CN113534028B - Special surface phased array receiving coil for skin - Google Patents
Special surface phased array receiving coil for skin Download PDFInfo
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- CN113534028B CN113534028B CN202110742322.3A CN202110742322A CN113534028B CN 113534028 B CN113534028 B CN 113534028B CN 202110742322 A CN202110742322 A CN 202110742322A CN 113534028 B CN113534028 B CN 113534028B
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- G—PHYSICS
- G01—MEASURING; TESTING
- G01R—MEASURING ELECTRIC VARIABLES; MEASURING MAGNETIC VARIABLES
- G01R33/00—Arrangements or instruments for measuring magnetic variables
- G01R33/20—Arrangements or instruments for measuring magnetic variables involving magnetic resonance
- G01R33/28—Details of apparatus provided for in groups G01R33/44 - G01R33/64
- G01R33/32—Excitation or detection systems, e.g. using radio frequency signals
- G01R33/34—Constructional details, e.g. resonators, specially adapted to MR
- G01R33/341—Constructional details, e.g. resonators, specially adapted to MR comprising surface coils
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- Y—GENERAL 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
- Y02—TECHNOLOGIES OR APPLICATIONS FOR MITIGATION OR ADAPTATION AGAINST CLIMATE CHANGE
- Y02D—CLIMATE CHANGE MITIGATION TECHNOLOGIES IN INFORMATION AND COMMUNICATION TECHNOLOGIES [ICT], I.E. INFORMATION AND COMMUNICATION TECHNOLOGIES AIMING AT THE REDUCTION OF THEIR OWN ENERGY USE
- Y02D30/00—Reducing energy consumption in communication networks
- Y02D30/70—Reducing 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 the long-distance cable and outputs the coil antenna to the preamplifier, and the preamplifier amplifies signals and outputs the amplified signals 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
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 made great benefit 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 a magnetic resonance system mainly consists of a superconducting magnet, a gradient coil, a radio frequency coil, a spectrometer system, etc., wherein the performance of the radio frequency receiving coil directly determines the quality of an image as a terminal for receiving a magnetic resonance signal. 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 sizes of large and small manufacturers of the conventional single-channel small-field annular coil are different, 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 a single-channel small-field annular coil is used at present, a hard shell of the coil is not convenient to match with the skin, and the imaging depth and the 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 return 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 in order to form the return circuit jointly with little coil antenna, second inductance L2's one end be connected to direct current input, the other end is connected to between parallel resonance return 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 surface phased array receiving coil special for the skin comprises a parallel resonant circuit, a first inductor L1, a diode D1, a first detuning circuit capacitor C2 and a second detuning 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 detuning circuit capacitor C2 and the second detuning circuit capacitor C3.
The special surface phased array receiving coil for the skin comprises a phase-shifting capacitor C5 and a phase-shifting inductor L3, wherein the phase-shifting capacitor C5 is connected to one input end of a preamplifier in series, 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, 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 belt manufactured by 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 is capacitive according to the present invention.
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 structure according to the present invention.
Fig. 5 is a disassembled schematic view of the antenna portion 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-shifting 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 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 the signals of the small areas are effectively connected together after the measurement is finished. 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 and guarantee better imaging depth.
The control circuit in this embodiment includes 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 in order to form the return circuit jointly with little coil antenna, second inductance L2's 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. The matching capacitor C1 is mainly used for realizing input and output matching under the loading condition, so as to achieve the best effect of signal transmission efficiency. The frequency modulation capacitor C4 is an adjustable capacitor, and because a certain error exists in the inductance and capacitance values of the antenna coil, the frequency of the coil needs to be tuned by the adjustable capacitor, so that the central frequency of the coil reaches the working frequency of the system.
