CN113534028A - Special surface phased array receiving coil for skin - Google Patents

Special surface phased array receiving coil for skin Download PDF

Info

Publication number
CN113534028A
CN113534028A CN202110742322.3A CN202110742322A CN113534028A CN 113534028 A CN113534028 A CN 113534028A CN 202110742322 A CN202110742322 A CN 202110742322A CN 113534028 A CN113534028 A CN 113534028A
Authority
CN
China
Prior art keywords
coil
capacitor
skin
preamplifier
phased array
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Granted
Application number
CN202110742322.3A
Other languages
Chinese (zh)
Other versions
CN113534028B (en
Inventor
刘军
胡俊蛟
曾瑛
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Second Xiangya Hospital of Central South University
Original Assignee
Second Xiangya Hospital of Central South University
Priority date (The priority date 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 date listed.)
Filing date
Publication date
Application filed by Second Xiangya Hospital of Central South University filed Critical Second Xiangya Hospital of Central South University
Priority to CN202110742322.3A priority Critical patent/CN113534028B/en
Publication of CN113534028A publication Critical patent/CN113534028A/en
Application granted granted Critical
Publication of CN113534028B publication Critical patent/CN113534028B/en
Active legal-status Critical Current
Anticipated expiration legal-status Critical

Links

Images

Classifications

    • GPHYSICS
    • G01MEASURING; TESTING
    • G01RMEASURING ELECTRIC VARIABLES; MEASURING MAGNETIC VARIABLES
    • G01R33/00Arrangements or instruments for measuring magnetic variables
    • G01R33/20Arrangements or instruments for measuring magnetic variables involving magnetic resonance
    • G01R33/28Details of apparatus provided for in groups G01R33/44 - G01R33/64
    • G01R33/32Excitation or detection systems, e.g. using radio frequency signals
    • G01R33/34Constructional details, e.g. resonators, specially adapted to MR
    • G01R33/341Constructional details, e.g. resonators, specially adapted to MR comprising surface coils
    • YGENERAL TAGGING OF NEW TECHNOLOGICAL DEVELOPMENTS; GENERAL TAGGING OF CROSS-SECTIONAL TECHNOLOGIES SPANNING OVER SEVERAL SECTIONS OF THE IPC; TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
    • Y02TECHNOLOGIES OR APPLICATIONS FOR MITIGATION OR ADAPTATION AGAINST CLIMATE CHANGE
    • Y02DCLIMATE CHANGE MITIGATION TECHNOLOGIES IN INFORMATION AND COMMUNICATION TECHNOLOGIES [ICT], I.E. INFORMATION AND COMMUNICATION TECHNOLOGIES AIMING AT THE REDUCTION OF THEIR OWN ENERGY USE
    • Y02D30/00Reducing energy consumption in communication networks
    • Y02D30/70Reducing energy consumption in communication networks in wireless communication networks

Abstract

The invention discloses a special surface phased array receiving coil for skin, which comprises a coil unit, a long-distance cable and an amplifying circuit, wherein the coil unit is connected with the amplifying circuit through the long-distance cable so that the amplifying circuit is far away from a coil antenna; the amplifying circuit comprises a phase-shifting circuit and a preamplifier, the phase-shifting circuit is connected to the coil antenna through a long-distance cable and outputs the coil antenna to the preamplifier, and the preamplifier amplifies a signal and outputs the amplified signal to an external processor. The invention has the technical effects that the coil antenna and the amplifying circuit are connected in a long-distance cable mode, so that the amplifying circuit which can generate heat when in use is far away from the skin of a patient, the burn risk when in use is effectively avoided, meanwhile, the invention adopts the flexible shell, the surface shape has better fitness, and the flexible and flat appearance can better conform to the skin.

