CN102551716A - Magnetic resonance system and magnetic resonance method - Google Patents
Magnetic resonance system and magnetic resonance method Download PDFInfo
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- CN102551716A CN102551716A CN2010106129821A CN201010612982A CN102551716A CN 102551716 A CN102551716 A CN 102551716A CN 2010106129821 A CN2010106129821 A CN 2010106129821A CN 201010612982 A CN201010612982 A CN 201010612982A CN 102551716 A CN102551716 A CN 102551716A
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Abstract
The invention discloses a magnetic resonance system and an operation method thereof. The magnetic resonance system comprises a multichannel coil assembly capable of working in a first mode and a second mode. The multichannel coil assembly comprises a plurality of coil components and a plurality of mode switches, wherein each mode switch is connected between at least two coil components in switch mode. When the multichannel coil assembly works in the first mode, the at least one mode switch is operated so as to lead the coil components to be disconnected, and the disconnected coil components are configured to respond to a plurality of first input signals to emit first radio-frequency signals. When the multichannel coil assembly works in the second mode, the at least one mode switch is operated so as to lead the coil components to be connected, and the connected coil components are configured to respond to a plurality of second input signals to emit or receive second radio-frequency signals. The invention further discloses the coil assembly used in the magnetic resonance system.
Description
Technical field
The present invention relates to magnetic resonance system; Be particularly related to a kind of magnetic resonance system that thermotherapeutic function and nuclear magnetic resonance function are organically combined, and relate to a kind of this magnetic resonance system of operating to be implemented in the operational approach of switching between thermotherapeutic function and the nuclear magnetic resonance function.
Background technology
Numerous clinical researches show, auxiliary thermotherapy is a kind of effective means for cancer or oncotherapy when combination with radiotherapeutic and chemotherapy are used together.Make the temperature of tumor tissues between 41 degrees centigrade to 43 degrees centigrade, keep one section preset time at interval through auxiliary thermotherapy, can significantly improve the kill ratio (kill-rate) of tumor cell.Based on security consideration, the temperature of the normal health tissue around the tumor tissues must maintain under the specific temperature.Therefore, in the process of thermotherapy, be necessary to measure in real time the temperature regime of heating region.Traditionally, generally through intrusive mood element (invasive means), for example, and thermocouple, critesistor, perhaps optical fiber probe is measured temperature.Yet use the intrusive mood mode to measure temperature and have following problem: through the above-mentioned measuring cell temperature of energy measurement probe peripheral region only, thereby the spatial sampling density of temperature (spatial sampling density) is lower; In addition, the insertion of probe possibly make sufferer that pain is arranged and have risk.
Magnetic resonance is as a kind of non-intrusion type and unionized technology, and it can be with the anatomical image that generates on any direction.In addition, can also realize temperature survey through nuclear magnetic resonance to imaging region.Yet traditional magnetic resonance system does not consider to merge thermal therapy system as yet in design.Therefore, simply traditional RF thermotherapeutic equipment being inserted in the magnetic resonance scanner (MR scanner) of standard, to realize having concurrently the system of thermotherapy and nuclear magnetic resonance function, is very challenging.Such system combination need the two makes very big change to thermal therapy system and magnetic resonance system; Avoiding the problem of (crosstalk) problem of crosstalking between the different system and magnetic resonance thermotherapy data variation, and this will can influence the ability of the thermotherapy dosage of the required transmission of accurate tracking to a great extent.
Therefore, being necessary to provide a kind of has the magnetic resonance system of thermotherapy and nuclear magnetic resonance function concurrently and operates this method with complex function magnetic resonance system to solve the above-mentioned technical problem of mentioning.
Summary of the invention
One aspect of the present invention is to provide a kind of multichannel coil block.This multichannel coil block can be operated in first pattern and second pattern.This multichannel coil block comprises a plurality of coil parts and a plurality of mode switch.Each mode in these a plurality of mode switch with switch be connected these a plurality of coil parts at least between the two.When this multichannel coil block was operated in first pattern, this at least one mode switch was operated to coil part and breaks off each other, and this coil part that breaks off each other is configured to respond a plurality of first input signals to send first radiofrequency signal.When this multichannel coil block was operated in second pattern, this at least one mode switch was operated to coil part and interconnects, and this interconnective coil part is configured to respond a plurality of second input signals and sends or receive second radiofrequency signal.
Another aspect of the present invention is to provide a kind of magnetic resonance system.This magnetic resonance system comprises main magnet, gradient coil and multichannel coil block.This magnetic resonance system is used to produce main field.This gradient coil is used on selected gradient axes, gradient magnetic being affacted main field.This multichannel coil block comprises a plurality of coil parts and a plurality of mode switch.These a plurality of mode switch are connected with the first group of coil that comprises two coil parts with the mode of switch at least, and the mode of switch is connected with the second group of coil that comprises two coil parts at least.When these a plurality of mode switch are turned off; Each of at least two coils of each of at least two coil parts of this first group of coil and this second group of coil is configured to receive first input signal that has particular phases and amplitude; And independently send first radiofrequency signal, so that area-of-interest is heated.When these a plurality of mode switch are closed; At least two coils of this first group of coil are configured to be received in jointly second input signal that has particular phases and amplitude of first passage transmission, and at least two coils of this second group of coil are configured to be received in jointly second input signal that has particular phases and amplitude of second channel transmission.Second group of coil of this first group of coil and this sends or receives second radiofrequency signal, to monitor the temperature of area-of-interest through the nuclear magnetic resonance mode.
Another aspect of the present invention is to provide a kind of method of operating magnetic resonance system.This magnetic resonance system comprises a plurality of coil parts and a plurality of mode switch that are connected with these a plurality of coil parts with the mode of switch.This operational approach comprises the steps: to turn-off in these a plurality of mode switch at least one at least to break off these a plurality of coil parts; A plurality of coil parts through this disconnection send multichannel first radiofrequency signal to area-of-interest; In closed these a plurality of mode switch at least one is to form a plurality of coil group, and this each coil group comprises at least two coil parts that interconnect; And send multichannel second radiofrequency signal comes from this area-of-interest to this area-of-interest or reception multichannel second radiofrequency signal through this a plurality of coil group.
