION
The present invention is a method for acquiring and producing MRA images using the phase contrast technique, and more particularly, acquiring the NMR data using a series of projection acquisitions in which no phase encoding gradients are employed. Rather than phase encoding the acquired NMR data differently in each of a plurality of views, the readout gradient is changed in each acquisition to rotate the projection angle. The NMR data is velocity encoded with a bipolar gradient and a phase image is produced by reconstructing an image from the acquired projection data.
A general object of the invention is to reduce the time required to acquire an MRA image using the phase contrast (PC) technique or to increase the resolution of the MRA image. It has been discovered that far fewer projection views are required to produce a quality MRA image than phase encoded views. Artifacts that normally result when fewer projections are acquired are of less concern in MRA images of the vasculature which typically do not contain large bright objects such as bones.
Another aspect of the invention is to acquire phase contrast MRA data in which velocity encoding along a plurality of directions is employed. For each velocity encoding direction a set of projections are acquired from which a phase image can be reconstructed. The projection angles of each set of velocity encoded acquisitions are distributed substantially throughout 180° and the projection angles of each set are interleaved with the projection angles of the other set or sets. As a result, a phase contrast MRA can be acquired with projection acquisitions in approximately the same scan time as a time-of-flight MRA using a spin-warp acquisition technique.


REFERENCES:
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patent: 5093620 (1992-03-01), Pelc et al.
patent: 5133357 (1992-07-01), Dumoulin et al.
patent: 5204625 (1993-04-01), Cline et al.
patent: 5408180 (1995-04-01), Mistretta et al.
patent: 6031374 (2000-02-01), Epstein et al.

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