CN106842088A - A kind of receiving channel for magnetic resonance radio frequency coil merges device - Google Patents
A kind of receiving channel for magnetic resonance radio frequency coil merges device Download PDFInfo
- Publication number
- CN106842088A CN106842088A CN201710202548.8A CN201710202548A CN106842088A CN 106842088 A CN106842088 A CN 106842088A CN 201710202548 A CN201710202548 A CN 201710202548A CN 106842088 A CN106842088 A CN 106842088A
- Authority
- CN
- China
- Prior art keywords
- circuit
- magnetic resonance
- receiving channel
- phase
- coil
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Granted
Links
Classifications
-
- G—PHYSICS
- G01—MEASURING; TESTING
- G01R—MEASURING ELECTRIC VARIABLES; MEASURING MAGNETIC VARIABLES
- G01R33/00—Arrangements or instruments for measuring magnetic variables
- G01R33/20—Arrangements or instruments for measuring magnetic variables involving magnetic resonance
- G01R33/28—Details of apparatus provided for in groups G01R33/44 - G01R33/64
- G01R33/32—Excitation or detection systems, e.g. using radio frequency signals
- G01R33/36—Electrical details, e.g. matching or coupling of the coil to the receiver
Landscapes
- Physics & Mathematics (AREA)
- Condensed Matter Physics & Semiconductors (AREA)
- General Physics & Mathematics (AREA)
- Magnetic Resonance Imaging Apparatus (AREA)
Abstract
Merge device the invention discloses a kind of receiving channel for magnetic resonance radio frequency coil, including the 1st coil loop~the n-th coil loop, also include the 1st passage preamplifier~the n-th passage preamplifier, also include the 1st receiving channel phase-shift circuit~the n-th receiving channel phase-shift circuit, also include multi-circuit combiner, also include preamplifier power supply circuit, also include interface plug, i-th coil loop passes sequentially through the i-th passage preamplifier, i-th receiving channel phase-shift circuit is connected with the input of multi-circuit combiner, the output end of multi-circuit combiner is connected with interface plug.Multiple receiving channels of magnetic resonance radio frequency coil can be merged into single port output by the device, for only having a magnetic resonance tool for receiving port, can conveniently and effectively be upgraded and extension pertinent instruments function, with potential significant application value.
Description
Technical field
The present invention relates to NMR spectrum and magnetic resonance imaging arts, and in particular to a kind of multi-channel magnetic resonance radio frequency line
The interface adaptive device of circle and magnetic resonance tool main frame.
Background technology
Radio-frequency coil is the significant components in magnetic resonance tool, and it carries launches driving pulse and connect to imaging nuclei
Receive the effect of magnetic resonance signal.Realizing the method for multi-channel measurement generally has following several：
1) in order to improve the signal to noise ratio of the sampling sensitivity of radio-frequency coil and imaging, for different application purposes, at present
Multichannel phase array coil is generally configured with magnetic resonance tool.It is proton for the quite ripe observing nuclear of current technology
Conventional magnetic resonance imaging, for example, can be configured with Siemens, the magnetic resonance tool main frame of PHILIPS Co. multiple signals reception
Port and data processing channel.When multi-channel coil connects magnetic resonance tool main frame, system can be called and coil channel number
Corresponding receiver port and data processing channel, to realize the parallel processing of the magnetic resonance signal that each channel reception of coil is arrived
[1](SIEMENS.Technical document volume 1of2,siemens AG,2004.).Here, the method for using
It is multiple signals receiving port and equal number of data processing channel+data processing channel.Thus, magnetic is constantly complicated to be total to
Shake apparatus structure, also increases the cost and cost of use of magnetic resonance tool；
2) for specific demand, some resonance spectrometers or Image-forming instrument have other atoms in addition to proton
Core is (for example129Xe,23Na) measurement or imaging capability, that is, possess multi-nuclear magnetic resonance measurement or imaging capability, these magnetic resonance
Instrument is configured with the signal receiving channel corresponding to heteronuclear on traditional structure.But, such heteronuclear magnetic resonance signal is received
Passage may only have one of those.On multichannel transmitting and reception of the heteronuclear magnetic resonance measurement with imaging is solved the problems, such as,
LI You et al. [2] (LI You, MAO wen-ping, WANG Hui-wang et al.Design and
Implementation of an RF power amplifier used in nuclear magnetic resonance
imaging.Chinese journal of magnetic resonance imaging,2011,28(3):326-338.) grind
A kind of wide frequency RF power amplifier worked in 300MHz~500MHz frequency ranges is made, it is combined using multiple drive power
The mechanism of power amplification, the auxiliary circuit comprising 2 operational modules and based on broadband directional coupler, is applied to 500MHz high
On resolution ratio liquid H NMR spectroscopy instrument, realize under High-Field1H with13The amplification of C core frequency RF signals.Other connecing in heteronuclear signal
It is also relatively conventional to the way that the heteronuclear magnetic resonance signal for receiving is amplified using wideband pre-amplifier in receipts, BAO
Chang-hong et al. [3] (BAO Chang-hong, SUNHui-jun, BAO Li-jun et al.Design of
Broadband Preamplifier for High-Field NMR Spectrometers.Chinese journal of
magnetic resonance imaging,2011,28(2):216-226.) have developed one kind and be operated in 15MHz~300MHz
Wideband pre-amplifier in frequency range, for the reception of heteronuclear magnetic resonance signal on nuclear magnetic resonance chemical analyser.Using work
The module of a frequency is operated in the module in broadband is instead of conventional magnetic resonance instrument, the working frequency of conventional magnetic resonance is increased
Width, this allows that the coil interface on magnetic resonance tool is adapted to various nuclear imaging coils.Also heteronuclear is just solved many
The signal transmitting and receiving problem of passage coil.But such way has certain defect.The equipment in broadband sets compared to a frequency
For standby, its related performance indicators is simultaneously not so good as the latter, and the wideband equipment of better performances generally requires cost higher.
