Cable harness and magnetic resonance system with multiple RF chokes

Abstract

According to the invention, a cable harness 7 for a magnetic resonance system is provided, said cable harness 7 adapted to be connected at one end to a power feed point of a magnetic resonance radio frequency coil arrangement 1 and at the other end to an input / output unit 6 for connecting the magnetic resonance radio frequency coil arrangement 1 to a control and analysis unit of the magnetic resonance system, the cable harness 7 having at least one transmission line 8 for connecting the power feed point to the input / output unit 6 and to a number of radio frequency chokes 10 arranged within the cable harness 7. In this way, bulky resonant RF traps can be avoided and the B1 excitation field of the MR system can be compensated and coupling to nearby local coils can be reduced.

Description

[Technical Field]

[0001] The present invention relates to the field of magnetic resonance (MR) systems, and in particular to cable harnesses and magnetic resonance coil devices. [Background technology]

[0002] With respect to magnetic resonance systems, particularly magnetic resonance imaging (MRI) systems, there is a continuing effort to increase the number of radio frequency (RF) receive coils used to increase the speed of image acquisition. It is not uncommon to have up to 64 RF receive coils in a magnetic resonance coil array. The RF receive coils are typically connected by coaxial cables to an RF receiver, which samples and digitizes the received RF signals. Due to these increases in the number of RF channels, MRI system designers are under continuous pressure to reduce the size of the components and subassemblies used with the RF receive coils. Summary of the Invention [Problem to be solved by the invention]

[0003] Magnetic resonance imaging (MRI) is an imaging technique based on the principle of nuclear magnetic resonance, i.e., atomic nuclei with non-zero spin have a magnetic moment. In medical MRI, the atomic nuclei with non-zero spin are usually the nuclei of hydrogen atoms present in human or animal bodies. Radio frequency (RF) waves forming a B1 excitation field are directed at the atomic nuclei in an external magnetic field, resulting in proton excitation and subsequent proton relaxation processes. As a result of the proton relaxation, RF signals are emitted by the atomic nuclei, which can be detected and processed to form images.

[0004] A typical MRI system generally includes a magnet, such as a superconducting electromagnet, that generates a strong static magnetic field; gradient coils that generate linear variations in the static magnetic field; an RF transmit coil that generates a B1 excitation field; and an RF receive coil that detects magnetic resonance RF signals emitted by relaxed atomic nuclei. A coaxial cable is typically used in MRI systems for controlled transmission of RF signals within the coil. The coaxial cable has an outer shield and an inner conductor separated from each other by a dielectric material. The outer shield serves to protect the inner conductor from picking up unwanted frequencies.

[0005] However, sources external to the coaxial cable can induce unintended currents in the outer shield and thus generate unintended magnetic fields that adversely affect the signal-to-noise ratio of the RF receive coil array. For these reasons, RF traps, such as baluns or RF chokes, are used in conjunction with coaxial cables in MR systems.

[0006] Typically, multiple RF receive coils are used in MR systems to form a receive coil array. Conventional RF receive coils and RF receive coil arrays tend to be bulky and / or rigid and are configured to be maintained in fixed positions relative to other RF receive coils in the coil array and relative to the imaging subject, respectively. The bulkiness and lack of flexibility often prevent the RF receive coil from most efficiently coupling with the desired anatomical structure of the imaging subject and tend to make the imaging process uncomfortable for the imaging subject.

[0007] Increasing the number of RF receive coils in a coil array can shorten the time required for image acquisition. However, increasing the number of RF receive coils necessitates the need to miniaturize the components used with the RF receive coils, namely, RF cables, RF traps such as RF chokes, preamplifiers, and printed circuit boards (PCBs). Along with the goal of miniaturizing RF receive coil arrays, the RF receive coils and electronics are closer to the imaging subject compared to conventional RF receive coils, and the shape, size, and weight of the receive coils and coil electronics become more important to the imaging subject's experience and the operator's handling experience. However, because MRI systems in hospitals are placed in harsh environments, the RF receive coils and components still need to be designed to be robust so that the system can withstand daily clinical routines.

[0008] WO 2018 / 077679(A1) provides a balun suitable for use with miniaturized coaxial cables, which eliminates the need to cut the cables to install the balun. A portion of each coaxial cable extending from an RF receiving coil to an RF receiver is wound multiple times around the device to form an inductor.

[0009] The object of the present invention is to provide the possibility of an RF receive coil arrangement for an MR system, which avoids bulky resonant RF traps, while still allowing the B1 excitation field of the MR system to be compensated and coupling to nearby local coils to be reduced. [Means for solving the problem]

[0010] According to the present invention, this object is addressed by the subject matter of claim 1. Preferred embodiments of the invention are set forth in the dependent claims.