The method of magnetic resonance system of the present invention and operation magnetic resonance system is switched its mode of operation through the mode switch in the operation multichannel coil block, can solve traditional magnetic resonance system technological deficiency of integrated thermotherapeutic function well at least.Switching through pattern can also solve the cross-interference issue that passes through traditionally between the integrated system of simple functions at least, to reach the technique effect of magnetic resonance image-forming temperature measurement function and the organic set of thermotherapeutic function at least.
Description of drawings
Describe for embodiment of the present invention in conjunction with the drawings, can understand the present invention better, in the accompanying drawings:
Shown in Figure 1 is the module diagram of a kind of embodiment of magnetic resonance system of the present invention.
Shown in Figure 2 is the schematic perspective view of a kind of embodiment of the multichannel coil block in the magnetic resonance system shown in Figure 1.
The simplification module diagram that is operated in a kind of embodiment of thermotherapy pattern for magnetic resonance system shown in Figure 1 shown in Figure 3.
The simplification module diagram that is operated in a kind of embodiment of magnetic resonance pattern for magnetic resonance system shown in Figure 1 shown in Figure 4.
The simplification module diagram that is operated in the another kind of embodiment of magnetic resonance pattern for magnetic resonance system shown in Figure 1 shown in Figure 5.
Shown in Figure 6 is the flow chart of a kind of embodiment of the operation magnetic resonance system with complex function shown in Figure 1.
Shown in Figure 7ly be operated in Electromagnetic Simulation that the special absorbance of a kind of embodiment under the thermotherapy pattern distributes sketch map as a result for the magnetic resonance system with complex function shown in Figure 1.
Excitation field (the B1 that is operated in a kind of embodiment under the magnetic resonance pattern for the magnetic resonance system with complex function shown in Figure 1 shown in Figure 8
+) the simulation result sketch map that distributes.
The specific embodiment
One or more specific embodiment of the present invention below will be described.It is to be noted that at first in the specific descriptions process of these embodiments, in order to carry out brief and concise description, this description can not all be done detailed description to all characteristics of the embodiment of reality.Should it is understandable that; In the actual implementation process of any one embodiment; As in the process of any engineering project or design object, in order to realize developer's objectives, in order to satisfy the relevant or commercial relevant restriction of system; Usually can make various concrete decision-makings, and this can change also from a kind of embodiment to another kind of embodiment.In addition; It will also be appreciated that; Though the effort of having done in this development process possibly be complicated and tediously long, yet for those of ordinary skill in the art relevant with content disclosed by the invention, some designs of on the basis of the technology contents that the disclosure discloses, carrying out; Make or produce the technological means that waits change just conventional, be not to be understood that into content of the present disclosure insufficient.
Only if define in addition, technical term that uses in claims and the description or scientific terminology should be the ordinary meaning that the personage understood that has general technical ability in the affiliated technical field of the present invention.
Any order, quantity or importance do not represented in " first " " second " of using in patent application specification of the present invention and claims and similar word, and just are used for distinguishing different ingredients.
" one " perhaps similar words such as " one " does not represent restricted number, but there is at least one in expression.
" comprise " that similar word such as perhaps " comprising " means and appear at the element that perhaps " comprises " " comprising " front or object and contain and appear at " comprising " and perhaps " comprise " element or object and the equivalent element thereof that the back is enumerated, and does not get rid of other elements or object.
" connection " similar word such as perhaps " link to each other " is not to be defined in connection physics or machinery, but can comprise electrical connection, no matter be directly or indirect.
To go through hereinafter, the specific embodiment that the disclosure is described relates generally to the magnetic resonance system that is integrated with thermotherapeutic function.More specifically say it, this magnetic resonance system provides specially designed coil block.This coil block can switch mode work at least the first pattern and second pattern.In one embodiment, this first pattern can be heating mode or thermotherapy pattern.Under this thermotherapy pattern, this coil block can be configured to through with realization function perhaps being treated in the heating of this area-of-interest to the region of interest emission RF energy.This second pattern can comprise magnetic resonance emission and/or reception for the magnetic resonance pattern.Under this magnetic resonance pattern, this identical coil block can be configured to through send and/or received RF signal to realize imaging function or temperature-monitoring function to area-of-interest.Compare with the hybrid system that traditional simple combination of passing through thermal therapy system and magnetic resonance system obtains, the disclosure uses the single coil block with different working modes more effectively to make magnetic resonance system possess thermotherapeutic function.Since this coil block can switch mode move, to carry out thermotherapeutic function and magnetic resonance temperature measurement function, can alleviate or eliminate the cross-interference issue between thermal therapy system and the magnetic resonance system at least.In addition, this newly-designed coil block real-time implementation heating and parallel imaging (parallel imaging) basically in some embodiments.Can improve signal to noise ratio near human body (signal to noise ratio SNR) and through parallel imaging can improve the running speed (acquisition speed) that magnetic resonance temperature is measured through coil block being placed to more.
For understanding the present invention better, below will be at first the overall structure of magnetic resonance system be described in detail.
See also diagram, shown in Figure 1 is magnetic resonance (magnetic resonance, MR) module diagram of a kind of embodiment of system.The operation of magnetic resonance system 10 can be controlled from operator's console 12, and operator's console 12 comprises keyboard or other input equipment 13, control panel 14 and display 16.Control station 12 communicate by letter with computer system 20 through link 18, and provides interface confession operator to be used for the regulation magnetic resonance imaging, demonstration gained image, and to the image carries out image processing, and with data and picture archiving.Input equipment 13 can comprise mouse, stick, keyboard, trace ball, touch screen, optical wand, voice control appliance or any similar or equivalent input equipment, and can be used for interactive geometric specification.
Computer system 20 comprises a plurality of modules, and these modules are through for example communicating with one another through electricity and/or the data connection that utilizes backboard 20a to provide.It can be direct wire link or wireless communication link etc. that data connect.The module of computer system 20 comprises image processor block 22, CPU module 24 and memory module 26.Memory module 26 can comprise the frame buffer that is used for the storing image data array.In the embodiment of replacement, image processor block 22 can be substituted by the image processing function of operation on the CPU module 24.Computer system 20 can be linked to archives media device, permanent or backup of memory memory device or network.Computer system 20 also can communicate through link 34 and system's Control Computer 32 independently.