Description

Special surface phased array receiving coil for skin
Technical Field
The invention relates to a surface phased array receiving coil special for skin.
Background
Magnetic Resonance Imaging (MRI) systems are today advanced diagnostic devices in the field of medical imaging. It can provide high quality soft tissue tomograms incomparable with other imaging devices, and its emergence revolutionized conventional radiology and imaging diagnostics. It can realize imaging of various tissue parameters, tomography in any direction, tissue perfusion metabolism and the like. Medical magnetic resonance imaging has been widely used in various systems of the body, such as the most common nervous and skeletal systems, and has brought enormous benefits to the diagnosis, treatment and prognosis of diseases. However, on top of the skin system, MRI applications are not widespread, or even rare. The reason for this is that: regarding the tissue structure of the skin, high-resolution MRI (HR-MRI) imaging is required to achieve the effect of auxiliary diagnosis, but the HR-MRI imaging requirement of the skin cannot be met due to the limitation of an MRI system at present.
The limitations of MRI systems are mainly due to the increase of the main magnetic field, which is difficult and takes almost 50 years for us to spend in clinical practice, and the improvement of surface receiving coils, which is widely used commercially from 0.3T to 3.0T. It is known that magnetic resonance systems are mainly composed of superconducting magnets, gradient coils, radio frequency coils, spectrometer systems, etc., wherein the performance of the radio frequency receiving coils directly determines the quality of the images as a terminal for receiving magnetic resonance signals. In order to obtain better image quality, improving the performance of the receiving coil is also an important direction for the development of the current superconducting magnetic resonance.
The small-field surface coil has higher sensitivity and application value in the aspects of thyroid imaging, talar cartilage imaging, skin surface imaging and the like compared with the traditional array coil. At present, a receiving coil used for skin HR-MRI imaging is a single-channel micro-coil (loop) with different models of various manufacturers, which is also called a small field loop coil, the single-channel loop coil is not used for skin imaging, and the single-channel loop coil is developed to be suitable for superficial tissue imaging of a human body, such as superficial tissue structures of fingers, toes and the like, and is one of the reasons for making the loop into a loop hollow structure. The diameters of the hard shell are different, all manufacturers produce the hard shell with the diameter of 2CM to 7CM, and the hard shell is made of PC materials and cannot be well attached to and fixed on the skin of a human body.
The principle of using a single-channel small-field annular coil to perform skin HR-MRI imaging is mainly characterized in that the smaller the diameter of the used coil is, the higher the receiving sensitivity is, and the higher the signal-to-noise ratio of the image can be ensured under the condition of reducing the voxel under the condition of keeping the strength of the main magnetic field unchanged, so that the small-FOV high-spatial-resolution image can be obtained.
However, the size of each large manufacturer is different in the conventional single-channel small-field annular coil, and the satisfactory combination between the imaging depth and the high resolution cannot be achieved. Secondly, the single-channel small-field annular coils are all annular hollow, and the hard PC shell is shaped, so that the single-channel small-field annular coils cannot be well fixed and attached to the skin, and great difficulty is brought to imaging operation. And the existing coils connect the antenna and the corresponding amplifying circuit together in a short distance, so that the coil can feel uncomfortable and even burn to a patient due to heat generated by the amplifying circuit when in use.
Disclosure of Invention
The invention provides a surface phased array receiving coil special for skin, and aims to solve the technical problems that a burn risk exists due to the fact that an amplifying circuit generates heat when an existing single-channel small-field annular coil is used, a hard shell of the coil is not convenient to match with the skin, and imaging depth and high resolution cannot be considered at the same time.
In order to achieve the technical purpose, the technical scheme of the invention is that,
a surface phased array receiving coil special for skin comprises a coil unit, a long-distance cable and an amplifying circuit, wherein the coil unit is connected with the amplifying circuit through the long-distance cable so that the amplifying circuit is far away from a coil antenna; the amplifying circuit comprises a phase-shifting circuit and a preamplifier, the phase-shifting circuit is connected to the coil antenna through a long-distance cable and outputs the coil antenna to the preamplifier, and the preamplifier amplifies a signal and outputs the amplified signal to an external processor.
The surface phased array receiving coil special for the skin comprises a coil unit and a control unit, wherein the coil unit comprises at least two small coil antennas and control circuits, the number of the control circuits is equal to that of the small coil antennas, each small coil antenna is connected to one control circuit and is connected to an independent amplifying circuit through a long-distance cable through the control circuit, and the number of the amplifying circuits is also equal to that of the small coil antennas;
the small coil antennas are partially overlapped with each other for contacting the skin and receiving signals.
The surface phased array receiving coil special for the skin is characterized in that the small coil antennas are circular, and the distance between the circle centers of any two small coil antennas is 75% of the diameter of each small coil antenna.
The surface phased array receiving coil special for the skin further comprises a flexible panel, wherein the flexible panel is made of a waterproof and breathable material, and the small coil antenna is sealed in the flexible panel and used for directly contacting the skin.
