Abstract:
A magnetic resonance examination system comprises a main magnet with superconducting coils to generate a main magnetic field and a gradient system to apply a gradient magnetic field superposed on the main magnetic field. A cooling system cools the superconducting coils to below their critical superconductivity temperature. A transfer monitor assesses the transfer of energy from the gradient system to the cooling system. The transfer monitor being configured to measure pressure changes in the cooling system. This leads to a simple manner to evaluate the transfer of energy from the gradient coils into the cooling system.

Description:
FIELD OF THE INVENTION 
       [0001]    The invention pertains to a magnetic resonance examination system with superconducting coils to generate a main magnetic field. The magnetic resonance examination system also includes a gradient system to apply a magnetic gradient field superposed on the main magnetic field. 
       BACKGROUND OF THE INVENTION 
       [0002]    Such a magnetic resonance examination system is known from the US-patent application U.S.  2003 / 0206015 . 
         [0003]    The known magnetic resonance examination system has a control unit which automatically determines system-specific acoustic and mechanical resonances. Resonant oscillations are caused by pulsed operation of the gradient coil. In particular, periodically repeated gradient pulses (i.e. pulsed gradient magnetic fields) cause a forced mechanical oscillation of the magnetic resonance examination system. These gradient pulses cause eddy currents in structures surrounding the gradient coil and due to interaction with the main magnetic field exert (Lorentz) forces to cause these structures to move. All structures that are mechanically coupled, move or vibrate due to these forces. When periodically repeated gradient pulses are applied, forced mechanical oscillation of the system can occur and resonant amplification occurs if excitation occurs at the natural resonant frequencies of the mechanically coupled structures. When the superconducting coils of the main magnet are excited to oscillate, then increased evaporation occurs of Helium that is employed to cool the superconducting coils below their superconducting critical temperature. The excitation of mechanical or acoustic resonances is dependent on the imaging sequences in which gradient pulses are switched. Based on these dependencies the imaging sequences can be limited so that an excitation of mechanical resonances no longer occurs. In the known magnetic resonance examination system this dependency is obtained by forming a resonance curve as a function of the time spacing of the gradient pulses. 
       SUMMARY OF THE INVENTION 
       [0004]    An object of the invention is to provide a magnetic resonance examination system in which the transfer function that represents energy transfer from the gradient coil into the magnetic resonance examination system is determined simpler and more accurately. 
         [0005]    This object is achieved in the magnetic resonance examination system comprising 
         [0000]    a main magnet with superconducting coils to generate a main magnetic field
 
a gradient system to apply a gradient magnetic field superposed on the main magnetic field
 
a cooling system to cool the superconducting coils to below their critical superconductivity temperature
 
a transfer monitor to assess the transfer of energy from the gradient system to the cooling system,
 
the transfer monitor being configured to measure pressure changes in the cooling system.
 
         [0006]    The gradient system includes one or more gradient coils which generate gradient magnetic fields when an electrical current is passed through the gradient coil windings. Notably switching of the gradient fields causes eddy currents by which energy is transferred from the gradient coils into the cooling system and notably into the cooling medium such as liquid Helium in the cooling system. The pressure changes in the cooling system are representative of the transfer of energy from the gradient system to the cooling system. Notably, when the cooling system includes a cryostat and a Helium vessel, from the pressure changes the transfer of energy from the gradient coil into the Helium (He) vessel can be accurately derived. Moreover, the pressure changes are easily measured. 
         [0007]    The accurately determined transfer function can be employed to control the settings of acquisition sequences including switching of gradient pulses to avoid settings that are associated with a very efficient energy transfer from the gradient system. Thus, the acquisition sequences can be adapted so that the energy transfer is less. Consequently, when the adapted acquisition sequences are employed, dynamic boil-off of helium from the He-vessel is reduced and further the acoustic noise level is lower. 
         [0008]    Accuracy of the transfer function also includes that according to the invention the transfer function represents most or even all energy transfer mechanisms between the gradient coil and the cooling system. Hence, the energy transfer more accurately represents the energy transfer and the ensuing He boil off as compared to taking only mechanical energy transfer mechanisms into account. 
         [0009]    These and other aspects of the invention will be further elaborated with reference to the embodiments defined in the dependent Claims. 
         [0010]    According to a further aspect of the invention in order to calibrate the energy transfer function, a test gradient magnetic field having a gradually increasing gradient strength is applied during pre-set active time intervals, alternated with the gradient magnetic field switched off during intervals between successive active time intervals. Then the pressure in the cooling system, notably in the He-vessel is measured during the test gradient field switched on and off, respectively. The transfer function is computed from the difference between measured pressures at gradient on and off. From the difference between measured pressures at gradient on and off, drift of the pressure due to other causes which are common for gradient on and off are eliminated and do not corrupt the computed transfer function. 
         [0011]    Preferably, the test gradient field encompasses a wide range of excitation frequencies so that accurate results for the transfer function are obtained for most of the relevant frequencies involved. Typically, a wide range of frequencies from 100 Hz to 6 kHz is employed. Good results are obtained for active time intervals of about 20 ms which also repeated at about 20 ms intervals. The differential measurement avoids the need for long waiting time for the cooling system with the He-vessel to reach a stationary state during excitations. Typically, the cooling system has a response time of up to 20 minutes. The actual measurement over a number of active time intervals is much less. For each separate frequency (range) and individual (x,y, or z) gradient measurement of the transfer function takes only a few minutes. Thus, the transfer function for the entire frequency range and all three gradient directions can be obtained within a few hours. Thus, a full re-calibration of the transfer function can be done overnight when the magnetic resonance examination system is not needed in operation. 
         [0012]    According to another aspect of the invention, the transfer monitor computes an expected He consumption from (i) the computed transfer function and (ii) a selected acquisition sequence including a particular gradient pulse train, i.e. a succession of pulsed gradient magnetic fields. The computed expected He-consumption for the selected acquisition sequence is presented to the operator, e.g. shown on a display included in the user interface of the magnetic resonance examination system. Thus, the operator is put in a position where he/she may take the expected He-consumption into account when considering a particular acquisition sequence or adapting the acquisition sequence before it is activated. 
     
