CN102551716B - Magnetic resonance system and magnetic resonance method - Google Patents
Magnetic resonance system and magnetic resonance method Download PDFInfo
- Publication number
- CN102551716B CN102551716B CN201010612982.1A CN201010612982A CN102551716B CN 102551716 B CN102551716 B CN 102551716B CN 201010612982 A CN201010612982 A CN 201010612982A CN 102551716 B CN102551716 B CN 102551716B
- Authority
- CN
- China
- Prior art keywords
- coil
- magnetic resonance
- channel
- gauge tap
- mode
- 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.)
- Expired - Fee Related
Links
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, in particular to a kind of magnetic resonance system thermotherapeutic function and nuclear magnetic resonance function organically combined, and relate to a kind of this magnetic resonance system that operates to realize the operational approach switched between thermotherapeutic function and nuclear magnetic resonance function.
Background technology
Numerous clinical researches shows, auxiliary thermotherapy, when combination with radiotherapeutic uses together with chemotherapy, is a kind of effective means for cancer or oncotherapy.Make the temperature of tumor tissues keep one period of predetermined time interval between 41 degrees Celsius to 43 degrees Celsius by auxiliary thermotherapy, the kill ratio (kill-rate) of tumor cell can be significantly improved.Based on security consideration, the temperature of the normal healthy tissues around tumor tissues must maintain under specific temperature.Therefore, in the process of thermotherapy, be necessary the temperature regime measuring heating region in real time.Traditionally, general by intrusive mood element (invasive means), such as, thermocouple, critesistor, or optical fiber probe carrys out measuring tempeature.But there are the following problems to use intrusive mood mode measuring tempeature: only can the temperature of measuring probe peripheral region by above-mentioned measuring cell, thus the space sampling densities of temperature (spatial sampling density) be lower; In addition, the insertion of probe may make sufferer have pain and there is risk.
Magnetic resonance is as a kind of non-intrusion type and unionized technology, and it can be used for generating the anatomical image on any direction.In addition, the temperature survey to imaging region can also be realized by nuclear magnetic resonance.But traditional magnetic resonance system is not yet considered to merge thermal therapy system in design.Therefore, traditional radio-frequency (RF) thermotherapeutic equipment being inserted in the magnetic resonance scanner (MR scanner) of standard simply, to realize the system having thermotherapy and nuclear magnetic resonance function concurrently, is very challenging.Such system combination needs to make very large change to both thermal therapy system and magnetic resonance system, with the problem avoiding crosstalk (crosstalk) problem between different system and magnetic resonance thermotherapy data to be deteriorated, and this will can affect the ability of accurately following the trail of the required thermotherapy dosage transmitted to a great extent.
Therefore, be necessary that providing a kind of has the magnetic resonance system of thermotherapy and nuclear magnetic resonance function concurrently and operate this method with complex function magnetic resonance system to solve the above-mentioned technical problem mentioned.
Summary of the invention
One aspect of the present invention is to provide a kind of multi-channel coil assembly.This multi-channel coil assembly can be operated in first mode and the second pattern.This multi-channel coil assembly comprises multiple coil part and multiple mode switch.Each in the plurality of mode switch with the mode of switch be connected to the plurality of coil part at least between the two.When this multi-channel coil component operation is at first mode, this at least one mode switch is operated to coil part and mutually disconnects, and this coil part mutually disconnected is configured to multiple first input signal of response to send the first radiofrequency signal.When this multi-channel coil component operation is in the second pattern, this at least one mode switch is operated to coil part and is interconnected, and this interconnective coil part is configured to multiple second input signal of response and sends or receive the 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 multi-channel coil assembly.This magnetic resonance system is for generation of main field.This gradient coil in selected gradient axes by Actions of Gradient Magnetic Field to main field.This multi-channel coil assembly comprises multiple coil part and multiple mode switch.The plurality of mode switch is connected with the first group of coil comprising at least two coil parts in the mode of switch, and the mode of switch is connected with the second group of coil comprising at least two coil parts.When the plurality of mode switch is turned off, the each of each of at least two coil parts of this first group of coil and at least two coils of this second group of coil is configured to the first input signal received with particular phases and amplitude, and independently send the first radiofrequency signal, to heat area-of-interest.When the plurality of mode switch is closed, at least two coils of this first group of coil are configured to jointly to be received in second input signal with particular phases and amplitude of first passage transmission, and at least two coils of this second group of coil are configured to jointly to be received in second input signal with particular phases and amplitude of second channel transmission.This first group of coil and this second group of coil are sent or receive the second radiofrequency signal, to be monitored the temperature of area-of-interest by nuclear magnetic resonance mode.
Another aspect of the invention is to provide a kind of method operating magnetic resonance system.Multiple mode switch that this magnetic resonance system comprises multiple coil part and is connected with the plurality of coil part in the mode of switch.This operational approach at least comprises the steps: to turn off at least one in the plurality of mode switch to disconnect the plurality of coil part; Multichannel first radiofrequency signal is sent to area-of-interest by multiple coil parts of this disconnection; At least one in closed the plurality of mode switch is to form multiple coil group, and this each coil group comprises at least two coil parts interconnected; And come from multichannel second radiofrequency signal of this area-of-interest to this area-of-interest or reception by the plurality of coil group transmission multichannel second radiofrequency signal.
The method of magnetic resonance system of the present invention and operation magnetic resonance system, switches its mode of operation by the mode switch in operation multi-channel coil assembly, and at least can solve traditional magnetic resonance system can not the technological deficiency of integrated thermotherapeutic function well.The cross-interference issue traditionally between the integrated system of simple functions at least can also be solved, at least to reach the technique effect of magnetic resonance image-forming temperature measurement function and the organic set of thermotherapeutic function by the switching of pattern.
Accompanying drawing explanation
Be described for embodiments of the present invention in conjunction with the drawings, the present invention may be better understood, in the accompanying drawings:
Figure 1 shows that the module diagram of a kind of embodiment of magnetic resonance system of the present invention.
Figure 2 shows that the schematic perspective view of a kind of embodiment of the multi-channel coil assembly in the magnetic resonance system shown in Fig. 1.
Figure 3 shows that the magnetic resonance system shown in Fig. 1 is operated in the simplification module diagram of a kind of embodiment of thermotherapy pattern.
Figure 4 shows that the magnetic resonance system shown in Fig. 1 is operated in the simplification module diagram of a kind of embodiment of magnetic resonance pattern.
Figure 5 shows that the magnetic resonance system shown in Fig. 1 is operated in the simplification module diagram of the another kind of embodiment of magnetic resonance pattern.
Figure 6 shows that the flow chart with a kind of embodiment of the magnetic resonance system of complex function shown in application drawing 1.
Figure 7 shows that the magnetic resonance system with complex function shown in Fig. 1 be operated in thermotherapy pattern under a kind of Electromagnetic Simulation result schematic diagram of special absorption distribution of embodiment.