A special surface phased array receiving coil of skin, control circuit include second inductance L2 and the matching capacitance C1, parallel resonance circuit and the frequency modulation electric capacity C4 that establish ties in proper order, wherein matching capacitance C1 and frequency modulation electric capacity C4 are connected to the both ends of little coil antenna respectively and form the return circuit jointly with little coil antenna, second inductance L2 one end be connected to direct current input, the other end is connected to between parallel resonance circuit and the frequency modulation electric capacity C4, matching capacitance C1's both ends are connected to amplifier circuit through the long-distance cable respectively, frequency modulation electric capacity C4 be adjustable electric capacity.
The parallel resonant loop comprises a first inductor L1, a diode D1, a first detuning loop capacitor C2 and a second detuning loop capacitor C3 which are connected in series, and the first inductor L1 and the diode D1 are connected in series and then connected in parallel with the first detuning loop capacitor C2 and the second detuning loop capacitor C3.
The phase-shifting circuit comprises a phase-shifting capacitor C5 and a phase-shifting inductor L3, wherein the phase-shifting capacitor C5 is connected in series to one input end of the preamplifier, the other input end of the preamplifier is grounded, and the phase-shifting inductor L3 is connected between the two input ends of the preamplifier in parallel.
The phase-shifting circuit comprises a phase-shifting capacitor C5 and a phase-shifting inductor L3, wherein the phase-shifting inductor L3 is connected in series to one input end of the preamplifier, the other input end of the preamplifier is grounded, and the phase-shifting capacitor C5 is connected between the two input ends of the preamplifier in parallel.
The surface phased array receiving coil special for the skin is characterized in that the small coil antenna and the long-distance cable are both made of coaxial wires, and each coaxial wire comprises a metal braided layer, an insulating layer, a supporting layer and a conductor from outside to inside.
The surface phased array receiving coil special for the skin is characterized in that the small coil antenna is a foam-shaped metal conductor strip manufactured through a powder sintering process.
The invention has the technical effects that the coil antenna and the amplifying circuit are connected in a long-distance cable mode, so that the amplifying circuit which can generate heat when in use is far away from the skin of a patient, the burn risk when in use is effectively avoided, meanwhile, the invention adopts the flexible shell, the surface shape has better fitness, and the flexible and flat appearance can better conform to the skin. The coil antenna adopts a multi-channel coil array combination mode, a plurality of independent small coils are used for covering an imaging area together, and because the noise of a small area close to the coils can enter the coils, the signal to noise ratio can be effectively improved, the size of an FOV (field of view) can be controlled, and the purpose of high-resolution imaging of skin is achieved.
Drawings
FIG. 1 is a schematic structural diagram of the present invention.
FIG. 2 is a schematic diagram of phase modulation when the front end coil unit of the present invention is capacitive.
Fig. 3 is a schematic diagram of phase modulation when the front end coil unit is inductive.
Fig. 4 is a schematic diagram of the antenna portion according to the present invention.
Fig. 5 is a disassembled schematic view of the antenna part of the present invention.
Detailed Description
Referring to fig. 1, the present embodiment includes a coil unit, a long-distance cable, and an amplifying circuit. Since it is considered that the circuit connected to the coil generates heat due to its operation, which may cause burn to the skin of the human body, the present embodiment is improved for the circuit configuration to match the longer cable connected to the preamplifier. The coil unit and the amplifying circuit of the present embodiment are connected by a long distance cable, so that the amplifying circuit is far away from the coil antenna. The amplifying circuit comprises a phase shifting circuit and a preamplifier, which is used for matching a capacitor to the input end of the preamplifier, and has the phase requirement besides the decoupling requirement of the preamplifier, and the circuit structure of the required phase shifting can be determined according to the actual situation. This embodiment confirms actual use condition through the cable between control coil and the preamplifier, if it is enough to separate preamplifier and coil unit distance, can make the amplifier part keep away from the human body, and the antenna unit position is close to the human body, can only be to unit position design laminating material and structure this moment, makes the patient more comfortable. The phase shift circuit is connected to the coil antenna through the long-distance cable and outputs the signal to the preamplifier, and the preamplifier amplifies the signal and outputs the amplified signal to the external processor.
The coil unit of the embodiment comprises at least three small coil antennas and control circuits with the same number as the small coil antennas, each small coil antenna is connected to one control circuit and is connected to an independent amplifying circuit through a long-distance cable through the control circuit, and the number of the amplifying circuits is the same as that of the small coil antennas. Two or more small coil antennas may also be used in practice. The small coil antennas in this embodiment form a coil structure mode of the small coil units of the multi-channel phased array, the small coil units are adjacent to each other to form a large imaging interval, so that the effective space of the imaging interval is increased, wherein each small coil antenna is circular, and the distance between the centers of any two small coil antennas is 75% of the diameter of the small coil antenna. Each small coil can receive the NMR signals of the corresponding small area at the same time, and after the measurement is finished, the signals of the small areas are effectively connected together. Here, each coil unit can be regarded as an independent coil, noise in the independent coil is only from a small area corresponding to the independent coil, data can be acquired from a larger range, and the SNR of the independent coil unit is equal to that of the independent coil unit. If the same area is imaged with a large coil of the same area, the SNR drops off significantly due to the expansion of the noise source, although this coil will also acquire the same amplitude signal as the phased array coil above. Therefore, the coil unit of the present embodiment can effectively reduce the SNR.
