CN101872001A - Parallel emitting and receiving radio-frequency interface circuit and phased array emitting and receiving head coil - Google Patents
Parallel emitting and receiving radio-frequency interface circuit and phased array emitting and receiving head coil Download PDFInfo
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Abstract
The invention relates to a parallel emitting and receiving radio-frequency interface circuit and a phased array emitting and receiving head coil. The phased array emitting and receiving head coil comprises an outer shell and an inner shell with two through ends, wherein the inner shell and the outer shell are both provided with full-open viewing windows corresponding to the positions of eyes of a tester; and the outer surface of the inner shell is provided with eight phased array surface loops distributed in an upper ring and a lower ring, wherein the phased array surface loops are arranged around the full-open viewing windows. The parallel emitting and receiving radio-frequency interface circuit comprises a power divider, the power divider is connected with eight phase shifters; each phase shifter carries out linear phase shift on each input radio-frequency signal, and each input radio-frequency signal subjected to the linear phase shift is emitted to the eight phased array surface loops of the phased array emitting and receiving head coil through the input/output end of an emitting and receiving change-over switch; the eight phased array surface loops emit radio-frequency signals and receive human body hydrogen atoms to generate eight magnetic resonance signals, and the eight magnetic resonance signals are respectively input to a preamplifier through the input/output end of each emitting and receiving change-over switch; and the control end of each emitting and receiving change-over switch is connected with a control system of a scanner. The invention can be widely used for various magnetic resonance high-field imaging systems and especially for ultrahigh-field imaging systems.
Description
Technical field
The present invention relates to magnetic resonance High-Field and super high field imaging system, be meant a kind of parallel emitting and receiving radio-frequency interface circuit and phased array emitting and receiving head coil that is applicable in magnetic resonance High-Field and the super high field imaging system especially.
Background technology
The speed of development of mr imaging technique in the period of in the past surplus in the of ten is rapid, it not only becomes the indispensable instrument of clinical diagnose, more become " astronomical telescope " or " microscope " of direct observation brain cognitive activities, thoroughly changed the research looks of brain and cognition scientific domain.The main bottleneck of restriction mr techniques development is signal to noise ratio (S/N ratio), resolution and the image taking speed of image.The main path that addresses this problem at present is to improve main field strength, improves the emission and the receiving function of coil, realizes the multi-channel parallel imaging, improves image taking speed.Current High-Field (being generally 3T) and super high field (7T and more than) magnetic resonance imaging system and parallel imaging technique are the most compelling technology trends in magnetic resonance imaging field.
With existing clinical main flow 1.5T magnetic resonance system relatively, High-Field and super high field whole body magnetic resonance system all are improved largely on several key indexs such as signal to noise ratio (S/N ratio), function signal intensity and spectral resolution.The 7T magnetic resonance imaging system can reach the resolution below 0.1 millimeter at present, and body tissue structure and the functional activity thereof trickleer for observation provide possibility.Although High-Field and super high field whole body magnetic resonance system have so outstanding ability, give full play to its effect, also have many technical barriers to need to solve, as existing in the super high field system because the dielectric resonance effect of human body causes the unevenness of radio-frequency field emission, influence the signal noise ratio (snr) of image of magnetic resonance imaging system, human body is to the taken in excess of electromagnetic energy, promptly high SAR value, the problem such as highly difficult of static magnetic field shimming.
Summary of the invention
At the problems referred to above, the purpose of this invention is to provide a kind of radio-frequency field emission evenly, signal noise ratio (snr) of image height, parallel emitting and receiving radio-frequency interface circuit and phased array emitting and receiving head coil that the electromagnetic energy emission is low.