In one embodiment, system's Control Computer 32 comprises a pack module that intercoms mutually via electricity and/or data connection 32a.It can be wire link or wireless communication link etc. that data connect 32a.In interchangeable embodiment, computer system 20 can realize on identical computer system or a plurality of computer system with the module of system Control Computer 32.The module of system's Control Computer 32 comprises CPU module 36 and is connected to the pulse generator module 38 of operator's console 12 through communication link 40.
In one embodiment, pulse generator module 38 can be integrated in the scanner device (like resonance assembly 52).System's Control Computer 32 receives the order that will carry out scanning sequence from operator's indication through link 40.Pulse generator module 38 is operated the system unit of emitting the pulse train that (that is, carrying out) expect through send describing with instruction, order and/or the request of the timing of sequential, intensity and the shape of radio-frequency pulse that produces and pulse train and data acquisition window and length.Pulse generator module 38 is connected to gradient amplifier system 42, and produces the data be called gradient waveform, the sequential and the shape of the gradient pulse that these gradient waveforms controls will be used in scan period.
In one embodiment, pulse generator module 38 also can receive patient datas from physiology acquisition controller 44, and physiology acquisition controller 44 receives signals from a plurality of different sensors that are connected to the patient, for example from the ECG signal of the electrode that is attached to the patient.Impulse generator module 38 is connected to scan room interface circuit 46, the signal that scan room interface circuit 46 is associated with the situation of patient and magnet system from various pick off receptions.Patient positioning system 48 also receives through scan room interface circuit 46 patient table is moved on to the order that the position of expectation is scanned.
In one embodiment, the gradient waveform of impulse generator module 38 generations is applied gradient amplifier system 42.Gradient amplifier system 42 comprises X axial gradient amplifier, Y axial gradient amplifier and Z axial gradient amplifier.Corresponding physical gradient coil in each gradient amplifier excitation gradient coil assembly (generally marking 50), and produce magnetic field gradient pulse, to be used for that the signal of being gathered is carried out space encoding.Gradient coil assembly 50 forms the part of resonance assembly 52, and resonance assembly 52 comprises the polarization superconducting magnet with superconduction main coil 54.Resonance assembly 52 can comprise whole body radio frequency coil 56, surface or parallel imaging coil 76 or both.The coil 56,76 of radio frequency coil assemblies can be configured for transmitting and receive or only transmit or receive only.Patient or imaging object 70 can be placed in the cylinder type patient imaging volume 72 of resonance assembly 52.Transceiver module 58 in system's Control Computer 32 produces pulse, and these pulses are amplified by radio frequency amplifier 60, and are coupled to radio-frequency coil 56,76 through transmit/receive switch 62.The gained signal that is sent by the excited nucleus among the patient can be by identical radio-frequency coil 56 sensings, and are coupled to preamplifier 64 through transmit/receive switch 62.Perhaps, the signal that is sent by excited nucleus can be by the independent receiving coil sensing such as parallel coil or surface coils 76.In the receptor part of transceiver 58, the magnetic resonance signal that amplifies is carried out demodulation, filtering and digitized.Transmit/receive switch 62 so that during emission mode, radio frequency amplifier 60 is electrically connected to radio-frequency coil 56, and is connected to radio-frequency coil 56 with preamplifier 64 by controlling from the signal of impulse generator module 38 during receiving mode.Transmit/receive switch 62 also can make it possible in emission or receiving mode, use independent radio-frequency coil (for example, parallel or surface coils 76).
By transceiver module 58 digitizeds, and send the memory module 66 in system's Control Computer 32 to by the magnetic resonance signal of radio-frequency coil 56 or parallel or surface coils 76 sensings.Usually, be stored in the memory module 66, up to subsequently they being carried out conversion to create image corresponding to the Frame of magnetic resonance signal temporarily.AP 68 utilizes known alternative approach (modal have Fourier transformation) to create image from magnetic resonance signal.These images send computer system 20 to through link 34, and in computer system 20, it is stored in the memorizer.Order in response to receiving from operator's console 12 can be archived in this view data in the long-term storage device, perhaps can do further processing, pass to operator's console 12 and be presented on the display 16 it through image processor 22.
In one embodiment, this system's Control Computer 32 comprises that also a heating signal source 69 is to produce the thermotherapy radiofrequency signal.
Schematic perspective view for the mixed model coil block 100 that can in magnetic resonance system for example shown in Figure 1, use shown in Figure 2.Be meant the coil block that can be configured to work at least two kinds of patterns at this so-called " mixed model coil block ".For example, coil block 100 can be configured to operate in first pattern or thermotherapy pattern, to realize the thermotherapy purpose to the region of interest emission electromagnetic radiation.Coil block 100 can be configured to operate in second pattern or magnetic resonance pattern.Under the magnetic resonance pattern, coil block 100 is configured to the region of interest emission radiofrequency signal, and receives the radiofrequency signal that comes from area-of-interest.Through the radiofrequency signal that analysis receives, can confirm the temperature and/or the Temperature Distribution of area-of-interest.When coil block 100 is used for when transmitting and receiving radiofrequency signal with the temperature of measuring area-of-interest or Temperature Distribution by control, the magnetic resonance pattern also can be known as the magnetic resonance temperature measurement pattern.
In one embodiment, coil block 100 can be implemented as the whole-body coil that supplies magnetic resonance system 10 to use.In other embodiment, coil block 100 also can be implemented as the head coil that supplies magnetic resonance system 10 to use, torso coil, spine coils, wrist coil, perhaps knee coil etc.
See also Fig. 2, in one embodiment, coil block 100 can be implemented as the transverse field solenoid, to be used to walk abreast emission (parallel transmit) and/or parallel imaging (parallel imaging)." parallel emission " is meant a plurality of coil parts by a plurality of driver drives in that this is so-called, and " parallel imaging " be meant a plurality of coil parts through a plurality of channel receiving signals to be used for fast imaging.This coil block 100 can be configured to have a plurality of coil 110a of group, 110b, 110c.As shown in Figure 2, in one embodiment, coil block 100 can comprise 16 coil groups.In other embodiments, coil block 100 can comprise more than perhaps being less than 16 coil group.For example, in some embodiments, eight coil groups can be set, 12 coil groups, 24 coil groups, perhaps 32 coil groups according to the demand of reality.Further, when controlling coil block 100, can make first group of work especially and transmit and receive the multichannel radiofrequency signal, and with eight coil groups second group do not worked with eight coil groups with 16 coil groups.