This embodiment employs a flexible panel in which a small coil antenna is sealed for direct contact with the skin. The flexible panel is made by waterproof ventilative material, and this embodiment uses the polyethylene foam to be the exterior material of coil, and the polyethylene foam is flexible material, has fine laminating skin, and it is also very convenient when the scanning is fixed, and patient's discomfort obviously reduces, great improvement skin MRI imaging's success nature, thereby also can make the coil apart from the target skin distance shorten better imaging depth.
The control circuit in this embodiment includes a second inductor L2, and a matching capacitor C1, a parallel resonant circuit, and a frequency modulation capacitor C4 that are connected in series in this order, wherein the matching capacitor C1 and the frequency modulation capacitor C4 are connected to the both ends of the small coil antenna respectively to form a loop together with the small coil antenna, one end of the second inductor L2 is connected to the dc input, the other end is connected between the parallel resonant circuit and the frequency modulation capacitor C4, and the both ends of the matching capacitor C1 are connected to the amplifying circuit through long-distance cables respectively. The matching capacitor C1 is mainly used to realize matching between input and output under loading condition, so as to achieve the best effect of signal transmission efficiency. The frequency modulation capacitor C4 is an adjustable capacitor, and since the inductance and capacitance values on the antenna coil have certain errors, an adjustable capacitor is needed to tune the frequency of the coil, so that the central frequency of the coil reaches the system working frequency.
The parallel resonant circuit of the embodiment comprises a first inductor L1, a diode D1, and a first detuned circuit capacitor C2 and a second detuned circuit capacitor C3 which are connected in series, wherein the first inductor L1 and the diode D1 are connected in series and then connected in parallel with the first detuned circuit capacitor C2 and the second detuned circuit capacitor C3. When a current signal is input by direct current, the diode D1 is turned on, and at this time, a parallel resonance circuit is formed among the first detuning circuit capacitor C2, the second detuning circuit capacitor C3 and the first inductor L1, the parallel resonance is in a high-impedance state, which is equivalent to a coil disconnection state, and when the transmitting coil works, the receiving coil is equivalent to disconnection, and the two do not interfere with each other.
In this embodiment, C1 to C4 are integrated with L1, D1 and L2 on a circuit board, so that all circuits at the coil end are integrated together, and then the two ends of the circuit board are directly connected to the antenna, thereby achieving simplicity and convenience in manufacturing, installation and maintenance.
Referring to fig. 2 and 3, there are two possibilities of phase shifting that may be required, depending on the particular situation: when the front end coil unit is capacitive, the front end is phase-adjusted in a series-inductor-parallel-capacitor mode, and when the front end coil unit is inductive, the front end is phase-adjusted in a series-capacitor-parallel-inductor mode. The phase shift circuit in this embodiment includes a phase shift capacitor C5 and a phase shift inductor L3. The two different embodiments provide different positions of the two components, which are mainly determined according to the different wire lengths from the coil unit to the preamplifier. In practical use, the distance between the antenna and the amplifier can be adjusted according to practical use conditions, and only the phase is affected when coaxial lines transmit signals, so that when the distance between the coil and the front amplifier is determined according to needs, the phase of the coil can be changed when viewed from the front amplifier end, at the moment, the phase shift circuit is determined according to the practical phase, and the purpose is to match the phase of the front amplifier to realize the optimal transmission of the signals. The front-end phase used in this embodiment is 180 degrees, so when the front-end is inductive, the phase-shift circuit adopts a mode of connecting an inductor in parallel with a series capacitor, wherein the C5 mainly functions to adjust the phase, the L3 mainly functions to correct the matching change caused by the series C5, so that the matching is consistent with the original matching, when the front-end is capacitive, the phase-shift circuit adopts a mode of connecting an inductor in parallel with a capacitor, wherein the L mainly functions to adjust the phase, and the C5 mainly corrects the matching change caused by the series L3, so that the matching is consistent with the original matching.
The small coil antenna and the long-distance cable in the embodiment adopt coaxial lines to adapt to the condition that the coil is bent for multiple times. The coaxial line is sequentially from outside to inside: metal braid, insulating layer, supporting layer and conductor. Wherein the insulating layer is a sheath made of fur, rubber and the like; the metal braid is woven by metal wires; the supporting layer is made of aramid fiber and filled insulating materials outside the aramid fiber. The supporting layer is made of aramid fiber materials and can be repeatedly bent for multiple times.
According to the requirements, the foam metal conductor strip can be manufactured by adopting a powder sintering process, so that the current distribution can be effectively improved, the quality factor of the coil is improved, and the signal-to-noise ratio is improved. Through process adjustment, a flexible antenna coil is realized.
Referring to fig. 4, fig. 5, the antenna conductor of this embodiment adopts novel ultralow impedance conductor, and is soft, resistant buckling, and three unit rational distribution, antenna part adopt waterproof ventilative material, and is lighter, soft comfortable, and the laminating is human, and whole coil can directly be pasted the skin surface with medical sticky tape, convenient to use improves SNR and patient's comfort level simultaneously.

