• 专利附录
  • 专利说明
  • 权利要求
  • 类似技术
  • 同族专利
  • 引用文献
  • 法律状态
  • 优先权
    • 专利摘要:
    The present invention relates to a nuclear magnetic resonance device (100) patch resonator comprising: a ground plane (4), a conductive element (1), a dielectric element (3) positioned between said ground plane (4) and said conductive element (1), said resonator (100) being able to emit a circularly polarized radiofrequency signal when the resonator is powered by a first transmission line (14a) connected to said conductive element (1) by means of a first connection point (5) and adapted to alternately receive a radiofrequency signal polarized circularly in the opposite direction when the resonator is connected to a second transmission line (14b) via a second connection point (6), said resonator comprising a switching means (13) mounted in parallel on each transmission line (14a, 14b) at a distance from the ground plane (4) corresponding to (2n + 1) λ / 4 with n a natural integer, and λ the wavelength of the guided wave in the transmission line (14a, 14b) at the operating frequency of the resonator, said switching elements for connecting / disconnecting said transmission lines (14a, 14b).
    公开号:FR3018361A1
    申请号:FR1451923
    申请日:2014-03-10
    公开日:2015-09-11
    发明作者:Guillaume Ferrand；Michel Luong
    申请人:Commissariat a lEnergie Atomique CEA；Commissariat a lEnergie Atomique et aux Energies Alternatives CEA；
    IPC主号:
    专利说明:

    [0001] FIELD OF THE INVENTION The present invention relates to a circular polarization transceiver for magnetic resonance imaging (MRI). The technical field of the invention is that of high frequency antennas (in English "RF coil") and their use in Nuclear Magnetic Resonance ("Nuclear Magnetic Resonance") devices for humans or animals.
    [0002] In Magnetic Resonance Imaging (MRI), an antenna is used in transmission to generate a radiofrequency field having a magnetic component B1 orthogonal to the static field Bo, capable of exciting the nuclei. atoms, especially those of hydrogen (for so-called proton MRI) within the sample placed in the antenna. During the relaxation phenomenon, a radiofrequency signal also having a very low amplitude component B1 is re-emitted by the sample. It can then be detected either by the same antenna switched at this time on the reception channel provided with amplifiers with very low noise, or by another dedicated antenna. The static magnetic field Bo in which the sample is immersed determines the frequency of the signal which is proportional to it. Thus, it goes from 64 MHz to 128 MHz for a Bo field of 1.5 and 3 teslas respectively. For high field MRI scanners, that is to say with a Bo field larger than 3 tesla, an antenna is usually composed of several networked resonators in order to obtain, on the one hand, a uniform excitation at through the parallel transmission process and, on the other hand, a better reception sensitivity which improves the quality of the image. These resonators emit and receive radio frequency signals. The subject of the invention is a type of resonator which is particularly suitable for the exploration, by imaging or spectroscopy, of a region situated in the axis 5 of the magnetic field Bo, in particular the top of the head in humans or the large ones. primates. STATE OF THE ART The operation of high field MRI antennas (that is to say beyond 3 Tesla) is characterized by an inhomogeneity of the radiofrequency magnetic fields emitted or perceived by a single resonator: B1 + in emission and B1 - in reception. The quantity B1 + corresponds to the circular polarization of the magnetic field rotating in the same direction as the nuclear spins used for imaging. In contrast, the amount B1- is the polarization which rotates in the opposite direction and which characterizes the reception sensitivity. The inhomogeneity of magnetic fields is inherent to the equations of electromagnetism. It increases with the frequency of the signal and consequently with the magnetic field Bo. In emission, the inhomogeneity of B1 + is reflected in an image by the appearance of shadows or artificial contrast, difficult to interpret. To remedy this, a network antenna formed by a multitude of resonators must be used to directly equalize B1 + as well as the flip angle (flip angle in English) This compensation will be more effective than the number of resonators in a network antenna will be high. In reception, a larger number of resonators will provide a more uniform overall reception pattern with increased signal-to-noise ratio. This increase can be used to increase the resolution of the image or to reduce the acquisition time by using an acceleration method that uses the differential sensitivity between resonators due to their construction or distribution around the sample . Conventionally, there are two types of resonators that are used in high-field MRI: linear resonators ("stripline" in English) and circular resonators or loops ("loop" in English). When the sample to be studied is a human head, these resonators are placed around it on a surface parallel to the head-to-feet axis of the patient, which also coincides with the direction of the static field Bo. In this configuration, the resonators do not illuminate the region of the brain at the top of the head. Conversely, they receive as little signal from this region. Given the geometry of the head and the antennas, a first improvement solution would be to place, at the top of the head, a transceiver resonator having a symmetrical shape with respect to the head-to-feet axis, as per for example a loop resonator whose resonator surface would be orthogonal to this head-to-feet axis. However, the magnetic field radiated by a loop is substantially orthogonal to its surface. Thus, the B1 component would be essentially parallel to Bo, thus ineffective in magnetic resonance. Only the region