3) G.shajan et al. [4] (Shajan G, Mirkes C, Buckenmaier K, et al.Three-layered
radio frequency coil arrangement for sodium MRI of the human brain at
9.4Tesla.Magnetic resonance in medicine,2016,75(2):906-916.) in the west of 32 receiving channels
3 layers of brain radio-frequency coil of their making are tested on the sub- magnetic resonance tool of door.Coil is by a 4 passage dipole subcoils, one
Individual 27 channel reception coil and a 4 passage phase array dispatch coils composition for being used to contrast imaging effect.Due to magnetic resonance device
Device only has 32 receiving channels, and the overall channel number of coil has added up 35, therefore in 4 passage phase arrays of contrast imaging
On coil, an interface arrangement is used, it is combined by 4 orthocouplers, the magnetic resonance pulse signal warp of transmitting
Cross one-to-two, it is equal to become four road power after two point four, and each between have 90 degree of signals of phase difference.When signal is received, letter
Number opposite step of process, reaches the signal output of device.The way of G.shajan et al. is 4 passages made based on them
Orthorhombic phase array coil, four passage normal orthogonals on locus of coil, therefore constituted from 4 orthocouplers
Interface arrangement is configured between magnetic resonance tool and coil.It is repetition but the way has certain defect, in the device
Component mutually splices, and the insertion loss of each component can add up in this process so that either in transmitting or reception
Stage, energy has larger loss.In addition, in multi-channel coil, the coupling between coil channel be it is inevitable,
When coupled noise between coil is not eliminated well, transmitting and the receiving efficiency of orthocoupler can receive larger shadow
Ring.Secondly, in the interface arrangement that G.shajan et al. makes, signal is preceding after the output end of orthocoupler merges
Amplifier amplification is put, such way make use of and supply voltage is put before being carried on magnetic resonance tool interface, but by multichannel line
The reception signal of circle is amplified again after merging, and the signal to coil each passage before signal amplification introduces volume
Outer noise.Finally, the concept of " quadrature detection " is earliest Hoult DI et al. [5] (Hoult D I, Chen C N, Sank V
J.QUADRATURE DETECTION COILS-A FURTHER[square root]2IMPROVEMENT IN
SENSITIVITY.Journal of Computer Assisted Tomography,1984,8(1):193.) propose, he
Think quadrature coil because producing the magnetic field of circular polarisation, its detectivity can propose sensitivity compared to single channel coil
It is high 2 times.But for the coil of nonopiate placement, if still using interface arrangement as orthocoupler, tend not to
The excitation being optimal and receiving efficiency.
When a certain imaging nuclei passage of magnetic resonance tool only has all the way, multi-channel rf is completed using single channels
Signal excitation and the reception of coil then have certain difficulty.Try to using more logical on these single channel magnetic resonance tools
Road radio-frequency coil simultaneously obtains, even preferably imaging effect close compared to single channel coil, then must make full use of limited hard
Part condition.In addition, when multi-channel coil hardware or debugging sequence is tested, if a signal transmitting and receiving passage can utilized
Realize the excitation of multi-channel coil and receive, then enormously simplify the complexity of the debugging of hardware and sequence.Mentioned above
Two kinds of situations in, if the reception signal of multi-channel coil can be incorporated in a single channel and connect by certain interface arrangement
Receiving end mouthful, then can provide a kind of effective means of testing.
The content of the invention
For above-mentioned problem in the prior art, the invention provides a kind of receiving channel conjunction for magnetic resonance radio frequency coil
And device, it is capable of achieving to be adapted to connection between multi-channel magnetic resonance radio-frequency coil and the single receiving port of magnetic resonance tool main frame.
A kind of receiving channel for magnetic resonance radio frequency coil merges device, including the 1st coil loop~the n-th coil loop
Road, also including the 1st passage preamplifier~the n-th passage preamplifier, also including the 1st receiving channel phase-shift circuit~the n-th
Receiving channel phase-shift circuit, also including multi-circuit combiner, also including preamplifier power supply circuit, also including interface plug, i-th
The input that coil loop passes sequentially through the i-th passage preamplifier, the i-th receiving channel phase-shift circuit and multi-circuit combiner connects
Connect, the output end of multi-circuit combiner is connected with interface plug, i ∈ { 1~n }.
I-th receiving channel phase-shift circuit as described above is transmission line or is T-shaped circuit or pi-network.
The magnetic resonance signal of the input of multi-circuit combiner is input to after the 1~n receiving channel phase-shift circuit phase shift
Phase is equal.
Multi-circuit combiner as described above is the combiner of Wilkinson circuit structure.
Preamplifier power supply circuit as described above, for loading DC offset voltage to the output of multi-circuit combiner
End, DC offset voltage passes sequentially through multi-circuit combiner, the i-th receiving channel phase-shift circuit and is carried in the i-th passage preamplifier
Output end and for the i-th passage preamplifier is powered.
The output end of multi-circuit combiner as described above is connected by partiting dc capacitor with interface plug.
