Method for displaying signal values ​​of a combined magnetic resonance-positron emission tomography device and a correspondingly designed magnetic resonance-positron emission tomography device

Abstract

Method for displaying signal values ​​of a combined magnetic resonance positron emission tomography device (1), comprising the steps: - Assignment (13) of a first image data set with signal values ​​resulting from a magnetic resonance measurement to a second image data set with signal values ​​resulting from a positron emission tomography measurement, - Assignment (14) of at least one signal parameter of the first image data set to at least one signal parameter of the second image data set in the form of an n-tuple (20), where n indicates the number of assigned signal parameters and the n-tuples (20) indicate spatially corresponding signal values ​​and - Output (15) of an n-dimensional scatterplot (17) by displaying the n-tuples (20), where each signal parameter is assigned a coordinate axis.

Description

[0001] The present invention relates to a method for displaying signal values ​​of a combined magnetic resonance-positron emission tomography device, a corresponding computer program that enables the execution of such a method, an electronically readable data carrier, and a combined magnetic resonance-positron emission tomography device therefor.

[0002] Imaging techniques for displaying objects under examination, in particular for determining material properties, material arrangement and extent or similar, are widespread, particularly in their medical application.

[0003] The image data from various known medical examination facilities allow different conclusions to be drawn. While X-ray-based image data allows for statements about the attenuation coefficient of the imaged object, magnetic resonance imaging can provide insights into the proton density or the density of the excited nuclei, relaxation parameters, and other parameters. Positron emission tomography, on the other hand, enables functional imaging without achieving the spatial resolution of, for example, magnetic resonance imaging. Therefore, there is a need for combined medical examination facilities that allow the acquisition of image data from multiple examination facilities to ultimately obtain fused image data.From these fused image data, better information can then be derived, particularly for diagnosis, than when only individual image data, i.e. image data from a single examination facility, is considered.

[0004] Magnetic resonance imaging (MRI) is an imaging technique that enables the high-resolution generation of cross-sectional images of living organisms, such as humans. The patient is positioned in a homogeneous magnetic field B0. Gradient coils modify the external magnetic field in the FOV (field of view) in such a way that, on the one hand, a body slice is selected and, on the other hand, the generated MR signals are spatially encoded. The subsequent reconstruction of the MR signals, for example, using Fourier transformation, creates an image of the selected slice, which is used for medical diagnostics. The MR signals are generated and detected using a radiofrequency system comprising a transmitting antenna that radiates RF excitation pulses into the patient and a receiving antenna that detects the emitted RF resonance signals and transmits them for image reconstruction.By selecting a suitable pulse sequence, such as a spin echo sequence or a gradient echo sequence, and the associated sequence parameters, the contrast of the MR images can be varied in many ways depending on the diagnostic task. MRI depicts body structures and is therefore a structural imaging technique.

[0005] Positron emission tomography (PET) is a common functional imaging technique. During a test, a subject is administered a weakly radioactive substance, the distribution of which in the body is visualized using PET. This allows the biochemical and physiological functions of the organism to be imaged. The radiopharmaceuticals used are molecules labeled with a radionuclide that emits positrons. The high-energy photons created when the positron annihilates with an electron in the subject's body, which are emitted at an angle of 180° to each other, are recorded by a large number of detectors arranged in a ring around the subject. Only coincident events recorded by two opposing detectors are evaluated.

[0006] The recorded coincident decay events are used to infer the spatial distribution of the radiopharmaceutical within the body, and a series of cross-sectional images is calculated. Image reconstruction can be performed using a filtered backprojection or an iterative method, although the spatial resolution generally lags behind that of conventional computed tomography (CT) or magnetic resonance imaging systems.

[0007] The patent application DE 102007037103 A1 describes a method for imaging functional and electrical activities of the brain, wherein the images are acquired using a combined magnetic resonance positron emission tomography device.

[0008] The patent application US 2011 / 0160543 A1 describes a method for diagnosing a neurological disease based on magnetic resonance imaging or positron emission tomography image data.

[0009] The patent application US 2013 / 0004044 A1 describes a method for analyzing a lung disease based on magnetic resonance imaging or positron emission tomography image data.