Further as shown in Figure 2, in one embodiment, a plurality of coil 110a of group, 110b, 110c can be equably or are distributed in the outer surface of a hollow circular cylinder (scheming not shown) equally spacedly.This cylinder can be the dielectric housing (dielectric shell) that is used to wrap up human body.A plurality of coil 110a of group, 110b, 110c can use bonding method or metal depositional mode to be formed on the cylindrical outer surface.Be appreciated that in interchangeable embodiment a plurality of coil 110a of group, 110b, 110c also can anisotropically be distributed in cylindrical outer surface.In other embodiments, a plurality of coil 110a of group, 110b, 110c can be arranged on such as the cross section and be oval cylinder, the cylinder of eye shape, perhaps octagonal cylinder, and other can rationally think and the outer surface of any structure.
In one embodiment, each of a plurality of coil 110a of group, 110b, 110c can comprise three coil part 112a, 112b, 112c.In other embodiments, also can be configured in each coil group more than three coil parts that perhaps are less than three.In one embodiment, basic mode with linearity links together along same direction between the end of three coil part 112a in each coil group, 112b, 112c and the end.Be appreciated that the polarised direction that these three coil part 112a, 112b, 112c can regard electric field when coil block 100 is operated in the thermotherapy pattern as extends.Be further appreciated that main field (B when these three coil part 112a, 112b, 112c also can regard coil assembly 100 along the line as and be operated in the magnetic resonance pattern
0) direction extend.In one embodiment, these three coil part 112a, 112b, 112c can comprise dipole antenna.Though for purpose of description but not as to restriction of the present disclosure; Dipole antenna is used in context; Yet coil part 112a, 112b, 112c can also comprise the antenna of other types, for example paster antenna, metal micro-strip antenna, metal waveguide, Medium Wave Guide and resonant cavity etc.In one embodiment, dipole antenna 112a, 112b, 112c can be processed and comprised first conductive strips and second conductive strips by the metallic conduction band.
Please continue to consult Fig. 2, in each 110a of coil group, 110b, 110c, this dipole antenna 112a, 112b, 112c are connected with the mode of switch with 116b through a plurality of mode switch 116a.Mode switch 116a is connected between this dipole antenna 112a and the 112b, and mode switch 116b is connected between dipole antenna 112b and the 112c.These a plurality of mode switch 116a and 116b can be closed or turn-off with this dipole antenna 112a, 112b, 112c links together or break off.These a plurality of mode switch 116a and 116b are configured to make coil block 100 between at least two patterns, to switch.This each mode switch 116a and 116b can comprise the switch element of mechanical actuation or the switch element of electrical start.Each mode switch 116a can be controlled to optionally at least two adjacent dipole antennas linked together or break off it be connected with 116b independently.In one embodiment; A plurality of mode switch 116a and 116b among each 110a of coil group, 110b, the 110c can all be closed, so a plurality of dipole antenna 112a, 112b, 112c among each 110a of coil group, 110b, 110c can be electrically connected.Under this situation, coil block 100 can be operated in the magnetic resonance pattern.In another embodiment; A plurality of mode switch 116a and 116b among each 110a of coil group, 110b, the 110c can all be turned off, thereby make a plurality of dipole antenna 112a, 112b, 112c among each 110a of coil group, 110b, the 110c break off mutually.Under this situation, coil block 100 can be operated in heating or thermotherapy pattern.
Please continue to consult Fig. 2, coil block 100 further comprises a shielding element 160.Shielding element 160 can or be formed by other conductive materials by copper mesh.This shielding element 160 can constitute the closed resonance circuit of radiofrequency signal when coil block 100 is operated in the magnetic resonance pattern.Each 110a of coil group, 110b, 110c all electrically connect with shielding element 160.More specifically, the dipole antenna 112a that is positioned at the 110a of coil group, 110b, 110c one side is through conductor 162a and the mode switch 164a end electric connection with shielding element 160.The dipole antenna 112c that is positioned at the 110a of coil group, 110b, 110c opposite side is through conductor 162b and the mode switch 164b other end electric connection with shielding element 160.These two conductor 162a and 162b extend upward with respect to dipole antenna 112a, 112b, 112c so that this shielding element 160 can and a plurality of coil 110a of group, 110b, 110c between certain at interval distance.When coil block 100 was operated in the thermotherapy pattern, these two mode switch 164a and 164b all were turned off, so that dipole antenna 112a and 112c all break off with shielding element 160.When coil block 100 is operated in the magnetic resonance pattern; These two mode switch 164a and 164b all are closed; So that shielding element 160 is connected with dipole antenna 112a, 112b, 112c among each 110a of coil group, 110b, the 110c, thereby constitute closed resonance circuit.
Please continue to consult Fig. 2, for each 110a of coil group, 110b, 110c, this coil block 100 can further be provided with a plurality of first gauge tap 118a, 118b, 118c.Each first gauge tap 118a, 118b, 118c are connected with corresponding dipole antenna 112a, 112b, a 112c with the mode of switch respectively.Each first gauge tap 118a, 118b, 118c can be closed and turn-off independently, to allow perhaps to stop passing through of RF thermotherapeutic signal.When magnetic resonance system 10 was operated in the thermotherapy pattern, a plurality of first gauge tap 118a, 118b, 118c can be closed, and arrived dipole antenna 112a, 112b, 112c to allow the RF thermotherapeutic signal.When magnetic resonance system 10 was operated in the magnetic resonance pattern, a plurality of first gauge tap 118a, 118b, 118c can be turned off, and arrived dipole antenna 112a, 112b, 112c to stop the RF thermotherapeutic signal.
Please consult Fig. 2 and Fig. 3 together, each first gauge tap 118a, 118b, 118c are connected between corresponding a dipole antenna 112a, 112b, 112c and the thermotherapy signal source 132.Thermotherapy signal source 132 is configured to transmit the RF thermotherapeutic signal through these a plurality of first gauge tap 118a, 118b, 118c to each dipole antenna 112a, 112b, 112c.This thermotherapy signal source 132 can provide frequency range at the RF thermotherapeutic signal of 40MHz to 1000MHz.In some embodiments, in order to realize degree of depth heating, the frequency range of this RF thermotherapeutic signal may be limited to 40MHz to 200MHz.
