Patent Description:
Magnetic resonance imaging (MRI) systems are sometimes combined with another diagnostic system, such as a positron emission tomography (PET) system. These hybrid systems allow to acquire additional information, in particular without the need to reposition a patient in between different measurements, e.g. in between MRI and PET measurements. Hence it is possible to conduct examinations simultaneously or with only little time delay. This may be beneficial for some examinations, e.g. concerning cardiologic or neurological aspects. While providing two systems in one place can be beneficial, additional problems arise because of interferences between the different systems or between the components of the different systems. In particular, local radiofrequency (RF) coils of an MRI systems may disturb the measurement with another system. For example, a PET signal may be attenuated by local RF coils. This problem tends to increase when a lot of electronic components are comprised by the local RF coils of the MRT system.

In the state of the art, there are attempts to correct these attenuated signals after the measurement. One option is to generate an attenuation map of the coils, e.g. with a Computed Tomography (CT) scanner, in order to calculate and correct the attenuation of the PET signals. While those attenuation maps may be generated before the actual measurements, a problem arises with flexible surface coils which may be positioned more or less at any position on the patient. Hence the position of the local coils must be determined, possibly before each measurement. It has been proposed to use markers built into the coil in order to help detecting the coil via MRI or another measuring means, such as PET, infrared cameras or ultrasonic sensors. However, none of these solutions has been successfully implemented yet without giving rise to further disadvantages. In particular, markers that are detectable by MRI have the disadvantage that they are also visible during an MRI examination. This may lead to false or less reliable diagnoses, e.g. due to aliasing artefacts.

For example, <NPL>, describe the concept of a markers-based localization. However, they come to the conclusion that the current implementation is not an ideal technique due to the interference of the these "fiducial markers" with the MR images.

<CIT> discloses a magnetic resonance imaging system comprising an RF coil provided with a plurality of fiducial markers that are configured for emitting magnetic resonance signals and a method to suppress magnetic resonance signals emitted from one or more fiducial markers.

<CIT> discloses an RF coil for a magnetic resonance imaging system with multiple markers allowing selective activation of one or more markers based on a scan prescription or configuration file.

It is therefore an object of the invention to provide an MRI-PET system, wherein the problem of local coils being in the way of a measurement with the PET measurement method can be accounted for without significantly disturbing the MRI measurement.

This object is achieved by an MRI-PET system according to claim <NUM>.

According to a first aspect of the invention, an MRI-PET system, consisting in an MRI system combined with a PET system, is provided. The MRI-PET system comprises at least one local RF coil and at least one marker element, wherein the MRI-PET system and the marker element are configured such that the at least one marker element may be activated to be detectable by the MRI system at a predetermined position relative to the coil, wherein the MRI-PET system and the marker element are configured such that the at least one marker element may be deactivated not to be detectable by the MRI system. The MRI-PET is a hybrid system, namely an MR system combined with a positron emission tomography (PET) system. Any further reference to an/the MRI system corresponds to an/the MRI system of the MRI-PET system according to the invention. A "local RF coil" is in particular a receive coil or receive/transmit coil, which is not integrated into the bore of the MRI main magnet, but which is placed close to the body part to be examined just before the MRI examination. The local RF coil is often interchangeable, depending on the body part to be examined. In the context of this invention the local RF coil may also be referred to as "coil". The coil may be a flexible surface coil, which can be placed at various regions with respect to the MRI scanner and/or the patient. Advantageously, the marker element may allow to determine the position of the coil and thus to predetermine its influence on the measurement of another measuring system, here the PET system. In the case of a PET system, the attenuation effect of the coils (the position of which is determined via the marker element) on a PET measurement may be calculated in order to subtract this effect from the data and/or adjust the PET measurement accordingly. A review of methods to apply such an attenuation correction in the case of MRI-PET systems is described for example in<NPL>.

The MRI-PET system is in particular configured to determine the position of the at least one coil based on the activated marker element, in particular by taking an MR image of a scan area including the marker element. Preferably, during this measurement the coil and relative to it the marker element, i.e. placed in a predetermined position relative to the coil, may be placed in essentially the same position as later during a diagnostic measurement. The marker element may for example be attached to the coil, integrated into the coil and/or be arranged at least partially around the coil. In contrast to the state of the art, the inventive system takes care of the problem that the marker element might influence an examination via the MRI-PET system by providing a marker element that can be deactivated. The MRI-PET system may preferably be configured to deactivate the marker element prior to executing a diagnostic MRI measurement. Thus, the marker element will not or will barely have any influence on the MRI diagnostic measurement due to being invisible to the MRI scanner. The MRI-PET system may be configured to automatically deactivate the marker element and/or to deactivate the marker element based on user input. The marker element may for example be deactivated by removing it from the coil and/or the MR field of view, by shielding it against high frequency radiation and/or by destroying the phase coherence of the signal of an MR visible substance of the marker element.