[0010] The patent application US 2012 / 0184843 A1 describes a method for correcting a brain perfusion measurement using magnetic resonance imaging.

[0011] The patent application US 2004 / 0264752 A1 describes a method for segmenting tissue types in image data acquired by magnetic resonance imaging.

[0012] The patent application WO 2012 / 147011 A1 describes a method for comparing two medical images. The object of the invention is to provide a suitable output of signal values ​​of a combined magnetic resonance positron emission tomography device.

[0013] This object is achieved by a method according to claim 1. This object is further achieved by a combined magnetic resonance positron emission tomography device according to claim 14, a computer program according to claim 16, and a computer-readable storage medium according to claim 17. Advantageous embodiments of the invention are specified in the respective dependent claims.

[0014] The invention utilizes the spatial correspondence obtained after image registration between signal values ​​resulting from a magnetic resonance measurement and signal values ​​resulting from a positron emission tomography measurement. The corresponding signal values ​​are arranged in a matrix and graphically displayed as a multidimensional scatter plot (also known as a scatter diagram).

[0015] A method is provided for displaying the signal values ​​of a combined magnetic resonance positron emission tomography device, comprising the following steps: - Assigning a first image data set with signal values ​​resulting from a magnetic resonance measurement to a second image data set with signal values ​​resulting from a positron emission tomography measurement, - Assigning at least one signal parameter of the first image data set to at least one signal parameter of the second image data set in the form of an n-tuple, where n indicates the number of assigned signal parameters and the n-tuples indicate spatially corresponding signal values, and - Output of an n-dimensional scatterplot by displaying the n-tuples, where each signal parameter is assigned a coordinate axis.

[0016] The scatterplot generated in this way enables a superimposed display of image information from a magnetic resonance measurement and a positron emission tomography measurement. This allows image data sets that depict the same anatomical structure in different ways to be directly compared. Differences, for example, in contrast values, are visualized even more clearly.

[0017] Examples of signal values ​​resulting from a magnetic resonance measurement include the apparent diffusion coefficient (ADC), which indicates the self-diffusion of water in tissue fluid, the T2-weighted intensity, the T1-weighted intensity, the proton density, the T1 relaxation time, the T2 relaxation time, the susceptibility, the perfusion (e.g. ASL (arterial spin labeling) signal intensity or contrast agent inflow), the water content, the fat content or the content of other signal-generating atomic nuclei (such as phosphorus, sodium, fluorine, etc.).

[0018] Examples of signal values ​​resulting from a positron emission tomography measurement include the SUV value (standardized uptake value), which quantifies regional radioactivity concentrations, the attenuation-corrected PET intensity, or the uncorrected PET intensity.

[0019] In a preferred embodiment, exactly one signal parameter of the first image data set is assigned to exactly one signal parameter of the second image data set in the form of a two-dimensional matrix of pixels, and a two-dimensional scatterplot of the corresponding pixel values ​​is output. This allows for a simple, direct comparison of two spatially correlated signal parameters.

[0020] In an advantageous embodiment, exactly one signal parameter of the first image data set is assigned to exactly two signal parameters of the second image data set, or exactly two signal parameters of the first image data set are assigned to exactly one signal parameter of the second image data set in the form of a three-dimensional matrix of voxels, and a three-dimensional scatterplot of the corresponding voxel values ​​is output. This three-dimensional representation also allows for an intuitive comparison of spatially correlated signal parameters.

[0021] In another embodiment, the image data set from the magnetic resonance measurement is acquired in a common time window with the image data set from the positron emission tomography measurement. This achieves not only the spatial correlation established by the first process step (often referred to as image registration), but also a temporal correlation. For optimal temporal correlation, the common time window should be selected so small that just two image acquisitions are possible with the two imaging techniques. This minimizes artifacts resulting from large time intervals between the image acquisitions.

[0022] One embodiment of the invention involves applying a correction method to at least one image data set, either before or after the first method step. This allows further artifacts to be minimized. Possible correction methods include, for example, attenuation corrections of the PET data, distortion corrections of the MR data, motion corrections, or partial volume corrections.

[0023] A further embodiment of the invention provides that the n-tuples displayed in the scatter plot are selected using at least one selection criterion, and that a user is provided with at least one selection tool for selecting at least one distinguished area. This makes it possible to directly select significant image regions and thus, for example, to highlight areas with particular contrast ratios.

