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EP-4742280-A1 - MAGNET APPARATUS WITH COMMUNICATION LINK TO POWER SUPPLY AND ASSOCIATED METHOD

EP4742280A1EP 4742280 A1EP4742280 A1EP 4742280A1EP-4742280-A1

Abstract

An apparatus includes a magnet comprising an electrically superconductive coil adapted to function in a driven mode. A magnet controller (210) is connected to the magnet. A power supply (122) adapted to provide direct current (DC) power to the magnet. An electrical connection is provided between the magnet to provide the DC power to the magnet. A communication interface (206) adapted to communicate signals across the cable between the power supply (122) and the magnet controller (210). The signals between the communication interface (206) and the magnet controller (210) are high-frequency (HF) signals that do not substantially interfere with the DC power transmitted across the cable.

Inventors

  • LIPS, OLIVER
  • FORTHMANN, PETER
  • VERNICKEL, PETER

Assignees

  • Koninklijke Philips N.V.

Dates

Publication Date
20260513
Application Date
20241112

Claims (15)

  1. A superconducting apparatus, comprising: a magnet comprising an electrically superconductive coil adapted to function in a driven mode; a magnet controller (210) connected to the magnet; a power supply (122) adapted to provide direct current, DC, power to the magnet; an electrical connection disposed between the magnet to provide the DC power to the magnet; and a communication interface (206) adapted to communicate signals across a cable between the power supply (122) and the magnet controller (210), wherein the signals from between the communication interface (206) and the magnet controller (210) are high-frequency, HF, signals that do not substantially interfere with the DC power transmitted across the cable.
  2. The superconducting apparatus of claim 1, wherein the HF signals have a frequency of at least 10 kHz.
  3. The superconducting apparatus of claim 1, wherein the HF signals have a frequency in the range of approximately 10 kHz to approximately 100 MHz.
  4. The superconducting magnet of claim 1, further comprising a processor (214) and a tangible non-transitory computer readable medium that stores instructions, which when executed by the processor (214), cause the processor (214) to initiate a connection between the power supply (122) and the magnet to supply the DC power supply (122) to the magnet based on the HF signals indicative of a compatible DC power supply (122).
  5. The superconducting magnet of claim 1, further comprising a processor (214) and a tangible non-transitory computer readable medium that stores instructions, which when executed by the processor (214), cause the processor (214) to prevent a connection between the power supply (122) and the magnet to supply the DC power supply (122) to the magnet based on the HF signals indicative of an incompatible DC power supply (122).
  6. The superconducting magnet of claim 4, wherein after the magnet is functioning in the driven mode, the instructions further cause the processor (214) to initiate a controlled emergency ramp-down of the magnet based on the HF signals indicative of an abnormal condition in the power supply (122).
  7. The superconducting magnet of claim 1, wherein the HF signals are adapted to log information in the magnet controller (210) comprising maintenance information, operational data of the power supply (122), or both.
  8. The superconducting magnet of claim 7, wherein the operational data comprises at least one of: power supply (122) type, maintenance intervals, total hours of operation, temperature, and ripple amplitude.
  9. A magnetic resonance imaging, MRI, device (100), comprising a superconducting apparatus according to any of the claims 1 to 8.
  10. A method (300) of controlling a magnet comprising an electrically superconductive coil adapted to be operated in a driven mode, the method (300) comprising: providing direct current, DC, power to the magnet over a cable between a power supply (122) and the magnet; and communicating signals across the cable between the power supply (122) and the magnet controller (210), wherein the signals from between the communication interface (206) and the magnet controller (210) are high-frequency, HF, signals that do not substantially interfere with the DC power transmitted across the cable.
  11. The method (300) of claim 10, wherein the HF signals have a frequency of at least 10 kHz.
  12. The method (300) of claim 10, wherein the HF signals have a frequency in the range of approximately 10 kHz to approximately 100 MHz.
  13. The method (300) of any of the claims 10 to 12, further comprising initiating a connection between the power supply (122) and the magnet to supply the DC power supply (122) to the magnet based on the HF signals indicative of a compatible DC power supply (122).
  14. The method (300) of any of the claims 10 to 13, further comprising preventing a connection between the power supply (122) and the magnet to supply the DC power supply (122) to the magnet based on the HF signals indicative of an incompatible DC power supply (122).
  15. The method (300) of any of the claims 10 to 14, wherein after the magnet is functioning in the driven mode, the method (300) further comprising initiating a controlled emergency ramp-down of the magnet based on the HF signals indicative of an abnormal condition in the power supply (122).