close to the driver of the loop has a properly oriented and efficient component B1. This observation led to a strategy where a large number of loops of reduced size are used in networks in search, on the one hand, of the increase of the edge effect by the increase of the cumulative length of the conductors forming loops and, on the other hand, a more favorable orientation of the radiated magnetic fields. Despite its relevance, this solution has two major drawbacks. In the first place, the realization and the setting of the loop network are very complex. Indeed, each loop must resonate at the Larmor frequency, have a precise terminal impedance and not be coupled to neighboring loops so as not to reduce the efficiency of the transmission network or increase the noise correlated reception. Then, the network does not allow to explore with a good sensitivity the deeper regions of the brain, especially above the thalamus because the depth of penetration of the radiated field decreases with the size of the loops. The precession of spins induces a circular polarization to the magnetic fields radiofrequency brought into play in MRI. For a given resonator, the channel that emits polarization B1 + will be used to excite the spins and the channel that emits polarization B1- will be used to receive the relaxation signal under the principle of reciprocity. A channel is a physical port through which the resonator is connected to the outside world. The linear or circular resonators emit a linearly polarized magnetic field. However, a linear polarization is the result of the superposition of two circular polarizations rotating in the opposite direction, in this case B1 + and B1-. Thus, the same channel can be used alternately in transmission and reception. However, half of the available power is not exploited each time. Consequently, the efficiency and the field sensitivity of the resonator are reduced by 40% respectively in transmission and reception. A particularly advantageous solution consists in using a circular resonator of the "patch" type. Such a resonator has been used in addition to a grating antenna to emit circular polarization ([1] Hoffmann, J. et al., (2013), Human Brain Imaging at 9.4 T Using a Tunable Patch Antenna for Transmission. Medicine, 69: 1494-1500). Typically, this resonator consists of a metal surface deposited on a dielectric plate whose second face is covered by a ground plane.
    [0003] This type of resonator is known and used in the field of radio frequency antennas for data communication. The resonator described in WO 2007/14105 requires a disc 320 mm in diameter of poly tetrafluoroethylene (PTFE) for a resonance frequency of 400 MHz. The diameter of the radiating element is 210 mm. The feed is performed through a hybrid coupler 90 ° at two points located at the periphery of the radiating element and on two orthogonal axes passing through its center to form a transmission channel. For a "patch" resonator, the diameter of the disk is larger the lower the resonant frequency. Thus, for an application with an MRI scanner of 7 Tesla at 298 MHz, the diameter of the radiating element according to the teaching of this document would exceed 320 mm while retaining the same PTFE substrate. A large diameter, apart from the problem of congestion in an MRI scanner, would increase the mutual coupling to 15 linear or circular resonators which must be placed closer to the head and with which the resonator "patch" must integrate to form a network antenna. Thus for an application in medical imaging, the outer diameter of the "patch" resonator should not exceed 180 mm so that the latter 20 can be placed about 40 mm from the top of the head. Three methods are known to reduce the size of a "patch" resonator. A first method is to choose a substrate with a much higher dielectric constant (typically an alumina ceramic) to reduce the wavelength of the propagated signal in the substrate. This varies in first approximation as the inverse of the square root of the dielectric constant. However, the realization of a ceramic printed circuit is more difficult and expensive compared to a polymer substrate. It also makes the device more mechanically fragile vis-à-vis the acoustic vibrations generated by the gradient magnets in an MRI scanner. A second method of arranging suitably oriented slots also makes it possible to reduce the resonance frequency for a given geometry, and by extension, to reduce the resonator size for a given frequency ([2] Wong, K.-L. and Lin Y.F. (1998), Circularly Polarized Microstrip Antenna with Tuning Stub, Electronic Letters, Vol 34, No. 9: 831-832). However, the slits as they appear in the document have a major disadvantage in that they significantly reduce the magnetic field in the useful area in MRI, close to the resonator and around the axis of symmetry. A third method consists in mounting capacitors between the radiating element and the ground plane so as to reduce the size of a "patch" resonator. This method is particularly described in document WO 2007/141505. However, the capacitors have intrinsic losses characterized by a quality factor. These losses increase proportionally with the value of the capacity, and inversely with the quality factor. In addition, the capacitors must withstand voltages greater than 2000 volts for an incident power of 1 kW when the resonator is used in transmission. However, among the industrial capacitors available, the higher the allowable voltage, the lower the quality factor. The losses reduce the efficiency and sensitivity of the resonator, respectively in transmission and reception. This approach is therefore valid only in the case where performance and sensitivity are not decisive criteria, as may be the case in the field of RFID (radiofrequency identification in English) and as is exactly the case reverse in the field of MRI.