Figure 8 shows that the magnetic resonance system with complex function shown in Fig. 1 be operated in magnetic resonance pattern under a kind of excitation field (B1 of embodiment
+) the simulation result schematic diagram that distributes.
Detailed description of the invention
One or more detailed description of the invention of the present invention below will be described.First it is to be noted, in the specific descriptions process of these embodiments, in order to carry out brief and concise description, this description can not all do detailed description to all features of the embodiment of reality.Should be understandable that; in the actual implementation process of any one embodiment; as in the process of any one engineering project or design object; in order to realize the objectives of developer; in order to meet that system is correlated with or that business is relevant restriction; usually can make various concrete decision-making, and this also can change to another kind of embodiment from a kind of embodiment.In addition, it will also be appreciated that, although effort done in this development process may be complicated and tediously long, but for those of ordinary skill in the art relevant to content disclosed by the invention, some designs that the basis of the technology contents of disclosure exposure is carried out, manufacture or production etc. changes just conventional technological means, not should be understood to content of the present disclosure insufficient.
Unless otherwise defined, the technical term used in claims and description or scientific terminology should be in the technical field of the invention the ordinary meaning that the personage with general technical ability understands.
" first " " second " used in patent application specification of the present invention and claims and similar word do not represent any order, quantity or importance, and are only used to distinguish different ingredients.
The similar word such as " one " or " one " does not represent that quantity limits, but represents to there is at least one.
" comprise " or the similar word such as " comprising " mean to appear at " comprising " or " comprising " before element or object contain the element or object and equivalent element thereof that appear at " comprising " or " comprising " presented hereinafter, do not get rid of other elements or object.
" connection " or " being connected " etc. similar word be not defined in physics or the connection of machinery, no matter but can comprise electrical connection, be direct or indirectly.
To hereafter discuss in detail, the detailed description of the invention that the disclosure describes relates generally to the magnetic resonance system being integrated with thermotherapeutic function.More specifically, this magnetic resonance system provides specially designed coil block.This coil block the mode of switch can work at least first mode and the second pattern.In one embodiment, this first mode can be heating mode or thermotherapy pattern.Under this thermotherapy pattern, this coil block can be configured to by region of interest emission radio-frequency (RF) energy to realize the heating of this area-of-interest or treatment function.This second pattern can be launched for magnetic resonance pattern comprises magnetic resonance and/or receive.Under this magnetic resonance pattern, this identical coil block can be configured to by send and/or received RF signal to realize the imaging function of area-of-interest or temperature-monitoring function.With traditional simple combination by thermal therapy system and magnetic resonance system and the hybrid system that obtains is compared, the disclosure uses the single coil block with different working modes more effectively to make magnetic resonance system possess thermotherapeutic function.Because this coil block the mode of switch can carry out action, to perform thermotherapeutic function and magnetic resonance temperature measurement function, at least can alleviate or eliminate the cross-interference issue between thermal therapy system and magnetic resonance system.In addition, this newly-designed coil block can real-time implementation heat and parallel imaging (parallel imaging) in some embodiments substantially.By coil block is placed to closer to human body can improve signal to noise ratio (signal to noise ratio, SNR) and by parallel imaging can improve magnetic resonance temperature measure running speed (acquisition speed).
For understanding the present invention better, will first the overall structure of magnetic resonance system be described in detail below.
Refer to diagram, Figure 1 shows that the module diagram of a kind of embodiment of magnetic resonance (magnetic resonance, MR) system.The operation of magnetic resonance system 10 can control 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 is communicated with computer system 20 by link 18, and provides interface to be used for regulation magnetic resonance imaging for operator, and display gained image, performs image procossing to image, and by data and picture archiving.Input equipment 13 can comprise mouse, stick, keyboard, trace ball, touch screen, optical wand, voice control device or any similar or equivalent input equipment, and can be used for interactive geometric specification.
Computer system 20 comprises multiple module, and these modules are by such as communicating with one another by the electricity that utilizes backboard 20a to provide and/or data cube computation.Data cube computation can be direct wire link or wireless communication link etc.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 for storing array of image data.In the embodiment replaced, image processor block 22 can be substituted by the image processing function that CPU module 24 runs.Computer system 20 can be linked to archives media device, permanent or backup of memory memory device or network.Computer system 20 also communicates with independently System control computer 32 by link 34.
In one embodiment, System control computer 32 comprises the one group of module intercomed via electricity and/or data cube computation 32a phase.Data cube computation 32a can be wire link or wireless communication link etc.In interchangeable embodiment, computer system 20 can realize with the module of System control computer 32 in identical computer system or multiple computer system.The module of System control computer 32 is comprised CPU module 36 and is connected to the pulse generator module 38 of operator's console 12 by communication link 40.
In one embodiment, pulse generator module 38 can be integrated in scanner device (as resonance assembly 52).The instruction that System control computer 32 is received from operator by link 40 will perform the order of scanning sequence.Pulse generator module 38 is by sending the system unit describing and the instruction of the timing of the sequential of the radio-frequency pulse of generation and pulse train, intensity and shape and data acquisition window and length, order and/or request are operated the pulse train that releasings (that is, execution) is expected.Pulse generator module 38 is connected to gradient amplifier system 42, and produces and be called the data of gradient waveform, and these gradient waveforms control the sequential of gradient pulse that uses in scan period and shape.
In one embodiment, pulse generator module 38 also can receive patient data from physiological acquisition controller 44, physiological acquisition controller 44 from the multiple different sensors Received signal strength being connected to patient, such as, from the ECG signal of electrode being attached to patient.Impulse generator module 38 is connected to scan room interface circuit 46, and scan room interface circuit 46 receives the signal be associated with the situation of patient and magnet system from various sensor.Patient positioning system 48 also receives the order carrying out scanning in position patient table being moved on to expectation by scan room interface circuit 46.
In one embodiment, the gradient waveform that impulse generator module 38 produces is applied gradient amplifier system 42.Gradient amplifier system 42 comprises X-axis gradient amplifier, Y-axis gradient amplifier and Z axis gradient amplifier.Physics gradient coil corresponding in each gradient amplifier excitation gradient coil assembly (generally marking 50), and produce magnetic field gradient pulse, carry out space encoding for gathered signal.Gradient coil assembly 50 forms a part for 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 receiving 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 control computer 32 produces pulse, and these pulses are amplified by radio frequency amplifier 60, and is coupled to radio-frequency coil 56,76 by transmit/receive switch 62.The gained signal sent by the excited nucleus in patient can be sensed by identical radio-frequency coil 56, and is coupled to preamplifier 64 by transmit/receive switch 62.Or the signal sent by excited nucleus can be sensed by the separate receive coil of such as parallel coil or surface coils 76.In the receptor part of transceiver 58, demodulation, filtering and digitized are carried out to the magnetic resonance signal amplified.Transmit/receive switch 62 is controlled by the signal from impulse generator module 38, radio frequency amplifier 60 is electrically connected to radio-frequency coil 56 during emission mode, and during receiving mode, preamplifier 64 is connected to radio-frequency coil 56.Transmit/receive switch 62 also can make it possible in transmitting or receiving mode, use individual radio frequency coil (such as, parallel or surface coils 76).