[0024] In an advantageous embodiment, the at least one selection means comprises a geometric shape. Suitable geometric shapes include, for example, ellipses, rectangles, triangles, cuboids, or pyramids, which can be used particularly easily to mark corresponding geometric regions in the scatter plot. These regions can, for example, be point clouds of various sizes.

[0025] In an advantageous embodiment, the at least one selection means comprises a separation function. Possible separation functions include, for example, straight lines, polynomials, exponential functions, or trigonometric functions, which can be used particularly easily to separate different regions, such as point clouds in a scatter plot.

[0026] In another embodiment, the data within the selected area is arranged differently from data outside the selected area. This can be achieved, for example, by displaying the marked area of ​​n-tuples in a different color than the area of ​​n-tuples that was not marked. This allows a viewer to quickly and directly identify a relevant image area.

[0027] In a preferred embodiment, the at least one selection criterion leads to a selection of image data in the first and / or second image dataset. This immediately highlights the selected region in the anatomical image dataset, making it easy to see which regions in the image datasets correspond to the selected n-tuples in the scatterplot.

[0028] In a further embodiment, at least one selection criterion is applied to at least one image data set acquired in a further time window. This allows, for example, temporal changes in the image data sets to be tracked. This allows a viewer to quickly and directly detect relevant changes in an image area.

[0029] In a further embodiment, image data and / or signal values ​​of the first and / or second image data set, which are encompassed by the selected area when the first image data set is superimposed with the second image data set, are weighted and can thus influence the superimposition. In this way, for example, the selected area from the scatter plot can be taken from the image data set with signal values ​​resulting from a magnetic resonance measurement, and the remaining area from the image data set with signal values ​​resulting from a positron emission tomography measurement. The reverse procedure is also feasible. Weighting can also comprise the formation of a difference image, in the context of which signal values ​​resulting from a magnetic resonance measurement and signal values ​​resulting from a positron emission tomography measurement are multiplied by factors, such as real numbers.This allows image parameters, such as different contrasts, to be optimized.

[0030] In a preferred embodiment, the at least one area selected by the user is used for segmentation in the first and / or second image data set. Assuming that selected, significant regions represent a particularly salient part of the underlying image data sets, it may be advantageous to segment this region. For this purpose, information from the scatterplot, e.g., bounding edges or curves, can be used to describe the connected area. This leads to a faster workflow, especially for routines that already require segmentation. Furthermore, anomalies in the image data sets can be directly identified.

[0031] Within the scope of the present invention, a combined magnetic resonance positron emission tomography device for displaying signal values ​​is also provided. The combined magnetic resonance positron emission tomography device comprises a detection unit, a processing unit, a control device, and an output unit, and is designed to perform the following steps: - Assigning a first image data set with signal values ​​resulting from a magnetic resonance measurement to a second image data set with signal values ​​resulting from a positron emission tomography measurement by means of the acquisition unit, - Assigning at least one signal parameter of the first image data set to at least one signal parameter of the second image data set in the form of an n-tuple, where n indicates the number of assigned signal parameters and the n-tuples indicate spatially corresponding signal values, by means of the processing unit and - Output of an n-dimensional scatterplot by displaying the n-tuples, where each signal parameter is assigned a coordinate axis, using the output unit.

[0032] Furthermore, the present invention describes a computer program, in particular software, which can be loaded into a memory of a programmable controller or a processing unit of a combined magnetic resonance-positron emission tomography device. With this computer program, all or various previously described embodiments of the method according to the invention can be executed when the computer program is running in the controller or control device of the combined magnetic resonance-positron emission tomography device. The computer program may require programming resources, e.g., libraries and auxiliary functions, to implement the corresponding embodiments of the method.In other words, the claim directed to the computer program is intended to protect, in particular, a computer program or software with which one of the above-described embodiments of the method according to the invention can be carried out or which carries out this embodiment. The software may be source code that still needs to be compiled and linked, or that only needs to be interpreted, or it may be executable software code that only needs to be loaded into the corresponding processing unit for execution.