Please continue to consult Fig. 3, can use a power divider 134 to be divided into multichannel signal from the RF thermotherapeutic signal that thermotherapy signal source 132 produces.As shown in Figure 3, in one embodiment, give an example as a kind of, power divider 134 is told three road RF thermotherapeutic signals, this three road RF thermotherapeutics signal through three independently passage be transported to three dipole antenna 112a, 112b, 112c.In other embodiments, more than one dipole antenna, for example two or three, can be configured to receive jointly single pass RF thermotherapeutic signal.For example, in some embodiments, dipole antenna 112a, 112b, 112c can receive the RF thermotherapeutic signal by single channel transfer jointly.
Please continue to consult Fig. 3, can further use a plurality of vector modulators (vector modulator) 136a, 136b, 136c to regulate respectively phase place and amplitude at the RF thermotherapeutic signal of a plurality of channel transfer.In one embodiment, each vector modulator 136a, 136b, 136c can comprise that a phase shifter (phase shifter) and an attenuator (attenuator) are to be used for regulating the phase place and the amplitude of RF thermotherapeutic signal respectively.Be appreciated that; Affact the phase place and the amplitude of the RF thermotherapeutic signal of each dipole antenna 112a, 112b, 112c through independent regulation, can control focus point or focal zone by the RF energy of these dipole antennas 112a, 112b, 112c emission.In one embodiment; Can realize that to the phase place of the RF thermotherapeutic signal of each dipole antenna 112a, 112b, 112c and amplitude three-dimensional focal controls through regulating regulating action; Thereby obtain best special absorbance (specific absorption rate, SAR) control.
Please continue to consult Fig. 3, a plurality of vector modulator 136a recited above, 136b, 136c electrically connect with a plurality of radio frequency amplifier 138a, 138b, 138c respectively.These a plurality of radio frequency amplifier 138a, 138b, 138c are used for necessary signal amplification quantity (gain) to dipole antenna 112a, 112b, 112c emitting radio frequency signal being provided.
Please return and consult Fig. 2, coil block 100 may further include a plurality of second gauge tap 122a, 122b, 122c.Each second gauge tap 122a, 122b, 122c are connected with each 110a of coil group, 110b, 110c with the mode of switch.Each second gauge tap 122a, 122b, 122c can be closed or turn-off, to allow perhaps to stop passing through of magnetic resonance radiofrequency signal.When being closed for one among the second gauge tap 122a, 122b, the 122c; When for example the second gauge tap 122a is closed; The corresponding 110a of coil group can be configured to the pumping signal in receiving magnetic resonance signals source and emitting radio frequency signal perhaps is configured to receive the radiofrequency signal that comes from area-of-interest.When magnetic resonance system 10 was operated in the thermotherapy pattern, a plurality of second gauge tap 122a, 122b, 122c can be turned off, to stop the arrival coil 110a of group, 110b, the 110c of magnetic resonance radiofrequency signal.When magnetic resonance system 10 was operated in the magnetic resonance pattern, a plurality of second gauge tap 122a, 122b, 122c can be closed, to allow the arrival coil 110a of group, 110b, the 110c of magnetic resonance radiofrequency signal.
See also Fig. 4, in one embodiment, each 110a of coil group, 110b, 110c can pass through one and magnetic resonance signal source corresponding among a plurality of second gauge tap 122a, 122b, the 122c 142 and electrically connect.This magnetic resonance signal source 142 can use pulse generator module as shown in Figure 1 38 through the second gauge tap 122a, 122b, 122c the magnetic resonance radiofrequency signal to be provided.
Please continue to consult Fig. 4, can use a power divider 144 will be from the magnetic resonance signal source the 142 magnetic resonance radiofrequency signals that produce be divided into multichannel signal.Further, use a plurality of vector modulator 146a, 146b, 146c, regulate the phase place and the amplitude of the multi channel signals of telling from power divider 144 with correspondence.In other embodiments, can use independently element, for example phase shifter and attenuator replace phase place and the amplitude that vector modulator is regulated magnetic resonance signal.In one embodiment, the radiofrequency signal of in any two adjacent coil groups, transmitting can be arranged to have equal phase contrast.This phase contrast can calculate according to formula as follows:
Δφ＝360°/N (1)，
In formula (1), N is the number of the coil group in the coil block 100, and Δ φ is the phase contrast between any adjacent two coil groups.When coil block 100 has 16 coil groups, can confirm that through formula (1) numerical value of phase difference φ is 22.5 °.In one embodiment, the magnetic resonance radiofrequency signal that is transferred to a plurality of coil group through multichannel can independent regulation become have equal range value.In other embodiments, the magnetic resonance signal that in each passage, transmits can independently carry out amplitude adjusted and phase adjusted according to radio frequency shimming designing technique (RF shimming design technique).Therefore, the magnetic resonance radiofrequency signal of transmission can be passed through appropriate quantification and phase shifts in each passage, and produces basic excitation field (B uniformly
1Field).
Please continue to consult Fig. 4, a plurality of vector actuator 146a, 146b, 146c and a plurality of radio frequency amplifier 148a, 148b, 148c electrically connect.These a plurality of radio frequency amplifier 138a, 138b, 138c are used for necessary signal amplification quantity (gain) to the 110a of coil group, 110b, 110c emitting radio frequency signal being provided.
Please further consult Fig. 4, a plurality of transmit-receive switch 124a, 124b, 124c are electrically connected between a plurality of second gauge tap 122a, 122b, 122c and corresponding a plurality of coil 110a of group, 110b, the 110c.These a plurality of transmit-receive switch 124a, 124b, 124c can carry out switch motion under the control of the signal that pulse generator module as shown in Figure 1 38 is exported.When under the magnetic resonance pattern, needing emitting radio frequency signal, these a plurality of transmit-receive switch 124a, 124b, 124c are operated so that a plurality of radio frequency amplifier 148a, 148b, 148c are connected with corresponding a plurality of coil 110a of group, 110b, 110c respectively.When under the magnetic resonance pattern, needing received RF signal; These a plurality of transmit-receive switch 124a, 124b, 124c are operated so that a plurality of preposition radio frequency amplifier 126a, 126b, 126c are connected with corresponding a plurality of coil 110a of group, 110b, 110c, so that the radiofrequency signal that receives is carried out preposition amplification.