Preamplifier power supply circuit as described above is connected by bandstop filter with the output end of multi-circuit combiner.
I-th coil loop as described above receives switching switch and connects with the i-th passage preamplifier by the i-th channel emission
Connect, the i-th channel emission is received switching switch and is connected with power splitter by the i-th sendaisle phase-shift circuit, and power splitter is inserted with interface
Head connection.
The phase shift angle difference of the sendaisle of jth -1 phase-shift circuit as described above and jth sendaisle phase-shift circuit and the
J-1 coil loops are identical with the angle of the B1 field vectors that jth coil loop is produced in space, wherein, j ∈ { 2~n }.
It is the adjacent lines ring for being adapted to multi-channel coil that a kind of receiving channel for magnetic resonance radio frequency coil merges device
Application in the shared multi-channel coil situation of the unequal transmitting/reception of angle of the B1 field vectors that road produces in space.
To sum up, the shifted circuit of output signal of each road preamplifier of multi-channel coil is connected with combiner, combining
The one branch connection preamplifier power supply circuit of device output end, another branch receives holding wire and imports interface as a MRI
Plug.Each road transmission signal line of multi-channel coil and transmitting/reception control line also import interface plug.Interface plug is total to magnetic
Vibrating system connectivity port is connected.
The present invention can be not only used for transmitting/reception and share coil, it can also be used to single receiving coil.The present invention is not related to signal to send out
Part is penetrated, either any radiation pattern, can match somebody with somebody the suitable present apparatus, but can be more effective if in non-homogeneous phase excitation
The situation of rate, such as quadrature coil need the scene of transformation, for launching efficiency higher, also relates to transmission channel phase
Adjustment.
Compared with prior art, the present invention has following features：
The present apparatus make use of component as few as possible that the reception signal of multi-channel magnetic resonance radio-frequency coil is merged into single channel
Signal, realizes being adapted to connection between multi-channel coil and the single receiving port of main frame.
The Wilkinson structural circuit that the present apparatus is utilized has preferable interport isolation, coordinates phase shifter to be closed for signal
The influence coupled between Cheng Shi, coil channel is smaller.
The preamplifier power supply circuit of the present apparatus can be simultaneously to coil each passage preamplifier supply
Electricity, and interlock circuit is simple and reliable for structure.In addition, being merged again after the signal of coil each passage is amplified, keep away
The noise for having exempted from late-class circuit is exaggerated.
The present apparatus can be used for the single port efficient reception of the signal under the mode of excitation of uneven phase intervals.Particularly
For the coil of the nonopiate placement of two passages, compared to traditional quadrature exciting and reception, with reference to the nonopiate of present apparatus use
Launch higher with the sensitivity that the mode for receiving obtains signal.
To sum up, the present apparatus take full advantage of phase array coil sensitivity it is high the characteristics of, realized in single channel reception device compared with
The magnetic resonance imaging of good quality, simple structure, strong adaptability.
Brief description of the drawings
Fig. 1 is apparatus of the present invention structural representation in use.
In figure：1- phase-shift circuits；2- multi-circuit combiners；3- preamplifier power supply circuits；4- interface plugs；5- multichannels
Coil；6- preamplifiers.
Fig. 2 is the overall structure and annexation schematic diagram of second embodiment.
In figure：The receiving channel phase-shift circuits of 112- the 1st；The receiving channel phase-shift circuits of 122- the 2nd；The receiving channels of 132- the 3rd
Phase-shift circuit；The receiving channel phase-shift circuits of 142- the 4th；2- multi-circuit combiners；3- preamplifier power supply circuits；4- interfaces are inserted
Head；The coil loops of 501- the 1st；The coil loops of 502- the 2nd；The coil loops of 503- the 3rd；The coil loops of 504- the 4th；601- the 1st leads to
Road preamplifier；The passage preamplifiers of 602- the 2nd；The passage preamplifiers of 603- the 3rd；The preposition amplifications of passage of 604- the 4th
Device；7- bandstop filters；8- partiting dc capacitors.
Fig. 3 is the overall structure and annexation schematic diagram of fourth embodiment.
In figure：The sendaisle phase-shift circuits of 111- the 1st；The sendaisle phase-shift circuits of 121- the 2nd；The receiving channels of 112- the 1st
Phase-shift circuit；The receiving channel phase-shift circuits of 122- the 2nd；2- multi-circuit combiners；3- preamplifier power supply circuits；4- interfaces are inserted
Head；The coil loops of 501- the 1st；The coil loops of 502- the 2nd；The passage preamplifiers of 601- the 1st；The preposition amplifications of passage of 602- the 2nd
Device；7- bandstop filters；8- partiting dc capacitors；9- two-way power splitters；The channel emissions of 1001- the 1st receive switching switch；1002-
2nd channel emission receives switching switch.
Fig. 4 is the schematic diagram of two-way power splitter in fourth embodiment.
In figure：11- input ports；The output ports of 1201- first；The output ports of 1202- second.
Specific embodiment
Reference picture 1, the magnetic resonance coil reception device in the present invention, can be used for some has many nuclear imaging capabilities, but
The magnetic resonance tool of only one of which heteronuclear signal receiving channel, also or for being imaged to conventional protic in proton signal all the way
Receiving channel connecting multi-channel coil is adapted to.It is final to realize that multi-channel magnetic resonance radio-frequency coil connects single receiving channel magnetic
The interface conversion of resonance instrument main frame.