For achieving the above object, the present invention takes following technical scheme: a kind of parallel emitting and receiving radio-frequency interface circuit and phased array emitting and receiving head coil, it is characterized in that: described phased array emitting and receiving head coil comprises an inner casing and the shell that two ends are penetrating, the position of the corresponding tester's eye of described inner casing and shell all offers the form of a standard-sized sheet, the outside surface of described inner casing is provided with upper and lower two circles totally eight phased array surface loops, and one of them described phased array surface loop is around described form setting; Described parallel emitting and receiving radio-frequency interface circuit comprises a power splitter, and the single channel radiofrequency signal of importing is divided into eight tunnel radiofrequency signals; Described power splitter connects eight phase shifters, each road radiofrequency signal that each described phase shifter will be imported is carried out linear phase shift, the I/O end that receives switch by an emission through dephased each road radiofrequency signal is emitted to eight phased array surface loops on the described phased array emitting and receiving head coil, make that the phase shift difference between the adjacent described two phased array surface loops is a definite value in every circle, the phase differential of radiofrequency signal are definite value between the corresponding described two phased array surface loops of upper and lower two circles; Described eight phased array surface loop emitting radio frequency signals are also accepted the human body hydrogen atom and are produced eight road magnetic resonance signals, and described eight road magnetic resonance signals are imported a prime amplifier by the I/O end that each described emission receives switch respectively; The control end that each described emission receives switch all connects the control system of scanner, with the emission that receives described control system output or the switching controls instruction of reception.
Described phase shifter is a concentric cable, and the length of described concentric cable determines the phase-shift phase of described phase shifter.
Phase shift difference in every circle between the adjacent described two phased array surface loops is 90 °, and the phase differential of radiofrequency signal is 180 ° between the described two phased array surface loops of upper and lower two circle correspondences.
Wherein three pairs of described upper and lower phased array surface loops on the outside surface of described inner casing are for being symmetrical arranged.
Described parallel emitting and receiving radio-frequency interface circuit also comprise be connected each described phase shifter and emission receive between the switch, regulate eight attenuators that each road radiofrequency signal amplitude is used.
Each described phased array surface loop comprises three fixed capacities, three tunable capacitors and inductance on the described phased array emitting and receiving head coil, and three fixed capacities wherein, two tunable capacitors and inductance are connected into a resonant tank.
The two ends of the tunable capacitor in the described resonant tank receive switch by the emission that another described tunable capacitor connects in the described radio-frequency interface circuit; Described fixed capacity is the high pressure resistant fixed capacity of no magnetic, and described tunable capacitor is the high pressure resistant tunable capacitor of no magnetic; Inductance is made of four sections copper sheets in the described phased array surface loop.
The present invention is owing to take above technical scheme, it has the following advantages: 1, the radio-frequency interface circuit that adopts of the present invention is divided into eight tunnel radiofrequency signals equably from the single channel radiofrequency signal of single channel power amplifier output, and the radiofrequency signal on each road is carried out linear phase shift obtains uniform launching site; The emission that the control system of radio-frequency interface circuit reception scanner is sent or the switch controlling signal of reception, when radio-frequency interface circuit is in emission state, it is to different uniform eight tunnel radiofrequency signals of head coil transmitter, phase, the hydrogen atom that is in the human brain soft tissue in the head coil is encouraged, make the human body hydrogen atom produce NMR signal, when radio-frequency interface circuit is in accepting state, head coil receives eight road magnetic resonance signals that human body hydrogen atom excited target produces respectively, and, flow to reconstruction and aftertreatment that magnetic resonance imaging system carries out image with after the amplification of eight road magnetic resonance signals.2, because the present invention adopts power splitter that the single channel radiofrequency signal is divided into eight tunnel radiofrequency signals, eight tunnel radiofrequency signals of power splitter being told by eight phase shifters are carried out linear phase shift respectively again, by each radiofrequency signal is carried out phase shift, until the shimming that obtains radio-frequency field, the present invention is with respect to the multi-channel parallel emission coefficient of using a plurality of power amplifiers, adopt merit branch mode to save the expense of buying or develop expensive magnetic resonance power amplifier, can use lower cost to reach the effect of multi-channel parallel emission and radio-frequency field shimming.3, owing to offer the form of a standard-sized sheet on the head coil of the present invention, compare with traditional form, the form of standard-sized sheet can make the visual field of right and left eyes open fully, helps testing the tested visual stimulus clearly of carrying out.4, because emitting and receiving head coil of the present invention has adopted the phased array surface loop, the resonance frequency of each phased array surface loop satisfies 123.2MHz, make each resonant tank have high-quality-factor simultaneously, thereby provide advantageous conditions for improving signal noise ratio (snr) of image.5, since of the present invention two adjacent phased array surface loops between have overlapping area, by suitable overlapping area to remove mutual coupling; Then by public electric capacity, reach the effect of uncoupling between the two phased array surface loops of adjacent diagonal line, guaranteed the high s/n ratio of image.6, because the emission that the two ends of a tunable capacitor of resonant tank are passed through in another tunable capacitor connection radio-frequency interface circuit in each phased array surface loop of the present invention receives switch, therefore the phased array head coil can be adjusted to phase place and impedance phase coupling with prime amplifier, further improve the signal to noise ratio (S/N ratio) of image.7, owing to coil framework of the present invention, copper sheet inductance, fixed capacity and tunable capacitor all are non-magnetic mechanical material and electronic devices and components, and mechanical material not imaging in the magnetic resonance experiment, therefore can further improve signal noise ratio (snr) of image.The present invention can be widely used in various magnetic resonance High-Field imaging system, especially super high field imaging systems.