    [0004] Finally, still with the objective of reducing the size of the resonator, it is advantageous to find a solution to obtain a "patch" resonator without resorting to a hybrid circuit. Reference [2] proposes a "patch" resonator without the use of a hybrid circuit. The resonator described has two possible connection positions, one for transmitting and receiving an LHCP polarization and the other for transmitting and receiving an RHCP polarization. The joint use of the two positions has not been considered for this resonator. But if the two positions were to be connected simultaneously, there would be a strong mutual coupling at the connection points in transmission and reception which would result in a loss of power, about 40% of power. Such a resonator is therefore not suitable for use in the field of nuclear magnetic resonance imaging. In addition, the resonator described in reference [2] has irreversible adjustment means for the polarization efficiency and the operating frequency. These do not offer the necessary flexibility to a resonator used in the field of nuclear magnetic resonance imaging because these adjustments depend on the size and shape of the human head placed in its vicinity.
    [0005] Given all these constraints and this state of the art, "patch" resonators, although widely used in telecommunications, are still very little used in the field of MRI. Indeed, none of the solutions described is satisfactory for a Magnetic Resonance Imaging (MRI) application with a very high magnetic field.
    [0006] Thus, the proposed solutions do not solve the problem of size "patches" (because they require the addition of additional electrical components, or even the problem of sufficient performance for an application in MRI.
    [0007] SUMMARY OF THE INVENTION In this context, the present invention aims to solve the aforementioned problems by proposing a compact planar resonator, called "patch" resonator, for Magnetic Resonance Imaging and alternatively to emit a left circular polarized signal. (LHCP for Left Hand Circular Polarization in English) and to receive a right circular polarized (RHCP) signal through two separate radio frequency ports.
    [0008] To this end, the invention proposes a "patch" resonator for a nuclear magnetic resonance apparatus comprising: a ground plane, a conductive element, a dielectric element positioned between said ground plane and said conductive element, said resonator being able to emit a radiofrequency signal circularly polarized when the resonator is fed by a first transmission line connected to said conductive element by means of a first connection point and adapted to receive alternately a radiofrequency signal polarized circularly in the opposite direction when the resonator is connected to a second transmission line via a second connection point, said resonator having a switching means mounted in parallel on each transmission line at a distance from the ground plane corresponding to (2n + 1) 2.14 with n a natural integer, and at the wavelength of the guided wave in the transmission line ion to the operating frequency of the resonator, said switching elements for connecting / disconnecting said transmission lines. Thus, the invention relates to a compact planar resonator for transmitting and receiving a compact circular polarization radiofrequency signal of dimensions less than or equal to X0 / 5, where X0 is the wavelength of the signal propagated in the air. The resonator according to the invention comprises an active switching means, advantageously formed by PIN diodes, alternatively for transmitting an LHCP circular polarized signal and for receiving a polarized signal RHCP through two distinct radio frequency ports, economizing it. a 90 ° hybrid circuit to minimize the bulk of such a resonator. The "patch" resonator according to the invention may also have one or more of the following characteristics, considered individually or in any technically possible combination: said switching means is a PIN diode having a locked state and a conducting state, said diode PIN associated with the first transmission line being blocked in transmit and receive pass, said PIN diode associated with the second receive transmission line being transmitting and blocked in reception; said resonator has a shield; the shielding thus makes it possible to avoid mutual coupling with linear or circular resonators which must be placed closer to the head and with which the "patch" resonator must integrate to form a network antenna; said resonator has a first upper shield and a second lateral shield on the edge of said resonator; said resonator comprises four variable capacitors for adjusting the operating frequency of the resonator and / or adjusting the impedance at the first connection point and the second connection point to the operating frequency of the resonator, and / or adjusting the efficiency of circular polarizations; advantageously the four variables are very low values and therefore have a very limited power dissipation, and allow to independently adjust the three parameters important for the operation of the resonator MRI; the resonator comprises four appendages arranged around the conductive element and electrically connected to said conductive element forming a triplate line impedance transformer; the appendages positioned at the periphery acting as an impedance transformer in triplate line topology advantageously reduce a capacitive effect, almost without power dissipation, ensuring excellent voltage withstand; said conductive element is in the form of a disk and has a plurality of radial slots, each of the radial slots extending from the edge of the conductive disk to a given distance from the center of the conductive disk; the resonator has eight slots; the two connection points are positioned on the surface of the conductive disk on two orthogonal lines, called main axes, intersecting at the center of the conductive disk, the two points being at an identical distance from the center of the conductive disk; the resonator comprises four variable capacitors, said variable capacitors being positioned along two orthogonal lines, called secondary axes, the secondary axes having an angular offset of 45 ° with respect to the main axes; said variable capacitors are positioned at the intersections of the outer edges of the appendages and the two secondary axes.