According to an embodiment, the marker element may comprise a magnetic resonance (MR) visible substance, such as a magnetic resonance visible fluid, in particular liquid, and/or a magnetic resonance visible solid substance. The MR visible substance may for example comprise water, an aqueous solution, silicone, synthetics, or a gas such as xenon or fluor. A low TR may be particularly advantageous, since it may enable fast T1 weighted MR imaging. Thus, a measurement for the localisation of the at least one coil can be relatively fast, i.e. the time needed for non-diagnostic scans may be short. The solid substance may preferably be soluble in an imaging fluid, such as water, have a low TR and/or have a high susceptibility. For example, the solid substance may be or may comprise a lanthanide, in particular Gadolinium. Gadolinium is also commonly used in MR contrast agents. However, the marker element may also comprise a water solution containing another substance. Possible substances may for example be a compound containing iron, such as iron sulphate iron chloride, iron bromide, iron iodide, iron nitrate, chemical compounds containing nickel, cobalt and/or chromium such as chromium sulphate, chromium chloride, nickel sulphate and/or cobalt sulphate, and/or non-metal compounds, in particular salts, such as neodymium sulphate. Iron sulphate, for example, may be cheaper than Gadolinium while advantageously providing comparable results concerning MR contrast for fast 3D MR measurements, due to having a comparable susceptibility. The susceptibility may be adapted by varying the concentration of the substance, in particular iron sulphate, in the water solution, i.e. between <NUM> and saturation at <NUM>/l at <NUM> for iron sulphate. In particular the concentration may be adapted with respect to image contrast, needing high concentration, and low magnetic flux (B0) distortion close to the marker element, needing low concentration.

According to an embodiment, the MRI-PET system may comprise a relocation system configured to relocate the marker element with respect to the coil and/or the MRI-PET system, wherein the relocation system is configured to deactivate the marker element by removing it from the coil and/or from the field of view of the MRI system and to activate the marker element by moving it to a predetermined position in the proximity of the coil or inside the coil. In particular the system may be configured to remove the marker element prior to a diagnostic MR scan. The relocation system may comprise a cable mechanism and/or a fluid pump system configured to relocate the marker element. Advantageously, the relocation system may allow to provide a way of removing the marker element from the field of view of the MRI system and thus ensuring that it is undetectable by the MRI system. Hence, the marker element may be deactivated with respect to the MRI system by removing it from the area to be imaged.

Advantageously, the relocation system may comprise a fluid conducting element, in particular a tube, and a fluidic pump, wherein the marker element comprises a magnetic resonance (MR) visible fluid, in particular liquid, wherein the fluid conducting element is configured such that a first part of the fluid conducting element is arranged at or within the coil and a second part of the fluid conducting element is arranged outside of the detectable area of the MRI system, wherein the fluidic pump is configured to move the magnetic resonance visible fluid from the first part into the second part and vice versa. The fluid conducting element, in particular its second part, may at least partially be positioned within a patient table of the MRI-PET system. The second part may preferably be positioned at least <NUM> outside of the iso center of the MRI-PET system. In particular, the second part may, for example, be positioned at the foot end of the patient table. The first part of the fluid conducting element may be positioned close by all components of the coil and optionally of other components outside the coil which are relevant with respect to the attenuation of PET signals. Relevant components may for example be at least one pre-amplifier and/or at least one braid-breaker. The MR visible fluid may be a fluid and/or a solution as described above. The fluidic pump may be configured to move the MR visible fluid based on overpressure (positive pressure) and/or underpressure (negative pressure). The fluid conducting element may at least partially be filled with the MR visible fluid. In this case the marker element may comprise the MR visible fluid along its whole distribution within the fluid conducting element. The marker element in the form of the MR visible fluid may appear as a 3D network marking all relevant components of the coil and/or attached to the coil. The 3D network may for example have the shape of a spiral or a meandering shape or any other shape which is expedient to mark the relevant components. Alternatively, the MR visible fluid may be contained in at least one capsule, in particular a capsule as described below, preferably a plurality of capsules, which are positioned inside the fluid conducting element. The fluid conducting element may further contain a guiding fluid, e.g. compressed air with positive and/or negative pressure. The pump may be configured to move the at least one capsule via manipulation of the guiding fluid, wherein the pump may in particular push and/or pull the at least one capsule within the fluid conducting element via the guiding fluid in between the first and the second part of the fluid conducting element.

According to an embodiment, the MRI-PET system may comprise a tube connector. An outside part of the fluid conducting element, in particular comprising the first part, may be attached to the coil and comprise a fluid plug, wherein the fluid plug is configured to be plugged into the tube connector. Preferably, the tube connector may comprise a locking means, configured to lock the tube connector to the fluid plug, in particular when fluid is in the first part of the fluid conducting element. The locking means may comprise a bolt configured to lock the tube connector and the fluid plug. The MRI-PET system, in particular at the tube connector and/or at the fluid plug, may comprise an activating means, e.g. a push button, wherein the MRI-PET system is configured, as a reaction to the push button being pushed, to activate the fluidic pump such that the MR visible fluid is pumped out of the outside part of the fluid conducting element and the locking means is unlocked afterwards such that the fluid plug can be unplugged. Advantageously the locking means can thus prevent leakage of fluid when disconnecting the outside part of the fluid conducting element. The tube connector and/or the fluid plug may comprise a connecting valve, configured to prevent leakage of fluid when the tube connector and the fluid plug are not connected to each other.