To enable the above objects, features and advantages of the present invention more obvious understandable, 1~4 distinguishes below in conjunction with the accompanying drawings
To four kinds of specific embodiments of the invention (receiving phase of adjacent windings loop poor equal n-channel coil situation, adjacent lines
The folder of the B1 field vectors that the poor 4 equal passage coil situations of the receiving phase on ring road, adjacent windings loop are produced in space
The angle of the B1 field vectors that the unequal n-channel transmitting in the angle/shared coil situation of reception, adjacent windings loop are produced in space is not
Equal two channel emissions/reception shares coil situation) it is described in detail.
Embodiment 1
In the present embodiment, described invention device is used to be adapted to the poor equal multichannel of receiving phase of adjacent windings loop
Receiving coil., this position and direction that would correspond to each coil channel is in the situation mesh that axle surrounds detected space to journey distribution
Be that the signal for receiving multi-channel coil 5 each coil loop is merged into all the way, feeding only possesses to certain imaging nuclei
In one magnetic resonance tool of receiving channel.
A kind of receiving channel for magnetic resonance radio frequency coil merges device, including the 1st receiving channel phase-shift circuit~the n-th
Receiving channel phase-shift circuit, also including multi-circuit combiner 2, also including preamplifier power supply circuit 3, also including interface plug 4.
I-th coil loop passes sequentially through the i-th passage preamplifier, the i-th receiving channel phase-shift circuit and multi-circuit combiner 2
Input connection, the output end of multi-circuit combiner 2 is connected by partiting dc capacitor 8 with interface plug 4, and wherein n leads to for coil
Road number, i ∈ { 1~n }.
Preferably, the phase of jth receiving channel phase-shift circuit and the receiving channel phase-shift circuit of jth+1 differs 360 degree/n, its
In, n is coil channel number, j ∈ { 1~(n-1) }.Multi-path combination is input to after the 1~n receiving channel phase-shift circuit phase shift
The signal phase of the input of device 2 is equal.
Under regular situation, the DC offset voltage carried inside magnetic resonance tool receives line by the signal in interface plug
It is connected to the output end of the preamplifier of coil and it is powered.In the present embodiment, each coil channel is equipped with
Respective preamplifier 6, therefore the interface overload of coil is connected in order to avoid magnetic resonance tool, there is provided external preceding storing
Big device power supply circuit 3 is connected to the output end of multi-circuit combiner 2, Wilkinson circuit of the multi-circuit combiner 2 from n input interfaces
Structure combiner, the i-th receiving channel phase-shift circuit is transmission line, and the angle of phase shift is set by the length of controlling transmission line
Put.Preamplifier power supply circuit 3 is connected to the output end of multi-circuit combiner 2, the direct current of the output of preamplifier power supply circuit 3
Bias voltage is carried in the output end of multi-circuit combiner 2 and is delivered to the input of multi-circuit combiner 2, and DC offset voltage leads to again
Cross the output that the i-th receiving channel phase-shift circuit being connected with the input of multi-circuit combiner 2 is carried in the i-th passage preamplifier
End, and then powered into the i-th passage preamplifier and to the i-th passage preamplifier, preamplifier 6 can be used Shajan
G et al. [6] (Shajan G, Hoffmann J, Budde J, et al.Design and evaluation of an RF
front‐end for 9.4T human MRI[J].Magnetic resonance in medicine,2011,66(2):
In work 594-602.), the preamplifier architectures that Fig. 3 .B are used.
Preferably, also including bandstop filter 7, bandstop filter 7 is LC of the resonance in magnetic resonance signal frequency
Shunt circuit, preamplifier power supply circuit 3 is flowed to for blocking magnetic resonance signal.Partiting dc capacitor 8 is used to separate driving electricity
Source direct current flows into magnetic resonance tool.
Embodiment 2
In the case of four-way coil present embodiment describes adjacent windings loop 90 degree of receiving phase difference to each other,
Four road signals merge into specific embodiment all the way.
A kind of receiving channel for magnetic resonance radio frequency coil merges device, and the multi-channel coil 5 for using is a four-way
Road receiving coil, multi-circuit combiner 2 is a four road combiners of four ports.
As shown in Fig. 2 multi-channel coil 5 includes the 1st coil loop 501, the 2nd coil loop 502, the 3rd coil loop
503rd, the 4th coil loop 504.
Preamplifier 6 includes that the 1st passage preamplifier 601, the 2nd passage preamplifier 602, the 3rd passage are preposition
Amplifier 603, the 4th passage preamplifier 604.
1st coil loop 501 is connected with the 1st passage preamplifier 601, and the signal of the 1st passage preamplifier 601 is defeated
Go out end to be connected with multi-circuit combiner 2 by the 1st receiving channel phase-shift circuit 112.
2nd coil loop 502 is connected with the 2nd passage preamplifier 602, and the signal of the 2nd passage preamplifier 602 is defeated
Go out end to be connected with multi-circuit combiner 2 by the 2nd receiving channel phase-shift circuit 122.
3rd coil loop 503 is connected with the 3rd passage preamplifier 603, and the signal of the 3rd passage preamplifier 603 is defeated
Go out end to be connected with multi-circuit combiner 2 by the 3rd receiving channel phase-shift circuit 132.
4th coil loop 504 is connected with the 4th passage preamplifier 604, and the signal of the 4th passage preamplifier 604 is defeated
Go out end to be connected with multi-circuit combiner 2 by the 4th receiving channel phase-shift circuit 142.
