Magnetic resonance probes

Abstract: In a magnetic resonance apparatus a patient is subjected to radio frequency signals and the magnetic resonance signals from the patient produced in response to the radio frequency signals are received by a patient head probe (22). The head probe includes an upper probe portion (60) and a lower probe portion (62) which are selectively separable. The upper probe portion has a window (66) of about 90° at the top so the patient can see out easily and feel less claustrophobic. The upper and lower probe portions each include two coil sections (50, 52; 54, 56) connected in series. The coil sections include a plurality of conductor branches (40) connected in parallel around a cylinder. The position of the conductor branches is arbitrarily selected to accommodate the patient window and the like. From the Biot-Savart Law, the current flow through each of the conductor branches is determined. Capacitors C₁, . . .,C n are connected into the current branches such that actual current flow I₀, I₁, . . ., I n through each branch substantially meets the currents specified by the Biot-Savart Law.

Description: This invention relates to magnetic resonance probes. The invention finds particular application in conjunction with probes or coil designs which are not circularly symmetric and will be described with particular reference thereto. However, it is to be appreciated that the invention is also applicable to circularly symmetric probes or coils in which conductor placement is not fully symmetric relative to all axes. NMR probes are most commonly constructed either of wide foil sheets or a small cross section of wire conductors. The foil conductor probes include slotted tube resonators and Adelman-Grant resonators. In foil probes, the current distribution on the foil is determined by electromagnetic laws governing the nature of sheet currents and are not necessarily uniform. The wire type probes are exemplified by saddle coils and loop-type surface coils. Unlike foil probes which provide the designer with relatively little design discretion to adjust current densities, wire probes are readily adjustable. In wire type probes, the designer can shape the current distribution by choosing the proper location for conductors. For example, in saddle coils, angular locations of 120° and 60° have been determined to yield the best transverse uniformity. Hybrid probes in which wire type coils are constructed of foil strips in a saddle, loop, or like configuration, provide a compromise between the advantages of foil type probes and the design flexibility of wire type probes. Previously, many efforts have been made to optimize the field uniformity of NMR probes. The geometries of single turn saddle coils and slotted tube resonators along a circular cylinder have been optimized for various diameters. Multi turn saddle coils provide increased uniformity for low frequency magnetic resonance imaging, but stray capacitive effects limit their utility at higher frequencies. Among the most uniform probes is the bird cage coil illustrated in U.S. Patent Nos. 4,680,548 and 4,694,255. In bird cage coils, a plurality of conductors are mounted longitudinally at equal spacings on the surface of a circular cylinder. Each conductor is interrupted by a capacitor, each of which has the same capacitance. Field uniformity is improved by increasing the number of symmetrically disposed conductors. The amplitude of the parallel conductor currents are weighted as a cosine function which yields an optimum uniformity. This optimum weighting is the result of the symmetrical arrangement of identical longitudinal conductor branches. Another drawback to the bird cage coil resides in the complexity of fine tuning. In order to maintain the symmetry around the circular cylinder, during tuning it is necessary for all capacitors to be adjusted to the same capacitance value. Another approach for optimizing field uniformity is illustrated in US. Patent No. 4,591,818. A plurality of conductors are arranged at spaced positions around a circular cylinder. The conductors, whose positions are mirror imaged about two orthogonal axes, have different cross sections. The conductors are arranged at precise 30° intervals and have different diameters. This difference in conductor diameter changes the relative impedance of the conductors, hence the amount of current flowing therethrough. EP-A-0142 760 discloses an NMR radio-frequency coil having upper and lower coil assemblies. Each coil assembly includes a tuned circuit. In operation only one of the tuned circuits is energized, while the other is mutually inductively coupled such that they resonate together as one circuit at substantially the same frequency. A first set of latches is provided to fasten the lower coil assembly to a patient cradle. A second set of latches is utilized to fasten the upper coil assembly to the lower while permitting relative longitudinal motion between the two assemblies. J.Magn. Res. 63 (1985) pages 622-628 describes radio-frequency coils for high-field head And whole body imaging which achieve near optimal radio-frequency field homogeneity and signal to noise ratio. Biot-Savart law is used to obtain current flows through the conductor branches which optimize radio-frequency field homogeneity by connecting reactances in the branches which are sized in accordance with the self inductance of each conductor branch and the mutual inductances between the conductor branches. According to the present invention