According to an embodiment, the coil may comprise at least one ceramic element arranged around at least one electronic component of the coil, wherein the ceramic element may comprise at least one fluid channel connected to the fluid conducting element, wherein the magnetic resonance visible fluid is configured to work as a cooling fluid, wherein the fluidic pump is configured to move the magnetic resonance visible fluid through the at least one fluid channel. The fluid channel may be considered to be part of the fluid conducting element. Thus "connected to the fluid conducting element" may be interpreted to mean "connected to the part of the fluid conducting element not being part of the fluid channel of the ceramic element". In particular the fluid channel may be the first part or a portion of the first part of the fluid conducting element. Preferably the ceramic element is thermally conductive. The ceramic element may for example be made of at least epoxy resin and ceramic powder. The ceramic powder may comprise aluminium nitride, boron nitride and/or silicon carbide. Such a ceramic element may, for example have a thermal conductivity of up to about <NUM> W/mK. Alternatively, the ceramic element may be a sintered ceramic form. The thermal conductivity may thus reach up to about <NUM> W/mK. The at least one electronic component may be an electronic board, a pre-amplifier, a diode, in particular PET diode, an electronic choke and/or a capacitor. Advantageously, the MR visible fluid may thus also serve as a cooling agent. The MRI-PET system may for example be configured to apply a cooling process via the MR visible fluid running through the fluid channel of the ceramic element in measurement breaks and/or during localisation of the coil position via the MR visible fluid. In addition, the ceramic element may serve to improve the PET imaging. Electronic components, due to having high electron densities and small overall sizes often appear as sharp and highly visible spots in a PET image. Due to the ceramic element, the electron density in between the components is also increased and thus spots will advantageously appear less sharp as compared to an embodiment without the ceramic element. Instead, a uniform background may be created, which does not disturb the overall PET image as much as single sharp spots. According to a preferred embodiment, the edge areas of the ceramic element may be thinner than the central area of the ceramic element. This may lead to the electron density decreasing towards the edge of the ceramic element, further leading to less pronounced edges in the PET image. At least one temperature sensor may be located at the at least one component and/or at blocks of components and/or at the ceramic element. The MRI-PET system may be configured to control a cooling process of the electronic component(s) using the temperature sensor.

According to an embodiment, the MRI-PET system may comprise a cable mechanism configured to activate and deactivate the at least one marker element. The cable mechanism may be configured to pull the marker element in and out of the field of view of the MRI scan area. Alternatively, the cable mechanism may be configured to move a shielding element which is configured to shield the marker element from a shielding position to a non-shielding position and vice versa. The MRI-PET system comprising the cable and/or hauling mechanism according to any embodiment described herein may further comprise a tube through which the cable and/or the marker elements are guided. The tube may preferably be flexible, e.g. be a hose. The tube may be separable and connectable, wherein a coil portion of the tube is attached to the coil and a base portion comprises a cable connector, wherein the coil portion comprises a cable plug connectable or connected to the cable connector. The cable may be separable into two parts, wherein the two parts are connectable to each other. For example, both parts may comprise hooks configured to enable a connection of the two parts. The MRI-PET system may be configured to enable a separation of the tube portions, wherein one part of the cable may remain in the coil portion of the tube and the other part of the cable may remain in the base portion when the tube parts are disconnected from each other. According to an embodiment the MRI-PET system may comprise a hauling mechanism, in particular a cable mechanism, wherein the hauling mechanism is configured to move the at least one marker element with respect to the coil and/or in and out of the detectable area of the MRI-PET system in order to activate and deactivate the at least one marker. Preferably, the hauling mechanism may comprise a movable cable extending from the coil to an area outside of the detectable area of the MRI system, wherein the at least one marker element is attached to the cable such that it can be moved between the coil and the area outside of the detectable area of the MRI system via the cable. Preferably, a plurality of marker elements may be attached to the cable. Different marker elements may be configured to mark different electronic components of the coil, in particular at a predetermined distance with respect to each other. The cable may consist of polyamide fibres, preferably synthesized polyamide fibres, more preferably aramid fibres. The cable may comprise a first part onto which marker elements, in particular capsules containing an MR visible fluid, are attached, and a second part onto which no marker elements are attached to. The MRI-PET system may be configured to activate the marker elements by pulling the first part of the cable into or at a position adjacent to the coil and to deactivate the marker elements by pulling the first part of the cable to the area outside of the detectable area of the MRI system. In a deactivated state of the marker elements, the second part of the cable may be positioned at and/or in the coil. The hauling mechanism may partially be located inside the patient table, in particular the area outside the detectable area of the MRI system may at least partially be inside the patient table. The cable may be separable into two parts, in particular the first part and the second part, wherein the two parts are connectable to each other.

According to an embodiment, the MRI-PET system may comprise an MR compatible motor configured to drive the cable mechanism and/or the hauling mechanism as described herein. An MR compatible motor is in particular a motor that can be used while a magnetic field created by the MRI-PET system is activated. The motor may be built into the patient table. The MRI-PET system may further comprise a control unit configured to control the MR compatible motor.

