RF Interface circuit for use in magnetic resonance imaging

Abstract: A magnetic imaging apparatus includes an RF coil in electrical communication with an RF signal generator and a receiver through an interface circuit (E). The signal generator transmits resonance excitation signals at one of at least two resonance frequencies, e.g. the resonance frequencies of hydrogen helium 3, fluorine, phosphorous, carbon, or xenon. During the transmit cycle, PIN diode (30) is forward biased forming a filter at a first resonance frequency, electrically isolating the receiver from first frequency excitation signals. Simultaneously during the transmit cycle, PIN diode (32) is forward biased forming a filter at a second resonance frequency electrically isolating the receiver from second frequency excitation signals. During a receive cycle, the diodes are reverse biased turning both filters into low impedance circuits around the first and second resonance frequencies allowing a received magnetic resonance signal to pass unimpeded from the RF coil to the receiver.

Description: The present invention relates to the field of radio frequency interface circuits. The invention finds particular application in interfacing between the transmission and reception of magnetic resonance signals and will be described with particular reference thereto. It is to be appreciated however, that the invention may find further application in other fields in which high power, multiple-frequency radio signals are alternately transmitted and received through a common antenna. Heretofore, magnetic resonance imagers have commonly been used to generate images based on hydrogen nuclei in a subject. Typically, a radio frequency generator generates a high powered RF signal at the resonance frequency of hydrogen which is passed through an interface circuit to an RF coil. The generated RF signals induce magnetic resonance in the hydrogen in an imaged volume. During the passing of the excitation signals, the interface circuit uses quarter wavelength cables, other inductive and capacitive elements, and PIN diodes to create narrow, but effective bandpass filters at the resonance frequency. After excitation, the bias on the PIN diodes is changed such that the narrow bandpass filter becomes a low Impedance interconnection between the RF coil and the receiver. For example, in L. Tropp et al.: "A Dual-Tuned Probe and Multiband Receiver Front End for X-Nucleus Spectroscopy with Proton Scout Imaging in Vivo", Magn. Res. Med. 11 (1989), No. 3, p. 405-412, disclosing an interface circuit according to the preamble of claim 1, an integrated multiband receiver front end comprising probes, diplexers, and receiver protection circuitry is described, designed to permit switching between proton and X-nucleus NMR. Signals from a dual-tuned probe are combined in a low loss passive diplexer and fed to a protection circuit, which utilizes a coaxial cable of three-quarter wavelength at 1 H, to provide simultaneous transmitter/receiver isolation at high band ( 19 F to 1 H) and low band ( 13 C to 31 P) frequencies. Further, in W.-F. Wong et. al. "A Passive Dual-Frequency Transmit-Receive Probe Interface", J. Magn. Res. A 104(1993), No. 3, p. 331-333 a band pass filter is mentioned which is obtained by transforming a low pass filter by replacing the inductor with a series LC circuit and the capacitors with a parallel LC circuit. In this manner a network design in the form of a band-pass or band-reject filter for dual-frequency operation is provided. This filter is only operating at two different frequencies, for instance at proton (100 MHz) and phosphorus (40.5 MHz) frequencies. The present invention is based on an alternative interface circuit useful for multinuclear spectroscopy, considering that there are many paramagnetic nuclei of potential diagnostic interest, such as helium 3, fluorine, phosphorous, carbon, and xenon. At a given magnetic field strength, each of these nuclei have a distinctly different resonance frequency. In accordance with the present invention, a high power, multiple-frequency transmit and receive interface circuit directs transmit signals at one of at least a first selected frequency and a second selected frequency from an RF source input to an RF coil node while isolating an RF receiver junction. The interface circuit includes a first isolation circuit connected with the RF coil for selectively presenting a high impedance to the first frequency in a transmit mode and a low impedance to a first and second frequency in a receive mode. The interface circuit also includes a second isolation circuit connected between the first isolation circuit and the receiver junction, in series with the first isolation circuit, for selectively presenting a high impedance to the second frequency in the transmit mode