Description

BACKGROUND Magnetic Resonance Imaging (MRI) devices comprise superconducting magnets used to generate the DC magnetic fields needed for MR imaging. Typical MR magnets comprise main coils and shield coils, with the main coils adapted to generate the main magnetic field and the shield coils adapted to shield the MRI device from stray fields often generated by gradient coils of the MRI device. A large static magnetic field (B0 field or main magnetic field) is used by Magnetic Resonance Imaging (MRI) scanners to align the nuclear spins of atoms as part of the procedure for producing images within the body of a patient. Traditionally MRI scanners have used superconducting coils that have their current ramped up with a power supply and then the power supply is removed. These magnets are operated in the so-called persistent mode. Although additional electrical current is not needed, such magnetic resonance imaging magnets use a cryostat to keep the superconducting windings, and this may be costly. Some newer magnetic resonance imaging magnets use superconducting coils from high temperature superconductors or other materials such as MgB2 which have less stringent cooling requirements. Such magnets may be operated in a so-called driven mode, where amounts of current are continuously supplied to the superconducting coils to maintain the main magnetic field. Overall, these newer magnetic designs have shown to have the potential to reduce the overall operating cost for a magnetic resonance imaging system. In driven mode operation, a power supply remains connected to the superconducting magnet and provides current to the superconducting magnet during operation. As such, the power supply is an essential element of the MR system. Notably, if the function of the power supply is compromised, severely deleterious result can occur. For example, if the power supply fails while the magnet is energized, an undesirable quench of the superconducting magnet can occur. Moreover, a disconnection of the power supply during operation is not desirable and should be avoided. Accordingly, while superconducting magnets configured to function in driven mode show promise for future applications, including applications in the medical field, known systems are deficient in proper safeguards to prevent unintended interruption of power to the superconducting magnet during driven mode operation. What is needed, therefore, is an apparatus that overcomes at least the noted drawbacks of known superconducting magnets adapted to operate in driven mode. SUMMARY In accordance with a representative embodiment, an apparatus, comprises: a magnet comprising an electrically superconductive coil adapted to function in a driven mode; a magnet controller connected to the magnet; a power supply adapted to provide direct current (DC) power to the magnet; an electrical connection disposed between the magnet to provide the DC power to the magnet; and a communication interface adapted to communicate signals across the cable between the power supply and the magnet controller. The signals between the communication interface and the magnet controller are high-frequency (HF) signals that do not substantially interfere with the DC power transmitted across the cable. In accordance with another representative embodiment, a magnetic resonance imaging (MRI) device, comprises: a magnet comprising an electrically superconductive coil adapted to function in a driven mode; a magnet controller connected to the magnet; a power supply adapted to provide direct current (DC) power to the magnet; an electrical connection disposed between the magnet to provide the DC power to the magnet; and a communication interface adapted to communicate signals across the cable between the power supply and the magnet controller. The signals between the communication interface and the magnet controller are high-frequency (HF) signals that do not substantially interfere with the DC power transmitted across the cable. BRIEF DESCRIPTION OF THE DRAWINGS The example embodiments are best understood from the following detailed description when read with the accompanying drawing figures. It is emphasized that the various features are not necessarily drawn to scale. In fact, the dimensions may be arbitrarily increased or decreased for clarity of discussion. Wherever applicable and practical, like reference numerals refer to like elements. Fig. 1 is a simplified schematic diagram of a medical system according to a representative embodiment.Fig. 2 is a simplified schematic diagram of a power supply connected to a magnet controller of a magnet according to a representative embodiment.Fig. 3 is a flow-chart of a method of initiating ramp-up of a magnet in driven mode according to a representative embodiment.Fig. 4 is a flow-chart of a method of checking on a status of a power supply and actions taken by a magnet controller based on the status of the power supply according to a representative embodiment.Fig. 5 is a