According to an embodiment, the at least one marker element may be a capsule containing a magnetic resonance (MR) visible fluid, in particular liquid. The capsule may be attached to the cable of the cable mechanism. The capsule may be made of glass and/or plastic. The capsule may have the shape of an ellipsoid or of a cuboid, in particular a rectangular cuboid, or of a cylinder. The capsule may have a diameter of <NUM> to <NUM> and a length of about <NUM> to <NUM>. The MR visible liquid may in particular be the MR visible liquid as described above. A capsule may be an easy and reliable way of providing an MR visible fluid for a marker element, which may in particular be flexible with respect to the arrangement and positioning of the fluid.

According to an embodiment, the MRI-PET system may comprise a shielding element, wherein the shielding element is adjustable, in particular movable and/or activatable, in such a way that it can be in a shielding mode to shield the marker element from RF radiation and/or from detection by the MRI system and be in a non-shielding mode to allow detection of the marker element by the MRI system and/or such that the marker element is not shielded from RF radiation. The MRI-PET system may be configured to activate the shielding element during a diagnostic scan. The marker element may be fixed at its position, in particular within the coil. The shielding element may be made of carbon fibres. This may be advantageous compared to other options such as the shielding element being made of copper, since copper or other metals tend to enable eddy currents and have strong PET damping properties. Carbon fibres, on the other hand, tend to be mostly transparent for PET measurements and have no significant eddy currents compared to eddy currents in metals. The shielding element may be a tube and/or have the shape of a tube. Preferably the shielding element may have the same geometrical shape as the marker element, wherein the inner diameter and/or inner volume is greater than the outer diameter and/or outer volume of the marker element. The shielding element may have a wall thickness no more than <NUM>, in particular of <NUM>,<NUM> to <NUM>, preferably of <NUM>,<NUM> to <NUM>. Advantageously, a shielding element with such a thickness may be basically transparent with respect to PET measurements.

According to a preferred embodiment, the shielding element may permanently enclose the marker element and be activatable, wherein the shielding element is configured such that it shields the marker element when it is activated and does not shield the marker element when it is deactivated. The shielding element may be installed immovably around the marker element and/or inside or around the coil. The shielding element may be configured such that its RF damping is electronically controllable. The MRI-PET system may comprise a control unit configured to control the RF damping of the shielding element electronically. The shielding element may comprise at least one temperature-dependent resistor, preferably a plurality of temperature-dependent resistors, in particular a negative temperature coefficient thermistor or a positive temperature coefficient thermistor. In particular a network of temperature-dependent resistors may be arranged around the marker element. The conductivity of the shielding element may be controlled via controlling the temperature of the temperature-dependent resistor and/or of the shielding element. The MRI-PET system may comprise a heating element, in particular made from carbon, and/or a cooling circuit configured to control the temperature of the temperature-dependent resistor and/or of the shielding element.

According to the invention, the MRI-PET system comprises a, in particular movable, shielding element, wherein the shielding element is movable in such a way that it can be moved into a shielding position and into a non-shielding position and/or wherein the marker element is movable in such a way that it can be moved into a shielding position and into a non-shielding position, wherein the shielding element encloses the marker element such that the marker element is shielded from the MRI-PET system and/or from RF radiation when the shielding element and/or the marker element is in the shielding position, and wherein the shielding element is apart from the marker element such that the marker element is detectable by the MRI system and/or not shielded from RF radiation when the shielding element and/or the marker element is in the non-shielding position. The shielding element may in particular be slidable over the marker element and/or the marker element may be slidable into the shielding element. Using a shielding element may in particular be advantageous since no PET visible components and no electronic components or electronic lines need to be used. Thus, the shielding element may be neutral with respect to magnetic resonance measurements as well as to PET measurements. The range of movement of the shielding element and/or of the marker element may correspond to and/or be essentially equal to the length of the marker element in the direction of movement of the shielding element and/or marker element. The shielding element may be dimensioned such that its inner dimensions are slightly larger than the outer dimensions of the marker element, in particular such that there is a gap of about <NUM>,<NUM> to <NUM>,<NUM> between the shielding element and the marker element when the shielding element encloses the marker element.

According to an embodiment, the MRI-PET system may comprise an air pressure chamber and a fluid conducting element, in particular an air hose or air tube, connected to the air pressure chamber, wherein the shielding element and the marker element are arranged inside the air pressure chamber, wherein the air pressure chamber and the shielding element are configured such that the shielding element is movable by air pressure provided via the fluid conducting element. The MRI-PET system may comprise a pump and a control unit configured to control the air pressure inside the fluid conducting element and the air pressure chamber. The control unit may be configured to control the air pressure such that the marker element is shielded and thus deactivated during a diagnostic scan and non-shielded and thus activated for determining the position of the coil. The control unit and the pump may be configured to control movement of the shielding element by providing overpressure and/or underpressure inside the air pressure chamber via the fluid conducting element. For example, moving the shielding element over the marker element may be achieved by overpressure while moving the shielding element away from the marker element may be achieved by underpressure or vice versa. The air pressure chamber may comprise a first portion and a second portion. An air inlet connected to the fluid conducting element may be arranged in the first portion. An air outlet may be arranged in the second portion. Preferably the shielding element may at least partially be arranged inside the air pressure chamber movably in between the air inlet and the air outlet and/or in between the first portion and the second portion. The shielding element and the air pressure chamber may be configured such that positive air pressure in the first portion pushes the shielding element towards the second portion and over the marker element. The marker element may be positioned in the second portion and/or at any position suitable to allow pushing the shielding element over the marker element via the air pressure. The shielding element and the air pressure chamber may be configured such that negative air pressure in the first portion pulls the shielding element back towards the first portion and away from the marker element. Equivalently, the shielding element and the air pressure chamber may be configured such that positive air pressure in the first portion pushes the shielding element towards the second portion and away from the marker element. The marker element may thus be positioned in the first portion and/or at any position suitable to allow pushing the shielding element away from the marker element via the air pressure. The shielding element and the air pressure chamber may be configured such that negative air pressure in the first portion pulls the shielding element back towards the first portion and over the marker element. The air outlet may be configured to balance the air pressure in the second portion, in particular when the shielding element is moved. According to an alternative embodiment, the shielding element may be fixed and the marker element may be movable via air pressure according to the above description. According to a further embodiment, both the marker element and the shielding element may be movable, in particular towards and away from one another, according to the above description.