    [0009] The invention also relates to a high frequency antenna for nuclear magnetic resonance apparatus characterized in that it comprises a "patch" resonator according to the invention. Advantageously, the high frequency antenna for nuclear magnetic resonance apparatus is a multi-channel antenna comprising a plurality of linear resonators having a rectilinear radiating element and / or a plurality of loop resonators comprising a radiating element forming a loop, said radiating elements being used for transmitting a radiofrequency excitation signal and / or for receiving a radiofrequency relaxation signal. BRIEF DESCRIPTION OF THE FIGURES Other features and advantages of the invention will emerge more clearly from the description which is given below, by way of indication and in no way limiting, with reference to the appended figures, among which: FIGS. 1 to 3 illustrate different perspective views of a "patch" resonator according to the invention; - Figure 4 illustrates a radial sectional view through a connection point of the "patch" resonator according to the invention illustrated in Figures 1 to 3; FIG. 5 schematically illustrates a switching circuit of the "patch" resonator according to the invention; Figure 6 is an illustration of a Smith chart; FIGS. 7a to 7c are representations of Pascal's various snails.
    [0010] DESCRIPTION OF AT LEAST ONE EMBODIMENT FIGS. 1 to 3 diagrammatically represent a circular resonator 100, called a "patch" resonator, according to the invention that can be used in transmission and reception for Magnetic Resonance Imaging (MRI).
    [0011] Figure 4 shows a radial sectional view of the circular resonator 100 shown in Figures 1 to 3 showing the details of the connections. Figures 1 to 4 will be described together. The "patch" resonator 100 according to the invention comprises: a conductive disk 1; a disk of dielectric material called lower substrate 3, on which the conductive disk 1 is fixed; a ground plane 4 covering the lower face of the lower substrate 3; - Two connection points 5 and 6, each electrically connecting the conductive disk 1 to the central core 22 of a transmission line formed by a coaxial cable 14a, 14b, the outer conductor 21 is electrically connected to the ground plane 4; four arc-shaped appendices 7 electrically connected in their middle to the conductive disk 1 and positioned at the periphery of the conductive disk 1; - Four variable capacitors 8 of low value, typically from 0.5 to 2 pF, one for each appendix 7, allowing the adjustment of the resonator 100 in impedance matching, operating frequency, and yield of circular polarizations.
    [0012] The conductive disk 1 is advantageously made of copper and has a thickness corresponding to about six times the skin thickness (penetration of the electromagnetic wave in the conductor) at the operating frequency of the resonator. Advantageously, the conductive disk 1 has radially oriented cuts forming slots 2. The presence of the slots 2 on the conductive disk 1, advantageously eight in number, makes it possible to reduce the resonance frequency of the resonator 100 for a given geometry. Therefore, these slots 2 can reduce the size of the conductive disk 1, and therefore its size, for the desired frequency of use in MRI, and especially for a frequency of 298 MHz corresponding to the nuclear magnetic resonance frequency of the protons at 7. Teslas (T). According to a preferred embodiment of the invention, the slots 2 do not pass through the center of the conductive disk 1 so as to improve the efficiency of the resonator 100, particularly in the field of MRI where the resonator operates in the near field. Advantageously, the slots 2 extend radially to the edge of the conductive disk 1, so as to avoid the appearance of currents induced by the pulsed gradient magnets of the Nuclear Magnetic Resonance equipment. The disk forming the lower substrate 3 has a larger diameter than the diameter of the conductive disk 1 on which it rests. Advantageously, its thickness is chosen so as to obtain a good understanding between the radiation and the stability of the adjustment of the frequency. Advantageously, the thickness of the lower substrate 3 is between 1 / 10th and 1 / 4th of the diameter of the conductive disk 1, and preferably of the order of 1 / 5th of the diameter of the conductive disk 1. Preferably, the lower substrate 3 is made of a material with very low dielectric loss. The connection points 5 and 6 are placed on the conductive disk 1 and positioned along two orthogonal lines, hereinafter called main axes AP1 and AP2, intersecting at the center of the conductive disk 1. The two connection points 5 and 6 are positioned at an equal distance from the center of the conductive disk 1. The appendices 7 positioned around the conductive disk 1 have a role of impedance transformer to reduce a capacitive effect. They therefore advantageously replace capacitors used in resonators "patches" according to the state of the art to reduce their size and which are a source of loss of efficiency and sensitivity of the resonator. The variable capacitors 8 are electrically connected on the one hand to conducting wells 9 passing through the lower substrate 3 and connected to the appendices 7 and on the other hand to the ground plane 4. The variable capacitors 8 are positioned along two orthogonal lines called secondary axes AS1 and AS2. The secondary axes are in the same plane as that formed by the main axes AP1, AP2 and have an angular offset of 45 ° with respect to the main axes AP1 and AP2.