Claims (10)

1. The surface phased array receiving coil special for the skin is characterized by comprising a coil unit, a long-distance cable and an amplifying circuit, wherein the coil unit is connected with the amplifying circuit through the long-distance cable so that the amplifying circuit is far away from a coil antenna; the amplifying circuit comprises a phase-shifting circuit and a preamplifier, the phase-shifting circuit is connected to the coil antenna through a long-distance cable and outputs the coil antenna to the preamplifier, and the preamplifier amplifies a signal and outputs the amplified signal to an external processor.
2. The surface phased array receiving coil special for skin as claimed in claim 1, wherein the coil unit comprises at least two small coil antennas and control circuits with the same number as the small coil antennas, each small coil antenna is connected to one control circuit and connected to independent amplifying circuits through long distance cables through the control circuits, and the number of the amplifying circuits is the same as that of the small coil antennas;
the small coil antennas are partially overlapped with each other for contacting the skin and receiving signals.
3. The phased array receiver coil as claimed in claim 1, wherein the small coil antennas are circular and wherein the distance between the center of any two small coil antennas is 75% of the diameter of the small coil antennas.
4. The skin specific surface phased array receive coil of claim 1, further comprising a flexible panel made of a waterproof and breathable material and enclosing the small coil antenna therein for direct contact with the skin.
5. The phased array receiver coil as claimed in claim 2, wherein the control circuit comprises a second inductor L2, and a matching capacitor C1, a parallel resonant loop and a frequency modulation capacitor C4 connected in series in sequence, wherein the matching capacitor C1 and the frequency modulation capacitor C4 are respectively connected to two ends of the small coil antenna to form a loop together with the small coil antenna, one end of the second inductor L2 is connected to the dc input, the other end of the second inductor L2 is connected between the parallel resonant loop and the frequency modulation capacitor C4, two ends of the matching capacitor C1 are respectively connected to the amplifying circuit through a long-distance cable, and the frequency modulation capacitor C4 is an adjustable capacitor.
6. The surface phased array receiver coil for skin use according to claim 5, wherein said parallel resonant tank comprises a first inductor L1, a diode D1, and a first detuned tank capacitor C2 and a second detuned tank capacitor C3 connected in series, said first inductor L1 and diode D1 connected in series and then connected in parallel with said first detuned tank capacitor C2 and said second detuned tank capacitor C3.
7. The phased array receiver coil as claimed in claim 1, wherein the phase shifting circuit comprises a phase shifting capacitor C5 and a phase shifting inductor L3, the phase shifting capacitor C5 is connected in series to one input terminal of the preamplifier, the other input terminal of the preamplifier is connected to ground, and the phase shifting inductor L3 is connected in parallel between the two input terminals of the preamplifier.
8. The phased array receiver coil as claimed in claim 1, wherein the phase shifting circuit comprises a phase shifting capacitor C5 and a phase shifting inductor L3, the phase shifting inductor L3 is connected in series to one input terminal of the preamplifier, the other input terminal of the preamplifier is connected to ground, and the phase shifting capacitor C5 is connected in parallel between the two input terminals of the preamplifier.
9. The phased array receiver coil as claimed in claim 1, wherein said small coil antenna and said long distance cable are made of a coaxial cable, said coaxial cable comprising a metal braid, an insulating layer, a supporting layer and a conductor from outside to inside.
10. The phased array receiver coil as claimed in claim 1, wherein the small coil antenna is a foam-like metal conductor strip made by a powder sintering process.
CN202110742322.3A 2021-06-30 2021-06-30 Special surface phased array receiving coil for skin Active CN113534028B (en)

