Abstract: RF/MRI compatible leads include at least one conductor that turns back on itself at least twice in a lengthwise direction, and can turn back on itself at least twice at multiple locations along its length. The at least one electrical lead can be configured so that the lead heats local tissue less than about 10 degrees Celsius (typically about 5 degrees Celsius or less) or does not heat local tissue when a patient is exposed to target RF frequencies at a peak input SAR of at least about 4 W/kg and/or a whole body average SAR of at least about 2 W/kg. Related devices and methods of fabricating leads are also described.

Abstract: A device with at least one channel for measuring high dynamic range, radio frequency (RF) power levels over broad-ranging duty cycles includes a power sensor circuit comprising at least one logarithmic amplifier; at least one directional RF coupler electrically connected to the at least one power sensor; at least one RF attenuator electrically connected to the at least one RF coupler; and at least one sampling circuit electrically connected to the at least one RF attenuator and the at least one RF coupler. The at least one sampling circuit performs analog-to-digital conversion of electrical signals received to provide digitals signals for measuring the RF power level in the at least one channel.

Abstract: RF/MRI compatible leads include at least one conductor that turns back on itself at least twice in a lengthwise direction, and can turn back on itself at least twice at multiple locations along its length. The at least one electrical lead can be configured so that the lead heats local tissue less than about 10 degrees Celsius (typically about 5 degrees Celsius or less) or does not heat local tissue when a patient is exposed to target RF frequencies at a peak input SAR of at least about 4 W/kg and/or a whole body average SAR of at least about 2 W/kg. Related devices and methods of fabricating leads are also described.

Abstract: MRI/RF compatible leads include at least one conductor, a respective conductor having at least one segment with a multi-layer stacked coil configuration. The lead can be configured so that the lead heats local tissue less than about 10 degrees Celsius (typically about 5 degrees Celsius or less) or does not heat local tissue when a patient is exposed to target RF frequencies at a peak input SAR of at least about 4 W/kg and/or a whole body average SAR of at least about 2 W/kg. Related leads and methods of fabricating leads are also described.

Abstract: RF/MRI compatible leads include at least one conductor that turns back on itself at least twice in a lengthwise direction, and can turn back on itself at least twice at multiple locations along its length. The at least one electrical lead can be configured so that the lead heats local tissue less than about 10 degrees Celsius (typically about 5 degrees Celsius or less) or does not heat local tissue when a patient is exposed to target RF frequencies at a peak input SAR of at least about 4 W/kg and/or a whole body average SAR of at least about 2W/kg. Related devices and methods of fabricating leads are also described.

Abstract: MRI/RF compatible leads include at least one conductor, a respective conductor having at least one segment with a multi-layer stacked coil configuration. The lead can be configured so that the lead heats local tissue less than about 10 degrees Celsius (typically about 5 degrees Celsius or less) or does not heat local tissue when a patient is exposed to target RF frequencies at a peak input SAR of at least about 4 W/kg and/or a whole body average SAR of at least about 2 W/kg. Related leads and methods of fabricating leads are also described.

Abstract: MRI/RF compatible leads include at least one conductor, a respective conductor having at least one segment with a multi-layer stacked coil configuration. The lead can be configured so that the lead heats local tissue less than about 10 degrees Celsius (typically about 5 degrees Celsius or less) or does not heat local tissue when a patient is exposed to target RF frequencies at a peak input SAR of at least about 4 W/kg and/or a whole body average SAR of at least about 2 W/kg. Related leads and methods of fabricating leads are also described.

Abstract: Some embodiments are directed to MRI/RF compatible medical interventional devices. A plurality of spaced apart high impedance circuit segments are configured to have a high impedance at a high range of radiofrequencies and a low impedance at a low range of frequencies. The high impedance circuit segments may comprise co-wound coiled inductors and can reduce, block or inhibit RJ-transmission along the lead system (20) during exposure to RF associated with a high-Held magnet MRI systems, while permuting passage of low frequency physiologic signals, treatments and/or stimuli. The devices can include at least one electrode.