[0033] Furthermore, the present invention relates to a computer-readable storage medium, e.g., a DVD, a magnetic tape, or a USB stick, on which electronically readable control information, in particular software, is stored. If this control information is read from the data carrier and stored in a controller or processing unit of a combined magnetic resonance positron emission tomography device, all embodiments of the method described above can be carried out.

[0034] The advantages of the combined magnetic resonance positron emission tomography device according to the invention, the computer program according to the invention, and the computer-readable storage medium according to the invention essentially correspond to the advantages of the method according to the invention, which have been detailed above. Features, advantages, or alternative embodiments mentioned herein are also applicable to the other claimed subject matter, and vice versa. In other words, the claims in question, which are directed, for example, to a device, can also be further developed with the features described or claimed in connection with a method. The corresponding functional features of the method are implemented by corresponding modules, in particular by hardware modules.

[0035] In the following, the invention is described and explained in more detail with reference to the embodiments shown in the figures.

[0036] They show: Fig. 1 a schematic representation of a combined magnetic resonance positron emission tomography device according to the invention, Fig. 2 a flow diagram of a method according to the invention and Fig. 3 a schematic representation of the assignment of signal parameters to 2-tuples.

[0037] Fig. Figure 1 shows a schematic representation of a combined magnetic resonance-positron emission tomography device 1 according to the invention. The device consists of a magnetic resonance imaging device 2 and a PET imaging device 3. Instead of the PET imaging device 3, it is equally conceivable to use another radionuclide imaging device, such as a SPECT imaging device. In addition to other components known to those skilled in the art, the PET imaging device 3 has a radiation detector unit 6 for positron recombination radiation with an energy of approximately 511 keV. The preferred embodiment comprises scintillation crystals that convert the high-energy PET radiation into photons detectable by photodiodes. During the annihilation of a positron and an electron (pair formation), two photons with an energy of approximately 511 keV each are produced, whose trajectories enclose an angle of 180°.With the help of the PET radiation detector 6, these photon pairs can be measured coincidentally, allowing a back calculation of the trajectories and thus a spatial determination of the origin of the detected photon pairs in an examination object U. This back calculation allows the determination of the spatial concentration of the tracer in the examination object U. In conjunction with the image information of the magnetic resonance imaging device 2, high-resolution, detailed combination images of the examination object U can be acquired, in which the tracer concentration in its anatomical environment can be recognized. In the exemplary embodiment, the radiation detector unit 6 is arranged in a ring around a center axis ZL of a measuring chamber 4 of the combined magnetic resonance-positron emission tomography device 1, which is oriented essentially parallel to a spatial direction z that corresponds to the orientation of a basic magnetic field of the combined magnetic resonance-positron emission tomography device 1. The ring-shaped arrangement allows a substantially identical distance of an examination object U arranged in the center or in the region of the center axis ZL of the measuring chamber 2 to all pixels of the radiation detector unit 6. For positioning the examination object U, a patient table 5 is arranged in the measuring chamber 2, with the aid of which the examination object U can be displaced along the center axis ZL.

[0038] For magnetic resonance imaging, the measurement chamber 2 of the combined magnetic resonance-positron emission tomography device 1 is surrounded by a superconducting basic field magnet of the magnetic resonance imaging device 2, which generates a homogeneous basic magnetic field oriented in the z-direction in the measurement chamber 2. The current measurement range of the examination object U should lie within a homogeneity volume of the basic magnetic field. Furthermore, the magnetic resonance imaging device 2 has a transmission coil, usually a body coil permanently installed around the measurement chamber in the device, with which radio-frequency signals can be transmitted at the desired magnetic resonance frequency in order to excite the spins in a specific region of the examination object. Furthermore, the magnetic resonance imaging device 2 comprises a gradient coil system, with the aid of which the spatial resolution of magnetic resonance image information can be achieved. The magnetic resonance image information, i.e.The magnetic resonance signals excited in the subject under examination are usually acquired using local coils. In addition, the local coils can also be designed to generate radiofrequency fields that excite the spins, and / or the resulting magnetic resonance signals can be acquired using a body coil. The image processing for the superimposed magnetic resonance and positron emission tomography image representation takes place in a computing unit 7, which in this embodiment consists of a detection unit 8, a processing unit 9 and a control device 10.