Description of drawings
Fig. 1 is a parallel emitting and receiving radio-frequency interface circuit block diagram of the present invention
Fig. 2 is the structural representation of emitting and receiving head coil of the present invention
Fig. 3 is the distribution schematic diagram of phased array surface loop on the shell of emitting and receiving head coil of the present invention
Fig. 4 is the circuit connection diagram of phased array surface loop on the shell of emitting and receiving head coil of the present invention
Embodiment
Below in conjunction with drawings and Examples the present invention is described in detail.
As shown in Figure 1, the present invention includes the phased array emitting and receiving head coil 2 that a parallel emitting and receiving radio-frequency interface circuit 1 and is set in human body head.After parallel emitting and receiving radio-frequency interface circuit 1 will be divided into eight tunnel identical radiofrequency signals from the single channel radiofrequency signal A of single channel power amplifier output, eight tunnel radiofrequency signals are carried out linear phase shift respectively, and make the phase shift of eight tunnel radiofrequency signals differ certain numerical value successively, reach even until the radio-frequency field of launching.Simultaneously, parallel emitting and receiving radio-frequency interface circuit 1 sends eight tunnel radiofrequency signals for phased array emitting and receiving head coil 2, so that the hydrogen atom that is in the human brain soft tissue in the phased array emitting and receiving head coil 2 is encouraged, make the human body hydrogen atom produce magnetic resonance signal.Phased array emitting and receiving head coil 2 feeds back to parallel emitting and receiving radio-frequency interface circuit 1 with eight road magnetic resonance signals that produced again, after by parallel emitting and receiving radio-frequency interface circuit 1 eight road magnetic resonance signals being enlarged into B, flow to reconstruction and aftertreatment that magnetic resonance imaging system carries out image.
Parallel emitting and receiving radio-frequency interface circuit 1 of the present invention comprises that a power splitter 11, eight phase shifters 12, eight attenuators 13, eight emissions receive switch 14 and eight prime amplifiers 15.Wherein:
The input end of power splitter 11 connects the output terminal of single channel power amplifier, being divided into eight tunnel identical radiofrequency signals equably from the single channel radiofrequency signal A of single channel power amplifier output.In the present embodiment, what power splitter 11 adopted is eight equal parts Wilkinson merit parallel circuit, and this merit parallel circuit is made of the discrete component of high-frequency non-magnetic, and the centre frequency of its work is 123.2MHz.8 output ports have connected high-power heat radiation isolation resistance respectively, and avoiding when the output terminal impedance mismatching, signal is reflected and is coupled to other passage, influences merit branch result.