Preferably the MRI-PET system may further comprise a tube connector and a fluid plug, in particular as described above. The tube connector may comprise an air socket and the fluid plug may be configured to engage with the air socket such that no or only little compressed air is lost. A locking means as described above is an option here as well. However, it may not be necessary for this embodiment, since the used pressure may be relatively low and further security measures may thus not be required.

According to an embodiment, the MRI-PET system may comprise a cable mechanism, wherein the cable mechanism is configured to move the shielding element from the shielding position to the non-shielding position and/or vice versa. The cable mechanism may comprise a cable, in particular made of aramid fibre, which is connected to the shielding element. The cable mechanism may comprise a tube or hose, in particular made of plastic, within which the cable is guided. The cable according to the invention may in particular be a rope or pull rope. The MRI-PET system may further comprise a spring, in particular a non-magnetic spring, configured to move the shielding element to the shielding position or to the non-shielding position. Accordingly, the cable mechanism may be configured to move the shielding element against the force of the spring. For example, the spring may pretension the shielding element in the shielding position and the cable mechanism may be configured to pull the shielding element into the non-shielding position when the position of the coil is to be determined. The cable mechanism may comprise an MR compatible motor, in particular as described above, a rotary shaft driven by the motor, an eccentric connected to the rotary shaft, a bolt movable by the eccentric, and a lever movable by the bolt. The eccentric may be configured such that a rotation of the rotary shaft drives the bolt which in turn flips the lever and a further rotation drives the bolt further such that the lever flips back. The lever may be connected to the cable in such a way that flipping the lever pulls the cable and thus pulls the shielding element connected to the cable while flipping the lever back loosens the cable, in particular enabling the spring to pull the shielding element back into its original position.

According to an embodiment, the MRI-PET system may comprise an ultrasound emitter, wherein the ultrasound emitter may in particular be arranged adjacent to the marker element, wherein the ultrasound emitter is configured to provide ultrasound waves at the marker element in order to deactivate the marker element with the ultrasound waves, in particular by destroying phase coherence in the marker element. It has been shown that ultrasound waves can influence the nuclear spin and MRI (Meinert Lewerenz: "Signalerhöhung durch Ultraschall in der Magnetresonanztomographie", Diplomarbeit, Mathematisch-Naturwissenschaftliche Fakultät der Rheinischen Friedrich-Wilhelms-Universität Bonn, November <NUM> and Ole Benjamin Oehms: "Wechselwirkung des Kernspinsystems mit Ultraschall in einfachen Flüssigkeiten", Diplomarbeit, Mathematisch-Naturwissenschaftliche Fakultät der Rheinischen Friedrich-Wilhelms Universität Bonn, Mai <NUM>). In particular, using an appropriate frequency of ultrasound waves may destroy the MR phase coherence of the spins. Accordingly, ultrasound waves may temporarily turn the marker element invisible for MRI. The ultrasound emitter may for example comprise a piezo crystal. The MRI-PET system may comprise a control unit configured to control the ultrasound emitter. This control unit and other control units described herein may be the same control unit or may be different control units. The control unit may be connected to the ultrasound emitter via at least one control line, preferably two control lines. Additionally or alternatively, the ultrasound emitter may be digitally controlled via an inter-integrated circuit (I<NUM>C) and/or a serial peripheral interface (SPI).

According to an embodiment the MRI-PET system may further comprise at least one additional marker element and at least one braid-breaker, wherein the braid-breaker is in particular positioned along a connecting cable of the coil, wherein the MRI-PET system and the marker element are configured such that the at least one additional marker element may be activated to be detectable by the MRI system at a predetermined position relative to the braid-breaker, wherein the MRI-PET system and the additional marker element are configured such that the at least one additional marker element may be deactivated not to be detectable by the MRI system. A braid-breaker is in particular a shielding element that shields of the MR signal from the marker element. The braid-breakers may comprise a RF shield. Preferably the system may comprise a plurality of braid-breakers and a plurality of corresponding marker elements. More preferably the system may comprise two marker elements for each braid-breaker, wherein the marker elements may in particular be positioned on opposite sites adjacent to the braid-breaker, preferably before and behind the braid-breaker along the cable of the coil. The braid-breakers may for example be positioned at the cable at intervals of <NUM> to <NUM>. It is also conceivable to provide the at least one additional marker element for the at least one braid-breaker independently of the at least one marker element for the coil. Braid-breakers usually have a relatively high electron density, which may lead to a strong PET damping. This embodiment may thus allow to determine the position of the at least one braid-breaker along the cable of the coil. The RF shield of the at least one braid-breaker may be made of carbon fibre. This may be advantageous since a braid-breaker made of carbon is less visible for PET (though usually still visible due to its thickness) than usual braid-breaker materials, such as copper, while still being able to providing RF shielding.