and a low impedance to the first and second frequencies in the receive mode. In accordance with the present invention, a method of magnetic resonance imaging in which radio frequency resonance excitation signals are generated at at least first and second frequencies is defined in claim 8. The invention provides a multiple-frequency transmit-receive switch. Ways of carrying out the invention will now be described in detail, by way of example, with reference to the accompanying drawings, in which: FIGURE 1 is a diagrammatic illustration of a magnetic resonance imaging apparatus in accordance with the present invention; FIGURE 2 is a circuit diagram of an interface circuit in accordance with the present invention; FIGURE 3 is a circuit diagram of an equivalent circuit when the PIN diodes are forward biased; and FIGURE 4 is an equivalent circuit diagram of the interface circuit when the PIN are reverse biased. With reference to FIGURE 1, a magnetic resonance imaging apparatus includes a main magnetic field generator A for establishing a temporally constant, main magnetic field longitudinally through an examination region. Gradient magnetic field control circuit and coils B selectively produce magnetic field gradients transversely across the main magnetic field of the image region. A magnetic resonance excitation generator, particularly an RF transmitter C , selectively transmits radio frequency resonance excitation and manipulation pulses during a transmit portion of each transmit/receive cycle. The RF transmitter C selects an appropriate transmit frequency based on a desired paramagnetic nuclei to be imaged as entered at an operator interface and controller D . The generated RF pulses are transmitted through a transmit-receive switching circuit (interface circuit) E to an RF coil or antenna F . It is appreciated that antenna F could be a bird-cage coil, some elements from which have been omitted for illustration purposes only. During a receive portion of each transmit/receive cycle, the RF coil F receives magnetic resonance signals from resonating nuclei in an imaged volume of a subject or sample within the examination region. The interface circuit E , which blocks passage of the RF signals to the receiver at the resonance frequencies of all imaged nuclei during transmit portions of the cycle, passes the RF signals received by the antenna F to a receiver G during receive portions of the cycle. An imager H , such as a two-dimensional Fourier transform imaging processor, reconstructs one or more electronic image representations from the received radio frequency resonance signals from the imaged nuclei at two or more resonant frequencies. Typically, the electronic images are representative of density, position, relaxation time, and other characteristics of the resonating nuclei in each voxel of the imaging volume. A video monitor or other display means I converts the electronic image representations to human readable images. Referring now to FIGURE 2, the transmit signal from the RF signal generator C enters the interface circuit E at junction 10. Components in the path between input junction 10 and RF coil junction 12 comprise the transmitter to coil path. A PIN diode 14 and a PIN diode 16 are on, or forward biased during the transmit cycle portions and off, or reversed biased during the receive cycle portions. When biased on during the transmit cycle, the diodes 14 , 16 , along with an inductor 18 , a capacitor 20 , and an inductor 22 form a VHF low-pass filter J and pass all frequencies up to the cut-off frequency with low or no attenuation. On the other hand, when the diodes 14, 16 are biased off during the receive cycle portions, the diodes 14, 16 are equivalent to a small value of capacitance. In this case, a voltage is divided between the diode 14 and the capacitor 20 and between the diode 16 and the low impedance load on the junction 12 offering high attenuation to any low power broadband noise that might be coming from the RF transmitter C . The components in the path between the junction 12 and a junction 24 define a coil to receiver path. As above, PIN diodes 30, 32, 34 are on, or forward biased, during the transmit cycle portion and off, or reversed biased during the receive cycle position. When on in the transmit cycle portion, diode 30, an inductor 36, and a capacitor 38 form a high impedance parallel resonant circuit K at a first selected frequency corresponding to one of the RF transmitter C frequencies. This high impedance prevents transmit power at the first transmit frequency from flowing to the receiver G . Similarly, when on, or forward biased, the diode 32 along with a capacitor 40 , and an inductor 42 form a second parallel resonant circuit L at a second selected transmit frequency of the RF signal generator C . The first circuit