Abstract: A device with at least one channel for measuring high dynamic range, radio frequency (RF) power levels over broad-ranging duty cycles includes a power sensor circuit comprising at least one logarithmic amplifier; at least one directional RF coupler electrically connected to the at least one power sensor; at least one RF attenuator electrically connected to the at least one RF coupler; and at least one sampling circuit electrically connected to the at least one RF attenuator and the at least one RF coupler. The at least one sampling circuit performs analog-to-digital conversion of electrical signals received to provide digitals signals for measuring the RF power level in the at least one channel.

Abstract: Some embodiments are directed to MRI/RF compatible medical interventional devices. A plurality of spaced apart high impedance circuit segments are configured to have a high Impedance at a high range of radiofrequencies and a low impedance at a low range of frequencies. The high impedance circuit segments may comprise co-wound coiled inductors and can reduce, block or inhibit RJ-transmission along the lead system (20) during exposure to RF associated with a high-Held magnet MRI systems, while permuting passage of low frequency physiologic signals, treatments and/or stimuli. The devices can include at least one electrode.

Abstract: Disclosed herein is a magnetic resonance imaging (MRI) device noise dampening system, including an adjustable vibration dampening suspension system arranged between a gradient winding assembly of the MRI device and a support structure supported by a primary magnet assembly of an MRI device, wherein the adjustable vibration dampening suspension system comprises: a plurality of separately inflatable support elements; a vibration reducing material coupled to at least one of a plurality of connecting elements associated with a gradient winding assembly of an MRI device; and/or an acoustic noise absorbing material at least partially filling a space containing a gradient winding assembly of an MRI device.

Abstract: MRI/RF compatible leads include at least one conductor, a respective conductor having at least one segment with a multi-layer stacked coil configuration. The lead can be configured so that the lead heats local tissue less than about 10 degrees Celsius (typically about 5 degrees Celsius or less) or does not heat local tissue when a patient is exposed to target RF frequencies at a peak input SAR of at least about 4 W/kg and/or a whole body average SAR of at least about 2 W/kg. Related leads and methods of fabricating leads are also described.

Abstract: RF/MRI compatible leads include at least one conductor that turns back on itself at least twice in a lengthwise direction, and can turn back on itself at least twice at multiple locations along its length. The at least one electrical lead can be configured so that the lead heats local tissue less than about 10 degrees Celsius (typically about 5 degrees Celsius or less) or does not heat local tissue when a patient is exposed to target RF frequencies at a peak input SAR of at least about 4 W/kg and/or a whole body average SAR of at least about 2 W/kg. Related devices and methods of fabricating leads are also described.

Abstract: The present invention provides an apparatus for reducing acoustic noise in a magnetic resonance imaging device including passive shielding located outside the actively shielded gradient winding elements in order to reduce the magnitude of fields that spread outside the gradient coil assembly in unwanted directions and interact with the magnet cryostat or other metallic magnet parts, inducing eddy currents that cause consequent acoustic noise. The passive shielding elements are conducting layers located on the outer radius of the cylindrical gradient coil assembly in a cylindrical magnet system, conducting layers located at the ends of the gradient coil assembly in a cylindrical magnet system, and conducting layers located inside the actively shielded gradient winding inner elements in a cylindrical magnet system. The passive shielding could also be located on separate structures that are vibrationally isolated from the magnet cryostat.

Abstract: The present invention provides an apparatus for reducing acoustic noise in a magnetic resonance imaging device including passive shielding located outside the actively shielded gradient winding elements in order to reduce the magnitude of fields that spread outside the gradient coil assembly in unwanted directions and interact with the magnet cryostat or other metallic magnet parts, inducing eddy currents that cause consequent acoustic noise. The passive shielding elements are conducting layers located on the outer radius of the cylindrical gradient coil assembly in a cylindrical magnet system, conducting layers located at the ends of the gradient coil assembly in a cylindrical magnet system, and conducting layers located inside the actively shielded gradient winding inner elements in a cylindrical magnet system. The passive shielding could also be located on separate structures that are vibrationally isolated from the magnet cryostat.