[0011] Therefore, according to the present invention, there is provided a cable harness for a magnetic resonance system, the cable harness being adapted to be connected at one end to a feed point of a magnetic resonance radio frequency coil device and at the other end to an input / output unit for connecting the magnetic resonance radio frequency coil device to a control and analysis unit of the magnetic resonance system, the cable harness having at least one transmission line connecting the feed point with the input / output unit and a plurality of radio frequency chokes arranged within the cable harness.

[0012] As mentioned above, miniaturization of components used in radio frequency receiving coils is important. The RF receiving coils and electronics are closer to the imaging subject than conventional RF receiving coils. To improve the imaging subject's experience and the operator's operating experience by avoiding heavy and bulky equipment, the RF receiving coils can be placed in a flexible structure, i.e., a mat, that is placed on the imaging subject during the examination. Typically, radio frequency chokes are also placed in this coil array of the magnetic resonance radio frequency coil device. To improve the flexibility of the equipment placed on the imaging subject during the examination, according to the present invention, the radio frequency chokes can still be placed in the coil array, but a cable harness with such RF chokes is provided, adapted to be connected at one end to the feed point of the magnetic resonance radio frequency coil device and at the other end to an input / output unit for connecting the magnetic resonance radio frequency coil device to the control and analysis unit of the magnetic resonance system. Thus, the present invention at least provides the possibility of placing individual RF chokes for different RF receiving coils outside the array, i.e., within the cable harness.

[0013] In this way, the B1 excitation field of the MR system can be compensated, coupling to nearby local coils can be reduced, and bulky resonant RF traps can be avoided.

[0014] According to a preferred embodiment of the present invention, the cable harness has a plurality of transmission lines for connecting the power supply point to the input / output unit, each of the transmission lines having at least one high frequency choke disposed within the cable harness.

[0015] According to a preferred embodiment of the present invention, the high frequency choke is arranged in the cable harness in a configuration extending along the longitudinal extension of the cable harness, the longitudinal extension of the cable harness being the extension of the cable harness from the connection terminal to the input / output unit, where in the case of a flexible cable harness this longitudinal direction does not have to follow a straight line.

[0016] According to a preferred embodiment of the present invention, the high frequency chokes are arranged in a line within the cable harness. By arranging the individual micro traps in a line in this manner, relatively thin traps can be realized, and thus a relatively thin cable harness can be realized.

[0017] According to a preferred embodiment of the present invention, the high-frequency chokes each have a choke housing, and the cable harness includes a plurality of transmission lines, each of which is a coaxial cable wound around the choke housing in a self-compensating winding pattern to at least partially compensate for the B1 excitation field of a magnetic resonance system. The coaxial cable has a first end and a second end, and a portion of the coaxial cable between the first end and the second end is wound around the choke housing in a self-compensating winding pattern. A high-frequency choke having such a self-compensating winding pattern is also referred to as a self-compensating RF choke. The self-compensating winding pattern provides compensation for the B1 excitation field of the magnetic resonance system and eliminates coupling to nearby local coils. In this way, the self-compensating winding pattern helps the self-compensating RF choke behave as an ideal inductor. The stray capacitance of the self-compensating winding pattern causes the self-compensating RF choke to self-resonate at a self-resonant frequency. Generally, the self-resonant frequency of an inductor is the frequency at which the stray capacitance of the inductor resonates with the inductor's ideal inductance, resulting in a very high impedance. Therefore, the self-resonance of the self-compensating RF choke helps increase the impedance of the self-compensating RF choke. The self-resonant frequency of a self-compensating RF choke typically depends on the specific geometry of the choke housing, the self-compensating winding pattern, and the diameter of the coaxial cable. According to a preferred embodiment of the present invention, the choke housing is implemented on a flexible PCB structure. Furthermore, according to a preferred embodiment of the present invention, the housing is implemented using a flexible housing manufactured by an inkjet printer. Furthermore, according to the present invention, the cable harness may vary in diameter and width. Even if the self-resonant frequency is not the same frequency as or close to the frequency of the B1 excitation field of the MRI system, the self-compensating RF choke still provides a sufficiently high impedance. Therefore, the signal-to-noise ratio of the MRI system is improved without having to design the RF choke to have a resonant frequency equal to or close to the B1 excitation field, as required for conventional resonant RF traps.According to a preferred embodiment of the present invention, the individual RF chokes are tuned to different frequencies, for example, one RF choke is tuned to 1.5 Tesla and another RF choke is tuned to 3 Tesla, allowing the cable harness to be used for both magnetic field strengths.