The phase shift angle of the 1st receiving channel phase-shift circuit 112 is -90 degree；
The phase shift angle of the 2nd receiving channel phase-shift circuit 122 is 180 degree；
The phase shift angle of the 3rd receiving channel phase-shift circuit 132 is 90 degree；
The phase shift angle of the 4th receiving channel phase-shift circuit 142 is 0 degree.
Multi-circuit combiner 2 is the combiner of four port Wilkinson circuit structures.
Phase-shift circuit 1 can be the transmission line of different length, according to the different phase shift angle of each passage and magnetic resonance
Signal frequency determines the length of transmission line.Phase-shift circuit 1 can also be π types/T-shaped circuit that lump original paper is constituted.
In order to reduce the possibility that signal puts introducing noise before amplifier 6 before entry, four passages difference of coil
Be configured with preamplifier, therefore the interface overload of coil connected in order to avoid magnetic resonance tool, provided in device it is extra before
Put the output end that amplifier power supply circuit 3 is connected to multi-circuit combiner 2, the direct current biasing of the output of preamplifier power supply circuit 3
Voltage-drop loading multi-circuit combiner 2 output end and be delivered to the input of multi-circuit combiner 2, DC offset voltage again by with
4 receiving channel phase-shift circuits of the input connection of multi-circuit combiner 2 are carried in the defeated of corresponding 4 preamplifiers respectively
Go out end, and then respectively enter 4 preamplifiers and 4 preamplifiers are powered respectively.Preamplifier 6 can be used
Shajan G et al. [6] (Shajan G, Hoffmann J, Budde J, et al.Design and evaluation of an
RF front‐end for 9.4T human MRI[J].Magnetic resonance in medicine,2011,66(2):
In work 594-602.), the preamplifier architectures that Fig. 3 .B are used.
Preferably, also including bandstop filter 7, bandstop filter 7 is LC of the resonance in magnetic resonance signal frequency
Shunt circuit, preamplifier power supply circuit 3 is flowed to for blocking magnetic resonance signal, and partiting dc capacitor 8 is used to separate driving electricity
Source direct current flows into magnetic resonance tool.
Embodiment 3
In the present embodiment, described invention device is used to be adapted to the folder of the B1 field vectors that multiple coil loops are produced in space
The shared multi-channel coil 5 of the unequal transmitting/reception in angle.Now in order to improve launching efficiency and gather the sensitivity of signal,
Need special modification transmitting and receiving path.Purpose is closed in the signal for receiving multi-channel coil 5 each coil loop
And for all the way while, it is ensured that coil has optimal launching efficiency.
A kind of receiving channel for magnetic resonance radio frequency coil merges device, including the 1st receiving channel phase-shift circuit~the n-th
Receiving channel phase-shift circuit, also including multi-circuit combiner 2, also including preamplifier power supply circuit 3, also including interface plug 4.
I-th coil loop passes sequentially through the i-th passage preamplifier, the i-th receiving channel phase-shift circuit and multi-circuit combiner 2
Input connection, the output end of multi-circuit combiner 2 is connected by partiting dc capacitor 8 with interface plug 4, i ∈ { 1~n }.
Preferably, the i-th coil loop receives switching switch and is connected with the i-th passage preamplifier by the i-th channel emission,
I-th channel emission is received switching switch and is connected with power splitter 9 by the i-th sendaisle phase-shift circuit, power splitter 9 and interface plug
4 connections.
Preferably, the phase shift angle difference and jth -1 of the sendaisle of jth -1 phase-shift circuit and jth sendaisle phase-shift circuit
Coil loop is identical with the angle of jth coil loop.
Preferably, the phase shift angle difference and jth -1 of the receiving channel of jth -1 phase-shift circuit and jth receiving channel phase-shift circuit
Coil loop is identical with the angle of jth coil loop, wherein, j ∈ { 2~n }.Through the 1~n receiving channel phase-shift circuit phase shift
The signal phase for being input to the input of multi-circuit combiner 2 afterwards is equal.
Under regular situation, the DC offset voltage carried inside magnetic resonance tool receives line by the signal in interface plug
It is connected to the output end of the preamplifier of coil and it is powered.In this example, each coil channel is equipped with each
Preamplifier 6, therefore in order to avoid magnetic resonance tool connect coil interface overload, there is provided external preamplifier
Power supply circuit 3 is connected to the output end of multi-circuit combiner 2, Wilkinson circuit structure of the multi-circuit combiner 2 from n input interfaces
Combiner, the i-th receiving channel phase-shift circuit is transmission line, and the angle of phase shift is configured by the length of controlling transmission line.
Preamplifier power supply circuit 3 is connected to the output end of multi-circuit combiner 2, and the direct current of the output of preamplifier power supply circuit 3 is inclined
Voltage-drop loading is put in the output end of multi-circuit combiner 2 and the input of multi-circuit combiner 2 is delivered to, DC offset voltage passes through again
The i-th receiving channel phase-shift circuit being connected with the input of multi-circuit combiner 2 is carried in the output of the i-th passage preamplifier
End, and then powered into the i-th passage preamplifier and to the i-th passage preamplifier, preamplifier 6 can be used Shajan
G et al. [6] (Shajan G, Hoffmann J, Budde J, et al.Design and evaluation of an RF
front‐end for 9.4T human MRI[J].Magnetic resonance in medicine,2011,66(2):
In work 594-602.), the preamplifier architectures that Fig. 3 .B are used.