The input end of each phase shifter 12 all connects the output terminal of corresponding power splitter 11, carries out linear phase shift respectively with eight tunnel radiofrequency signals that power splitter 11 is told, and obtains equally distributed radio-frequency field.In the present embodiment, what phase shifter 12 adopted is concentric cable, the phase-shift phase of every concentric cable is by the decision of its length, such as: the cable length of per 90 ° of phase-shift phases is approximately 41cm (this length comprises the connector adapter of concentric cable) in Siemens 3T system.Input one emission received switch 14 after the radiofrequency signal of each phase shifter 12 output was regulated amplitude through an attenuator 13.The present invention is with respect to the multi-channel parallel emission coefficient of using a plurality of power amplifiers, adopt merit branch mode to save the expense of buying or develop expensive magnetic resonance power amplifier, can use lower cost to reach the effect of multi-channel parallel emission and radio-frequency field shimming.
The control end of each emission reception switch 14 all connects the control system (not shown) of scanner, is used for the switching controls instruction U of the emission or the reception of receiving control system output.The I/O end that each emission receives switch 14 connects phased array emitting and receiving head coil 2, and the output terminal that each emission receives switch 14 is connected with the input end of a prime amplifier 15 respectively, the output terminal of each prime amplifier 15 connects magnetic resonance imaging system respectively, is used for that phased array emitting and receiving head coil 2 is produced magnetic resonance signal B and amplifies back input magnetic resonance imaging system.Prime amplifier 15 also has the decoupling function, thereby can improve the signal to noise ratio (S/N ratio) of the image of magnetic resonance imaging system output.In the present embodiment, the frequency of operation that emission receives switch 14 is 123.2MHz, controls the sequential of parallel emitting and receiving radio-frequency interface circuit 1 by the high-low level of magnetic resonance system.What prime amplifier 15 adopted is the low-noise factor that Siemens Company provides, the 3T prime amplifier of high-gain.
As shown in Figure 2, phased array emitting and receiving head coil 2 of the present invention comprises an inner casing 21 and the shell 22 that two ends are penetrating, the position of inner casing 21 and shell 22 corresponding tester's eyes all offers a rectangular form 23, after the tester can be enclosed within phased array emitting and receiving head coil 2 on the head, tester's eyes can be observed visual pattern by form 23, the cerebral function district of tester's correspondence will obtain stimulating in the functional MRI experiment, produce excited and function corresponding magnetic resonance signal.The structure of form 23 of the present invention is different from the form that tradition is used, and has a dividing plate in the middle of traditional form, and the visual field of right and left eyes is separated.And the present invention has removed middle dividing plate, and the visual field of right and left eyes is opened fully, helps testing the tested visual stimulus clearly of carrying out.
As shown in Figure 3, the outside surface of inner casing 21 is provided with upper and lower two circles totally eight phased array surface loops 24 in the phased array emitting and receiving head coil 2 of the present invention, as the ch1 among Fig. 3,2,3,4,5,6,7 and 8, i.e. four pairs of upper and lower phased array surface loops 24 are as the ch7 among Fig. 3 and 3, ch8 and 4, ch5 and 1, ch6 and 2.Wherein, three pairs of upper and lower phased array surface loops 24, be symmetrical arranged as the ch7 among Fig. 3 and 3, ch8 and 4, ch6 and 2, remaining a pair of upper and lower phased array surface loop 24, phased array surface loop 24 as ch5 among Fig. 3 and 1 middle and lower part surrounds form 23, thereby make to be asymmetric setting to upper and lower phased array surface loop 24 as the ch5 among Fig. 3 and 1.
Owing to all have the effect of intercoupling between the two adjacent phased array surface loops 24 and between the two phased array surface loops 24 of adjacent diagonal line, therefore the present invention is overlapping with the part area of two adjacent phased array surface loops 24, but be not in contact with one another, purpose is to remove mutual inductance each other, reach the uncoupling effect, and then improve the signal to noise ratio (S/N ratio) and the imaging scope of magnetic resonance image (MRI) effectively.For the coupling between the two phased array surface loops 24 of adjacent diagonal line, the present invention realizes by some public capacitor C 1 ', C2 ', C3 ', C4, C5, C6, C7 and C8 are set; Equally, be to reach the decoupling effect between the corresponding asymmetrical phase control battle array surface loop 24 in the phased array surface loop 24 that wherein surrounds form 23 and another circle by a public capacitor C 9, thereby further improve the signal to noise ratio (S/N ratio) and the imaging scope of magnetic resonance image (MRI), be functional MRI experiment and cognitive science experiment service better.