[0039] Fig. Figure 2 shows a flow diagram of a method according to the invention. The method comprises method steps 12 to 16, wherein the description of method steps 12 to 16 also includes description parts including the corresponding ones related to Fig. 1 introduced reference symbols may be used.

[0040] In method step 12, the display of signal values ​​from a combined magnetic resonance-positron emission tomography device 1 is started, and a first image data set with signal values ​​resulting from a magnetic resonance measurement and a second image data set with signal values ​​resulting from a positron emission tomography measurement are acquired. The image data set from the magnetic resonance measurement can advantageously be acquired in a common time window with the image data set from the positron emission tomography measurement. Likewise, a correction method can be applied to at least one image data set.

[0041] During method step 13, the first image data set with signal values ​​resulting from a magnetic resonance measurement is assigned to the second image data set with signal values ​​resulting from a positron emission tomography measurement by means of the acquisition unit 8 of the combined magnetic resonance-positron emission tomography device 1.

[0042] In method step 13, exactly one signal parameter of the first image data set can be assigned to exactly one signal parameter of the second image data set in the form of a two-dimensional matrix of pixels and a two-dimensional scatterplot 17 of the corresponding pixel values ​​is output; it is also conceivable that exactly one signal parameter of the first image data set is assigned to exactly two signal parameters of the second image data set or exactly two signal parameters of the first image data set are assigned to exactly one signal parameter of the second image data set in the form of a three-dimensional matrix of voxels and that a three-dimensional scatterplot 17 of the corresponding voxel values ​​is output. In method step 14, at least one signal parameter of the first image data set is assigned to at least one signal parameter of the second image data set in the form of an n-tuple 20 by means of the processing unit 9 of the combined magnetic resonance-positron emission tomography device 1, where n indicates the number of assigned signal parameters and the n-tuples 20 indicate spatially corresponding signal values. Finally, in method step 15, an n-dimensional scatterplot 17 is output by means of the output unit 11 of the combined magnetic resonance-positron emission tomography device 1 by displaying the n-tuples 20, with each signal parameter being assigned a coordinate axis. Method step 16 marks the end of the signal value display.

[0043] In method step 15, a selection of the n-tuples 20 displayed in the scatter plot 17 can also be made using at least one selection criterion, and at least one selection means for selecting at least one distinguished area can be made available to a user for the selection. The at least one selection means can comprise a geometric shape 18 or a separation function 19. The data within the selected area can be arranged differently than data outside the selected area, and the at least one selection criterion can lead to a selection of image data in the first and / or second image data set. It is also possible for the at least one selection criterion to be applied to at least one image data set acquired in a further time window. During method step 15, image data and / or signal values ​​of the first and / or second image data set, which are comprised by the selected area when the first image data set is superimposed with the second image data set, can be weighted, and it is possible for the at least one area selected by the user to be used for segmentation in the first and / or second image data set.

[0044] Fig. Figure 3 shows a schematic representation of the assignment 14 of signal parameters to 2-tuples 20. Signal parameters of the first image data set are represented as rectangles, and signal parameters of the second image data set are represented as circles. The 2-tuples 20 indicate spatially corresponding signal values. Exactly one signal parameter of the first image data set is assigned to exactly one signal parameter of the second image data set in the form of a two-dimensional matrix of pixels.

[0045] Furthermore, a selection of the 2-tuples 20 displayed in the scatterplot 17 is performed, with the selection means comprising a geometric shape 18, in this case a triangle. Ellipses, rectangles, cuboids, pyramids, and others can also be considered as geometric shapes 18, which can be used particularly easily to mark corresponding geometric areas in the scatterplot.

[0046] The selection means can also include a separation function 19, here, for example, in the form of a straight line. Separation functions 19 can also include, for example, polynomials, exponential functions, trigonometric functions, and others, which can be used particularly easily to separate different regions, such as point clouds in a scatter plot.

[0047] The 2-tuples 20 in the area selected by the selection means can, for example, be displayed in a different color than the area of ​​2-tuples 20 that does not correspond to the selected area. This area can then preferably also be highlighted in the underlying anatomical image datasets, so that it is easily visible which areas in the image datasets the selected 2-tuples 20 correspond to in the scatter plot. By creating difference images, image parameters, such as different contrasts, can also be optimized.