K defined by the diode 30 , the inductor 36, and the capacitor 38 is electrically in series with the second circuit L defined by the diode 32, the capacitor 40, and the inductor 42 . This series connection presents a high impedance to the coil node or junction 12 at both transmit frequencies. Transmit power is thus blocked from being delivered to the receiver port or junction 24 . The diode 34 offers additional receiver protection by shorting to ground any small value of transmit power that may have passed through the two tuned circuits. An equivalent circuit, corresponding to the diodes being forward biased, is shown in FIGURE 3 where like components are referenced with like numerals. When the diodes are in the off state during a receive cycle, the diode 30 effectively removes the inductor 36 from the first filter circuit K , and the diode 32 effectively removes the capacitor 40 from the second filter circuit L . The equivalent circuit, shown by reference to FIGURE 4, leaves capacitor 38 and inductor 42 in series to resonate at a frequency between the two parallel resonance frequencies of the transmit cycle portion. Signals at or near this intermediate frequency can pass with low attenuation (i.e. from the coil F to the receiver G ). The operating Q of this circuit E can be quite low and wide band operation is possible. In circuitry beyond the junction 24 , frequency selective preamplifiers (not shown) may be selected by low level PIN diode switches of the conventional design. Cross referencing FIGURES 2 and 4, the series tuned first and second filter circuits L, K can be used in narrow band applications connected directly to a preamplifier at the receiver junction 24 . A preferred embodiment uses the first and second filter circuits K, L as the input stage to a third bandpass filter M defined by a capacitor 50 , an inductor 52 , an inductor 54 , and a capacitor 56 . This allows a much wider spread of frequencies without requiring the capacitor 38 and the inductor 42 to define very low values of reactance. This interface circuit E can be modified to perform over three or more separate transmit frequencies by using these three or more parallel tuned filter circuits in series. It is appreciated that during the receive cycle, the interface circuit E reduces to a single tuned circuit as the input to the receiver G . For efficient use of a DC biasing current, all the PIN diodes are connected in series along a DC path. However, this is not necessary for proper operation of the circuit and alternate diode DC driving circuits are possible. The high power multiple frequency transmit-receive switch described and illustrated above has a number of advantages. One advantage resides in the multiple-frequency operation of the switch. Another advantage resides in employment of discrete components rather than tuned length transmission lines. Another advantage resides in isolating transmitter power from the receiver during the transmit cycle. Another advantage is that it facilitates multinuclear spectroscopy.

Claims: A high power transmit and receive interface circuit (E), which directs transmit signals at one of at least a first selected frequency and a second selected frequency from an RF source input (10) to an RF coil node (12), while isolating an RF receiver junction (24), from both the RF coil node (12), and the RF source input (10), in a transmit mode; and which directs signals around at least the first and second frequencies from the RF coil node (12) to the receiver output (24) in a receive mode, characterized in that the interface circuit comprises: a first isolation circuit (K) connected with the RF coil node (12) for selectively presenting a high impedance to the first frequency in the transmit mode; and a second isolation circuit (L) connected between the first isolation circuit (K) and the receiver junction (24), in series with the first isolation circuit, for selectively presenting a high impedance to the second frequency in the transmit mode, the first and second isolation circuits (K, L) presenting a low impedance to the first and second frequencies in the receive mode. A transmit and receive interface circuit (E) as claimed in claim 1, further including: a bandpass filter (M) connected between the second isolation circuit (L) and the RF receiver junction (24). A transmit and receive interface circuit (E) as claimed in claim 1 or claim 2, further including: a grounding PIN diode (34) connected at one end between the second isolation circuit (L) and the receiver junction (24) and connected at the other end with ground to form an effective short circuit to ground in response to a forward bias, the forward bias being applied in the transmit mode. A transmit and receive interface circuit (E) as claimed in any one of claims 1 to 3, further including: a source input isolation circuit (J) connected between the RF source input (10) and the RF coil node (12) for selectively presenting a high impedance to noise signals in the receive mode. A transmit and receive interface circuit (E) as claimed in claim 4, wherein the source input isolation circuit (J) includes: PIN diodes (14, 16) series across a capacitor (20) to ground, the PIN diodes (14, 16) selectively having a substantially non-conductive state and a substantially conductive state; and an inductor (22) in series with the diodes (14, 16); wherein in the conductive state of the PIN diodes, the PIN diodes (14, 16), the inductor (22) and the capacitor (20) forming a low pass filter; and in the non-conductive state of the PIN diodes, the PIN diodes (14, 16), the inductor (22) and the capacitor (20) forming a voltage divider between (a) one of the diodes (14) and the capacitor (20), and (b) the other of the diodes (16) and the RF coil node (12); the voltage division presenting a high attenuation to a broadband noise signal from the RF source (C). A transmit and receive interface circuit (E) as claimed in any one of claims 1 to 5, wherein the first isolation circuit (K) includes: a first PIN diode (30) selectively having a substantially non-conductive state and a substantially conductive state, a capacitive element (38) and an inductive element (36); the first isolation circuit (K) being equivalent to a capacitor (38) when the PIN diode (30) is biased to the substantially non-conductive state, and being electrically equivalent to a capacitive-inductive (38, 36) tank circuit presenting a high impedance to the first frequency when the PIN diode (30) is in the substantially conductive state. A transmit and receive interface circuit (E) as claimed in any one of claims 1 to 6, wherein the second isolation circuit (L) includes: a second PIN diode (32) selectively having a substantially non-conductive state and a substantially conductive state, a capacitive element (40), and an inductive element (42); the second isolation circuit (L) being equivalent to an inductor (42) when the PIN diode (32) is in the substantially non-conductive state, and being electrically equivalent to a capacitive-inductive (40, 42) tank circuit presenting a high impedance to the second frequency when the PIN diode (32) is in the substantially conductive state. A method of magnetic resonance imaging in which a temporally constant magnetic field is generated through an examination region, radio frequency resonance excitation signals are generated at at least first and second frequencies, the first frequency signals are transmitted into an examination region to induce a magnetic resonance in a first species of nuclei which after termination of the first frequency signals generate first magnetic resonance signals around the first frequency, and the second frequency signals are transmitted into the examination region to induce a second species of nuclei to resonate and generate second magnetic resonance signals around the second frequency, the signals of the first and second frequency being transmitted to a node (12) of an RF coil and the induced first and second magnetic resonance signals being received by said RF coil (F) and processed into at least one electronic image representation, characterized in that (a) in the transmit mode a high impedance is selectively presented to the first frequency by a first isolation circuit (K) connected with the RF coil node, and a high impedance is selectively presented to the second frequency by a second isolation circuit (L) connected between the first isolation circuit (K) and a receiver (G), in series with the first isolation circuit; and (b) in the receive mode a low impedance is presented to the first and second frequencies by the first and second isolation circuits (K, L). A method of magnetic resonance imaging as claimed in claim 8, further including: during receiving of the magnetic resonance by the RF coil: (a) electrically isolating from the receiver (G) any broadband noise signal from the signal generator (C); and (b) passing from the RF coil (F) to the receiver (G) the received magnetic resonance signal substantially unattenuated. A method as claimed in claim 8 or claim 9, further including: chaining a bias on PIN diodes (14, 16, 30, 32, 34) to change between (1) passing resonance signals around the first and second frequencies to the receiver (G) during receiving of magnetic resonance signals and (2) isolating the receiver (G) from receiving the first and second frequency signals during the excitation of resonance.

Inventors: BURL MICHAEL, GAUSS ROBERT C, BURL, MICHAEL, GAUSS, ROBERT C.
Applicants: KONINKL PHILIPS ELECTRONICS NV, KONINKLIJKE PHILIPS ELECTRONICS N.V.
Application year: 1999
Main classification: G01R33
IPC codes: G01R33