Embodiments of the invention are now described with reference to the attached figures. Similar or corresponding components are designated with the same reference signs.

<FIG> shows a schematic representation of a local RF coil <NUM> with several marker elements <NUM> according to an embodiment of the invention. The marker elements <NUM> may for example be capsules containing an MR visible fluid. The local RF coil <NUM> comprises a coil cable <NUM> with a fluid plug <NUM> which can be connected to ta tube connector <NUM> (not shown here). The coil cable <NUM> is configured to connect the coil <NUM> to a control unit <NUM> (not shown here) of the system. A fluid conducting element <NUM> is leading through the coil cable <NUM> and passing several electronic components <NUM>. The fluid conducting element <NUM> may be connected to a source of air pressure or to another part of the fluid conducting element <NUM> filled, for example, with MR visible fluid, which may be pumped through the fluid conducting element, via the tube connector <NUM>. The marker elements <NUM> may either be fixed at their position or they can be moved along the fluid conducting element <NUM>, for example by air pressure. If the marker elements <NUM> are fixed at their position they may for example be activated and deactivated by shielding elements <NUM> (not shown here) which may for example be moved over the marker elements <NUM> via air pressure guided through the fluid conducting element <NUM>. The electronic components <NUM> of the coil <NUM> can influence the imaging of other imaging methods carried out in parallel or consecutively to the MRI. For example, they may attenuate the signal of PET scans. It is therefore useful to correct this attenuation by calculating the effect of attenuation and adjusting the (PET) image data accordingly. For this, it is necessary to determine the position of the movable coil <NUM> and its components <NUM>. Since the marker elements <NUM> are or can be positioned at predetermined positions with respect to the electronic components <NUM> of the coil <NUM> and since the marker elements <NUM> are highly visible in MRI images when activated they can be used to determine the position of the coil <NUM> and of the electronic components <NUM> of the coil <NUM>. In the coil cable <NUM> there is at least one braid-breaker <NUM> which can also influence measurement signals such as a PET signal. According to this embodiment, the position of the braid breaker can also be determined via two marker elements <NUM> which are placed before and after the braid breaker <NUM> inside the coil cable <NUM>.

<FIG> shows a schematic representation of a local RF coil <NUM> with a fluid conducting element <NUM> according to another embodiment of the invention. In this embodiment, the marker element <NUM> is an MR visible fluid <NUM> which is pumped through the fluid conducting element <NUM>. The MR visible fluid <NUM> can be pumped into and out of the fluid conducting element <NUM> inside the coil <NUM> and the coil cable <NUM> via the fluid plug <NUM> which can be connected to a corresponding tube connector <NUM>. When the MR visible fluid <NUM> is inside the coil <NUM> and thus the marker element <NUM> is activated, it will appear as a bright network in an MR image which can be used to determine the position and orientation of the coil <NUM>. Thereby, the fluid conducting element <NUM> is guiding the MR visible fluid <NUM> around the electronic components <NUM> of the coil <NUM>. Hence it is possible to specifically determine the location of these components <NUM> as derived from the position and orientation of the fluid conducting element <NUM> filled with the MR visible fluid <NUM>. In order to carry out MRI scans, the MR visible fluid <NUM> is pumped out of the part of the fluid conducting element <NUM> that is inside the coil <NUM> and, via the fluid plug <NUM>, into a part not inside the field of view of the scanner (not shown) and thus it does not disturb the MR imaging process.

<FIG> shows a schematic representation of a local RF coil <NUM> with several marker elements <NUM> according to another embodiment of the invention. In this embodiment, the marker elements <NUM> are fixed to a cable <NUM>. The cable <NUM> may in particular be a pull rope. Preferably, the cable <NUM> or pull rope is guided by a hose or tube <NUM>. In the state shown, the marker elements are within the scan range of the MRI system and are thus activated. The cable <NUM> inside the coil <NUM> and the coil cable <NUM> can be connected via a cable plug <NUM> to a cable part outside the coil <NUM>. The cable part outside the coil <NUM> does not have marker elements <NUM> attached to it. Accordingly, the marker elements <NUM> can be pulled out of the coil <NUM> via the cable <NUM> such that there is only the part of the cable <NUM> without marker elements inside the coil <NUM> and the marker elements <NUM> can thus be deactivated by removing them from the coil via the cable <NUM>. In order to activate the marker elements <NUM> again, they can be pulled back into the coil <NUM> to their predetermined position.