Preferably, also including bandstop filter 7, bandstop filter 7 is LC of the resonance in magnetic resonance signal frequency
Shunt circuit, preamplifier power supply circuit 3 is flowed to for blocking magnetic resonance signal.Partiting dc capacitor 8 is used to separate driving electricity
Source direct current flows into magnetic resonance tool.
Embodiment 4
The angle of the B1 field vectors produced in space present embodiment describes the coil loop of binary channels coil is nonopiate,
Two paths of signals merges into specific embodiment all the way.Now in order to improve launching efficiency and collection signal sensitivity, it is necessary to
Special modification transmitting and receiving path.
A kind of receiving channel for magnetic resonance radio frequency coil merges device, and the multi-channel coil 5 for using is a transmitting
The binary channels coil of one is received, multi-circuit combiner 2 is a two-way combiner for dual-port.
Conventional binary channels quadrature coil typically by orthocoupler (hybrid) module with two-port with
One emission port of magnetic resonance tool main frame and a receiving port are connected.In signal launching phase, by orthocoupler
(hybrid) power of transmission signal is divided into two-way and two-way transmission signal has 90 degree of phase differences to realize quadrature exciting,
Signal receive the stage, and by orthocoupler (hybrid) by the magnetic resonance signal that two-way has 90 degree of phase differences merge with
Realize quadrature receiving.But in application scenes, due to factors such as tested sample shape, volumes, set with orthogonal angle
Coil is not optimal scheme, and now, the non-orthogonal coil with special angle is set and excitation scheme is often more effective
Rate.At this moment corresponding function cannot be realized using orthocoupler (hybrid), so that different interface schemes.
In the present embodiment, it is assumed that the angle of the B1 field vectors that two coils are produced in space is 60 degree.May certify that
During signal excitation, when the angle of the B1 field vectors that the phase difference of two coil excitation signals and two coils are produced in space
When equal, the circular polarisation component in the same direction of the elliptic polarization that coil is produced is maximum.Cut with transmitting reception using two passage power splitters 9
Changing switch 10 coordinates two channel receptions in the embodiment of the present invention to merge the non-orthogonal transmission that device can realize binary channels coil
The function of being received with single channel.
As shown in Fig. 2 multi-channel coil 5 includes the 1st coil loop 501, the 2nd coil loop 502.
Transceiver toggle switch 10 includes that the 1st channel emission receives switching the 1001, the 2nd channel emission of switch and receives switching switch
1002。
Preamplifier 6 includes the 1st passage preamplifier 601, the 2nd passage preamplifier 602.1st coil loop
501 receive switching switch 1001 with the 1st channel emission is connected, and the 1st channel emission receives the signal input part of switching switch 1001
It is connected with two-way power splitter 9 by the 1st sendaisle phase-shift circuit 111；1st channel emission receives the signal of switching switch 1001
Output end is connected with the input of the 1st passage preamplifier 601, then is closed by the 1st receiving channel phase-shift circuit 112 and multichannel
Road device 2 is connected.
2nd coil loop 502 receives switching switch 1002 and is connected with the 2nd channel emission, and the 2nd channel emission receives switching and opens
The signal input part for closing 1002 is connected by the 2nd sendaisle phase-shift circuit 121 with two-way power splitter 9；2nd channel emission is received
The signal output part of switching switch 1002 is connected with the input of the 2nd passage preamplifier 602, then by the 2nd receiving channel
Phase-shift circuit 122 is connected with multi-circuit combiner 2.
The phase shift angle of the 1st sendaisle phase-shift circuit 111 is 0；
The phase shift angle of the 2nd sendaisle phase-shift circuit 121 is 60 degree；
The phase shift angle of the 1st receiving channel phase-shift circuit 112 is 60 degree；
The phase shift angle of the 2nd receiving channel phase-shift circuit 122 is 0.
Multi-circuit combiner 2 is the combiner of two-port Wilkinson circuit structure.
Phase-shift circuit 1 is the transmission line of different length, according to the different phase shift angle of each passage and magnetic resonance signal
Frequency determines the length of transmission line.
In order to reduce the possibility that signal puts introducing noise before amplifier 6 before entry, it is to avoid magnetic resonance tool is connected
The interface overload of coil, provides the output end that extra preamplifier power supply circuit 3 is connected to multi-circuit combiner 2 in device,
The DC offset voltage of the output of preamplifier power supply circuit 3 is carried in the output end of multi-circuit combiner 2 and is delivered to multichannel conjunction
The input of road device 2,2 receiving channels that DC offset voltage is connected by the input with multi-circuit combiner 2 respectively again are moved
Circuitry phase is carried in the output end of corresponding 2 preamplifiers, so enter 2 preamplifiers and respectively to 2 roads before
Put amplifier to power, preamplifier 6 can be used Shajan G et al. [6] (Shajan G, Hoffmann J, Budde J, et
al.Design and evaluation of an RF front‐end for 9.4T human MRI[J].Magnetic
resonance in medicine,2011,66(2):In work 594-602.), the preamplifier architectures that Fig. 3 .B are used.
Preferably, also including bandstop filter 7, bandstop filter 7 is LC of the resonance in magnetic resonance signal frequency
Shunt circuit, preamplifier power supply circuit 3 is flowed to for blocking magnetic resonance signal, and partiting dc capacitor 8 is used to separate driving electricity
Source direct current flows into magnetic resonance tool.
It is above a part of specific embodiment of the invention, protection scope of the present invention is not limited thereto, any ripe
Know those skilled in the art the invention discloses technical scope in, the variations and alternatives that can be readily occurred in should all cover
Within protection scope of the present invention.