The magnetic resonance signal sensed by radio-frequency coil 56 or parallel or surface coils 76 by transceiver module 58 digitized, and sends the memory module 66 in System control computer 32 to.Usually, the Frame corresponding to magnetic resonance signal is stored in memory module 66 temporarily, until convert to create image to them subsequently.Array processor 68 utilizes known alternative approach (modal have Fourier transformation) to come to create image from magnetic resonance signal.These images send computer system 20 to by link 34, and in computer system 20, it stores in memory.In response to the order received from operator's console 12, this view data can be archived in long-term storage device, or by image processor 22, further process be done to it, pass to operator's console 12 and present on the display 16.
In one embodiment, this System control computer 32 also comprises a heating signal source 69 to produce thermotherapy radiofrequency signal.
Figure 2 shows that the schematic perspective view of the mixed model coil block 100 that can use in the magnetic resonance system such as shown in Fig. 1.The coil block that can be configured to work at least two kinds of patterns is referred at this so-called " mixed model coil block ".For example, coil block 100 can be configured to operate in first mode or thermotherapy pattern, to realize thermotherapy object to region of interest emission electromagnetic radiation.Coil block 100 can be configured to operate in the second pattern or magnetic resonance pattern.Under magnetic resonance pattern, coil block 100 is configured to region of interest emission radiofrequency signal, and receives the radiofrequency signal coming from area-of-interest.By analyzing the radiofrequency signal received, temperature and/or the Temperature Distribution of area-of-interest can be determined.When coil block 100 to be controlled to be used for by transmitting and receiving radiofrequency signal to measure temperature or the Temperature Distribution of area-of-interest, magnetic resonance pattern also can be referred to as magnetic resonance temperature measurement pattern.
In one embodiment, coil block 100 can perform as the whole-body coil for magnetic resonance system 10.In other implementations, coil block 100 also can perform as the head coil for magnetic resonance system 10, torso coil, spine coils, wrist coil, or knee coil etc.
Refer to Fig. 2, in one embodiment, coil block 100 can perform as transverse field solenoid, for carrying out transmitted in parallel (parallel transmit) and/or parallel imaging (parallel imaging).Refer to that multiple coil part is by multiple driver drives at this so-called " transmitted in parallel ", and " parallel imaging " refers to multiple coil part by multiple channel receiving signal for fast imaging.This coil block 100 can be configured to have multiple coil group 110a, 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 or be less than the coil group of 16.For example, in some embodiments, eight coil groups can be set according to the demand of reality, 12 coil groups, 24 coil groups, or 32 coil groups.Further, manipulate there is the coil block 100 of 16 coil groups time, can make to have first group of work of eight coil groups especially and transmit and receive multi-channel radio frequency signal, and making second group with eight coil groups and do not work.
Further as shown in Figure 2, in one embodiment, multiple coil group 110a, 110b, 110c can be distributed in the outer surface of a hollow circular cylinder (scheming not shown) equably or equally spacedly.This cylinder can for the dielectric housing (dielectric shell) for wrapping up human body.Multiple coil group 110a, 110b, 110c can use bonding method or metal depositional mode to be formed on cylindrical outer surface.Be appreciated that in interchangeable embodiment, multiple coil group 110a, 110b, 110c also can anisotropically be distributed in cylindrical outer surface.In other embodiments, it is oval cylinder that multiple coil group 110a, 110b, 110c can be arranged on such as cross section, the cylinder of eye shape, or octagonal cylinder, and other can rationally think and the outer surface of any structure.
In one embodiment, each of multiple coil group 110a, 110b, 110c can comprise three coil parts 112a, 112b, 112c.In other embodiments, also can be configured in each coil group more than three or the coil part that is less than three.In one embodiment, substantially link together in the same direction in a linear fashion between the end of three coil parts 112a, 112b, 112c in each coil group and end.Be appreciated that these three coil parts 112a, 112b, 112c can regard as the polarised direction extension of electric field when being operated in thermotherapy pattern along coil block 100.Be further appreciated that these three coil parts 112a, 112b, 112c also can regard as main field (B when being operated in magnetic resonance pattern along coil block 100
0) direction extend.In one embodiment, these three coil parts 112a, 112b, 112c can comprise dipole antenna.Although in order to the object that describes but not as to restriction of the present disclosure, dipole antenna is used within a context, but coil part 112a, 112b, 112c can also comprise the antenna of other types, such as 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 made up of metal conductor tracks and comprise the first conductive strips and the second conductive strips.
Please continue to refer to Fig. 2, in each coil group 110a, 110b, 110c, this dipole antenna 112a, 112b, 112c are connected in the mode of switch by multiple mode switch 116a with 116b.Mode switch 116a is connected between this dipole antenna 112a and 112b, and mode switch 116b is connected between dipole antenna 112b and 112c.The plurality of mode switch 116a and 116b can be closed or turn off that this dipole antenna 112a, 112b, 112c are linked together or disconnected.The plurality of mode switch 116a and 116b is configured to coil block 100 is switched between at least two patterns.This each mode switch 116a and 116b can comprise the switch element of mechanical actuation or the switch element of electrically start.Each mode switch 116a with 116b can be controlled to optionally be linked together or disconnect it by least two adjacent dipole antennas be connected independently.In one embodiment, multiple mode switch 116a and 116b in each coil group 110a, 110b, 110c can all be closed, and multiple dipole antenna 112a, 112b, 112c therefore in each coil group 110a, 110b, 110c can be electrically connected.In this case, coil block 100 can be operated in magnetic resonance pattern.In another embodiment, multiple mode switch 116a and 116b in each coil group 110a, 110b, 110c can all be turned off, thus multiple dipole antenna 112a, 112b, 112c in each coil group 110a, 110b, 110c are disconnected mutually.In this case, coil block 100 can be operated in heating or thermotherapy pattern.
Please continue to refer to Fig. 2, coil block 100 comprises a shielding element 160 further.Shielding element 160 can be formed by copper mesh or by other conductive materials.This shielding element 160 can form the closed resonance circuit of radiofrequency signal when coil block 100 is operated in magnetic resonance pattern.Each coil group 110a, 110b, 110c are all electrically connected with shielding element 160.More specifically, the dipole antenna 112a being positioned at coil group 110a, 110b, 110c side is electrically connected by one end of a conductor 162a and mode switch 164a and shielding element 160.The dipole antenna 112c being positioned at coil group 110a, 110b, 110c opposite side is electrically connected by the other end of a conductor 162b and mode switch 164b and shielding element 160.These two conductor 162a and 162b upwards extend relative to dipole antenna 112a, 112b, 112c, can and be spaced a distance between multiple coil group 110a, 110b, 110c to make this shielding element 160.When coil block 100 is operated in thermotherapy pattern, these two mode switch 164a and 164b are all turned off, and all disconnect with shielding element 160 to make dipole antenna 112a and 112c.When coil block 100 is operated in magnetic resonance pattern, these two mode switch 164a and 164b are all closed, to make shielding element 160 be connected with dipole antenna 112a, 112b, the 112c in each coil group 110a, 110b, 110c, thus form closed resonance circuit.