[0018] According to a preferred embodiment of the present invention, each transmission line comprises a pair of first and second coaxial cables, the first and second coaxial cables having an additional shield surrounding the first and second coaxial cables, and / or the first and second coaxial cables being twisted together to form a twisted transmission line. Preferably, the first and second coaxial cables each have an impedance of 50 Ω. By using twice the standard 50 Ω cable, the resulting impedance for signals between the inner conductors is given by 100 Ω, thus meeting the standards defined for most serial digital data transmission lines. Preferably, the first and second coaxial cables are micro-coaxial cables. Preferably, the micro-coaxial cables have an outer diameter of 0.2 to 1.0 mm. Such coaxial lines should preferably be selected based on a very thin type to obtain a flexible cable. The two cables may be the same type, but may also be different types. Preferably, a capacitor is placed at each end of each transmission line. Thus, the capacitors can be used to connect the two outer shields of the micro-coaxial cable, at least at the ends of the transmission lines, but also between the ends. A further preferred embodiment is a thin triaxial cable wound as a choke toroid, using a shorted quarter-wavelength line in the outer conductor. According to a preferred embodiment of the present invention, at least one twinaxial RF cable, or a combination of twinaxial and coaxial cables, or any other combination thereof, is used.

[0019] According to a preferred embodiment of the present invention, each choke has a choke housing made of a flexible foam material and / or a liquid-based material. Thus, the flexible trap is realized by using a flexible foam housing or a separate garment matrix housing. The foam housing is constructed locally for each individual trap. A different mechanical design is the realization of a liquid-based flexible housing for the trap.

[0020] According to a preferred embodiment of the present invention, the cable harness has a flexible support structure, and the RF choke is disposed within the flexible support structure. The flexible support structure allows the cable harness to bend, thereby providing more flexible positioning of a magnetic resonance radio frequency coil device that may be connected to the bendable cable harness. According to a preferred embodiment of the present invention, the harness includes, at least in part, a stretchable housing and a mechanical matrix material.

[0021] According to a preferred embodiment of the present invention, the RF choke is flexibly connected to the support structure such that the RF choke is rotatable and / or tiltable relative to the support structure. In this way, a flexible cable harness can be provided that allows the self-compensating RF choke to be positioned more flexibly, allowing the positioning to be based on the specific situation. In this way, a flexible cable harness can be provided that allows the self-compensating RF choke to be positioned more flexibly, allowing the positioning to be based on the specific situation.

[0022] According to a preferred embodiment of the present invention, each RF choke has a shield, which is located adjacent to the respective transmission line of the radio frequency choke and / or between two adjacent radio frequency chokes. This can reduce crosstalk. This design also provides differential mode capture between the individual transmission lines.

[0023] According to a preferred embodiment of the present invention, the choke housing has a toroidal, solenoidal, helical, or planar shape. Preferably, the choke housing of a toroidal choke has a diameter of approximately 11 mm and a thickness of 6 mm. Solenoid designs preferably have a diameter of 3 to 6 mm.

[0024] Furthermore, according to the present invention, a cable harness as claimed in any of the previous claims is used to connect a feed point of a magnetic resonance radio frequency coil device to an input / output unit of the magnetic resonance radio frequency coil device, and the input / output unit is used to connect the magnetic resonance radio frequency coil device to a control and analysis unit of a magnetic resonance system.

[0025] Further, the present invention provides a magnetic resonance coil device for a magnetic resonance system, comprising: an array having a plurality of magnetic resonance receive coils configured to receive magnetic resonance radio frequency signals, a plurality of individual connection lines, and a connection terminal, each of the magnetic resonance receive coils being connected to a connection terminal having one of the connection lines for transmitting the magnetic resonance radio frequency signals to the connection terminal; an input / output unit; and a cable harness having a plurality of transmission lines, one side of which is individually connected to each of the connection lines via the connection terminal, and the other side of which is connected to the input / output unit for transmitting the individual magnetic resonance radio frequency signals to an analysis and control unit of the magnetic resonance system via the input / output unit, each of the transmission lines having at least one radio frequency choke disposed within the cable harness. The connection terminal is a feed point for the receive coil array. In this way, a cluster of individual high-impedance chokes can be provided immediately after the feed point, avoiding bulky RF traps. Therefore, because the individual RF chokes are disposed within the flexible cable harness, a flexible trap can be achieved. Distributed flexible RF traps can be used to trap the output lines of RF antenna arrays.