there is provided a magnetic resonance probe comprising: first and second coil sections each including at least two conductor branches connected in parallel and a capacitor means (c₁) connected in series with at least one of the parallel connected conductor branches of each section such that the branches of each section have different capacitances to provide them with unequal reactance values for adjusting a ratio of RF magnetics field generating currents between the conductor branches of the first and second coil sections for RF field uniformity, the first and second coil sections being electrically connected and mounted with their branches in parallel geometrical relationship along a surface of a first half cylinder; third and fourth coil sections each of which includes at least two conductor branches connected in parallel and a capacitor means (c₁) connected in series with at least one of the conductor branches of each section such that the conductor branches of each section have different capacitances to provide them with unequal reactance values for adjusting a ratio of RF magnetic field generating currents between the conductor branches of the third and fourth coil sections for RF field uniformity, the third and fourth coil sections being electrically connected and mounted with their conductor branches in parallell geometrical relationship along a surface of a second half cylinder, and an electrical connection coupling for electrically connecting the third and fourth coil sections to the first and second coil sections as the first and second half cylinders are brought together to define a cylinder. One advantage of the present invention is that it provides a practical method for optimizing field uniformity. Another advantage of the present invention is that it facilitates the design of non-uniform and non-circular magnetic resonance probes and coils. Another advantage of the present invention is that it provides non-circular and non-symmetric magnetic resonance probes with improved magnetic field uniformity. Various magnetic resonance probes and a method of fabrication thereof will now be described, by way of example, with reference to the accompanying drawings in which: Figure 1 is a diagrammatic illustration of a magnetic resonance imaging apparatus incorporating a first probe; Figure 2 is a diagrammatic illustration of a radio frequency coil section of which the first probe includes at least one; Figure 3 is a general representation of a second probe with two parallel coil sections; Figure 4 is a representation of a third probe with two series coil sections; Figure 5 is an illustration of a fourth magnetic resonance probe with a combination of series and parallel connected coil sections; Figure 6 illustrates a saddle coil electrical diagram of the first probe of Figure 1; Figure 6A is an end view of the saddle coil of Figure 6; Figure 7 is an enlarged view of the first probe of Figure 1 illustrating the removability of a top portion; Figure 8 is an electrical diagram of the bottom half of the first probe of Figure 1; Figure 9 illustrates a fifth probe which is ideally suited for cervical spin studies; and Figure 10 is an equivalent circuit diagram of the coil section of Figure 2. Referring to Figure 1, a magnetic resonance imaging apparatus includes a magnetic field means A for generating magnetic fields and magnetic field gradients through an image or examination region 10. A plurality of superconducting, resistive, or permanent magnets 12 create a substantially uniform, static magnetic field through the image region. A main magnetic field controller 14 controls superconducting and resistive magnets to optimize field uniformity. Gradient field coils 16 under the control of a gradient field controller 18 selectively cause magnetic field gradients across the image region. Commonly, gradients of selectable slope are selectively applied along one or more mutually orthogonal axes having an apex adjacent a center of the image region. A resonance means B excites, manipulates, and recovers magnetic resonance of selected dipoles within the image region. More specifically, a radio frequency transmitter 20 selectively applies current pulses to a resonator probe 22 to excite selected dipoles in the image region to resonate or to tip or rotate the magnetization of resonating nuclei. The probe 22 functions as an antenna for a radio frequency receiver 24 to receive radio frequency magnetic resonance signals emanating from the resonating nuclei. An image reconstruction means C reconstructs an image representation from the received magnetic resonance signals. A transform means 30 applies a two dimensional inverse Fourier transform or other appropriate transform to each received magnetic resonance signal to generate transformed views. An image memory 32 accumulates the transformed views into an image representation. The completed image representation can be displayed on a video monitor 34 , stored on tape or disk, subject to further processing, or the like. An imaging sequence control means 36 controls the gradient field control means 18 , the radio frequency transmitter 20 , and other circuit components such that the imager implements a selected one of the many known magnetic resonance imaging sequences. With reference to FIGURE 2, the probe 22 includes a coil section that has a plurality n of conductor branches, 40₀ - 40 n . The conductor branches may lie in two or three dimensions. A tuning reactance 42, such as capacitor C t is connected across the