<FIG> shows a marker element <NUM> with a shielding element <NUM> according to an embodiment of the invention. The shielding element <NUM> is attached to a cable <NUM> that is guided via a tube <NUM>. The tube <NUM> may preferably be flexible, e.g. be a hose. The tube <NUM> comprises an opening <NUM> and the cable <NUM> is fixed to the shielding element <NUM> via a gripping unit <NUM>. The shielding element <NUM> can be pushed over a marker element <NUM> comprising an MR visible fluid <NUM> in order to deactivate the marker element <NUM> by shielding it and pulled away from the marker element <NUM> in order to activate it. The cable <NUM> is pretensioned by a non-magnetic spring <NUM> such that, if no additional force is applied to the cable <NUM>, the shielding element <NUM> is naturally kept in a position where it shields the marker element <NUM>. In this state the marker element is deactivated. In order to activate the marker element <NUM>, the cable <NUM> can be pulled (to the left in the figure) such that the shielding element <NUM> is pulled (to the left) away from the marker element <NUM>. Therein, the shielding element <NUM> is moved for a distance equivalent to the length of the marker element <NUM>. The two directions of movement (towards the marker element and away from it) of the shielding element <NUM> are marked by an arrow. Both, the marker element <NUM> and the shielding element <NUM> are comprised within a housing <NUM>, in particular a housing <NUM> made of plastic, which is configured to guide the shielding element <NUM> when the shielding element <NUM> is pulled by the cable <NUM>. The marker element <NUM>, on the other hand, is fixed to the housing <NUM>. The marker element <NUM> may for example have a diameter of <NUM> two <NUM> and a length (along the direction of the arrow) of <NUM> to <NUM>. The shielding element <NUM> on the other hand has a similar or essentially equal geometry, wherein its inner walls are dimensioned such that a gap of about <NUM>,<NUM> to <NUM>,<NUM> exists between the shielding element and the marker element.

<FIG> shows a marker element <NUM> with a shielding element <NUM> according to another embodiment of the invention. In this embodiment, the shielding element <NUM> is moved via air pressure. The air pressure is provided via a fluid conducting element <NUM> which is connected to a first portion <NUM> of an air pressure chamber <NUM> via an air inlet <NUM> in an airtight manner. Within the air pressure chamber <NUM> there are a marker element <NUM> and the shielding element <NUM>. The marker element is fixed to a wall of a second portion <NUM> of the air pressure chamber and the shielding element <NUM> is arranged between the first portion <NUM> and the second portion <NUM> of the air pressure chamber <NUM>. In order to deactivate the marker element <NUM>, the shielding element <NUM> can be pushed over the marker element <NUM> by providing a positive pressure (overpressure) in the first portion <NUM> via the fluid conducting element <NUM>. Reversely, in order to activate the marker element <NUM>, the shielding element <NUM> can be pulled away from the marker element <NUM> by providing a negative pressure (underpressure) in the first portion <NUM> via the fluid conducting element <NUM>. The second portion comprises an air outlet (<NUM>) in order to ensure that the pressure in the second portion <NUM> can remain essentially constant, in particular remain at ambient pressure, to allow free movement of the shielding element <NUM> without creating counterpressure in the second portion <NUM> due to the movement of the shielding element <NUM>.

<FIG> shows a marker element <NUM> with an ultrasound emitter <NUM> according to an embodiment of the invention. The ultrasound emitter <NUM> is directly attached to the marker element <NUM>. The marker element <NUM> can be deactivated via ultrasound waves created by the ultrasound emitter <NUM> by destroying the MR phase coherence of the marker element <NUM>. Accordingly, the marker element <NUM> may be deactivated during an MRI measurement by the ultrasound waves. In order to localize the coil <NUM>, the marker element <NUM> is activated by switching off the ultrasound emitter <NUM>.

<FIG> shows MRI images used for localization of the coil <NUM> via a marker element <NUM>. In the left picture, the marker element <NUM> was deactivated by shielding it with an RF shield and is thus not visible on the MRI image. In the centred picture, the marker element <NUM> was activated, i.e. not shielded, and thus appears as bright signal <NUM> in the MRI image. The right picture shows data, wherein the data of the left picture were subtracted from the data of the centred picture. Accordingly, the MRI image of the right picture only shows the bright signal <NUM> corresponding to the marker element <NUM>. It is thus easier to determine the position of the marker element <NUM> within the field of view in order to determine the position of the coil <NUM>, which is positioned at a predetermined position in relation to the marker element <NUM>.

<FIG> shows a cable plug <NUM> connected to a cable connector <NUM> according to an embodiment of the invention. This connection can in particular be used to move a shielding element <NUM> via a cable <NUM> which is guided through a coil cable <NUM> of a coil <NUM>. In this embodiment, the MRI system comprises an MR compatible motor <NUM> which is configured to drive a rotary shaft <NUM> in order to rotate an eccentric <NUM>. The motor <NUM>, the rotary shaft and the eccentric <NUM> are located in or at a patient table <NUM>. By rotating the eccentric, a bolt <NUM> within the cable connector <NUM> is pushed upwards against the force of a spring <NUM> thereby pushing a lever <NUM> inside the cable plug <NUM>. The cable <NUM> is connected to the other end of the lever <NUM>. As the lever <NUM> is pushed by the bolt <NUM> the cable <NUM> is pulled in the direction of the cable connector <NUM>. The cable <NUM> is connected to a shielding element <NUM> (see <FIG>) and by pulling the cable <NUM>, the shielding element <NUM> is pulled away from the marker element <NUM> thereby activating the marker element <NUM>. When the eccentric <NUM> is rotated further, the bolt <NUM> is no longer pushed by the eccentric <NUM> and is therefore pulled back by the spring <NUM> such that the lever <NUM> can also move back into its original position. Accordingly, the shielding element <NUM>, for example due to the force of a further spring <NUM> inside the coil <NUM> as shown in <FIG>, can move over the marker element <NUM> and thus deactivate the marker element <NUM>.