[0026] Therefore, part of the present invention is that RF chokes located within a cable harness connecting the feed point of a magnetic resonance receive coil array to an input / output unit use a cluster of individual RF chokes for each resonant receive coil. In this way, the RF chokes located within the cable harness can replace the conventional bulky resonant RF traps used in conventional receive coil arrays, thus enabling distributed cable routing to be implemented in an easy and efficient manner, with each RF receive coil connected to the input / output unit by an individual line with at least one individual RF choke. In contrast to conventional cable routing in which coaxial cables are routed along a fishbone structure, parallel routing of coaxial cables leads to thick, inflexible cable bundles and large RF traps, the distributed cable routing of the present invention, together with the placement of RF chokes within the cable harness, allows the complete magnetic resonance coil system to be flexible, which increases the experience of both the patient and the operator.

[0027] These and other aspects of the invention will be apparent from and elucidated with reference to the embodiments described hereinafter, but such embodiments do not necessarily represent the full scope of the invention, and reference should therefore be made to the claims and this specification for interpreting the scope of the invention. [Brief explanation of the drawings]

[0028] [Figure 1] 1 is a diagram illustrating a schematic representation of a magnetic resonance coil device having a cable harness according to a preferred embodiment of the present invention; [Figure 2] FIG. 2 is a diagram schematically illustrating a harness of the magnetic resonance coil device of FIG. 1. [Figure 3] 3 is a diagram illustrating a linear arrangement of RF chokes in the cable harness of FIG. 2. FIG. [Figure 4] 2 shows a schematic diagram of how the magnetic resonance coil device of FIG. 1 can be positioned on a subject under examination; [Figure 5]1 is a diagram illustrating a transmission line according to a preferred embodiment of the present invention; [Figure 6] FIG. 10 is a diagram illustrating a transmission line according to another preferred embodiment of the present invention. [Figure 7a] 1 is a top view schematically illustrating an RF choke according to a preferred embodiment of the present invention. [Figure 7b] FIG. 2 is a top view schematically illustrating another RF choke according to a preferred embodiment of the present invention. [Figure 8a] FIG. 2 is a side view schematically illustrating an RF choke according to another preferred embodiment of the present invention. [Figure 8b] FIG. 2 is a top view schematically illustrating another RF choke according to another preferred embodiment of the present invention. [Figure 9a] FIG. 2 is a perspective view of a choke housing according to a preferred embodiment of the present invention. [Figure 9b] FIG. 2 is a perspective view of a choke housing according to a preferred embodiment of the present invention. DETAILED DESCRIPTION OF THE INVENTION

[0029] The flexible cable harness according to the invention is particularly valuable for magnetic resonance coil devices having coil arrays, especially flexible coil arrays, and therefore, although the flexible cable harness can be used with different types of coil configurations, in the following preferred embodiments of the invention will be described with reference to such magnetic resonance coil devices having flexible coil arrays.

[0030] FIG. 1 schematically illustrates a magnetic resonance coil device 1 having a cable harness 7 according to a preferred embodiment of the present invention. The magnetic resonance coil device 1 includes a magnetic resonance coil array 2 having a plurality of RF receiving coils 3 arranged in a two-dimensional array. Each RF receiving coil 3 is connected to a connection terminal 5 via a connection line 4. The connection terminal 5 of the magnetic resonance coil array 2 thus serves as a power supply point for the magnetic resonance radio frequency coil device 1. All RF receiving coils 3 are connected to such connection lines 4, but for clarity, only six such connection lines 4 are shown in FIG. 4. Each individual connection line 4 connects the RF receiving coil 3 to the connection terminal 5 so as to transmit a magnetic resonance radio frequency signal directly to the connection terminal 5. This means that the connection lines 4 are not bundled together to form a cable bundle within the area defined by the two-dimensional array of the plurality of RF receiving coils 2. The connection lines 4 do not include self-compensating RF chokes 10. The receiving coils 3 are uniformly arranged across the area defined by the two-dimensional array 2. The connection terminal 5 can be connected to a control and analysis unit of the magnetic resonance system via the cable harness 7. Thereby, the cable harness 7 can be connected at one end to the connection terminal 5 and at the other end to the input / output unit 6 of the control and analysis unit. The magnetic resonance coil array 2 and the cable harness 7 each have a flexible support structure 9.

[0031] In this embodiment, the magnetic resonance receive coil device 1 is used as a receive coil array 2 of a magnetic resonance imaging system with a B1 excitation field.

[0032] FIG. 2 schematically illustrates the cable harness 7 of the magnetic resonance coil device 1 of FIG. 1. The cable harness 7 includes a plurality of transmission lines 8, each including an RF choke. The number of transmission lines 8 is equal to the number of RF receiving coils 3 of the magnetic resonance coil array 2, but for clarity, only five such transmission lines 8 are shown in FIG. 2. The transmission lines 8 connect the connection terminals 5 with the input / output unit 6. The RF chokes 10 are arranged sequentially along the longitudinal axis of the cable harness 7. Thus, the width of the cable harness (perpendicular to the longitudinal axis) can be kept relatively small. The RF chokes 10 are flexibly arranged within and connected to the support structure 9 such that the RF chokes are rotatable and / or tiltable relative to the support structure 9. This results in a fully flexible and bendable cable harness 7.