feed points 44, 46 of the coil section to adjust the resonant frequency of the coil to the Larmor frequency. The conductor branches include a plurality of reactances 48 , particularly capacitors C₁ - C n . The capacitors are selected so that the current I₀ - I n through each of the branches matches a precalculated current distribution. For a uniform magnetic field, or a magnetic field of other preselected characteristics, the Biot-Savart Law or other known relationships dictates the current flow through each of the conductor branches. Each conductor branch has a self inductance, as well as a mutual inductance with adjoining branches. The reactance of the self and mutual inductances and the capacitors determines the relative current flow through each of the conductor branches. The capacitors C₁ - C n are selected to adjust the reactances of each branch such that the resultant currents I₀ - I n match the currents prescribed by the Biot-Savart Law. With reference to FIGURE 3, two or more coil sections 50, 52 may be connected in parallel to provide more current branches for improved uniformity in the image region. For design simplicity, it is preferred that the two sections have a two fold or planar symmetry. As illustrated in FIGURE 4, two or more coil sections may be connected in series. Again, the sections are preferably arranged with two fold symmetry. With reference to FIGURE 5, four of the coil sections 50, 52, 54, 56 are connected in a combination of parallel and series. More specifically to the illustrated embodiment, two pairs of series connected coils are connected in parallel. For design simplicity, four fold symmetry is preferred. With reference to FIGURES 6 and 7, the probe 22 of the preferred embodiment is a saddle coil with four coil sections 50, 52, 54, and 56. Coil sections 50 and 52 are connected in series as are sections 54 and 56 . The two series connected pairs are connected in parallel about the feed points 44, 46 . In the preferred embodiment, each coil section has two conductor branches through which currents I₀ and I₁ flow. An adjustable capacitor C₁ , is connected with the two conductor branches for adjusting the ratio of the current flow therethrough. Preferably, there is a capacitor in one of the branches or conductors. The capacitor is adjusted to achieve the relative current flow designated by the Biot-Savart Law. Alternatively, the field may be monitored and the capacitor iteratively adjusted until the uniformity of the field within the coil is optimized. The tuning capacitor C t across the feed points adjusts the resonance frequency of the probe. The probe 22 includes two probe portions 60, 62, each of which extends generally around a half cylinder. A pair of electrical connectors 64 interconnect the two probe portions. The top probe portion, which is above the patient's face, is relatively open so as to be less claustrophobic. An open window 66 is defined in the center of the top portion and is open over 90° or more of arc. While window 66 provides openness in front of the patient's face, it's 90° span prevents the eight conductor branches of the preferred embodiment from being arranged symmetrically at like angles around the cylinder. With continuing reference to FIGURE 7 and further reference to FIGURE 8, the top portion 60 of the coil is selectively removable, which enables the lower coil probe portion 62 to function as a neck and cervical spin coil. A reactive module 68 is connected with the connectors 64 in place of the top coil portion 60. The reactive load of the reactive module 68 is selected to present the same reactance to the lower probe segment as the top coil segment presented. The reactive module maintains current continuity, tuning of the coil, and field uniformity without readjustment. In the embodiment of FIGURE 9, two series connected coils sections 70 and 72 are connected across the feed points 44, 46. Each section has three conductors or branches connected in parallel. The capacitors C₁, C₂ are selected such that the current flows I₀, I₁, and I₂ match the current flows predicted to create the optimum field uniformity in the region of interest. Alternately, the capacitors may be adjusted iteratively by monitoring the uniformity of the magnetic field in the region of interest and adjusting the capacitors until the field uniformity is optimized. Looking now to the preferred method for calculating design parameters, the capacitor C t resonates the probe or coil at a frequency ω. In the absence of capacitors in each branch, the ratio between the currents I₀, I₁, . . ., I n would be determined by geometry-dependent branch impedances. The impedance determined current distribution does not necessarily yield a desired field uniformity in the imaging region. To optimize the field uniformity, this method first determines the currents I₀, I₁, . . ., I n which produces the optimum field distribution and then selects the capacitors C₁, C₂ . . ., C n which causes the current to be divided among the branches such that the selected current distribution is achieved. The current distribution is determined by a straight forward application of the Biot-Savart Law. In the case of a circularly cylindrical coil volume, an angular cosine function for the currents yields optimum field uniformity. Numerical optimization techniques may also be utilized in some geometries. With reference again to Figure 2 in which there are n+1 coil branches 40₀ - 40 n , each of the coil branches has a self inductance L n and a mutual