Claims (10)
1. a kind of receiving channel for magnetic resonance radio frequency coil merges device, including the 1st coil loop~the n-th coil loop,
Characterized in that, also include the 1st passage preamplifier~the n-th passage preamplifier, also including the 1st receiving channel phase shift electricity
Road~the n-th receiving channel phase-shift circuit, also including multi-circuit combiner (2), also including preamplifier power supply circuit (3), also wraps
Interface plug (4) is included, the i-th coil loop passes sequentially through the i-th passage preamplifier, the i-th receiving channel phase-shift circuit and multichannel
The input connection of combiner (2), the output end of multi-circuit combiner (2) respectively with preamplifier power supply circuit (3) and interface
Plug (4) is connected, i ∈ { 1~n }.
2. a kind of receiving channel for magnetic resonance radio frequency coil according to claim 1 merges device, it is characterised in that
The i-th described receiving channel phase-shift circuit is transmission line or is T-shaped circuit or pi-network.
3. a kind of receiving channel for magnetic resonance radio frequency coil according to claim 2 merges device, it is characterised in that
The magnetic resonance signal phase phase of the input of multi-circuit combiner (2) is input to after the 1~n receiving channel phase-shift circuit phase shift
Deng.
4. a kind of receiving channel for magnetic resonance radio frequency coil according to claim 3 merges device, it is characterised in that
Described multi-circuit combiner (2) is the combiner of Wilkinson circuit structure.
5. a kind of receiving channel for magnetic resonance radio frequency coil according to claim 4 merges device, it is characterised in that
Described preamplifier power supply circuit (3) is inclined for loading DC offset voltage to the output end of multi-circuit combiner (2), direct current
Put voltage and pass sequentially through multi-circuit combiner (2), the i-th receiving channel phase-shift circuit and be carried in the output of the i-th passage preamplifier
Hold and for the i-th passage preamplifier is powered.
6. any one receiving channel for being used for magnetic resonance radio frequency coil according to claim 5 merges device, its feature
It is that the output end of described multi-circuit combiner (2) is connected by partiting dc capacitor (8) with interface plug (4).
7. any one receiving channel for being used for magnetic resonance radio frequency coil according to claim 5 merges device, its feature
It is that described preamplifier power supply circuit (3) is connected by bandstop filter (7) with the output end of multi-circuit combiner (2).
8. any one according to claims 1 to 7 is used for the receiving channel merging device of magnetic resonance radio frequency coil, and it is special
Levy and be, the i-th described coil loop receives switching switch and is connected with the i-th passage preamplifier by the i-th channel emission, the
I channel emissions receive switching switch and are connected with power splitter by the i-th sendaisle phase-shift circuit, power splitter and interface plug (4)
Connection.
9. a kind of receiving channel for magnetic resonance radio frequency coil according to claim 8 merges device, it is characterised in that
The phase shift angle difference of the described sendaisle of jth -1 phase-shift circuit and jth sendaisle phase-shift circuit and the coil loop of jth -1 and
The angle of the B1 field vectors that jth coil loop is produced in space is equal, wherein, j ∈ { 2~n }.
10. it is adaptation multichannel line that the receiving channel for magnetic resonance radio frequency coil described in a kind of claim 8 merges device
The shared multi-channel coil of the unequal transmitting/reception of angle of the B1 field vectors that the adjacent windings loop of circle is produced in space
Application in situation.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN201710202548.8A CN106842088B (en) | 2017-03-30 | 2017-03-30 | A kind of receiving channel merging device for magnetic resonance radio frequency coil |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN201710202548.8A CN106842088B (en) | 2017-03-30 | 2017-03-30 | A kind of receiving channel merging device for magnetic resonance radio frequency coil |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| CN106842088A true CN106842088A (en) | 2017-06-13 |
| CN106842088B CN106842088B (en) | 2019-06-21 |
Family
ID=59141138
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CN201710202548.8A Active CN106842088B (en) | 2017-03-30 | 2017-03-30 | A kind of receiving channel merging device for magnetic resonance radio frequency coil |
Country Status (1)
| Country | Link |
|---|---|
| CN (1) | CN106842088B (en) |
Cited By (2)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN109782204A (en) * | 2019-01-16 | 2019-05-21 | 中国科学院武汉物理与数学研究所 | A kind of multi-nuclear magnetic resonance radio-frequency channel device for polarization transfer enhancing technology |
| CN111538098A (en) * | 2020-04-28 | 2020-08-14 | 江苏大学 | Novel radio frequency excitation system based on overhauser effect |
Citations (8)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| WO2003081272A1 (en) * | 2002-03-21 | 2003-10-02 | Koninklijke Philips Electronics N.V. | Combiner/splitter device for an mri system |
| CN101872001A (en) * | 2010-06-29 | 2010-10-27 | 中国科学院生物物理研究所 | Parallel emitting and receiving radio-frequency interface circuit and phased array emitting and receiving head coil |