Abstract: The subject invention relates to a method and apparatus for producing stimulated MRI data. In an embodiment, a remote-controlled “smart phantom” can produce simulated data. The simulated data can be acquired from a MRI system. The subject device can generate control signals and send the generated control signals to secondary coils/probes placed in the subject smart phantom. The control signals determine the current flow in the secondary coils/probes, which act as local spin magnetization amplifiers and thus produce regions of variable contrast to noise ratio. The control signals can be generated with various parameters, such as BOLD models, different levels of contrast-to-noise ratio (CNR), signal intensities, and physiological signals. Comparisons can be made with the widely-used simulated data by computers. Validation of the subject smart phantom can be performed with both theoretical analysis and data of human subjects.

Abstract: The subject invention relates to a method and apparatus for producing stimulated MRI data. In an embodiment, a remote-controlled “smart phantom” can produce simulated data. The simulated data can be acquired from a MRI system. The subject device can generate control signals and send the generated control signals to secondary coils/probes placed in the subject smart phantom. The control signals determine the current flow in the secondary coils/probes, which act as local spin magnetization amplifiers and thus produce regions of variable contrast to noise ratio. The control signals can be generated with various parameters, such as BOLD models, different levels of contrast-to-noise ratio (CNR), signal intensities, and physiological signals. Comparisons can be made with the widely-used simulated data by computers. Validation of the subject smart phantom can be performed with both theoretical analysis and data of human subjects.

Abstract: The present invention provides an apparatus for reducing acoustic noise in a magnetic resonance imaging device including passive shielding located outside the actively shielded gradient winding elements in order to reduce the magnitude of fields that spread outside the gradient coil assembly in unwanted directions and interact with the magnet cryostat or other metallic magnet parts, inducing eddy currents that cause consequent acoustic noise. The passive shielding elements are conducting layers located on the outer radius of the cylindrical gradient coil assembly in a cylindrical magnet system, conducting layers located at the ends of the gradient coil assembly in a cylindrical magnet system, and conducting layers located inside the actively shielded gradient winding inner elements in a cylindrical magnet system. The passive shielding could also be located on separate structures that are vibrationally isolated from the magnet cryostat.

Abstract: The subject invention relates to a method and apparatus for producing stimulated MRI data. In an embodiment, a remote-controlled “smart phantom” can produce simulated data. The simulated data can be acquired from a MRI system. The subject device can generate control signals and send the generated control signals to secondary coils/probes placed in the subject smart phantom. The control signals determine the current flow in the secondary coils/probes, which act as local spin magnetization amplifiers and thus produce regions of variable contrast to noise ratio. The control signals can be generated with various parameters, such as BOLD models, different levels of contrast-to-noise ratio (CNR), signal intensities, and physiological signals. Comparisons can be made with the widely-used simulated data by computers. Validation of the subject smart phantom can be performed with both theoretical analysis and data of human subjects.

Abstract: The present invention provides an apparatus for reducing acoustic noise in a magnetic resonance imaging device including a suspension element including at least one resilient element and an active drivable element for applying a compensating force to reduce vibration transmission. The active drivable element is positioned so as to not directly support the weight of the gradient coil assembly, which avoids applying strong forces to relatively fragile active drivable elements, such as piezoelectric force transducers. Force signals for the active drivable element are derived in a feed-forward manner from the applied gradient waveform or from motion of the gradient coil assembly bracket. Alternatively, the active drivable element can be driven by signals derived from measured vibration or other motion of parts of the MRI magnet, gradient coils or rf coils.