Please continue to refer to Fig. 2, for each coil group 110a, 110b, 110c, this coil block 100 can arrange multiple first gauge tap 118a, 118b, 118c further.Each first gauge tap 118a, 118b, 118c is connected with corresponding dipole antenna 112a, 112b, a 112c in the mode of switch respectively.Each first gauge tap 118a, 118b, 118c can be closed independently and turn off, to allow or to stop passing through of radio-frequency (RF) thermotherapeutic signal.When magnetic resonance system 10 is operated in thermotherapy pattern, multiple first gauge tap 118a, 118b, 118c can be closed, and arrives dipole antenna 112a, 112b, 112c to allow radio-frequency (RF) thermotherapeutic signal.When magnetic resonance system 10 is operated in magnetic resonance pattern, multiple first gauge tap 118a, 118b, 118c can be turned off, and arrives dipole antenna 112a, 112b, 112c to stop radio-frequency (RF) thermotherapeutic signal.
Please also refer to Fig. 2 and Fig. 3, each first gauge tap 118a, 118b, 118c is connected between corresponding dipole antenna 112a, 112b, a 112c and thermotherapy signal source 132.Thermotherapy signal source 132 is configured to transmit radio-frequency (RF) thermotherapeutic signal by the 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 radio-frequency (RF) thermotherapeutic signal of 40MHz to 1000MHz.In some embodiments, in order to realize degree of depth heating, the frequency range of this radio-frequency (RF) thermotherapeutic signal may be limited to 40MHz to 200MHz.
Please continue to refer to Fig. 3, can use a power divider 134 that the radio-frequency (RF) thermotherapeutic signal produced from thermotherapy signal source 132 is divided into multichannel signal.As shown in Figure 3, in one embodiment, exemplify as one, power divider 134 separates three tunnel radio-frequency (RF) thermotherapeutic signals, this three tunnels radio-frequency (RF) thermotherapeutic signal by three independently passage be transported to three dipole antennas 112a, 112b, 112c.In other embodiments, more than one dipole antenna, can be configured to jointly receive single pass radio-frequency (RF) thermotherapeutic signal by such as two or three.For example, in some embodiments, dipole antenna 112a, 112b, 112c can receive the radio-frequency (RF) thermotherapeutic signal transmitted by single channel jointly.
Please continue to refer to Fig. 3, multiple vector modulator (vector modulator) 136a, 136b, 136c can be used further to regulate respectively in phase place and the amplitude of the radio-frequency (RF) thermotherapeutic signal of multiple channel transfer.In one embodiment, each vector modulator 136a, 136b, 136c can comprise a phase shifter (phase shifter) and attenuator (attenuator) to be used for regulating phase place and the amplitude of radio-frequency (RF) thermotherapeutic signal respectively.Be appreciated that, be applied to phase place and the amplitude of the radio-frequency (RF) thermotherapeutic signal of each dipole antenna 112a, 112b, 112c by independent regulation, focus point or the focal zone of the radio-frequency (RF) energy of being launched by these dipole antennas 112a, 112b, 112c can be controlled.In one embodiment, three-dimensional focal control can be realized to the phase place of the radio-frequency (RF) thermotherapeutic signal of each dipole antenna 112a, 112b, 112c and amplitude by regulating regulating action, thus obtain best special absorbance (specific absorption rate, SAR) control.
Please continue to refer to Fig. 3, multiple vector modulator 136a, 136b, 136c recited above are electrically connected with multiple radio frequency amplifier 138a, 138b, 138c respectively.The plurality of radio frequency amplifier 138a, 138b, 138c are used for providing necessary signal amplification quantity (gain) to dipole antenna 112a, 112b, 112c emitting radio frequency signal.
Please return and consult Fig. 2, coil block 100 may further include multiple second gauge tap 122a, 122b, 122c.Each second gauge tap 122a, 122b, 122c is connected with each coil group 110a, 110b, 110c in the mode of switch.Each second gauge tap 122a, 122b, 122c can be closed or turn off, to allow or to stop passing through of magnetic resonance radio frequency signal.When in second gauge tap 122a, 122b, 122c is closed, such as, when the second gauge tap 122a is closed, corresponding coil group 110a can be configured to the pumping signal in receiving magnetic resonance signals source and emitting radio frequency signal, or is configured to receive the radiofrequency signal coming from area-of-interest.When magnetic resonance system 10 is operated in thermotherapy pattern, multiple second gauge tap 122a, 122b, 122c can be turned off, to stop arrival coil group 110a, 110b, 110c of magnetic resonance radio frequency signal.When magnetic resonance system 10 is operated in magnetic resonance pattern, multiple second gauge tap 122a, 122b, 122c can be closed, to allow arrival coil group 110a, 110b, 110c of magnetic resonance radio frequency signal.
Refer to Fig. 4, in one embodiment, each coil group 110a, 110b, 110c can be electrically connected by one corresponding in multiple second gauge tap 122a, 122b, 122c and magnetic resonance signal source 142.This magnetic resonance signal source 142 can use pulse generator module 38 as shown in Figure 1 to provide magnetic resonance radio frequency signal by second gauge tap 122a, 122b, 122c.
Please continue to refer to Fig. 4, can use a power divider 144 that the magnetic resonance radio frequency signal produced from magnetic resonance signal source 142 is divided into multichannel signal.Further, use multiple vector modulator 146a, 146b, 146c, regulate phase place and the amplitude of the multi channel signals separated from power divider 144 with correspondence.In other embodiments, can use independently element, such as phase shifter and attenuator replace vector modulator to regulate phase place and the amplitude of magnetic resonance signal.In one embodiment, the radiofrequency signal transmitted in any two adjacent coil groups 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 coil block 100, and Δ φ is the phase contrast between arbitrary neighborhood Liang Ge coil group.When coil block 100 has 16 coil groups, can determine that the numerical value of phase difference φ is 22.5 ° by formula (1).In one embodiment, can independent regulation be become there is equal range value by the magnetic resonance radio frequency signal of channel transmission to multiple coil group.In other embodiments, the magnetic resonance signal transmitted in each passage independently can carry out amplitude adjusted and phase adjusted according to radio frequency shimming designing technique (RF shimming design technique).Therefore, the magnetic resonance radio frequency signal of transmission in each passage through appropriate quantification and phase shift, and can produce basic uniform excitation field (B
1field).
Please continue to refer to Fig. 4, multiple vector actuator 146a, 146b, 146c and multiple radio frequency amplifier 148a, 148b, 148c are electrically connected.The plurality of radio frequency amplifier 138a, 138b, 138c are used for providing necessary signal amplification quantity (gain) to coil group 110a, 110b, 110c emitting radio frequency signal.