| CN201691927U (en) * | 2010-06-29 | 2011-01-05 | 中国科学院生物物理研究所 | Parallel transmission receiving radio frequency interface circuit and phased array transmission receiver coil |
| JP2012080311A (en) * | 2010-10-01 | 2012-04-19 | Hitachi Kokusai Electric Inc | Signal receiving/analyzing device |
| CN102565733A (en) * | 2011-12-12 | 2012-07-11 | 中国科学院深圳先进技术研究院 | Magnetic resonance multi-core array radio frequency device and magnetic resonance signal receiving method |
| CN103513196A (en) * | 2012-06-19 | 2014-01-15 | 上海联影医疗科技有限公司 | Magnetic resonance system, magnetic resonance receiver and reception signal processing method and device of magnetic resonance receiver |
| CN103698725A (en) * | 2013-11-11 | 2014-04-02 | 深圳先进技术研究院 | Multi-channel radio frequency coil interface device for magnetic resonance imaging system |
| CN204302474U (en) * | 2014-12-19 | 2015-04-29 | 中国科学院深圳先进技术研究院 | Magnetic resonance radio frequency shimming system |
-
2017
- 2017-03-30 CN CN201710202548.8A patent/CN106842088B/en active Active
Patent Citations (8)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| WO2003081272A1 (en) * | 2002-03-21 | 2003-10-02 | Koninklijke Philips Electronics N.V. | Combiner/splitter device for an mri system |
| CN101872001A (en) * | 2010-06-29 | 2010-10-27 | 中国科学院生物物理研究所 | Parallel emitting and receiving radio-frequency interface circuit and phased array emitting and receiving head coil |
| CN201691927U (en) * | 2010-06-29 | 2011-01-05 | 中国科学院生物物理研究所 | Parallel transmission receiving radio frequency interface circuit and phased array transmission receiver coil |
| JP2012080311A (en) * | 2010-10-01 | 2012-04-19 | Hitachi Kokusai Electric Inc | Signal receiving/analyzing device |
| CN102565733A (en) * | 2011-12-12 | 2012-07-11 | 中国科学院深圳先进技术研究院 | Magnetic resonance multi-core array radio frequency device and magnetic resonance signal receiving method |
| CN103513196A (en) * | 2012-06-19 | 2014-01-15 | 上海联影医疗科技有限公司 | Magnetic resonance system, magnetic resonance receiver and reception signal processing method and device of magnetic resonance receiver |
| CN103698725A (en) * | 2013-11-11 | 2014-04-02 | 深圳先进技术研究院 | Multi-channel radio frequency coil interface device for magnetic resonance imaging system |
| CN204302474U (en) * | 2014-12-19 | 2015-04-29 | 中国科学院深圳先进技术研究院 | Magnetic resonance radio frequency shimming system |
Cited By (2)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN109782204A (en) * | 2019-01-16 | 2019-05-21 | 中国科学院武汉物理与数学研究所 | A kind of multi-nuclear magnetic resonance radio-frequency channel device for polarization transfer enhancing technology |
| CN111538098A (en) * | 2020-04-28 | 2020-08-14 | 江苏大学 | Novel radio frequency excitation system based on overhauser effect |
Also Published As
| Publication number | Publication date |
|---|---|
| CN106842088B (en) | 2019-06-21 |
Similar Documents
| Publication | Publication Date | Title |
|---|---|---|
| US8269498B2 (en) | Method and apparatus for MRI signal excitation and reception using non-resonance RF method (NORM) | |
| US9459331B2 (en) | RF coil and magnetic resonance imaging device | |
| CN106932743B (en) | Radio frequency coil unit and radio frequency coil for magnetic resonance imaging | |
| WO2020000818A1 (en) | Dual-core radio frequency coil device and dual-core radio frequency array coil device | |
| US7123012B2 (en) | Multiple tuned radio frequency coil for resonance imaging and spectroscopic analysis | |
| US5194811A (en) | Radio frequency volume resonator for nuclear magnetic resonance | |
| US6097186A (en) | Phased-array coil, receive signal processing circuit, and MRI apparatus | |
| US4684895A (en) | Interface system for NMR spectrometer and quadrature probe | |
| US4792759A (en) | Multi-frequency surface probe | |
| KR20080111338A (en) | Magnetic resonance imaging system | |
| CN106842088B (en) | A kind of receiving channel merging device for magnetic resonance radio frequency coil | |
| JP3611378B2 (en) | MRI equipment | |
| KR20170124966A (en) | Apparatus for transmission of magnetic resonance signals by means of differential cable routing | |
| US20040266362A1 (en) | Transmit/receive switch | |
| CN101971044A (en) | RF coil array comprising a coil element with two preamplifiers | |
| US7235973B2 (en) | Phased array coils utilizing selectable quadrature combination | |
| Abuelhaija et al. | Multi‐and dual‐tuned microstripline‐based transmit/receive switch for 7‐Tesla magnetic resonance imaging | |
| CN107121652A (en) | For the multifrequency point array RF receiving coil system in MR imaging apparatus | |
| US10197646B2 (en) | Decoupling of parallel transmission arrays in magnetic resonance imaging | |
| CN216285676U (en) | Magnetic resonance signal receiving device and magnetic resonance imaging system applying same | |
| JP2804907B2 (en) | RF coil device for magnetic resonance equipment | |
| CN205720622U (en) | Local coil assembly and MRI system link for MRI | |
| US11835606B2 (en) | Decoupled MRI coils through coil matching | |
| US20240288520A1 (en) | Nuclear magnetic resonance | |
| JP2007181711A (en) | Mri apparatus |
Legal Events
| Date | Code | Title | Description |
|---|---|---|---|
| PB01 | Publication | ||
| PB01 | Publication | ||
| SE01 | Entry into force of request for substantive examination | ||
| SE01 | Entry into force of request for substantive examination | ||
| GR01 | Patent grant | ||
| GR01 | Patent grant |