<FIG> shows a fluid plug <NUM> connected to a tube connector <NUM> according to an embodiment of the invention. The connection is in particular configured to allow the transfer of air into the fluid conducting element <NUM> of the coil <NUM>. Therefore, the tube connector <NUM> comprises an air socket <NUM> which is configured such, that the fluid plug of the coil <NUM> can be engage with the tube connector <NUM> thereby joining together the fluid conducting element <NUM> parts of the coil <NUM> and of the patient table <NUM>. The configuration according to this embodiment may in particular be used to drive the shielding element <NUM>, e.g. as shown in <FIG>.

<FIG> shows a fluid plug <NUM> connected to a tube connector <NUM> according to another embodiment of the invention. This configuration may in particular be used for an embodiment where the marker element <NUM> is an MR visible liquid <NUM> guided inside a fluid conducting element <NUM>, e.g. for the embodiment shown in <FIG>, or for an embodiment wherein cooling liquid is guided into the coil <NUM>. In addition to the embodiment of the fluid plug <NUM> and tube connector <NUM> as shown in <FIG> this embodiment has additional locking means. These are particularly useful in this case because a higher pressure may be needed to guide the MR visible liquid <NUM> as compared to guiding air and it is to be avoided that the MR visible liquid <NUM> might leak out when disconnecting the fluid plug <NUM>. The tube connector and/or the fluid plug <NUM> comprise an unlocking button <NUM> which needs to be pushed before disconnecting the fluid plug <NUM>. The fluid pump <NUM> is configured to pump the MR visible liquid out of the part of the fluid conducting element <NUM> that is located within the coil cable <NUM> and the coil <NUM>. Until the MR visible fluid <NUM> has been removed from the coil <NUM> and coil cable <NUM>, a locking element <NUM> is configured to ensures that a locking bolt <NUM> prevents removal of the fluid plug <NUM>. After pumping the MR visible fluid <NUM> out of the coil <NUM> and coil cable <NUM>, the locking bolt is pulled back and the fluid plug <NUM> can be removed. <FIG> shows an electronic component <NUM> of a coil <NUM> with a ceramic element <NUM> according to an embodiment of the invention. In this embodiment, the MR visible fluid <NUM> also serves as a cooling liquid. The electronic component <NUM> is encased in the ceramic element <NUM> which comprises a fluid channel <NUM> that is part of the fluid conducting element <NUM>. The electronic component <NUM> is cooled by the MR visible fluid <NUM> via the ceramic element <NUM>. In order to control the temperature of the electronic component <NUM>, a temperature sensor <NUM> is arranged within or at the electronic component <NUM>.

<FIG> shows a magnetic resonance imaging system <NUM> of the MRI-PET system according to an embodiment of the invention, wherein the PET system of the MRI-PET system of the invention is not shown. The system <NUM> comprises a patient table <NUM> on which a patient may lie during an examination and a coil <NUM> comprising the inventive marker element <NUM>. A diagnostic measurement, a localization of the coil <NUM> and/or an attenuation correction can be controlled and/or carried out by a control unit <NUM>.

Claim 1:
An MRI-PET system (<NUM>) consisting in a magnetic resonance imaging, MRI, system combined with a positron emission tomography, PET, system, and
comprising at least one local RF coil (<NUM>) and at least one marker element (<NUM>),
wherein the MRI-PET system (<NUM>) and the marker element (<NUM>) are configured such that the at least one marker element (<NUM>) may be activated to be detectable by the MRI system (<NUM>) at a predetermined position relative to the coil (<NUM>), wherein the MRI-PET system (<NUM>) and the marker element (<NUM>) are configured such that the at least one marker element (<NUM>) may be deactivated not to be detectable by the MRI system (<NUM>),
characterized in that
the MRI-PET system (<NUM>) comprises a shielding element (<NUM>),
wherein the shielding element (<NUM>) is movable in such a way that it can be moved into a shielding position and into a non-shielding position and/or wherein the marker element (<NUM>) is movable in such a way that it can be moved into a shielding position and into a non-shielding position,
wherein the shielding element (<NUM>) encloses the marker element (<NUM>) such that the marker element (<NUM>) is shielded from the MRI-PET system (<NUM>) when the shielding element (<NUM>) and/or the marker element (<NUM>) is in the shielding position, and
wherein the shielding element (<NUM>) is apart from the marker element (<NUM>) such that the marker element (<NUM>) is detectable by the MRI system (<NUM>) when the shielding element (<NUM>) and/or the marker element (<NUM>) is in the non-shielding position.