Please consult Fig. 4 further, multiple transmit-receive switch 124a, 124b, 124c are electrically connected between multiple coil group 110a, 110b, 110c of multiple second gauge tap 122a, 122b, 122c and correspondence.Switch motion is carried out under the control of the signal that the plurality of transmit-receive switch 124a, 124b, 124c can export at pulse generator module 38 as shown in Figure 1.When needing emitting radio frequency signal under magnetic resonance pattern, the plurality of transmit-receive switch 124a, 124b, 124c are operated multiple radio frequency amplifier 148a, 148b, 148c to be connected with corresponding multiple coil group 110a, 110b, 110c respectively.When needing received RF signal under magnetic resonance pattern, the plurality of transmit-receive switch 124a, 124b, 124c are operated multiple preceding radio frequency amplifier 126a, 126b, 126c to be connected with corresponding multiple coil group 110a, 110b, 110c, to carry out enlarge leadingly to the radiofrequency signal received.
In the description done with reference to figure 3 and Fig. 4, independently signal source, such as, radio-frequency (RF) thermotherapeutic signal source 132 and magnetic resonance radio frequency signal source 142, be used to produce corresponding radio-frequency (RF) thermotherapeutic signal and magnetic resonance radio frequency signal respectively.In other embodiments, also single signal source can be used produce the radiofrequency signal can shared for radio frequency heating and nuclear magnetic resonance.Can allow like this to use the public radio frequency transmitting channel can shared for two kinds of mode of operations, so can simplify system configuration, and the cost of clinical practice can be reduced.
Refer to Fig. 5, in the interchangeable embodiment of one, multiple magnetic resonance signal source also can be used to produce magnetic resonance radio frequency signal to replace single magnetic resonance signal source (describing in the diagram).As shown in Figure 5, multiple coil group 110a, 110b, 110c can be communicated with multiple magnetic resonance signal source 142a, 142b, 142c by multiple second gauge tap 122a, 122b, 122c.Each magnetic resonance signal source 142a, 142b, 142c are configured to produce the special rf pulse sequence of each coil group 110a, 110b, 110c.Because each coil group 110a, 110b, 110c are driven by independently rf pulse sequence, therefore the parameter of pulse train corresponding to design each coil group 110a, 110b, 110c is passed through, secondary lobe aliasing (aliasing sidelobes) can be reduced, to guide space-time transformation in the excitation field of compound by so-called " transmitted in parallel ".
Figure 6 shows that the flow chart of the method 200 of the magnetic resonance system 10 shown in application drawing 1.The 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 performed by computer or processor, each step as shown in the flowchart can be realized.Be appreciated that the medium of computer-readable can comprise volatibility with non-volatile, in any method or technology realize moveable and non-moveable medium.More specifically, the medium of computer-readable includes but not limited to random access storage device, read only memory, electrically erasable read-only memory, flash memories, or the memorizer of other technologies, compact disc read-only memory, digitized disk storage, or other forms of optical memory, cartridge, tape, magnetic disc, or other forms of magnetic storage, and the storage medium that can be used to the predetermined information that stored energy is accessed by instruction execution system of any other form.
In one embodiment, the method 200 can perform from step 202.In step 202., the image of the area-of-interest of thermotherapy is carried out in acquisition plan.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 region of interest emission radiofrequency signal to encourage atomic nucleus.This coil block 100 further by the radiofrequency signal that the excited atom core operating to receive area-of-interest produces, thus can obtain the image of area-of-interest.In other embodiments, can use and include but not limited to that such as computed tomography (computed tomography, CT) system is to obtain the image of area-of-interest.
In step 204, the method 200 can continue the Optimal Signals parameter determining the radiofrequency signal being applied to coil block 100 according to the image information obtained.Specifically, the image obtained in step 202. can by segmentation (segmented) process to identify the tissue that tumor etc. is different.Then, by performing electromagnetism numerical simulation to obtain the electric field of dipole antenna.After acquisition electric field and conductance distribution, can calculate and comprise the Optimal Signals such as antenna phase and amplitude parameter.
In step 206, after determining Optimal Signals parameter, at least one mode switch of coil block 100 can be operated carries out work so that coil block 100 is transformed into thermotherapy pattern.In one embodiment, mode switch 116a and 116b as shown in Figure 2 can be turned off, multiple dipole antenna 112a, 112b, 112c of coil block 100 to be disconnected connection each other.In addition, mode switch 164a and 164b also can be turned off, dipole antenna 112a, 112b, 112c and shielding element 160 to be disconnected.
In a step 208, the method 200 can continue to have the radio-frequency (RF) thermotherapeutic signal function of Optimal Signals parameter to coil block 100.Because dipole antenna 112a, 112b, 112c disconnect each other, each dipole antenna 112a, 112b, 112c can act on radio-frequency (RF) thermotherapeutic signal independently.In one embodiment, multiple first gauge taps be associated with the plurality of dipole antenna 112a, 112b, 112c can be closed, with the radio-frequency (RF) thermotherapeutic signal exported from thermotherapy signal source 132 by multiple passage conveying.The radio-frequency (RF) thermotherapeutic signal that power divider 134 can be used thermotherapy signal source 132 to be exported is divided into the radiofrequency signal of multiple channel transfer.Further, multiple vector modulator 136a, 136b, 136c can be used to regulate respectively in the phase place of the radio-frequency (RF) thermotherapeutic signal of multiple channel transfer and amplitude.Fig. 7 shows the simulation result that coil block 100 is operated in the special absorption distribution of the anti-body that thermotherapy pattern obtains.As shown in Figure 7, in XZ plane or in XY plane, the region of focus radio frequency energy can be controlled by control phase and amplitude, to realize the heating to area-of-interest.Therefore, not only realize three-dimensional special absorbance physically or electric field controls is possible, and can realize heating and alleviate injury to health tissues by controlling radio-frequency (RF) energy to sufferer tissue simultaneously.
In other embodiments, in a step 208, when coil block 100 is operated in thermotherapy pattern, the object (bolus) that can be comprised high-k liquid or deionization liquid to be placed in cylinder and to surround human body.This object (bolus) may be used for increasing the radio-frequency (RF) energy being coupled to human body, and may be used for the heat taking away human skin.
In the step 212, the method 200 can continue to determine whether it has received temperature survey instruction, and this temperature survey instruction is for detecting the temperature of the object receiving thermotherapy.In one embodiment, magnetic resonance system 10 instruction that can be inputted by input equipment 13 as shown in Figure 1 or control panel 14.If it is determined that go out to receive temperature survey instruction, then the flow process of the method 200 turns to step 214 to perform.If it is determined that go out not receive temperature survey instruction, then the flow process of the method 200 turns back to step 208, to continue to carry out thermotherapy to target area.