The parallel resonant circuit of the embodiment includes a first inductor L1, a diode D1, and a first detuning circuit capacitor C2 and a second detuning circuit capacitor C3 connected in series, where the first inductor L1 and the diode D1 are connected in series and then connected in parallel with the first detuning circuit capacitor C2 and the second detuning circuit capacitor C3. When a current signal is input by direct current, the diode D1 is conducted, a parallel resonance loop is formed among the first detuning loop capacitor C2, the second detuning loop capacitor C3 and the first inductor L1, the parallel resonance is in a high-resistance state and is equivalent to a coil disconnection state, and when the transmitting coil works, the receiving coil is equivalent to disconnection and the receiving coil and the transmitting coil are not interfered with each other.
In this embodiment, C1 to C4 are integrated with L1, D1 and L2 on one 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 by 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 the embodiment is 180 degrees, so when the front-end is inductive, the phase-shifting circuit adopts a mode of connecting an inductor in parallel with a series capacitor, wherein the C5 is mainly used for adjusting the phase, the L3 is mainly used for correcting 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-shifting circuit adopts a mode of connecting the inductor in parallel with the capacitor, wherein the L is mainly used for adjusting the phase, and the C5 is mainly used for correcting 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 an insulating material filled 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 and 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 skin surface with medical sticky tape, and convenient to use improves SNR and patient's comfort level simultaneously.
Claims (7)
1. A surface phased array receiving coil special for skin is characterized in that the receiving coil is special for the skin surface; the antenna comprises a plurality of coil units, a control circuit, a long-distance cable and an amplifying circuit, wherein each coil unit is connected with one control circuit, and the coil units are 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 signal to the preamplifier, the preamplifier amplifies the signal and outputs the amplified signal to an external processor, the phase adjustment of the phase-shifting circuit is determined according to the distance between the coil unit and the preamplifier, and when the coil unit is seen to be capacitive at the front end, the phase-shifting circuit adjusts the phase in a series inductance and capacitance mode; when the coil unit is inductive when viewed from the front end, the phase-shifting circuit adjusts the phase in a series capacitor-inductor mode;
the control circuit comprises a second inductor L2, a matching capacitor C1, a parallel resonant circuit and a frequency modulation capacitor C4 which are sequentially connected in series, wherein the matching capacitor C1 and the frequency modulation capacitor C4 are respectively connected to two ends of the coil unit, one end of the second inductor L2 is connected to a direct current input, the other end of the second inductor L2 is connected between the parallel resonant circuit and the frequency modulation capacitor C4, two ends of the matching capacitor C1 are respectively connected to the amplifying circuit through long-distance cables, and the frequency modulation capacitor C4 is an adjustable capacitor;
the parallel resonant circuit comprises a first inductor L1, a diode D1, a first detuning circuit capacitor C2 and a second detuning 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 detuning circuit capacitor C2 and the second detuning circuit capacitor C3;
the phase shift circuit comprises a phase shift capacitor C5 and a phase shift inductor L3;
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; or, the phase shift circuit comprises a phase shift capacitor C5 and a phase shift inductor L3, the phase shift 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 shift capacitor C5 is connected in parallel between the two input ends of the preamplifier.
2. The surface phased array receiving coil special for skin as claimed in claim 1, wherein the plurality of coil units comprises at least two small coil antennas and control circuits equal in number to the small coil antennas, each small coil antenna is connected to the independent amplifying circuit through the long distance cable by the control circuit;
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 2, wherein the small coil antennas are circular, and wherein the distance between the centers 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 2, 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 surface phased array receiver coil for skin use according to claim 2, wherein the matching capacitor C1 and the frequency modulation capacitor C4 are respectively connected to both ends of the small coil antenna to form a loop together with the small coil antenna.
6. The skin-specific surface phased array receiver coil as claimed in claim 2, wherein said small coil antenna and said long distance cable are made of a coaxial cable, and said coaxial cable comprises a metal braid, an insulating layer, a supporting layer and a conductor from outside to inside.
7. The skin-specific surface phased array receiver coil as claimed in claim 2, wherein said small coil antenna is a foam-like metal conductor strip made by a powder sintering process.
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