Oscillating dual-equilibrium steady state angiography using magnetic resonance imaging

• US 6,552,542 B1
• Filed: 09/28/2001
• Issued: 04/22/2003
• Est. Priority Date: 09/28/2001
• Status: Active Grant

• Current Assignee: Board of Trustees of the Leland Stanford Junior University (Stanford Management Co.)
• Original Assignee: Board of Trustees of the Leland Stanford Junior University (Stanford Management Co.)
• Inventors: Overall, William R.
• Primary Examiner(s): Lefkowitz, Edward
• Assistant Examiner(s): Shrivastav, Brij B.
• Application Number:
  US09/967,644
• Publication Number:
  US 20030062893A1
• Time in Patent Office: 571 Days
• Field of Search: 324/309, 324/307, 324/306, 324/312, 324/314, 324/322, 600/412, 128/653.2
• US Class Current: 324/309
• CPC Class Codes: G01R 33/5613 Generating steady state signals, e.g. low flip angle sequences [FLASH]
• CPC Class Codes: G01R 33/563 of moving material, e.g. flow contrast angiography

Abstract

A method of oscillating dual-equilibrium steady-state angiography (ODESSA), utilizes a modified steady state free precession (SSFP) pulse sequence. The SSFP sequence is modified such that flowing material reaches a steady state which oscillates between two equilibrium values, while stationary material attains a standard, non-oscillatory steady state. When alternating sequences are employed, subtraction of adjacent echoes results in large, uniform signal from all flowing spins and zero signal from stationary spins. Venous signal can be suppressed based on its reduced T₂. ODESSA arterial signal is more than three times as large as that of traditional phase-contrast angiography (PCA) in the same scan time, and also compares favorably with other techniques of MR angiography. Pulse sequences are implemented in 2D, 3D, and volumetric projection modes. Angiograms of the lower leg, generated in as few as 5 s, show high arterial SNR and full suppression of other tissues.

Claims

1. A method of magnetic resonance angiography comprising the steps of:

a) placing an object to be imaged in a static magnetic field,

b) applying an RF pulse and axial gradients to the object,

c) detecting first signals from nuclei in the object,

d) applying an RF pulse, axial gradient, and a bipolar flow-encoding pulse,

e) detecting second signals from nuclei in the object,

f) repeating steps b) and c) to establish a steady state of first signals,

g) repeating steps d) and e) to establish a steady state of second signals, and

h) subtracting the steady state of first signals from the steady state of second signals to obtain signals of non-static material.

2. The method as defined by claim 1 wherein steps b) and c) and steps d) and e) are repeated sequentially in order to produce a steady state which oscillates between first and second signals.

3. The method as defined by claim 1 wherein steps b) and c) are repeated a multiple of times for each of steps d) and e).

4. The method as defined by claim 1 wherein step b) includes applying a three-lobed compensation pulse to mitigate the effects of eddy currents, concomitant Maxwell gradients, and acceleration.

5. The method as defined by claim 1 wherein step d) the bipolar flow-encoding pulse follows step e).

6. The method as defined by claim 1 wherein in step d) the bipolar flow-encoding pulse precedes step e).

7. The method as defined by claim 1 wherein step h) provides two dimensional image signals.

8. The method as defined by claim 1 wherein step h) provides three dimensional image signals.

9. The method as defined by claim 1 wherein in step d) the bipolar pulse is applied on any axis.

10. The method as defined by claim 1 wherein in step d) bipolar pulse is applied on a combination of axes.

11. The method as defined by claim 1 wherein in step d) the bipolar pulse is changed at each iteration or groups of iterations.

12. The method as defined by claim 1 wherein in steps b) and d) RF phase is constant.

13. The method as defined by claim 1 wherein in steps b) and d) RF phase is incremented for each RF pulse.

14. A method of magnetic resonance angiography comprising the steps of:

a) placing an object to be imaged in a static magnetic field,

b) applying a first refocused steady state precession pulse and gradient sequence to obtain first signals from nuclei in the object;

c) applying a second refocused steady state precession pulse and gradient sequence including a bipolar flow encoding pulse to obtain second signals from nuclei in the object,

d) repeating step b) to establish a steady state of first signals,

e) repeating step c) to establish a steady state of second signals, and

f) subtracting the steady states of first signals and second signals to obtain signals of non-static material.

15. The method as defined by claim 14 wherein steps b) and c) are repeated sequentially in order to produce a steady state which oscillates between first and second signals.

16. The method as defined by claim 14 wherein step b) is repeated a multiple of times for each step c).

17. The method as defined by claim 14 wherein step b) includes applying a three-lobed compensation pulse to mitigate the effects of eddy currents, concomitant Maxwell gradients, and acceleration.

18. The method as defined by claim 14, wherein in step c) the bipolar flow-encoding pulse follows second signal detection.

19. The method as defined by claim 14 wherein in step c) the bipolar flow encoding pulse precedes second signal detection.

20. The method as defined by claim 14 wherein step f) provides two dimensional image segments.

21. The method as defined by claim 14 wherein step f) provides three dimensional image signals.

22. The method as defined by claim 14 wherein in step c) the bipolar pulse is applied on any axis.

23. The method as defined by claim 14 wherein in step c) the bipolar pulse is applied on a combination of axes.

24. The method as defined by claim 14 wherein in step c) the bipolar pulse is changed at each iteration or groups of iterations.

25. The method as defined by claim 14 wherein in steps b) and c) RF phase is constant.

26. The method as defined by claim 14 wherein in steps b) and c) RF phase is incremented for each sequence.