[0033] FIG. 3 shows a schematic diagram of a line-arrangement of RF chokes 10 in the cable harness 7 of FIG. 2. Instead of the typically large, bulky traps, relatively thin traps can be realized by arranging individual micro-traps in such a line. Thus, a relatively thin, bendable cable harness 7 can be realized. To reduce crosstalk, the individual RF traps 10 can be shielded, or shielding between the RF traps 10 can be optionally arranged (not shown in FIG. 3). This design also provides trapping of differential modes between individual transmission lines.

[0034] 4 shows schematically how the magnetic resonance coil device 1 of FIG. 1 can be arranged on an examination object 11. An array having a plurality of receive coils 2 is placed on the examination object 11. The array 2 is flexible so that its shape can be adapted to the shape of the examination object 11. A flexible, bendable cable harness 7 allows flexible positioning of the array 2 on the examination object 11 with respect to the input / output unit 6. For example, the lateral alignment of the receive coil array 2 or a possible rotation of the receive coil array 2 does not have to be taken into account during positioning, because the connections between the receive coil array 2 and, respectively, the connection terminals 5 and the usually permanently installed input / output unit 6 via the bendable cable harness 7 are flexible.

[0035] 5 is a cross-sectional view schematically illustrating a transmission line 30 according to a preferred embodiment of the present invention. The transmission line 30 includes a first coaxial cable 40 and a second coaxial cable 50. The first coaxial cable 40 includes a first inner conductor 41 and a first outer conductor 42. The second coaxial cable 50 includes a second inner conductor 51 and a second outer conductor 52. Both coaxial cables 40, 50 are electrically insulated from the outside by a sheath insulator 60. The first outer conductor 42 and the second outer conductor 52 are connected via a capacitor C1.

[0036] Figure 6 shows a schematic perspective view of a transmission line similar to that of Figure 5. The first coaxial cable 40 and the second coaxial cable 50 are further twisted together. Here, both ends of the transmission lines 31 and 32 are connected via capacitors C1 and C2, respectively.

[0037] FIG. 7a is a schematic top view of an RF choke 10 according to a preferred embodiment of the present invention. The RF choke 10 includes a choke housing 20. In this embodiment, the choke housing 20 has a toroidal shape. A transmission line consisting of a first coaxial cable 40 and a second coaxial cable 50 twisted together is wound around the choke housing 20, as shown in FIG. 6. The twisted coaxial cables 40, 50 are wound around the surface of the choke housing 20. The coaxial cables 40, 50 form a single winding that extends from the outside of the choke housing 20, through the entire center, and back to the outside of the choke housing 20.

[0038] Figure 7b shows a schematic top view of another RF choke 10 according to a preferred embodiment of the present invention. In this embodiment, the RF choke 10 comprises a solenoid configuration. A transmission line consisting of a first coaxial cable 40 and a second coaxial cable 50 twisted together, as shown in Figure 6, is wound around the choke housing 20. The transmission line is wound helically around the surface of the choke housing 20.

[0039] FIG. 8a is a side view schematic diagram of an RF choke 10 according to another preferred embodiment of the present invention. The RF choke 10 has two choke housings 20, 100. A transmission line including a first coaxial cable 40 and a second coaxial cable 50 is wound around the first choke housing 20 in a plane containing the rotation axis A1, wound around the first choke housing 20 in a plane perpendicular to the rotation axis A1 and along the outer periphery of a toroidal shape, wound around the additional choke housing 100 in a plane containing the rotation axis A1, and wound around the additional choke housing 100 in a plane perpendicular to the rotation axis A1 and along the outer periphery of a toroidal shape. Both choke housings 20, 100 are connected via the same twisted and wound coaxial cables 40, 50.

[0040] FIG. 8b shows a schematic top view of another RF choke 10 according to another preferred embodiment of the present invention. The RF choke 10 has two choke housings 20, 100. A transmission line including a first coaxial cable 40 and a second coaxial cable 50 is wound around the first choke housing 20 in a plane perpendicular to the rotation axis A2 of the choke housing 20, wound around the first choke housing 20 in a plane containing the rotation axis A2 of the choke housing 20 and along the outer periphery of the choke housing 20, wound around the additional choke housing 100 in a plane perpendicular to the rotation axis A2 of the choke housing 20, and wound around the additional choke housing 100 in a plane containing the rotation axis A2 of the choke housing 20 and along the rotation axis A2 of the choke housing 20. Both choke housings 20, 100 are connected via the same twisted and wound coaxial cables 40, 50.