In the description of being done with reference to figure 3 and Fig. 4, the separate signal source, for example, RF thermotherapeutic signal source 132 and magnetic resonance radio-frequency signal source 142 are used to produce corresponding RF thermotherapeutic signal and magnetic resonance radiofrequency signal respectively.In other embodiments, also can use single signal source to produce and to supply radio frequency heating and the shared radiofrequency signal of nuclear magnetic resonance.Can allow to use the public radio-frequency transmissions passage that can supply two kinds of mode of operations to share like this, so can simplify system configuration, and can reduce the cost of clinical practice.
See also Fig. 5, in a kind of interchangeable embodiment, also can use a plurality of magnetic resonance signals source to replace single magnetic resonance signal source (in Fig. 4, describing) to produce the magnetic resonance radiofrequency signal.As shown in Figure 5, a plurality of coil 110a of group, 110b, 110c can communicate through a plurality of second gauge tap 122a, 122b, 122c and a plurality of magnetic resonance signals source 142a, 142b, 142c.Each magnetic resonance signal source 142a, 142b, 142c are configured to produce to each 110a of coil group, 110b, rf pulse sequence that 110c is special.Because each 110a of coil group, 110b, 110c drive through rf pulse sequence independently; Therefore pass through the parameter of the pulse train of each 110a of coil group of design, 110b, 110c correspondence; Can reduce secondary lobe aliasing (aliasing sidelobes) through so-called " parallel emission ", in compound excitation field, to guide space-time transformation.
Shown in Figure 6 is the flow chart of the method 200 of operation magnetic resonance system 10 shown in Figure 1.This method 200 can be programmed for programmed instruction or computer software, and is kept on the storage medium that can be read by computer or processor.When this programmed instruction is carried out by computer or processor, can realize each step shown in flow chart.The medium that is appreciated that computer-readable can comprise volatibility with non-volatile, with any method or technology realize movably and non-movably medium.More specifically say it, the medium of computer-readable includes but not limited to random access storage device, read only memory, electrically erasable read-only memory; Flash memories, the perhaps memorizer of other technologies, compact disc read-only memory, digitized disk storage; Perhaps other forms of optical memory, cartridge, tape; Magnetic disc, perhaps other forms of magnetic storage, and any other form can be used to stored energy by the storage medium of the predetermined information of instruction execution system visit.
In one embodiment, this method 200 can begin to carry out from step 202.In step 202, the image of the area-of-interest of thermotherapy is carried out in the plan of obtaining.In one embodiment, magnetic resonance system 10 as shown in Figure 1 can be used for obtaining the image of area-of-interest.More specifically, coil block 100 can be manipulated into to the region of interest emission radiofrequency signal with the excitation atomic nucleus.This coil block 100 can further be examined the radiofrequency signal that produces by operation with the excited atom that receives area-of-interest, thereby can obtain the image of area-of-interest.In other embodiments, can use and include but not limited to for example computed tomography (computed tomography, CT) system obtains the image of area-of-interest.
In step 204, this method 200 can continue to confirm to affact according to the image information obtained the Optimal Signals parameter of the radiofrequency signal of coil block 100.Particularly, the image that in step 202, obtains can be handled with different tissues such as identification tumors through segmentation (segmented).Then, through carrying out the electromagnetism numerical simulation to obtain the electric field of dipole antenna.After obtaining the distribution of electric field and electric conductance, can calculate Optimal Signals parameters such as comprising antenna phase and amplitude.
In step 206, after confirming good Optimal Signals parameter, at least one mode switch of coil block 100 can be carried out work so that coil block 100 is transformed into the thermotherapy pattern by operation.In one embodiment, mode switch 116a and 116b as shown in Figure 2 can be turned off, and break off connection each other with a plurality of dipole antenna 112a, 112b, 112c with coil block 100.In addition, mode switch 164a and 164b also can be turned off, so that dipole antenna 112a, 112b, 112c and shielding element 160 are broken off.
In step 208, the RF thermotherapeutic signal that this method 200 can continue to have the Optimal Signals parameter affacts coil block 100.Because dipole antenna 112a, 112b, 112c break off connection each other, each dipole antenna 112a, 112b, 112c can act on the RF thermotherapeutic signal independently.In one embodiment, a plurality of first gauge taps that are associated with these a plurality of dipole antenna 112a, 112b, 112c can be closed, to carry from the RF thermotherapeutic signal of thermotherapy signal source 132 outputs through a plurality of passages.Can use power divider 134 the RF thermotherapeutic signal of thermotherapy signal source 132 outputs to be divided into the radiofrequency signal of a plurality of channel transfer.Further, can use a plurality of vector modulator 136a, 136b, 136c to be adjusted in the phase place and the amplitude of the RF thermotherapeutic signal of a plurality of channel transfer respectively.Fig. 7 shows the simulation result that special absorbance that coil block 100 is operated in the anti-body that the thermotherapy pattern obtains distributes.As shown in Figure 7, on the XZ plane or in the XY plane, can control the zone that RF energy focuses on, to realize heating to area-of-interest through control phase and amplitude.Therefore, not only realize that physically three-dimensional special absorbance or electric field controls are possible, and can realize simultaneously the sufferer tissue being heated and alleviate the injury to health tissues through the control RF energy.
In other embodiments, in step 208, when coil block 100 is operated in the thermotherapy pattern, can be placed in the cylinder object (bolus) that comprises high-k liquid or deionization liquid and the encirclement human body.This object (bolus) can be used to increase the RF energy that is coupled to human body, and can be used to take away the heat on human body skin surface.
In step 212, this method 200 can continue to judge whether receive the temperature survey instruction, and this temperature survey instruction is used to detect the temperature of the object that is receiving thermotherapy.In one embodiment, magnetic resonance system 10 can be through the instruction of input equipment as shown in Figure 1 13 or control panel 14 inputs.If determine and receive the temperature survey instruction, then the flow process of this method 200 turns to step 214 to carry out.Do not receive the temperature survey instruction if determine, then the flow process of this method 200 turns back to step 208, to continue that thermotherapy is carried out in the target area.
In step 214, this method 200 continues to work so that coil block 100 is converted under the magnetic resonance pattern through a plurality of mode switch of operation.As combining the description that Fig. 2 did, this coil block 100 can comprise a plurality of coil 110a of group, 110b, 110c.Under the magnetic resonance pattern, mode switch 116a and 116b in the 110a of coil group, 110b, the 110c are closed, so that dipole antenna 112a, 112b, 112c are linked together.Simultaneously; Mode switch 164a and 164b in the 110a of coil group, 110b, the 110c are closed; So that the dipole antenna 112a in the dipole antenna coil 110a of group, 110b, the 110c, 112b, 112c and shielding element 160 are linked together, and constitute closed resonance circuit.