In step 214, the method 200 continues through the multiple mode switch of operation, to convert coil block 100 at magnetic resonance MODE of operation to.As the description done at composition graphs 2, this coil block 100 can comprise multiple coil group 110a, 110b, 110c.Under magnetic resonance pattern, mode switch 116a and 116b in coil group 110a, 110b, 110c is closed, dipole antenna 112a, 112b, 112c to be linked together.Simultaneously, mode switch 164a and 164b in coil group 110a, 110b, 110c is closed, dipole antenna 112a, 112b, the 112c in dipole antenna coil group 110a, 110b, 110c and shielding element 160 to be linked together, and form closed resonance circuit.
In the step 216, the method 200 continuation effect magnetic resonance radio frequency signal to coil group 110a, 110b, 110c, to encourage nuclear radiofrequency signal to region of interest emission.In one embodiment, each coil group 110a, 110b, 110c can act on independently magnetic resonance radio frequency signal respectively.In one embodiment, multiple second gauge tap 122a, 122b, 122c can also be used to control to come from the multi-channel magnetic resonance radiofrequency signal in magnetic resonance signal source 142 respectively, and the magnetic resonance radio frequency signal using power splitter 144 to be exported by magnetic resonance signal 142 is divided into multiple signals.Further, multiple vector modulator 146a, 146b, 146c can also be used to regulate phase place and the amplitude of the magnetic resonance radio frequency signal transmitted in multiple passage respectively.Under Figure 8 shows that magnetic resonance system 10 is operated in magnetic resonance pattern, excitation field (B1
+) simulation result.The standard deviation of excitation field is less than 3%, thus can obtain more uniform excitation field.
In the step 216, the method 200 also continues to receive the radiofrequency signal produced due to area-of-interest generation magnetic resonance.From the above mentioned, this coil block 100 may comprise 16 coil groups.In one embodiment, when coil block 100 received RF signal, these 16 coil groups all can be used for received RF signal.In other embodiments, wherein eight coil groups also can be selected to carry out received RF signal, and make other eight coil groups can not received RF signal.Then, temperature and the Temperature Distribution of area-of-interest namely can be measured by analyzing the radiofrequency signal received.In one embodiment, difference Proton Resonance Frequency (proton resonance frequency, PRF) mobile temp measuring method can be used to come measuring tempeature and Temperature Distribution.Variations in temperature can use following governing equation to express:
Wherein in formula (2), α is thermal constant, and γ is gyromagnetic ratio, B
0be main field strength, TE is the echo time,
be heated into as the phase contrast between the benchmark image of front acquisition and the measurement image obtained during thermometric.In other embodiments, other relational expression also can be used to carry out measuring tempeature, such as, the relational expression between relaxation time and temperature can be used to carry out measuring tempeature.
In step 218, the method 200 can continue to judge whether the Temperature Distribution measured meets default standard.For example, in hyperthermia process, the Temperature Distribution between heating region and normal structure around should meet certain standard, to guarantee that the normal structure of surrounding is not heated excessively.When step 218 judges that this Temperature Distribution does not meet predetermined standard, the flow process of the method 200 turns back to step 204, to be modified for the Optimal Signals parameter of the radio-frequency (RF) thermotherapeutic signal using coil block 100.When step 218 judges that this Temperature Distribution meets predetermined standard, flow process turns to step 222 to continue to perform.
In step 222, the method continues to judge whether the Temperature Distribution measured reaches default temperature value.For example, in hyperthermia process, the temperature of heating region needs to remain in certain temperature range usually, such as, between 41 degrees Celsius to 43 degrees Celsius.Therefore, when step 222 judges that the temperature of heating region not yet reaches default temperature value, the flow process of the method 200 turns back in step 208, to continue effect radio-frequency (RF) thermotherapeutic signal to coil block 100, heats target area.When step 222 judges that the temperature of heating region has reached default temperature value, then flow process turns to end.
Should be understood that, above composition graphs 6 performs for the non-essential exact sequence will described according to Fig. 6 of the multiple steps described by method 200.The method 200 in fact can according to can think and suitable order perform.In addition, in some embodiments, the step more or more less than Fig. 6 can be had to be performed.
Although describe the present invention in conjunction with specific embodiment, those skilled in the art will appreciate that and can make many amendments and modification to the present invention.Therefore, recognize, the intention of claims is to be encompassed in all such modifications in true spirit of the present invention and scope and modification.
Claims (18)
1. a multi-channel coil assembly, this multi-channel coil arrangement of components becomes can be operated in first mode and the second pattern, it is characterized in that: this multi-channel coil assembly comprises:
Multiple coil part; And
Multiple mode switch, each in the plurality of mode switch with the mode of switch be connected in the plurality of coil part at least between the two;
Wherein, when this multi-channel coil component operation is at first mode, this at least one mode switch is manipulated into and coil part is disconnected mutually, and this coil part mutually disconnected is configured to multiple first input signal of response to send the first radiofrequency signal;
Wherein, when this multi-channel coil component operation is in the second pattern, this at least one mode switch is manipulated into and coil part is interconnected, and this interconnective coil part is configured to multiple second input signal of response and sends or receive the second radiofrequency signal;
This multi-channel coil assembly also comprises the first signal source and multiple first gauge tap, and each in the plurality of first gauge tap is electrically connected between one corresponding in the plurality of coil part and the first signal source; When this multi-channel coil component operation is at first mode, at least one in the plurality of first gauge tap is closure state, and this first signal source can be communicated with the coil part that this disconnects mutually; When this multi-channel coil component operation is in the second pattern, at least one in the plurality of first gauge tap is off state, this first signal source can not be communicated with this interconnective coil part, and the plurality of mode switch is not used in and controls the closed of multiple first gauge tap respectively or turn off.
2. multi-channel coil assembly as claimed in claim 1, is characterized in that: the plurality of first input signal is imported into this coil part mutually disconnected to carry out radio frequency heating to area-of-interest.
3. multi-channel coil assembly as claimed in claim 1, is characterized in that: each mode switch comprises the switch element of mechanical actuation.
4. multi-channel coil assembly as claimed in claim 1, is characterized in that: the plurality of second input signal is imported into this interconnective coil part with the temperature by nuclear magnetic resonance monitoring area-of-interest.
5. multi-channel coil assembly as described in claim 1, it is characterized in that: this multi-channel coil assembly also comprises secondary signal source and multiple second gauge tap, and each in the plurality of second gauge tap is connected with the one in the plurality of coil part with this secondary signal source in the mode of switch; When this multi-channel coil component operation is at first mode, the plurality of second gauge tap is off state, cannot communicate to make this secondary signal source with coil part; When this multi-channel coil component operation is in the second pattern, at least one in the plurality of second gauge tap is closure state, can communicate to make this secondary signal source with between interconnective coil part.
6. multi-channel coil assembly as claimed in claim 1, is characterized in that: the plurality of coil part comprises dipole antenna.
7. multi-channel coil assembly as claimed in claim 1, it is characterized in that: when the plurality of mode switch closes, the plurality of coil part forms a transverse electromagnetic coil for parallel imaging.
