Magnetic resonance tomography method and magnetic resonance tomography apparatus for performing the method

Claim 2

A magnetic resonance tomography method where a first slice selective rf pulse (HF a ) and a second rf pulse (HF b ) act on a slice (S a ) of an examination zone in the presence of a uniform, steady magnetic field, after which further slice selective pulses (HF1 . . . HF n ) act on the examination zone in order to excite the nuclear magnetisation in mutual parallel sub-slices (S 1 . . . S n ) which extend perpendicularly with respect to the slice (S a ), and where stimulated echo signals which occur in the associated sub-slice subsequent to each further rf pulse are received and subjected to a Fouzier transformation, characterized in that subsequent to each further rf pulse (HF1 . . . HF n ) and before the reception of the associated Stimulated echo signal a magnetic gradient field (for example G i1 ) is switched on and off in order to dephase the FID signal associated with the rf pulse, in that between the first and the second rf pulse (HF a , HF b ) a magnetic gradient field (G ip ) is switched on and off, and in that the gradients of these fields extend parallel or anti-parallel with respect to one another, the absolute value of their time integral being the same.

Claim 3

A method as claimed in claim 1, characterized in that the second rf pulse (HF b ) is a slice-selective rf pulse.

Claim 4

A method as claimed in claim 2, characterized in that the second rf pulse (HF b ) influences the same slice (S a ) as the first rf pulse.

Claim 5

A method as claimed in claim 2, characterized in that the slice which is influenced by the second rf pulse (HF b ) extends perpendicularly with respect to the slice (S a ) influenced by the first rf pulse (HF b ) and perpendicularly with respect to the sub-slices (S 1 . . . S n ).

Claim 6

A method as claimed in claim 1, where the echo signal is received in the presence of a magnetic gradient field, characterized in that after the reception of the stimulated echo signal (STE 1 ) the polarity of the gradient (G r ) is reversed, the rephased echo signals (STE 2 . . . STE 1 ) subsequently occurring being received and evaluated.

Claim 7

A method as claimed in claim 1, characterized in that the first rf pulse (HF a ) is preceded by a frequency selective rf pulse (HF 0 ) which excites fat-bound hydrogen protons after which a magnetic gradient field (G) is switched on and off.

Claim 8

A method as claimed in claim 1, characterized in that the sub-slices are excited at least twice using a different distance in time between the first rf pulse and the rf pulse for the relevant sub-slice, the longitudinal relaxation time being determined from the different nuclear magnetisation along the strips defined by the sub-slices and the slice.

Claim 9

A method as claimed in claim 1, characterized in that the ratio of the magnetic gradient field applied in conjunction with each further rf pulse to the bandwidth of the relevant rf pulse is varied so that upon excitation of the sub-slices strips rf different width are excited.

Claim 10

A magnetic resonance tomography apparatus comprising: a magnet (l) for generating a steady, uniform magnetic field in an examination zone, a coil system (ll) for generating rf magnetic fields in said zone, and gradient coils (3, 5, 7) for generating magnetic fields in said zone which extend in the direction of the uniform, steady magnetic field and which have a gradient which extends in the same direction or perpendicularly thereto, as well as a control unit (15) for controlling the rf coil (ll) and the gradient coil system (3, 5, 7), characterized in that the control unit (15) controls the rf coil system (ll) and the gradient coil system (3, 5, 7) so as to generate a first slice selective rf pulse (HF 1 ) and a second rf pulse (HF b ) acting on a slice ( a ) in said examination zone, after which further slice selective pulses (HF 1 . . . HF n ) act on the examination zone in order to excite the nuclear magnetization in mutual parallel sub-slices (S 1 . . . S n ) which extend perpendicularly with respect to the slice (S a ) and so that between the first and the second rf pulse as well as after each further rf pulse a magnetic gradient field is switched on and of, the time integral over the period from the instant of switching on until the instant of switching off having the same value each time.

Claim 11

A magnetic resonance tomography apparatus comprising: a magnet (l) for generating a steady, uniform magnetic field in an examination zone, a coil system (ll) for generating rf magnetic fields in said zone, and gradient coils (3, 5, 7) for generating magnetic fields in said zone which extend in the direction of the uniform, steady magnetic field and which have a gradient which extends in the same direction or perpendicularly thereto, as well as a control unit (15) for controlling the rf coil (ll) and the gradient coil system (3, 5, 7), characterized in that the control unit (15) controls the rf coil system (ll) and the gradient coil system (3, 5, 7) so as to generate a first slice selective rf pulse (HF 1 ) and a second rf pulse (HF b ) acting on a slice ( a ) in said examination zone, after which further slice selective pulses (HF 1 . . . HF n ) act on the examination zone in order to excite the nuclear magnetization in mutual parallel sub-slices (S 1 . . . S n ) which extend perpendicularly with respect to the slice (S a ) and so that between the first and the second rf pulse as well as after each further rf pulse a magnetic gradient field is switched on and of, the time integral over the period from the instant of switching on until the instant of switching off having the same value each time.

Claim 12

A method as claimed in claim 3, where the echo signal is received in the presence of a magnetic gradient field, characterized in that after the reception of the stimulated echo signal (STE 1 ) the polarity of the gradient (G r ) is reversed, the rephased echo signals (STE 2 . . . STE 4 ) subsequently occurring being received and evaluated.

Claim 13

A method as claimed in claim 4, where the echo signal is received in the presence of a magnetic gradient field, characterized in that after the reception of the stimulated echo signal (STE 1 ) the polarity of the gradient (G r ) is reversed, the rephased echo signals (STE 2 . . . STE 4 ) subsequently occurring being received and evaluated.

Claim 14

A method as claimed in claim 10, characterized in that the first rf pulse (HF a ) is preceded by a frequency selective rf pulse (HF 0 ) which excited fat-bound hydrogen protons, after which a magnetic gradient field (G) is switched on and off.

Claim 15

A method as claimed in claim 11, characterized in that the first rf pulse (HF a ) is preceded by a frequency selective rf pulse (HF 0 ) which excites fat-bound hydrogen protons, after which a magnetic gradient field (G) is switched on and off.

Claim 16

A method as claimed in claim 12, characterized in that the sub-slices are excited at least twice using a different distance in time between the first rf pulse and the rf pulse for the relevant sub-slice, the longitudinal relaxation time being determined from the different nuclear magnetization along the strips defined by the sub-slices and the slice.

Claim 17

A method as claimed in claim 13, characterized in that the sub-slices are excited at least twice using a different distance in time between the first rf pulse and the rf pulse for the relevant sub-slice, the longitudinal relaxation time being determined from the different nuclear magnetization along the strips defined by the sub-slices and the slice.

Claim 18

A method as claimed in claim 14, characterized in that the ratio of the magnetic gradient field applied in conjunction with each further rf pulse to the bandwidth of the relevant rf pulse is varied so that upon excitation of the sub-slices strips of different width are excited.

Claim 19

A method as claimed in claim 15, characterized in that the ratio of the magnetic gradient field applied in conjunction with each further rf pulse to the bandwidth of the relevant rf pulse is varied so that upon excitation of the sub-slices strips of different width are excited.