    [0013] According to an advantageous embodiment of the invention, and to further reduce the dimensions of the resonator by reducing the dimensions of the appendages 7 while maintaining the same capacitive effect, a second disc of dielectric material, called upper substrate 10 and a coronal shielding 31 are added to the resonator. The diameters, the thicknesses and the materials of the two substrates, lower 3 and greater 10, are preferably identical. The additional coronal shield 31 is positioned on the upper face of the upper substrate 10. The inner radius 32 of the ring formed by the corona shield 31 is adapted according to the desired compromise between the circular polarization efficiency and the mutual coupling of the "patch" resonator 100 with other resonators present in the vicinity, such as in a network antenna. Thus, the smaller the inner radius 32 of the corona shield 31, the larger the shield area will be, thereby minimizing the mutual coupling with other resonators but also reducing the efficiency of the resonator 100 due to the effect of the resonator. 'screening. In practice, and advantageously, for an application at 7T, this inner radius 32 will lie between the outer radius of the conductive disk 1 and the inner radius formed by the appendices 7, i.e. in the hatched zone Z1 in FIG.
    [0014] The resonator 100 also comprises a lateral shield 12 illustrated in FIG. 3 completing the upper corona shield 31. The lateral shield 12 also makes it possible to reduce the mutual coupling. Thus, the use of the two shields 12 and 31 optimally minimizes the mutual coupling. However, it is possible to use only the upper coronary shield 31 only to reduce the size of the appendices 7. To use the same "patch" resonator alternately in transmission and reception respectively in left circular polarization (LHCP for Left Hand Circular Polarization in English language) and right circular polarization (RHCP) without loss of efficiency or efficiency, the resonator 100 according to the invention comprises a switching circuit 23, illustrated more particularly in FIG. 5, composed of a PIN diode 13 (for Positive Intrinsic Negative in English language) connected to each connection point 5 and 6. Each PIN diode 13 is connected in parallel on each coaxial cable 14a, 14b at a distance equal to (2n + 1 ) At / 4 of the ground plane 4, with n natural integer, and at the wavelength in the coaxial cable at the operating frequency. More generally, the switching circuit 23 must consist of a switching element which must be: fast; that is to say at least a factor ten lower than the relaxation time of the atoms (for example 10 microseconds for protons whose relaxation time is 100 microseconds); - Can withstand the radio frequency power in general from a few kilowatts to a few tens of kilowatts. FIGS. 4 and 5 respectively show the details of the connections and the details of the switching circuit 23. It should be noted that the diagrams presented are just as valid for the transmission cable as for the cable for receiving the connection points.
    [0015] FIG. 4 represents a radial section passing through a connection point 5 or 6. FIG. 5 shows the composition of the switching circuit 23 between the two interface ports 19, on the side of the coaxial line 14a, 14b, and 20 of the side of the MRI scanner. Beyond the interface port 20, the electronic transmission or reception circuit is conventional, and is composed of at least one radiofrequency source of transmission power and a low noise preamplifier in reception. These elements being known they will not be detailed in the present application. Each PIN diode 13 is controlled independently by a voltage generator 15. Thus, for a positive polarity, for example +10 volts, the PIN diode 13 is said to be on; it behaves electrically as a resistance of very low value close to 0.5 ohm (almost a short circuit). Consequently, the impedance brought back to the ground plane 4 via the coaxial cable 14a, 14b is then in known manner, close to 5 kohms if the coaxial cable has a characteristic impedance of 50 ohms. Under these conditions, everything happens as if the associated connection point did not exist physically. On the other hand, if the polarity of the generator 15 is negative, for example -30 volts, the PIN diode 13 will be said to be blocked. It then behaves electrically as a capacitor of very low value (typically 0.7 pF) in parallel with a resistor of high value (typically 200 kohms). In the field of very high frequency electromagnetic waves VHF type (for Very High Frequency in English) and UHF (Ultra High Frequency in English), everything happens as if the PIN diode 13 did not exist.
    [0016] Thus, to transmit on the port connected to the connection point 5, the associated PIN diode 13 is driven with a negative polarity and the second PIN diode 13 connected to the connection point 6 is driven with a positive polarity simultaneously. In reception on the port connected to point 6, it suffices to invert the polarity of the two generators 15.
    [0017] Each control generator 15 is protected from high-frequency currents by a shock inductance 16, typically of the order of 10 111-1. Conversely, the high-frequency circuits are isolated from the direct current of the control generator 15 by two capacitors 17 and 18.
    [0018] EXAMPLE OF EMBODIMENT AND IMPLEMENTATION An exemplary embodiment is given for the construction and adjustment of a "patch" resonator 100 according to the invention operating at a frequency of 298 MHz, a frequency corresponding to the nuclear magnetic resonance frequency of the protons at 7 Teslas.