As shown in Figure 4, each phased array surface loop 24 comprises three fixed capacity C1, C2 and C3 in the phased array emitting and receiving head coil 2 of the present invention, three tunable capacitor Cf, Cp and Cs, and an inductance L 1.Wherein, fixed capacity C1, C2 and C3, tunable capacitor Cf, Cp, and inductance L 1 constitutes a resonant tank, the two ends of tunable capacitor Cp receive switch 14 by the emission that tunable capacitor Cs connects in the parallel emitting and receiving radio-frequency interface circuit 1, be used to receive from parallel emitting and receiving radio-frequency interface circuit 1 output through dephased eight tunnel radiofrequency signals, eight tunnel radiofrequency signals are divided into two groups up and down, respectively in order on driving, two enclose eight phased array surface loops 24 down, phase shift difference in every circle between the adjacent two phased array surface loops 24 is 90 °, on, the two phased array surface loops 24 that following two circles are corresponding (such as: the ch7 among Fig. 3 and 3, ch8 and 4, ch5 and 1, ch6 and 2) phase differential of radiofrequency signal is 180 ° between.The frequency that fixed capacity C1, C2 and C3 cooperate tunable capacitor Cf to come resonant tank, Cp and Cs are used for the impedance matching and the phase place of tuning phased array surface loop 24 respectively.Inductance L 1 is made of four sections copper sheets, and the resonance frequency of this resonant tank is 123.2MHz.In the present embodiment, C1, C2 and C3 are the high pressure resistant fixed capacity of no magnetic, and Cf, Cp and Cs are the high pressure resistant tunable capacitor of no magnetic.
During work of the present invention, power splitter 11 in the parallel emitting and receiving radio-frequency interface circuit 1 will be divided into eight tunnel radiofrequency signals from the single channel radiofrequency signal A of single channel power amplifier output, flow to each phase shifter 12 respectively, each road radiofrequency signal of 12 pairs of inputs of each phase shifter is carried out linear phase shift, obtains uniform launching site.Simultaneously, emission in the parallel emitting and receiving radio-frequency interface circuit 1 receives the emission that switch 14 sends according to the control system of scanner or the switch controlling signal U work of reception, when emission receives the switch controlling signal U that switch 14 receives emission, parallel emitting and receiving radio-frequency interface circuit 1 is in emission state, receive different uniform eight tunnel radiofrequency signals of switch 14 resonant tank transmitter, phase in the phased array surface loop 24 on phased array emitting and receiving head coil 2 by emission, the hydrogen atom that is in the human brain soft tissue in the phased array emitting and receiving head coil 2 is encouraged, make the human body hydrogen atom produce magnetic resonance signal; When emission receives the switch controlling signal U that switch 14 receives reception, parallel emitting and receiving radio-frequency interface circuit 1 is in accepting state, resonant tank on the phased array emitting and receiving head coil 2 in each phased array surface loop 24 receives switch 14 to each emission respectively and sends eight road magnetic resonance signals that human body hydrogen atom excited target produces, and after being enlarged into B by eight prime amplifiers 15 in the parallel emitting and receiving radio-frequency interface circuit 1, flow to reconstruction and aftertreatment that magnetic resonance imaging system carries out image.
The various embodiments described above only are used to illustrate the present invention, and wherein the structure of each parts, connected mode etc. all can change to some extent, and every equivalents of carrying out on the basis of technical solution of the present invention and improvement all should not got rid of outside protection scope of the present invention.