    
     
       BRIEF DESCRIPTION OF THE DRAWINGS 
         [0013]    These and other aspects of the invention will be elucidated with reference to the embodiments described hereinafter and with reference to the accompanying drawing wherein 
           [0014]      FIG. 1  shows diagrammatically a magnetic resonance imaging system in which the invention is used. 
           [0015]      FIG. 2  shows another diagrammatic representation of the magnetic resonance examination system in which the present invention is incorporated. 
           [0016]      FIG. 3  shows experimental results for the transfer characteristic. 
       
    
    
     DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS 
       [0017]      FIG. 1  shows diagrammatically a magnetic resonance imaging system in which the invention is used. The magnetic resonance imaging system includes a set of main magnet coils  10  whereby the steady, uniform magnetic field is generated. The main magnet coils are constructed, for example in such a manner that they enclose a tunnel-shaped examination space. The main magnet coils are superconducting. The windings of the superconducting main magnet coils are cooled to below the critical temperature by liquid Helium that is cooled to below its boiling point. The main magnet coils are enclosed in a He-vessel that is filled with liquid He. A cryostat  42  is provided for cooling and liquefying the Helium. The patient to be examined is placed on a patient carrier  14  which is slid into this tunnel-shaped examination space  30 . The magnetic resonance imaging system also includes a number of gradient coils  11 ,  12  whereby magnetic fields exhibiting spatial variations, notably in the form of temporary gradients in individual directions, are generated so as to be superposed on the uniform magnetic field. The gradient coils  11 ,  12  are connected to a gradient control  21  which includes one or more gradient amplifiers and a controllable power supply unit. The gradient coils  11 ,  12  are energised by application of an electric current by means of the power supply unit  21 ; to this end the power supply unit is fitted with an electronic gradient amplification circuit that applies the electric current to the gradient coils so as to generate gradient pulses (also termed ‘gradient waveforms’) of appropriate temporal shape. The strength, direction and duration of the gradients are controlled by control of the power supply unit. The magnetic resonance imaging system also includes transmission and receiving coils  13 ,  16  for generating the RF excitation pulses and for picking up the magnetic resonance signals, respectively. The transmission coil  13  is preferably constructed as a body coil  13  whereby (a part of) the object to be examined can be enclosed. The body coil is usually arranged in the magnetic resonance imaging system in such a manner that the patient to be examined is enclosed by the body coil  13  when he or she is arranged in the magnetic resonance imaging system. The body coil  13  acts as a transmission antenna for the transmission of the RF excitation pulses and RF refocusing pulses. Preferably, the body coil  13  involves a spatially uniform intensity distribution of the transmitted RF pulses (RFS). 
         [0018]    The same coil or antenna is usually used alternately as the transmission coil and the receiving coil. Furthermore, the transmission and receiving coil is usually shaped as a coil, but other geometries where the transmission and receiving coil acts as a transmission and receiving antenna for RF electromagnetic signals are also feasible. The transmission and receiving coil  13  is connected to an electronic transmission and receiving circuit  15 , which has a transmission and a receiver operating mode. 
         [0019]    It is to be noted that it is alternatively possible to use separate receiving and/or transmission coils  16 . For example, surface coils  16  can be used as receiving and/or transmission coils. Such surface coils have a high sensitivity in a comparatively small volume. The receiving coils, such as the surface coils, are connected to the electronic transmission and receiving circuit  15 . The electronic transmission and receiving circuit is connected to a preamplifier  23 . The received RF resonance signals are fed to a pre-amplifier  23  and then applied to a demodulator  24  and the received magnetic resonance signals (MS) are demodulated by means of the demodulator  24 . The preamplifier  23  amplifies the RF resonance signal (MS) received by the receiving coil  16  and the amplified RF resonance signal is applied to the demodulator  24 . The demodulator  24  demodulates the amplified RF resonance signal. The demodulated magnetic resonance signals (DMS) are applied to a reconstruction unit. The demodulated resonance signal contains the actual information concerning the local spin densities in the part of the object to be imaged. Furthermore, the transmission and receiving circuit  15  is connected to a modulator  22 . The modulator  22  and the transmission and receiving circuit  15  activate the transmission coil(s)  13 , 16  so as to transmit the RF excitation and refocusing pulses. Magnetic resonance signal data received by the surface coils  16  are transmitted to the transmission and receiving circuit  15  and control signals (e.g. to tune and detune the surface coils) are sent to the surface coils. 