    [0019] Thus, the conductive disc 1, with its slots 2 and its appendages 7 are etched by the technique of printed circuits on a copper double layer laminate. The second copper layer is used to form the ground plane 4. This laminate also forms the lower substrate 3. The connection points 5 and 6 are obtained by making metallized holes, generally called vias, which connect the two faces of the ground. lower substrate 3. These vias form the conductive wells 9. Advantageously, the same double-layer laminate is also used to achieve the coronal shield 31 and the upper substrate 10, except that on it the second copper layer is completely removed. The two laminates are then heat-bonded with a polyolefin film. The side shield 12 may be constituted by a copper adhesive tape, of the order of 80 lam thick, bonded to the edge of the resonator. Weld points are made to ensure the electrical connection between the corona shield 31 in the upper part of the resonator 100 and the ground plane 4 in the lower part of the resonator 100. The diameter of the conductive disk 1 and the substrates 3 and 10 are respectively 120 mm and 180 mm.
    [0020] The realization of the resonator 100 according to the invention requires a suitable choice of the dimensions of the appendices 7 and the slots 2, in order to reduce as much as possible the value of the variable capacitors 8 and thus to minimize the losses. If the appendices 7 are too short, the values of the capacitors will be too low. If the appendages are too long, the capacitors will be too bulky. The value of the capacitance brought back by an appendix of length 2L, is expressed approximately by the relation: 2 C tan PLa 604 where Zo and f3 are respectively the characteristic impedance and the propagation constant of the triplate line formed by the corona shielding 31, Appendix 7 and the ground plane 4. For an appendage characterized by an inner radius of 70 mm, an outer radius of 80 mm and a length of 110 mm, the equivalent capacity reduced is approximately 7 pF. The conductive disc 1 has eight slots 2 which reduce the dimensions of the resonator 100. The radial slots 2 are aligned on the bisectors formed between a primary axis AP1, AP2 and a secondary axis AS1, AS2. They begin at 10 mm from the center of the conductive disk 1 and extend to the edge of the latter. The width of the slots is typically 2 mm.
    [0021] The connection points 5 and 6 are arranged at 11.5 mm from the center of the conductive disk 1. This position is chosen to obtain a coarse impedance matching with respect to a 50 ohm characteristic impedance coaxial cable. With the arrangements described above, a maximum value of 1 pF for the variable capacitors 8 is sufficient to achieve fine impedance matching connection points 5 and 6, optimize the operating frequency to 298 MHz and maximize the efficiency of one of the circular polarizations. The method of adjustment is detailed below. For a use of the invention in magnetic resonance imaging, it is necessary that the plane of the conductive disk 1 is normal to the static magnetic field Bo of the main magnet. According to the direction of Bo, oriented from the ground plane 4 to the conductive disk 1 or vice versa, the connection point 5 will be used for the transmission and the connection point 6 for reception or vice versa. The adjustment of the "patch" resonator 100 according to the invention is done by means of the 4 variable capacitors 8 visible in FIG. 1. Each capacitor has a current value denoted: C1, C2, C3 and C4. The 4 variable capacitors 8 make it possible to adjust three parameters: the impedance presented by the connection points to the coaxial cables, the operating frequency, the efficiency or efficiency of the circular polarizations. The impedance of the "patch" resonator 100 decreases when increasing C1 while simultaneously decreasing C2 and maintaining an identical value for C3 and C4. The operating frequency increases when the sum Cl + C2 + C3 + C4 is decreased. The efficiency of the desired circular polarization varies when the (C1 + C2) / (C3 + C4) ratio is varied. The efficiency or the efficiency of a polarization is evaluated experimentally or in simulation by the average value of the B1 + field in the region of the sample located opposite the conductive disk 1.
    [0022] The adjustment of the impedance is done in a known manner thanks to the representation of the reflection coefficient as a function of the frequency. It aims to minimize the value of this coefficient at the operating frequency of the resonator 100.
    [0023] The tuning of the efficiency of the antenna is based on the representation of the reflection coefficient in a Smith chart, as illustrated in FIG. 6, that is to say a representation in the complex plane of this plane. coefficient for a linear variation of the frequency. In the general case, the path 41 has a shape resulting from a rotation and a translation applied to a curve known as Pascal's snail, illustrated in FIGS. 7a to 7c, of general equation r = a + bxcos (0) , where r is the radius in the center of the chart, the angle, with a and b parameters depending on the characteristics of the resonator and its setting.
    [0024] The optimal setting corresponds to the one where Pascal's snail degenerates into a cardioid, FIG. 7b, showing a double point 42 whose associated frequency will be the operating frequency. In the exemplary embodiment, the optimum values of the capacitors C1 to 04 are 0.7 pF, 0.9 pF, 0.8 pF and 0.8 pF respectively.