Claims (9)
1. parallel emitting and receiving radio-frequency interface circuit and phased array emitting and receiving head coil, it is characterized in that: described phased array emitting and receiving head coil comprises an inner casing and the shell that two ends are penetrating, the position of the corresponding tester's eye of described inner casing and shell all offers the form of a standard-sized sheet, the outside surface of described inner casing is provided with upper and lower two circles totally eight phased array surface loops, and one of them described phased array surface loop is around described form setting;
Described parallel emitting and receiving radio-frequency interface circuit comprises a power splitter, and the single channel radiofrequency signal of importing is divided into eight tunnel radiofrequency signals; Described power splitter connects eight phase shifters, each road radiofrequency signal that each described phase shifter will be imported is carried out linear phase shift, the I/O end that receives switch by an emission through dephased each road radiofrequency signal is emitted to eight phased array surface loops on the described phased array emitting and receiving head coil, make that the phase shift difference between the adjacent described two phased array surface loops is a definite value in every circle, the phase differential of radiofrequency signal are definite value between the corresponding described two phased array surface loops of upper and lower two circles; Described eight phased array surface loop emitting radio frequency signals are also accepted the human body hydrogen atom and are produced eight road magnetic resonance signals, and described eight road magnetic resonance signals are imported a prime amplifier by the I/O end that each described emission receives switch respectively; The control end that each described emission receives switch all connects the control system of scanner, with the emission that receives described control system output or the switching controls instruction of reception.
2. parallel emitting and receiving radio-frequency interface circuit as claimed in claim 1 and phased array emitting and receiving head coil is characterized in that: described phase shifter is a concentric cable, and the length of described concentric cable determines the phase-shift phase of described phase shifter.
3. parallel emitting and receiving radio-frequency interface circuit as claimed in claim 2 and phased array emitting and receiving head coil, it is characterized in that: the phase shift difference in every circle between the adjacent described two phased array surface loops is 90 °, and the phase differential of radiofrequency signal is 180 ° between the described two phased array surface loops of upper and lower two circle correspondences.
4. parallel emitting and receiving radio-frequency interface circuit as claimed in claim 1 and phased array emitting and receiving head coil is characterized in that: the wherein three pairs of described upper and lower phased array surface loops on the outside surface of described inner casing are for being symmetrical arranged.
5. as claim 1 or 2 or 3 or 4 described parallel emitting and receiving radio-frequency interface circuit and phased array emitting and receiving head coils, it is characterized in that: described parallel emitting and receiving radio-frequency interface circuit also comprise be connected each described phase shifter and emission receive between the switch, regulate eight attenuators that each road radiofrequency signal amplitude is used.
6. as claim 1 or 2 or 3 or 4 described parallel emitting and receiving radio-frequency interface circuit and phased array emitting and receiving head coils, it is characterized in that: each described phased array surface loop comprises three fixed capacities, three tunable capacitors and inductance on the described phased array emitting and receiving head coil, and three fixed capacities wherein, two tunable capacitors and inductance are connected into a resonant tank.
7. parallel emitting and receiving radio-frequency interface circuit as claimed in claim 5 and phased array emitting and receiving head coil, it is characterized in that: each described phased array surface loop comprises three fixed capacities, three tunable capacitors and inductance on the described phased array emitting and receiving head coil, and three fixed capacities wherein, two tunable capacitors and inductance are connected into a resonant tank.
8. parallel emitting and receiving radio-frequency interface circuit as claimed in claim 6 and phased array emitting and receiving head coil is characterized in that: the two ends of the tunable capacitor in the described resonant tank receive switch by the emission that another described tunable capacitor connects in the described radio-frequency interface circuit; Described fixed capacity is the high pressure resistant fixed capacity of no magnetic, and described tunable capacitor is the high pressure resistant tunable capacitor of no magnetic; Inductance is made of four sections copper sheets in the described phased array surface loop.
9. parallel emitting and receiving radio-frequency interface circuit as claimed in claim 7 and phased array emitting and receiving head coil is characterized in that: the two ends of the tunable capacitor in the described resonant tank receive switch by the emission that another described tunable capacitor connects in the described radio-frequency interface circuit; Described fixed capacity is the high pressure resistant fixed capacity of no magnetic, and described tunable capacitor is the high pressure resistant tunable capacitor of no magnetic; Inductance is made of four sections copper sheets in the described phased array surface loop.
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