[0041] 7a-8b show optional embodiments for the high impedance choke 10 using stranded coaxial cables 40, 50. The design can also be implemented using shielded or partially shielded stranded coaxial cables 40, 50. The individual conductors are implemented using CuL (CC1101 USB Lite) wire, stranded coaxial cables and / or insulated wire.

[0042] FIG. 9a is a schematic perspective view of the choke housing 20 of the self-compensating RF choke 10 according to the preferred embodiment of the present invention shown in FIG. 7a. The choke housing 20 has a toroidal shape. As previously described, the transmission line 30 is wound around the choke housing 30 in a self-compensating winding pattern as shown in FIG. 7a. To guide the winding of the transmission line 30 around the choke housing 20, the choke housing 20 has a first notch structure 91 and a second notch structure 92. The first notch structure 91 has a plurality of notches 91a, 91b, and 91c for guiding the first winding pattern of the self-compensating winding pattern, each of which is disposed in a plane containing the axis A1 of the toroidal shape. With respect to the second cutout structure 92, the second cutout structure 92 has another cutout 92 for guiding the reverse winding pattern of the self-compensating winding pattern, and the other cutout 92 is located along the periphery of the toroidal form in a plane perpendicular to the axis A1 of the toroidal form.

[0043] FIG. 9b is a perspective view of another choke housing 20 of the self-compensating RF choke 10 according to the preferred embodiment of the present invention shown in FIG. 7b. The choke housing 20 has a cylindrical shape. The transmission line 30 is wound around the choke housing 20 in a solenoid-shaped, self-compensating winding pattern, as shown in FIG. 7b. To guide the winding of the transmission line 30 around the choke housing 20, the choke housing 20 has a first notch structure 91 and a second notch structure 92. The first notch structure 91 has a plurality of notches 91a, 91b, and 91c for guiding the first winding pattern of the self-compensating winding pattern, each of which is located in a plane perpendicular to the axis A2 of the choke housing 20. With respect to the second cutout structure 92, the second cutout structure 92 has another cutout 92 for guiding the reverse winding pattern of the self-compensating winding pattern, and the other cutout 92 is arranged along the outer periphery of the choke housing 20 in a plane containing the axis A2 of the choke housing 20.

[0044] While the invention has been illustrated and described in detail in the drawings and the foregoing description, such illustration and description are to be considered illustrative or exemplary and not restrictive. The invention is not limited to the disclosed embodiments. Other variations to the disclosed embodiments can be understood and effected by those skilled in the art in practicing the claimed invention, from a study of the drawings, the disclosure, and the appended claims. In the claims, the word "comprising" does not exclude other elements or steps, and the indefinite article "a" or "an" does not exclude a plurality. The mere fact that certain measures are recited in mutually different dependent claims does not indicate that a combination of these measures cannot be used to advantage. Any reference signs in the claims should not be construed as limiting the scope of the claims. Moreover, for the sake of clarity, not all elements in the drawings have been labeled with reference signs. The following describes embodiments of the present invention. (Appendix 1) A cable harness for a magnetic resonance system, the cable harness being adapted to be connected at one end to a feed point of a magnetic resonance radio frequency coil device and at the other end to an input / output unit for connecting the magnetic resonance radio frequency coil device to a control and analysis unit of the magnetic resonance system, the cable harness having at least one transmission line connecting the feed point to the input / output unit, the cable harness having a flexible support structure and a plurality of radio frequency chokes within the flexible support structure, the radio frequency chokes being flexibly connected to the support structure such that the radio frequency chokes are rotatable and / or tiltable relative to the support structure. (Appendix 2) 2. The cable harness of claim 1, wherein the cable harness has a plurality of transmission lines connecting the feed point to the input / output unit, each of the transmission lines having at least one high frequency choke disposed within the cable harness. (Appendix 3) 3. The cable harness of claim 1 or 2, wherein the high frequency choke is disposed within the cable harness in a configuration extending along a longitudinal extension of the cable harness. (Appendix 4) 4. The cable harness of claim 3, wherein the high frequency chokes are arranged in a line within the cable harness. (Appendix 5) 5. The cable harness of any one of claims 1 to 4, wherein each of the high frequency chokes has a choke housing, and the cable harness has a plurality of transmission lines, the plurality of transmission lines being coaxial cables or micro-coaxial cables, wound around the choke housing in a self-compensating winding pattern to at least partially compensate for a B1 excitation field of the magnetic resonance system. (Appendix 6) 6. The cable harness of claim 5, wherein each of the transmission lines comprises a pair of first and second coaxial cables, the first and second coaxial cables having an additional shield surrounding the first and second coaxial cables, and / or the first and second coaxial cables are twisted together to form a twisted transmission line. (Appendix 7) 7. The cable harness of any one of claims 1 to 6, wherein each of the high frequency chokes has a choke housing made from a flexible foam material and / or a liquid-based material. (Appendix 8) 8. The cable harness of any one of claims 1 to 7, wherein each of the high frequency chokes has a shield, and each shield is positioned adjacent to a respective transmission line of the high frequency choke and / or between two adjacent high frequency chokes. (Appendix 9) 9. The cable harness of any one of claims 1 to 8, wherein the choke housing has a toroidal shape, a solenoidal shape, a spiral shape, or a planar shape. (Appendix 10) 10. Use of the cable harness according to any one of appendices 1 to 9 for connecting a power supply point of a magnetic resonance radio frequency coil device to an input / output unit of the magnetic resonance radio frequency coil device, the input / output unit being used to connect the magnetic resonance radio frequency coil device to a control and analysis unit of a magnetic resonance system. (Appendix 11) 1. A magnetic resonance coil device for a magnetic resonance system, comprising: an array having a plurality of magnetic resonance receive coils configured to receive magnetic resonance radio frequency signals; a plurality of individual connection lines and connection terminals, each of the magnetic resonance receive coils being connected to the connection terminals using one of the connection lines for transmitting the magnetic resonance radio frequency signals to the connection terminals; an input / output unit; The cable harness according to any one of Supplementary Notes 1 to 9, A magnetic resonance coil device in which one side of the cable harness is individually connected to each connection line via the connection terminal and the other side is connected to the input / output unit in order to transmit individual magnetic resonance high-frequency signals to a control and analysis unit of the magnetic resonance system via the input / output unit. (Appendix 12) a control and analysis unit; 12. A magnetic resonance coil device according to claim 11, connected to the control and analysis unit via an input / output unit; A magnetic resonance system having: [Explanation of symbols]