    权利要求:
    Claims (13)
    [0001]
    REVENDICATIONS1. Patch resonator (100) for a nuclear magnetic resonance apparatus comprising: a ground plane (4), a conductive element (1), a dielectric element (3) positioned between said ground plane (4) and said conductive element (1) said resonator (100) being adapted to transmit a circularly polarized radiofrequency signal when the resonator is powered by a first transmission line (14a) connected to said conductive element (1) by means of a first connection point (5) and adapted to alternatively receiving a circularly polarized radiofrequency signal of opposite direction when the resonator is connected to a second transmission line (14b) via a second connection point (6), said resonator having a switching means (13) mounted in parallel on each transmission line (14a, 14b) at a distance from the ground plane (4) corresponding to (2n + 1) 2/4 with n a natural integer, and At the wavelength of the g wave uidée in the transmission line (14a, 14b) to the operating frequency of the resonator, said switching elements for connecting / disconnecting said transmission lines (14a, 14b).
    [0002]
    2. Resonator patch (100) for nuclear magnetic resonance apparatus according to the preceding claim characterized in that said switching means is a PIN diode having a blocked state and an on state, said PIN diode associated with the first transmission line (14a). ) being blocked in transmitting and receiving pass, said PIN diode associated with the second transmission line (14b) receiving being transmitting and blocked in reception.
    [0003]
    3. Resonator patch (100) for nuclear magnetic resonance apparatus according to one of the preceding claims characterized in that said resonator has a shield (31, 12).
    [0004]
    4. A nuclear magnetic resonance apparatus (100) patch resonator according to one of the preceding claims, characterized in that said resonator has a first upper shield (31) and a second lateral shield (12) at the edge of said resonator ( 100).
    [0005]
    5. Resonator patch (100) for nuclear magnetic resonance apparatus according to one of the preceding claims characterized in that said resonator comprises four variable capacitors (8) for adjusting the operating frequency of the resonator (100) and / or adjust impedance at the first connection point (5) and the second connection point (6) to the operating frequency of the resonator (100), and / or to adjust the efficiency of the circular polarizations.
    [0006]
    6. nuclear magnetic resonance apparatus (100) patch resonator according to one of the preceding claims characterized in that said conductive element (1) has the shape of a disc and has a plurality of radial slots (2), each of radial slots (2) extending from the edge of the conductive disk (1) to a given distance from the center of the conductive disk (1).
    [0007]
    7. Resonator patch (100) for nuclear magnetic resonance apparatus according to the preceding claim characterized in that the resonator comprises eight slots (2).
    [0008]
    8. Resonator patch (100) for nuclear magnetic resonance apparatus according to one of claims 6 to 7 characterized in that the two connection points (5) and (6) are positioned on the surface of the conductive disc (1) on two orthogonal lines (AP1, AP2), said main axes, intersecting at the center of the conductive disk, the two points (5) and (6) being at an identical distance from the center of the conductive disk (1).
    [0009]
    9. Resonator patch (100) for nuclear magnetic resonance apparatus according to one of the preceding claims characterized in that it comprises four appendices (7) arranged around the conductive element (1) and electrically connected to said conductive element ( 1) forming a triplate line impedance transformer.
    [0010]
    10. Resonator patch (100) for nuclear magnetic resonance apparatus according to claim 8 characterized in that said resonator comprises four variable capacitors (8), said variable capacitors (8) being positioned along two orthogonal lines (AS1, AS2), said secondary axes, secondary axes (AS1, AS2) having an angular offset of 45 ° with respect to the main axes (AP1, AP2).
    [0011]
    11. Resonator patch (100) for nuclear magnetic resonance apparatus according to claims 9 and 10 characterized in that said variable capacitors (8) are positioned at the intersections of the outer edges of the appendages (7) and the two secondary axes (AS1, AS2 ).
    [0012]
    12.High frequency antenna for nuclear magnetic resonance apparatus characterized in that it comprises a patch resonator (100) according to one of the preceding claims.
    [0013]
    13.High frequency antenna for nuclear magnetic resonance apparatus according to the preceding claim characterized in that the antenna is a multi-channel antenna comprising a plurality of linear resonators having a rectilinear radiating element and / or a plurality of loop resonators comprising a radiating element forming a loop, said radiating elements being used to emit a radiofrequency excitation signal and / or to receive a radiofrequency relaxation signal.