8. multi-channel coil assembly as claimed in claim 7, it is characterized in that: this multi-channel coil assembly also comprises shielding element, this shielding element is connected with coil part by mode switch, when this multi-channel coil component operation is at first mode, the mode switch be connected with this shielding element is turned off, this shielding element and multiple coil part are disconnected, when this multi-channel coil component operation is in the second pattern, the mode switch be connected with this shielding element is closed, and makes this shielding element be connected to form current loop with the plurality of coil part.
9. a magnetic resonance system, is characterized in that: this magnetic resonance system comprises:
Main magnet is for generation main field;
Gradient coil in selected gradient axes by Actions of Gradient Magnetic Field to main field; And
Multi-channel coil assembly, this multi-channel coil assembly comprises:
Multiple coil part; And
Multiple mode switch, each in the plurality of mode switch with the mode of switch be connected in the plurality of coil part at least between the two;
Wherein, when this multi-channel coil component operation is at first mode, this at least one mode switch is manipulated into and coil part is disconnected mutually, and this coil part mutually disconnected is configured to multiple first input signal of response to send the first radiofrequency signal;
Wherein, when this multi-channel coil component operation is in the second pattern, this at least one mode switch is manipulated into and coil part is interconnected, and this interconnective coil part is configured to multiple second input signal of response and sends or receive the second radiofrequency signal;
This multi-channel coil assembly also comprises the first signal source and multiple first gauge tap, and each in the plurality of first gauge tap is electrically connected between one corresponding in the plurality of coil part and the first signal source; When this multi-channel coil component operation is at first mode, at least one in the plurality of first gauge tap is closure state, and this first signal source can be communicated with the coil part that this disconnects mutually; When this multi-channel coil component operation is in the second pattern, at least one in the plurality of first gauge tap is off state, this first signal source can not be communicated with this interconnective coil part, and the plurality of mode switch is not used in and controls the closed of multiple first gauge tap respectively or turn off.
10. magnetic resonance system as claimed in claim 9, it is characterized in that: the plurality of mode switch is also connected with the first group of coil comprising at least two coil parts in the mode of switch, and be connected with the second group of coil comprising at least two coil parts in the mode of switch;
Wherein, when the plurality of mode switch is turned off, the each of each of at least two coil parts of this first group of coil and at least two coils of this second group of coil is configured to the first input signal received with particular phases and amplitude, and independently send the first radiofrequency signal, to heat area-of-interest; And
Wherein, when the plurality of mode switch is closed, at least two coils of this first group of coil are configured to jointly to be received in second input signal with particular phases and amplitude of first passage transmission, at least two coils of this second group of coil are configured to jointly to be received in second input signal with particular phases and amplitude of second channel transmission, and this first group of coil and this second group of coil send or receive the second radiofrequency signal;
Be transferred to this secondary signal comprising second group of coil of at least two coil parts by second channel to be relatively transferred between this first signal comprising first group of coil of at least two coil parts by first passage there is phase shift.
11. magnetic resonance systems as claimed in claim 10, it is characterized in that: when the plurality of mode switch closes, this multi-channel coil assembly forms the transverse electromagnetic coil comprising multiple coil group, the plurality of coil group, by this second input signal of multiple channel reception, should be adjusted according to radio frequency shimming technique by the phase place of the secondary signal of multiple channel transfer and amplitude.
12. magnetic resonance systems as claimed in claim 9, is characterized in that: each mode switch comprises the switch element of mechanical actuation.
13. magnetic resonance systems as claimed in claim 9, it is characterized in that: this magnetic resonance system also comprises secondary signal source, this multi-channel coil assembly also comprises multiple second gauge tap, each in the plurality of second gauge tap in the mode of switch with this secondary signal source and be connected with the one in the plurality of coil part; The plurality of second gauge tap is configured to close or to turn off to allow or block this secondary signal source provides this second input signal.
14. 1 kinds of methods operating magnetic resonance system, this magnetic resonance system comprises multiple coil part, multiple mode switch and multiple first gauge tap, each in the plurality of mode switch be connected in the plurality of coil part at least between the two, it is characterized in that: the method at least comprises the steps:
Turn off at least one in the plurality of mode switch to disconnect the plurality of coil part;
Multichannel first radiofrequency signal is sent to area-of-interest by multiple coil parts of this disconnection;
At least one in closed the plurality of mode switch is to form multiple coil group, and this each coil group comprises at least two coil parts interconnected;
Come from multichannel second radiofrequency signal of this area-of-interest to this area-of-interest or reception by the plurality of coil group transmission multichannel second radiofrequency signal;
Each in multiple first gauge tap is electrically connected between one corresponding in the plurality of coil part and the first signal source;
At least one in closed the plurality of first gauge tap, to send multichannel first radiofrequency signal to area-of-interest by multiple coil parts of this disconnection; And
When being sent multichannel second radiofrequency signal by the plurality of coil group and coming from multichannel second radiofrequency signal of this area-of-interest to this area-of-interest or reception, turn off the plurality of first gauge tap; Wherein, the plurality of mode switch is not used in and controls the closed of multiple first gauge tap respectively or turn off.
The method of 15. operation magnetic resonance systems as claimed in claim 14, is characterized in that: the method also comprises the steps:
Utilize the switch element of mechanical actuation as each mode switch.
The method of 16. operation magnetic resonance systems as claimed in claim 14, wherein this magnetic resonance system also comprises multiple second gauge tap, it is characterized in that: the method also comprises the steps:
Each in multiple second gauge tap is electrically connected between one corresponding in the plurality of coil part and secondary signal source;
At least one in this second gauge tap closed, to come from multichannel second radiofrequency signal of this area-of-interest to this area-of-interest or reception by the plurality of coil group transmission multichannel second radiofrequency signal; And
When the multiple coil parts by this disconnection send multichannel first radiofrequency signal to area-of-interest, turn off the plurality of second gauge tap.
The method of 17. operation magnetic resonance systems as claimed in claim 14, is characterized in that: the method also comprises the steps:
Obtain the image of this area-of-interest; And
Image information based on the area-of-interest of this acquisition determines the Optimal Signals parameter of the input signal being applied to the plurality of coil part.