[0045] Magnetic resonance receiving coil device 1 Array with multiple receiving coils 2 Receiver coil 3 Connection line 4 Connection terminal 5 Input / Output Unit 6 Cable harness 7 Transmission Line 8 flexible support structure 9 RF Choke 10 Test subject 11 Choke housing 20 Transmission Line 30 First end 31 Second end 32 First Subsection 33 Second Subsection 34 First coaxial cable 40 First inner conductor 41 First outer conductor 42 Second coaxial cable 50 Second inner conductor 51 Second outer conductor 52 Shield 60 First winding pattern 70 Reverse winding pattern 80 First notch structure 91 Second cutout structure 92 Additional choke housing 100 Axis A1 Axis A2 Capacitor C1 Capacitor C2

Claims

1. 1. A cable harness for a magnetic resonance system, the cable harness being adapted to be connected at one end to a feed point of a magnetic resonance radio frequency coil device and at the other end to an input / output unit for connecting the magnetic resonance radio frequency coil device to a control and analysis unit of the magnetic resonance system, the cable harness having at least one transmission line connecting the feed point to the input / output unit, the cable harness having a flexible support structure and a plurality of high frequency chokes within the flexible support structure, the high frequency chokes being flexibly connected to the flexible support structure such that the high frequency chokes are rotatable and / or tiltable relative to the flexible support structure, the cable harness having a plurality of transmission lines connecting the feed point to the input / output unit, each of the transmission lines having at least one of the plurality of high frequency chokes disposed within the flexible support structure.

2. A cable harness for a magnetic resonance system, the cable harness being adapted to be connected at one end to a power supply point of a magnetic resonance radio frequency coil device and at the other end to an input / output unit for connecting the magnetic resonance radio frequency coil device to a control and analysis unit of the magnetic resonance system, the cable harness having at least one transmission line connecting the power supply point to the input / output unit, the cable harness having a flexible support structure and a plurality of high frequency chokes within the flexible support structure, the high frequency chokes being flexibly connected to the flexible support structure such that the high frequency chokes are rotatable and / or tiltable relative to the flexible support structure, each of the high frequency chokes having a choke housing, the cable harness having a plurality of transmission lines, the plurality of transmission lines being coaxial cables or micro-coaxial cables, wound around the choke housing in a self-compensating winding pattern to at least partially compensate for a B1 excitation magnetic field of the magnetic resonance system.