    类似技术:
    公开号 | 公开日 | 专利标题
    EP2921873B1|2020-04-08|Transceiver with circular polarisation for magnetic resonance imaging
    EP0575211B1|1997-12-10|Radiating element of an antenna with wide bandwidth and antenna array comprising such elements
    EP0954055B1|2007-08-22|Dual-frequency radiocommunication antenna realised according to microstrip technique
    EP2656438B1|2015-04-01|Radio cell with two phase states for transmit array
    CA2019181A1|1990-12-20|Diplexing radiating element
    EP0667984B1|1998-07-22|Monopolar wire-plate antenna
    EP2534499B1|2015-04-08|Linear resonator of a high-frequency antenna for a nuclear magnetic resonance imaging apparatus
    FR2623020A1|1989-05-12|DEVICE FOR EXCITATION OF A WAVEGUIDE IN CIRCULAR POLARIZATION BY A FLANE ANTENNA
    EP0209412B1|1989-08-09|High-frequency antenna for an apparatus mesuring nuclear magnetic resonance
    EP2772771B1|2018-02-07|Multi-channel high-frequency antenna, in particular for a nuclear magnetic resonance imaging apparatus
    WO2014202498A1|2014-12-24|Source for parabolic antenna
    FR2537345A1|1984-06-08|HIGH FREQUENCY TUNABLE CIRCUIT, FILTER USING THE CIRCUIT AND METHOD FOR MANUFACTURING THE SAME
    FR3070224A1|2019-02-22|PLATED ANTENNA HAVING TWO DIFFERENT RADIATION MODES WITH TWO SEGREGATED WORK FREQUENCIES, DEVICE USING SUCH ANTENNA
    EP3180816B1|2018-05-02|Multiband source for a coaxial horn used in a monopulse radar reflector antenna.
    EP3400454B1|2020-06-10|Antenna array, in particular for magnetic resonance imaging, comprising linear electromagnetic resonators and at least one decoupling device
    EP3264126B1|2021-06-30|Detunable volume coil for a nuclear magnetic resonance imaging apparatus
    FR3049714B1|2019-09-13|METHOD FOR CONTROLLING RADIOFREQUENCY MAGNETIC FIELD DISTRIBUTION IN A MAGNETIC RESONANCE IMAGING SYSTEM
    EP3942649A1|2022-01-26|Compact directional antenna, device comprising such an antenna
    BE480487A|
    同族专利:
    公开号 | 公开日
    EP2921873A1|2015-09-23|
    US20150253398A1|2015-09-10|
    FR3018361B1|2018-03-09|
    US9880241B2|2018-01-30|
    EP2921873B1|2020-04-08|
    引用文献:
    公开号 | 申请日 | 公开日 | 申请人 | 专利标题
    US20070229076A1|2006-04-04|2007-10-04|Hideta Habara|Coil apparatus and nuclear magnetic resonance apparatus using the same|
    WO2007141505A1|2006-06-09|2007-12-13|Wavetrend Technologies Limited|A patch antenna|
    US4853660A|1988-06-30|1989-08-01|Raytheon Company|Integratable microwave devices based on ferromagnetic films disposed on dielectric substrates|
    US5949311A|1997-06-06|1999-09-07|Massachusetts Institute Of Technology|Tunable resonators|
    WO2007014105A2|2005-07-22|2007-02-01|Tomotherapy Incorporated|Method and system for adapting a radiation therapy treatment plan based on a biological model|
    JP5238715B2|2006-12-22|2013-07-17|コーニンクレッカフィリップスエレクトロニクスエヌヴィ|RF coil used in MR imaging system|
    US8269498B2|2009-05-04|2012-09-18|The Regents Of The University Of California|Method and apparatus for MRI signal excitation and reception using non-resonance RF method |
    KR101541236B1|2014-03-11|2015-08-03|울산대학교 산학협력단|Radio frequency resonator and magnetic resonance imaging apparatus comprising the same|US8970217B1|2010-04-14|2015-03-03|Hypres, Inc.|System and method for noise reduction in magnetic resonance imaging|
    CN105223526A|2015-09-25|2016-01-06|沈阳东软医疗系统有限公司|A kind of radio-frequency sending coil impedance matching circuit and method|
    US10454165B2|2017-12-07|2019-10-22|Lockheed Martin Corporation|Stacked-disk antenna element with shaped wings|
    CN110364810B|2019-07-26|2021-03-30|哈尔滨工业大学|Three-dimensional composite reconfigurable dielectric resonant antenna|
    法律状态:
    2016-03-22| PLFP| Fee payment|Year of fee payment: 3 |
    2017-02-21| PLFP| Fee payment|Year of fee payment: 4 |
    2018-03-29| PLFP| Fee payment|Year of fee payment: 5 |
    2020-03-31| PLFP| Fee payment|Year of fee payment: 7 |
    2021-03-30| PLFP| Fee payment|Year of fee payment: 8 |
    优先权:
    申请号 | 申请日 | 专利标题
    FR1451923|2014-03-10|
    FR1451923A|FR3018361B1|2014-03-10|2014-03-10|CIRCULAR POLARIZATION RECEIVER-RECEIVER FOR MAGNETIC RESONANCE IMAGING|FR1451923A| FR3018361B1|2014-03-10|2014-03-10|CIRCULAR POLARIZATION RECEIVER-RECEIVER FOR MAGNETIC RESONANCE IMAGING|
    EP15158277.2A| EP2921873B1|2014-03-10|2015-03-09|Transceiver with circular polarisation for magnetic resonance imaging|
    US14/643,669| US9880241B2|2014-03-10|2015-03-10|Circularly polarized transceiver for magnetic resonance imaging|
    [返回顶部]