In step 216, these method 200 continuation effect magnetic resonance radiofrequency signals are to the 110a of coil group, 110b, 110c, to encourage nuclear radiofrequency signal to region of interest emission.In one embodiment, each 110a of coil group, 110b, 110c can act on independently magnetic resonance radiofrequency signal respectively.In one embodiment; Can also use a plurality of second gauge tap 122a, 122b, 122c to control the multi-channel magnetic resonance radiofrequency signal that comes from magnetic resonance signal source 142 respectively, and use the magnetic resonance radiofrequency signal demultiplexing signal of power splitter 144 magnetic resonance signal 142 outputs.Further, can also use a plurality of vector modulator 146a, 146b, 146c to be adjusted in the phase place and the amplitude of the magnetic resonance radiofrequency signal of transmission in a plurality of passages respectively.Shown in Figure 8ly be operated under the magnetic resonance pattern excitation field (B1 for magnetic resonance system 10
+) simulation result.The standard deviation of excitation field is less than 3%, thereby can obtain excitation field more uniformly.
In step 216, this method 200 also continues to receive the radiofrequency signal that produces owing to area-of-interest generation magnetic resonance.From the above mentioned, this coil block 100 possibly comprise 16 coil groups.In one embodiment, when coil block 100 received RF signals, these 16 coil groups can all be used for received RF signal.In other embodiments, can select also wherein that eight coil groups come received RF signal, and make other eight coil groups can not received RF signal.Then, the radiofrequency signal that receives through analysis promptly can be measured the temperature and the Temperature Distribution of area-of-interest.In one embodiment, can use and differ the proton resonance frequency (proton resonance frequency PRF) moves temp measuring method and measures temperature and Temperature Distribution.Variations in temperature can use following relation equation to express:
Wherein in formula (2), α is a thermal constant, and γ is a gyromagnetic ratio, B
0Be main field strength, TE is the echo time,
Be at the benchmark image and the phase contrast between the measurement image that obtains during the thermometric that are heated into as preceding acquisition.In other embodiments, also can use other relational expression to measure temperature, for example can use the relational expression between relaxation time and the temperature to measure temperature.
In step 218, this method 200 can continue to judge whether the Temperature Distribution of measurement meets preset standard.For example, in the thermotherapy process, the Temperature Distribution between heating region and the normal structure on every side should satisfy certain standard, to guarantee that normal structure on every side is not by superheated.When step 218 was judged this Temperature Distribution and do not met predetermined standard, the flow process of this method 200 turned back to step 204, to be modified for the Optimal Signals parameter of the RF thermotherapeutic signal of using coil block 100.When step 218 was judged this Temperature Distribution and met predetermined standard, flow process turned to step 222 to continue to carry out.
In step 222, this method continues to judge whether the Temperature Distribution of measuring reaches preset temperature value.For example, in the thermotherapy process, the temperature of heating region need remain in certain temperature range usually, for example between 41 degrees centigrade to 43 degrees centigrade.Therefore, when the temperature of judging heating region when step 222 did not reach preset temperature value as yet, the flow process of this method 200 turned back in the step 208,, to coil block 100 target area is heated with continuation effect RF thermotherapeutic signal.When the temperature of judging heating region when step 222 had reached preset temperature value, then flow process turned to end.
Should be understood that more than combining Fig. 6 is not to carry out according to the definite order that Fig. 6 described to method 200 described a plurality of steps.This method 200 in fact can according to can think and suitable order carry out.In addition, in some embodiments, can have than Fig. 6 and more Duo or still less step is performed.
Though the embodiment in conjunction with specific describes the present invention, those skilled in the art will appreciate that and to make many modifications and modification the present invention.Therefore, recognize that the intention of claims is to be encompassed in all such modifications and the modification in true spirit of the present invention and the scope.
Claims (19)
1. multichannel coil block, this multichannel coil block is configured to be operated in first pattern and second pattern, it is characterized in that: this multichannel coil block comprises:
A plurality of coil parts; And
A plurality of mode switch, each the mode in these a plurality of mode switch with switch be connected these a plurality of coil parts at least between the two;
Wherein, when this multichannel coil block was operated in first pattern, this at least one mode switch was manipulated into coil part is broken off each other, and this coil part that breaks off each other is configured to respond a plurality of first input signals to send first radiofrequency signal; And
Wherein, when this multichannel coil block was operated in second pattern, this at least one mode switch was manipulated into coil part is interconnected, and this interconnective coil part is configured to respond a plurality of second input signals and sends or receive second radiofrequency signal.
2. multichannel coil block as claimed in claim 1 is characterized in that: these a plurality of first input signals are imported into this coil part that breaks off each other area-of-interest is carried out the radio frequency heating.
3. multichannel coil block as claimed in claim 2; It is characterized in that: this multichannel coil block also comprises first signal source and a plurality of first gauge tap, and each of these a plurality of first gauge taps is corresponding one to be connected in the mode of switch and this first signal source and these a plurality of coil parts; When this multichannel coil block was operated in first pattern, at least one in these a plurality of first gauge taps was closure state, made this first signal source to communicate with this coil part that breaks off each other; When this multichannel coil block was operated in second pattern, at least one in these a plurality of first gauge taps was off state, made this first signal source not communicate with coil part.
4. multichannel coil block as claimed in claim 1 is characterized in that: these a plurality of second input signals are imported into this interconnective coil part with the temperature through nuclear magnetic resonance monitoring area-of-interest.
5. the multichannel coil block described in claim 4; It is characterized in that: this multichannel coil block also comprises secondary signal source and a plurality of second gauge tap, and each in these a plurality of second gauge taps is connected with one in the mode of switch and this secondary signal source and these a plurality of coil parts; When this multichannel coil block was operated in first pattern, these a plurality of second gauge taps were off state, so that this secondary signal source can't communicate with coil part; When this multichannel coil block was operated in second pattern, at least one in these a plurality of second gauge taps was closure state so that this secondary signal source can and interconnective coil part between communicate.
6. multichannel coil block as claimed in claim 1 is characterized in that: these a plurality of coil parts comprise dipole antenna.