inductance with adjoining coils M mn (m ≠ n). The equivalent circuit is illustrated in Figure 10. A ratio α n of the current in the nth branch I n , to the current in the first branch, I₀, is: α n = I n I o The self impedance x n of each branch is: x n = jωL n + 1 jωC n and x o = jωL o The mutual impedance x mn between branches is: x mn = jω M mn (m ≠ n) The impedance x n of the nth branch, when accounting for all of the mutual inductances is then expressed: where N is the total number of branches. The value of the capacitance C n for each branch is determined from Equation (2) to be: C n = 1 jωx n + ω 2 L n After all of the capacitor values are determined, the equivalent impedance of the coil when seen at the feed point X eq is: where V is the voltage at the feed point. Stated in terms of the voltage at the feed point: Thus, for the resonant condition, the impedance of the resonating capacitor should be equal to X eq , hence C t is expressed: Applying this theory, the self and mutual inductances of the coil tranches are measured first without the capacitor C n . The self inductance of each coil is measured with the other branches disconnected, e.g. an open circuit where the capacitor is to be inserted. The mutual inductance M mn between branches m and n can be calculated based on Ohm's Law: M mn = L cmn [ 1- (1- L m + L n L cmn + L m L n ) ½ L cmn 2 ] where L m and L n are self inductances of coils and L cmn is the inductance of the two branches in parallel. By way of example, in the embodiment of FIGURE 6 in which each section has two branches, the capacitance, by Equations 4 and 5, is: C 1 = ω 2 α 1 [α 1 L 1 - L o + M 01 (1-α)] With four fold symmetry, all four sections 50, 52, 54, 56 can be analyzed analogously. In each coil section, the ratio of I₁ to I₀ of an experimental prototype was determined to be α - 0.9 and the angles between the branches were selected as ₁ = 11.3° and ₂ = 44°. The self and mutual inductances for each branch were found to be L₁ = 650 nH, L₂ = 490 nH, and L c01 = 430 nH. From Equation (9), the mutual inductance M₀₁ = 160 nH. The capacitance C₁ is calculated from Equation (10) to be 49 pF.

Claims: A magnetic resonance probe comprising: first and second coil sections (50, 52) each including at least two conductor branches connected in parallel and a capacitor means (c₁) connected in series with at least one of the parallel connected conductor branches of each section such that the branches of each section have different capacitances to provide them with unequal reactance values for adjusting a ratio of RF magnetic field generating currents between the conductor branches of the first and second coil sections for RF field uniformity, the first and second coil sections (50, 52) being electrically connected and mounted with their branches in parallel geometrical relationship along a surface of a first half cylinder; third and fourth coil sections (54, 56) each of which includes at least two conductor branches connected in parallel and a capacitor means (c₁) connected in series with at least one of the conductor branches of each section such that the conductor branches of each section have different capacitances to provide them with unequal reactance values for adjusting a ratio of RF magnetic field generating currents between the conductor branches of the third and fourth coil sections for RF field uniformity, the third and fourth coil sections (54, 56) being electrically connected and mounted with their conductor branches in parallel geometrical relationship along a surface of a second half cylinder, and an electrical connection coupling (64) for electrically connecting the third and fourth coil sections (54, 56) to the first and second coil sections (50, 52) as the first and second half cylinders are brought together to define a cylinder. A probe according to Claim 1, wherein the first and second half cylinders together have an oval cross section and wherein the conductor branches are positioned at unequal angular increments around the cylinder. A probe according to Claim 1, wherein the conductor branches are arranged at unlike angular increments around the first and second half cylinders, the half cylinders defining a window (66) which spans at least 90° and is free of conductor branches. A probe according to Claim 1, wherein the first and second coil sections (50, 52) are connected in series between a pair of probe feed points (44, 46) and the third and fourth coil sections (54, 56) are connected in series between the probe feed points (44, 46) and further including an adjustable tuning capacitor (C t ) connected across the feed points (44, 46) for selectively adjusting a resonance frequency of the probe. A probe according to Claim 1 further including a module (68) that is connectable to the coil sections of the second half cylinder when the first and second half cylinders are electrically separated, the module including a reactive load which presents substantially the same reactance to the coil sections of the second half cylinder as the electrically connected first and second coil sections of the first half cylinder presented, whereby the module maintains current continuity, tuning of the coil sections of the second half cylinder and field uniformity without readjustment when the first and second half cylinders are electrically separated.

Inventors: MEHDIZADEH MEHRDAD, MEHDIZADEH, MEHRDAD
Applicants: PICKER INT INC, PICKER INTERNATIONAL, INC.
Application year: 1990
Main classification: G01R33
IPC codes: G01R33, A61B5