Priority Applications (1)

Application Number Priority Date Filing Date Title
CN202110742322.3A CN113534028B (en) 2021-06-30 2021-06-30 Special surface phased array receiving coil for skin

Applications Claiming Priority (1)

Application Number Priority Date Filing Date Title
CN202110742322.3A CN113534028B (en) 2021-06-30 2021-06-30 Special surface phased array receiving coil for skin

Publications (2)

Publication Number Publication Date
CN113534028A true CN113534028A (en) 2021-10-22
CN113534028B CN113534028B (en) 2023-03-10

Family

ID=78097504

Family Applications (1)

Application Number Title Priority Date Filing Date
CN202110742322.3A Active CN113534028B (en) 2021-06-30 2021-06-30 Special surface phased array receiving coil for skin

Country Status (1)

Country Link
CN (1) CN113534028B (en)

Citations (13)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JPH0998959A (en) * 1995-10-04 1997-04-15 Toshiba Corp Mri equipment
US20020180442A1 (en) * 2001-05-04 2002-12-05 Kamal Vij Magnetic resonance imaging coil arrays with separable imaging coil elements
WO2007030832A2 (en) * 2005-09-09 2007-03-15 State Or Oregon Acting By And Through The State Board Of Higher Education Of Behalf Of The University Of Oregon High impedance differential input preamplifier and antenna for magnetic resonance systems
CN201060261Y (en) * 2007-06-12 2008-05-14 刘军 Function magnetic resonance practical reaction collection system
WO2009076313A1 (en) * 2007-12-06 2009-06-18 Koninklijke Philips Electronics N.V. Rf coil array comprising a coil element with two preamplifiers
US20150099963A1 (en) * 2013-10-03 2015-04-09 Medical University Of Vienna METHOD AND SYSTEM FOR COMBINED TRANSCRANIAL MAGNETIC SIMULATION (TMS) AND FUNCTIONAL MAGNETIC RESONANCE IMAGING (fMRI) STUDIES
US20150099965A1 (en) * 2013-10-07 2015-04-09 University Of Utah Research Foundation System for high resolution fast acquisition magnetic resonance imaging using a catheter-mounted coil
WO2015171885A1 (en) * 2014-05-07 2015-11-12 Office Of Technology Transfer, National Institutes Of Health Negative resistance preamplifier for inductively coupled local mri coils
US20180275226A1 (en) * 2017-03-24 2018-09-27 Quality Electrodynamics, Llc Minimizing intravascular magnetic resonance imaging (mri) guidewire heating with single layer mri transmit/receive radio frequency coil
CN109313245A (en) * 2016-06-07 2019-02-05 皇家飞利浦有限公司 Low temperature field for compensating the changes of magnetic field in magnet for magnetic resonant imaging senses
CN109952061A (en) * 2016-11-23 2019-06-28 通用电气公司 Rf coil system for MR imaging
US20190277926A1 (en) * 2016-11-23 2019-09-12 General Electric Company Systems for a radio frequency coil for mr imaging
CN111381203A (en) * 2017-03-23 2020-07-07 苏州美柯医疗科技有限公司 Radio frequency coil unit and radio frequency coil for magnetic resonance imaging