7. multichannel coil block as claimed in claim 1 is characterized in that: when these a plurality of mode switch were closed, these a plurality of coil parts constituted a transverse-electromagnetic coil to be used for parallel imaging.
8. multichannel coil block as claimed in claim 7; It is characterized in that: this multichannel coil block also comprises shielding element; This shielding element is connected with coil part through mode switch, and when this multichannel coil block was operated in first pattern, the mode switch that is connected with this shielding element was turned off; Make this shielding element and a plurality of coil part break off; When this multichannel coil block was operated in second pattern, the mode switch that is connected with this shielding element was closed, and made a plurality of coil parts of this shielding element and this be connected to constitute current loop.
9. magnetic resonance system, it is characterized in that: this magnetic resonance system comprises:
Main magnet is to be used to produce main field;
Gradient coil is to be used on selected gradient axes, gradient magnetic being affacted main field; And
The multichannel coil block, this multichannel coil block comprises:
A plurality of coil parts; And
A plurality of mode switch, these a plurality of mode switch are connected with the first group of coil that comprises two coil parts with the mode of switch at least, and are connected with the second group of coil that comprises at least two coil parts with the mode of switch;
Wherein, When these a plurality of mode switch are turned off; Each of at least two coils of each of at least two coil parts of this first group of coil and this second group of coil is configured to receive first input signal that has particular phases and amplitude; And independently send first radiofrequency signal, so that area-of-interest is heated; And
Wherein, When these a plurality of mode switch are closed; At least two coils of this first group of coil are configured to be received in jointly second input signal that has particular phases and amplitude of first passage transmission; At least two coils of this second group of coil are configured to be received in jointly second input signal that has particular phases and amplitude of second channel transmission; Second group of coil of this first group of coil and this sends or receives second radiofrequency signal, to monitor the temperature of this area-of-interest through the nuclear magnetic resonance mode.
10. magnetic resonance system as claimed in claim 9 is characterized in that: the secondary signal that is transferred to this second group of coil that comprises at least two coil parts through second channel is transferred between first signal of this first group of coil that comprises two coil parts through first passage relatively at least has phase shifts.
11. magnetic resonance system as claimed in claim 9; It is characterized in that: when these a plurality of mode switch are closed; This coil block forms the transverse-electromagnetic coil that comprises a plurality of coil group; This a plurality of coil group receives these second input signals through a plurality of passages, and phase place and amplitude of secondary signal that should be through a plurality of channel transfer are adjusted according to radio frequency shimming technology.
12. magnetic resonance system as claimed in claim 9; It is characterized in that: this magnetic resonance system also comprises first signal source; This multichannel coil block also comprises a plurality of first gauge taps; The mode of these a plurality of first gauge taps through switch connect with this first signal source and with these a plurality of coil parts in corresponding one be connected, these a plurality of first gauge taps are configured to can be closed or turn-off so that allow or block this first signal source this first input signal is provided.
13. magnetic resonance system as claimed in claim 9; It is characterized in that: this magnetic resonance system also comprises and also comprises the secondary signal source; This multichannel coil block also comprises a plurality of second gauge taps, each in these a plurality of second gauge taps with the mode of switch and this secondary signal source and with these a plurality of coil parts in one be connected; These a plurality of first gauge taps are configured to and can closedly perhaps turn-off to allow or to block this secondary signal source that this second input signal is provided.
14. a method of operating magnetic resonance system, this magnetic resonance system comprise a plurality of coil parts and with the mode and a plurality of mode switch that these a plurality of coil parts are connected of switch, it is characterized in that: this method comprises the steps: at least
Turn-off in these a plurality of mode switch at least one to break off these a plurality of coil parts;
A plurality of coil parts through this disconnection send multichannel first radiofrequency signal to area-of-interest;
In closed these a plurality of mode switch at least one is to form a plurality of coil group, and this each coil group comprises at least two coil parts that interconnect; And
Send multichannel second radiofrequency signal comes from this area-of-interest to this area-of-interest or reception multichannel second radiofrequency signal through this a plurality of coil group.
15. operational approach as claimed in claim 14, wherein this magnetic resonance system also comprises a plurality of first gauge taps, it is characterized in that: this method also comprises the steps:
When a plurality of coil parts through this disconnection send multichannel first radiofrequency signal to area-of-interest, at least one in closed these a plurality of first gauge taps; And
Sending multichannel second radiofrequency signal through this a plurality of coil group when this area-of-interest or reception come from multichannel second radiofrequency signal of this area-of-interest, turn-off this a plurality of first gauge taps.
16. operational approach as claimed in claim 14, wherein this magnetic resonance system also comprises a plurality of second gauge taps, it is characterized in that: this method also comprises the steps:
Sending multichannel second radiofrequency signal through this a plurality of coil group to this area-of-interest or receive when coming from multichannel second radiofrequency signal of this area-of-interest at least one in this second gauge tap of closure; And
When a plurality of coil parts through this disconnection send multichannel first radiofrequency signal to area-of-interest, turn-off this a plurality of first gauge taps.
17. operational approach as claimed in claim 14 is characterized in that: this method also comprises the steps:
Obtain the image of this area-of-interest; And
Confirm to affact the Optimal Signals parameter of the input signal of these a plurality of coil parts based on the image information of this area-of-interest that obtains.
18. operational approach as claimed in claim 17 is characterized in that: this method also comprises the steps:
Measure the Temperature Distribution of area-of-interest through nuclear magnetic resonance;
Whether the Temperature Distribution of judging this measurement satisfies preset condition; And
When the Temperature Distribution of this this measurement does not satisfy preset condition, adjust this Optimal Signals parameter.
19. operational approach as claimed in claim 17 is characterized in that: this method also comprises the steps:
Measure the temperature value of area-of-interest through nuclear magnetic resonance;
Judge whether this temperature value measured satisfies preset value; And
A plurality of coil parts through this disconnection send multichannel first radiofrequency signals to this area-of-interest so that this area-of-interest is heated.
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| CN112763953A (en) * | 2020-12-10 | 2021-05-07 | 复旦大学 | Multipurpose radio frequency coil device for head/knee joint based on 7.0T magnetic resonance imaging system |
| CN112816923A (en) * | 2020-12-29 | 2021-05-18 | 深圳市联影高端医疗装备创新研究院 | Ultrahigh field emission shimming coil structure |
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