         [0020]    The reconstruction unit  25  derives one or more image signals from the demodulated magnetic resonance signals (DMS), which image signals represent the image information of the imaged part of the object to be examined. The reconstruction unit  25  in practice is constructed preferably as a digital image processing unit  25  which is programmed so as to derive from the demodulated magnetic resonance signals the image signals which represent the image information of the part of the object to be imaged. The signal on the output of the reconstruction unit  25  is applied monitor  26 , so that the monitor can display the magnetic resonance image. It is alternatively possible to store the signal from the reconstruction unit  25  in a buffer unit  27  while awaiting further processing. 
         [0021]    The magnetic resonance imaging system is also provided with a control unit  20 , for example in the form of a computer which includes a (micro)processor. The control unit  20  controls the execution of the RF excitations and the application of the temporary gradient fields. To this end, the computer program according to the invention is loaded, for example, into the control unit  20  and the reconstruction unit  25 . 
         [0022]    In accordance with the invention, the magnetic resonance examination system further comprises the transfer monitor  50 . The transfer monitor includes a pressure monitor that measures pressure in the cryostat  42  or within the He-vessel which encloses the main magnet coils  10 . The He-vessel filled with liquid Helium and the cryostat form the cooling system which cools the main magnet coils  10  to below their sup erconductivlity circuital temperature. In particular the pressure monitor  51  has a pressure sensor  511  which measures the pressure in the cryostat  42  and/or He-vessel and an electronic module that processes the pressure signal from the pressure sensor. Further, the pressure monitor is provided with a pressure controller  53 . When in operation in a calibration mode of the magnetic resonance examination system the pressure controller drives the gradient control  21  to generate the test gradient magnetic fields. These test gradient magnetic fields are switched on and off for active time intervals of about 20 ms and separated by 20 ms periods in which no test gradient magnetic field is applied. A pressure comparator  52  circuit is provided to differentially measure pressure. To that end the output pressure signal of the pressure monitor  51  is applied to the pressure comparator  52 . Differences are computed between pressure in the He-vessel and/or cryostat with and without test gradient magnetic field. From the differential measurement and the waveform of the test gradient magnetic field the transfer of energy from the gradient system to the cooling system is computed. The transfer characteristic that represents the energy transfer from the gradient system to the cooling system can be derived e.g. by an arithmetic unit  55  that is incorporated in the transfer monitor or by the (host) processor  20  of the magnetic resonance examination system. 
         [0023]    When the magnetic resonance examination system is in operation to image a patient to be examined He-consumption occurs due to evaporation caused by deposited energy. On the basis of the transfer characteristic and actually applied gradient waveforms the He-consumption can be calculated and presented to the operator. To that end the transfer monitor is provided with a He-consumption display unit  54  that computes the expected He-consumption for a selected gradient waveform. In practice the He-consumption display unit is implemented as another window of view port in the user interface of the magnetic resonance examination system. Thus, the operator is provided with a simple insight in the amount of He that is lost for a MR acquisition sequence selected by the operator and that includes pr-determined gradient waveforms. 
         [0024]      FIG. 2  shows another diagrammatic representation of the magnetic resonance examination system in which the present invention is incorporated.  FIG. 2  shows a cross sectional diagrammatic side elevation of the magnetic resonance examination system. The cross section is made along the longitudinal axis of the more or less cylindrically symmetric magnetic resonance examination system. The main magnet coils  10  are placed in the He-vessel  43 . The He in the He-vessel is kept liquid by the cryostat  42  so that the main magnet coils are cooled at superconductive temperature. In the embodiment of  FIG. 2 , the pressure sensor  511  is located within the He-vessel and measures pressure in the He-vessel as a function of applied test gradient magnetic field. 
         [0025]      FIG. 3  shows experimental results for the transfer characteristic. The curves show the energy transfer as a function of waveform frequency for the x,y and z gradient coils, respectively. Notably, there is a marked reduction in energy (heat) transfer around 1 kHz. Thus, by adapting the MR acquisition sequence by adjusting the repetition time (T R ) to have waveform frequencies near a transfer minimum (e.g. near 1 kHz)heat transfer can be reduced without affecting the performance of the magnetic resonance examination system.