3. A cable harness for a magnetic resonance system, the cable harness being adapted to be connected at one end to a power supply point of a magnetic resonance radio frequency coil device and at the other end to an input / output unit for connecting the magnetic resonance radio frequency coil device to a control and analysis unit of the magnetic resonance system, the cable harness having at least one transmission line connecting the power supply point to the input / output unit, the cable harness having a flexible support structure and a plurality of high frequency chokes within the flexible support structure, the high frequency chokes being flexibly connected to the flexible support structure such that the high frequency chokes are rotatable and / or tiltable relative to the flexible support structure, and each of the high frequency chokes having a choke housing made of a flexible foam material and / or a liquid-based material.

4. A cable harness for a magnetic resonance system, the cable harness being adapted to be connected at one end to a power supply point of a magnetic resonance radio frequency coil device and at the other end to an input / output unit for connecting the magnetic resonance radio frequency coil device to a control and analysis unit of the magnetic resonance system, the cable harness having at least one transmission line connecting the power supply point to the input / output unit, the cable harness having a flexible support structure and a plurality of high frequency chokes within the flexible support structure, the high frequency chokes being flexibly connected to the flexible support structure such that the high frequency chokes are rotatable and / or tiltable relative to the flexible support structure, each of the high frequency chokes having a shield, each shield being positioned adjacent to the respective transmission line of the high frequency choke and / or positioned between two adjacent high frequency chokes.

5. A cable harness for a magnetic resonance system, the cable harness being adapted to be connected at one end to a power supply point of a magnetic resonance radio frequency coil device and at the other end to an input / output unit for connecting the magnetic resonance radio frequency coil device to a control and analysis unit of the magnetic resonance system, the cable harness having at least one transmission line connecting the power supply point to the input / output unit, the cable harness having a flexible support structure and a plurality of high frequency chokes within the flexible support structure, the high frequency chokes being flexibly connected to the flexible support structure such that the high frequency chokes are rotatable and / or tiltable relative to the flexible support structure, each of the high frequency chokes having a choke housing, the choke housing having a toroidal shape, a solenoidal shape, a spiral shape, or a planar shape.

6. 6. The cable harness according to claim 2, wherein the cable harness has a plurality of transmission lines connecting the feed point to the input / output unit, and each of the transmission lines has at least one high frequency choke disposed within the cable harness.

7. The cable harness according to any one of claims 1 to 6, wherein the high frequency choke is arranged within the cable harness in a configuration extending along a longitudinal extension of the cable harness.

8. The cable harness of claim 7 , wherein the high frequency chokes are arranged in a line within the cable harness.

9. 9. The cable harness of claim 1, wherein each of the radio frequency chokes has a choke housing, and wherein the cable harness comprises a plurality of transmission lines, the plurality of transmission lines being coaxial cables or micro-coaxial cables, wound around the choke housing in a self-compensating winding pattern to at least partially compensate for a B1 excitation field of the magnetic resonance system.

10. 10. The cable harness of claim 9, wherein each of the transmission lines comprises a pair of first and second coaxial cables, the first and second coaxial cables having an additional shield surrounding the first and second coaxial cables, and / or the first and second coaxial cables are twisted together to form a twisted transmission line.

11. 11. The cable harness according to claim 1, wherein each of the high frequency chokes has a choke housing made from a flexible foam material and / or a liquid-based material.

12. 12. The cable harness according to claim 1, wherein each of the high frequency chokes has a shield, and each shield is arranged adjacent to a respective transmission line of the high frequency choke and / or between two adjacent high frequency chokes.

13. The cable harness according to any one of claims 2, 9 to 11, and claims 6 to 8 or 12 that directly or indirectly cite claim 2, wherein the choke housing has a toroidal shape, a solenoidal shape, a spiral shape, or a planar shape.

14. Use of the cable harness according to any one of claims 1 to 13 for connecting a feed point of a magnetic resonance radio frequency coil device to an input / output unit of said magnetic resonance radio frequency coil device, said input / output unit being used to connect said magnetic resonance radio frequency coil device to a control and analysis unit of a magnetic resonance system.

15. 1. A magnetic resonance coil device for a magnetic resonance system, comprising: an array having a plurality of magnetic resonance receive coils configured to receive magnetic resonance radio frequency signals; a plurality of individual connection lines and connection terminals, each of the magnetic resonance receive coils being connected to the connection terminals using one of the connection lines for transmitting the magnetic resonance radio frequency signals to the connection terminals; an input / output unit; The cable harness according to any one of claims 1 to 13, A magnetic resonance coil device in which one side of the cable harness is individually connected to each connection line via the connection terminal and the other side is connected to the input / output unit in order to transmit individual magnetic resonance high-frequency signals to a control and analysis unit of the magnetic resonance system via the input / output unit.

16. a control and analysis unit; a magnetic resonance coil device according to claim 15, which is connected to the control and analysis unit via an input / output unit; A magnetic resonance system having:

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