The method of 18. operation magnetic resonance systems as claimed in claim 17, is characterized in that: the method also comprises the steps:
The Temperature Distribution of area-of-interest is measured by nuclear magnetic resonance;
Judge whether the Temperature Distribution of this measurement meets the condition preset; And
When the Temperature Distribution of this measurement does not meet the condition preset, adjust this Optimal Signals parameter.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN201010612982.1A CN102551716B (en) | 2010-12-17 | 2010-12-17 | Magnetic resonance system and magnetic resonance method |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN201010612982.1A CN102551716B (en) | 2010-12-17 | 2010-12-17 | Magnetic resonance system and magnetic resonance method |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| CN102551716A CN102551716A (en) | 2012-07-11 |
| CN102551716B true CN102551716B (en) | 2015-01-21 |
Family
ID=46399294
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CN201010612982.1A Expired - Fee Related CN102551716B (en) | 2010-12-17 | 2010-12-17 | Magnetic resonance system and magnetic resonance method |
Country Status (1)
| Country | Link |
|---|---|
| CN (1) | CN102551716B (en) |
Families Citing this family (3)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN107320105B (en) * | 2017-07-24 | 2023-11-28 | 北京大学 | Combined nuclear magnetic resonance imaging and electromagnetic induction and radio frequency treatment system |
| CN112763953B (en) * | 2020-12-10 | 2021-10-26 | 复旦大学 | Multipurpose radio frequency coil device for head/knee joint based on 7.0T magnetic resonance imaging system |
| CN112816923B (en) * | 2020-12-29 | 2023-07-28 | 深圳市联影高端医疗装备创新研究院 | Ultra-high field emission shimming coil structure |
Citations (8)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US4554925A (en) * | 1982-07-07 | 1985-11-26 | Picker International, Ltd. | Nuclear magnetic resonance imaging method |
| US5284144A (en) * | 1989-11-22 | 1994-02-08 | The United States Of America As Represented By The Secretary Of The Dept. Of Health & Human Services | Apparatus for hyperthermia treatment of cancer |
| US5323778A (en) * | 1991-11-05 | 1994-06-28 | Brigham & Women's Hospital | Method and apparatus for magnetic resonance imaging and heating tissues |
| US5462055A (en) * | 1994-08-23 | 1995-10-31 | Northrop Grumman Corporation | MRI/hyperthermia dual function antenna system |
| US5492122A (en) * | 1994-04-15 | 1996-02-20 | Northrop Grumman Corporation | Magnetic resonance guided hyperthermia |
| CN1533291A (en) * | 2001-06-26 | 2004-09-29 | 西门子公司 | Magnetic resonance system and method for operation the same |
| CN1957263A (en) * | 2004-04-29 | 2007-05-02 | 皇家飞利浦电子股份有限公司 | A magnetic resonance imaging system, a method of magnetic resonance imaging and a computer program |
| CN101261315A (en) * | 2007-03-08 | 2008-09-10 | 株式会社东芝 | Magnetic resonance imaging apparatus |
-
2010
- 2010-12-17 CN CN201010612982.1A patent/CN102551716B/en not_active Expired - Fee Related
Patent Citations (8)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US4554925A (en) * | 1982-07-07 | 1985-11-26 | Picker International, Ltd. | Nuclear magnetic resonance imaging method |
| US5284144A (en) * | 1989-11-22 | 1994-02-08 | The United States Of America As Represented By The Secretary Of The Dept. Of Health & Human Services | Apparatus for hyperthermia treatment of cancer |
| US5323778A (en) * | 1991-11-05 | 1994-06-28 | Brigham & Women's Hospital | Method and apparatus for magnetic resonance imaging and heating tissues |
| US5492122A (en) * | 1994-04-15 | 1996-02-20 | Northrop Grumman Corporation | Magnetic resonance guided hyperthermia |
| US5462055A (en) * | 1994-08-23 | 1995-10-31 | Northrop Grumman Corporation | MRI/hyperthermia dual function antenna system |
| CN1533291A (en) * | 2001-06-26 | 2004-09-29 | 西门子公司 | Magnetic resonance system and method for operation the same |
| CN1957263A (en) * | 2004-04-29 | 2007-05-02 | 皇家飞利浦电子股份有限公司 | A magnetic resonance imaging system, a method of magnetic resonance imaging and a computer program |
| CN101261315A (en) * | 2007-03-08 | 2008-09-10 | 株式会社东芝 | Magnetic resonance imaging apparatus |
Also Published As
| Publication number | Publication date |
|---|---|
| CN102551716A (en) | 2012-07-11 |
Similar Documents
| Publication | Publication Date | Title |
|---|---|---|
| Chen et al. | Real-time three-dimensional microwave monitoring of interstitial thermal therapy | |
| US9116214B2 (en) | RF coil array having two or more switches built within each RF coil array element, compatible with both magnetic resonance and a temperature mapping | |
| Winter et al. | Design and evaluation of a hybrid radiofrequency applicator for magnetic resonance imaging and RF induced hyperthermia: electromagnetic field simulations up to 14.0 Tesla and proof-of-concept at 7.0 Tesla | |
| CN102448547B (en) | Mr imaging guided therapy | |
| EP2681576B1 (en) | Accelerated mr thermometry mapping involving an image ratio constrained reconstruction | |
| EP2745133B1 (en) | Reducing the radio-frequency transmit field in a predetermined volume during magnetic resonance imaging | |
| Adibzadeh et al. | Systematic review of pre-clinical and clinical devices for magnetic resonance-guided radiofrequency hyperthermia | |
| Kowalski et al. | Optimization of electromagnetic phased-arrays for hyperthermia via magnetic resonance temperature estimation | |
| Wang et al. | Real‐time active MR‐tracking of metallic stylets in MR‐guided radiation therapy | |
| Chopra et al. | MRI-controlled transurethral ultrasound therapy for localised prostate cancer | |
| EP2230720A1 (en) | An antenna array comprising at least one dipole antenna for magnetic resonance imaging | |
| Stakhursky et al. | Real-time MRI-guided hyperthermia treatment using a fast adaptive algorithm | |
| Weihrauch et al. | Adaptation of antenna profiles for control of MR guided hyperthermia (HT) in a hybrid MR‐HT system | |
| Bolomey et al. | Noninvasive control of hyperthermia | |
| EP3600101B1 (en) | Locating ablated tissues using electric properties tomography | |
| US20130147475A1 (en) | Magnetic resonance system and method thereof | |
| Eigentler et al. | Wideband self‐grounded bow‐tie antenna for thermal mr | |
| CN102551716B (en) | Magnetic resonance system and magnetic resonance method | |
| Quesson et al. | Automatic control of hyperthermic therapy based on real‐time Fourier analysis of MR temperature maps | |
| US11426080B2 (en) | Real-time imaging system for monitoring and control of thermal therapy treatments | |
| Navarro de Lara et al. | Evaluation of RF interactions between a 3T birdcage transmit coil and transcranial magnetic stimulation coils using a realistically shaped head phantom | |
| Eigentler et al. | 32‐Channel self‐grounded bow‐tie transceiver array for cardiac MR at 7.0 T | |
| EP2901954A1 (en) | System for field ablation prediction | |
| Kowalski et al. | Model-based optimization of phased arrays for electromagnetic hyperthermia | |
| Lee | Electromagnetic superficial heating technology |
Legal Events
| Date | Code | Title | Description |
|---|---|---|---|
| C06 | Publication | ||
| PB01 | Publication | ||
| C10 | Entry into substantive examination | ||
| SE01 | Entry into force of request for substantive examination | ||
| C14 | Grant of patent or utility model | ||
| GR01 | Patent grant | ||
| CF01 | Termination of patent right due to non-payment of annual fee | ||
| CF01 | Termination of patent right due to non-payment of annual fee |
Granted publication date: 20150121 Termination date: 20211217 |