Patent Citations (13)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JPH0998959A (en) * 1995-10-04 1997-04-15 Toshiba Corp Mri equipment
US20020180442A1 (en) * 2001-05-04 2002-12-05 Kamal Vij Magnetic resonance imaging coil arrays with separable imaging coil elements
WO2007030832A2 (en) * 2005-09-09 2007-03-15 State Or Oregon Acting By And Through The State Board Of Higher Education Of Behalf Of The University Of Oregon High impedance differential input preamplifier and antenna for magnetic resonance systems
CN201060261Y (en) * 2007-06-12 2008-05-14 刘军 Function magnetic resonance practical reaction collection system
WO2009076313A1 (en) * 2007-12-06 2009-06-18 Koninklijke Philips Electronics N.V. Rf coil array comprising a coil element with two preamplifiers
US20150099963A1 (en) * 2013-10-03 2015-04-09 Medical University Of Vienna METHOD AND SYSTEM FOR COMBINED TRANSCRANIAL MAGNETIC SIMULATION (TMS) AND FUNCTIONAL MAGNETIC RESONANCE IMAGING (fMRI) STUDIES
US20150099965A1 (en) * 2013-10-07 2015-04-09 University Of Utah Research Foundation System for high resolution fast acquisition magnetic resonance imaging using a catheter-mounted coil
WO2015171885A1 (en) * 2014-05-07 2015-11-12 Office Of Technology Transfer, National Institutes Of Health Negative resistance preamplifier for inductively coupled local mri coils
CN109313245A (en) * 2016-06-07 2019-02-05 皇家飞利浦有限公司 Low temperature field for compensating the changes of magnetic field in magnet for magnetic resonant imaging senses
CN109952061A (en) * 2016-11-23 2019-06-28 通用电气公司 Rf coil system for MR imaging
US20190277926A1 (en) * 2016-11-23 2019-09-12 General Electric Company Systems for a radio frequency coil for mr imaging
CN111381203A (en) * 2017-03-23 2020-07-07 苏州美柯医疗科技有限公司 Radio frequency coil unit and radio frequency coil for magnetic resonance imaging
US20180275226A1 (en) * 2017-03-24 2018-09-27 Quality Electrodynamics, Llc Minimizing intravascular magnetic resonance imaging (mri) guidewire heating with single layer mri transmit/receive radio frequency coil

Non-Patent Citations (2)

* Cited by examiner, † Cited by third party
Title
潘屏南: "《现代大型医用设备:原理、结构和临床应用》", 31 May 2002, 中国医药科技出版社 *
王洪: "《医用磁共振成像设备(MRI)设备技术学》", 30 September 2011, 中国医药科技出版社 *

Also Published As

Publication number Publication date
CN113534028B (en) 2023-03-10

Similar Documents

Publication Publication Date Title
US10921401B2 (en) Anterior radio frequency (RF) coil array for a magnetic resonance imaging (MRI) system
CN109952516B (en) Radio frequency coil system for MR imaging
US11402447B2 (en) Conforming posterior radio frequency (RF) coil array for a magnetic resonance imaging (MRI) system
US11280859B2 (en) Method and systems for a radio frequency coil assembly
US10197645B2 (en) Multi-channel endorectal coils and interface devices therefor
JP7086956B2 (en) Radio frequency coil system for MR imaging
US20060173284A1 (en) Radiofrequency coil and catheter for surface nmr imaging and spectroscopy
US7479784B2 (en) Arrangements, systems and methods for facilitating and collecting information associated with fluxes of magnetic fields provided at various angles from one another
JP2012223580A (en) Magnetic resonance signal detection using remotely positioned receive coils
CN104473644A (en) Coil control system and head and neck combined coil for magnetic resonance imaging
JP3341309B2 (en) Endoscope probe for MRI
US5646530A (en) Surface coil for high resolution imaging using a magnetic resonance imaging apparatus
US20200408860A1 (en) Systems for a radio frequency coil assembly
CN113534028B (en) Special surface phased array receiving coil for skin
CN103941203B (en) A kind of flexible winding displacement antenna assembly for magnetic resonance imaging
US8358131B2 (en) RF stripline antenna with impedance adaptation for MR imaging
CN105807242A (en) Open-type coil device for magnetic resonance imaging
KR101081339B1 (en) RF coil assembly for magnetic resonance image device
Mathieu et al. Towards brain MRI adaptable to head size: Bowing RF coil phased arrays
CN117518049A (en) Low inductance planar multilayer coil

Legal Events

Date Code Title Description
PB01 Publication
PB01 Publication
SE01 Entry into force of request for substantive examination
SE01 Entry into force of request for substantive examination
GR01 Patent grant
GR01 Patent grant