[0048] In summary, the invention relates to a method, a computer program, and a computer-readable storage medium for displaying signal values ​​from a combined magnetic resonance-positron emission tomography device. The spatial correspondence between signal values ​​resulting from a magnetic resonance measurement and signal values ​​resulting from a positron emission tomography measurement is utilized, and the corresponding signal values ​​are arranged in matrix form and graphically displayed as a multidimensional scatterplot.

Claims

[1] Method for displaying signal values ​​of a combined magnetic resonance positron emission tomography device (1), comprising the steps: - Assigning (13) a first image data set with signal values ​​resulting from a magnetic resonance measurement to a second image data set with signal values ​​resulting from a positron emission tomography measurement, - Assigning (14) at least one signal parameter of the first image data set to at least one signal parameter of the second image data set in the form of an n-tuple (20), where n indicates the number of assigned signal parameters and the n-tuples (20) indicate spatially corresponding signal values ​​and - Output (15) of an n-dimensional scatterplot (17) by displaying the n-tuples (20), wherein each signal parameter is assigned a coordinate axis. [2] Method according to claim 1, wherein exactly one signal parameter of the first image data set is assigned to exactly one signal parameter of the second image data set in the form of a two-dimensional matrix of pixels and wherein a two-dimensional scatterplot (17) of the corresponding pixel values ​​is output. [3] Method according to claim 1, wherein exactly one signal parameter of the first image data set is assigned to exactly two signal parameters of the second image data set or wherein exactly two signal parameters of the first image data set are assigned to exactly one signal parameter of the second image data set in the form of a three-dimensional matrix of voxels and wherein a three-dimensional scatterplot (17) of the corresponding voxel values ​​is output. [4] Method according to one of claims 1 to 3, wherein the image data set of the magnetic resonance measurement is acquired in a common time window with the image data set of the positron emission tomography measurement. [5] Method according to one of claims 1 to 4, wherein before or after the assignment (13) of a first image data set with signal values ​​resulting from a magnetic resonance measurement to a second image data set with signal values ​​resulting from a positron emission tomography measurement, a correction method for correcting image artifacts is applied to at least one image data set. [6] Method according to one of claims 1 to 5, wherein a selection of the n-tuples (20) shown in the scatterplot (17) is carried out by means of at least one selection criterion and at least one selection means for selecting at least one distinguished area is made available to a user for the selection. [7] The method of claim 6, wherein the at least one selection means comprises a geometric shape (18). [8] Method according to claim 6, wherein the at least one selection means comprises a separation function (19). [9] Method according to one of claims 6 to 8, wherein the data within the selected area are arranged differently from data outside the selected area. [10] Method according to one of claims 6 to 9, wherein the at least one selection criterion leads to a selection of image data in the first and / or second image data set. [11] Method according to one of claims 6 to 10, wherein at least one selection criterion is applied to at least one image data set acquired in a further time window. [12] Method according to one of claims 6 to 11, wherein image data and / or signal values ​​of the first and / or the second image data set, which are comprised by the selected area when the first image data set is superimposed with the second image data set, are weighted. [13] Method according to one of claims 6 to 12, wherein the at least one area selected by the user is used for segmentation in the first and / or second image data set. [14] Combined magnetic resonance positron emission tomography device (1) for displaying signal values, wherein the magnetic resonance positron emission tomography device (1) includes a detection unit (8), a processing unit (9), a control device (10) and an output unit (11) and is designed to carry out the following steps: - Assigning (13) a first image data set with signal values ​​resulting from a magnetic resonance measurement to a second image data set with signal values ​​resulting from a positron emission tomography measurement by means of the acquisition unit (8), - Assigning (14) at least one signal parameter of the first image data set to at least one signal parameter of the second image data set in the form of an n-tuple (20), where n indicates the number of assigned signal parameters and the n-tuples (20) indicate spatially corresponding signal values, by means of the processing unit (9) and - Output (15) of an n-dimensional scatterplot (17) by displaying the n-tuples (20), wherein each signal parameter is assigned a coordinate axis, by means of the output unit (11). [15] Combined magnetic resonance positron emission tomography device (1) according to claim 14, wherein the acquisition unit (8), the processing unit (9), the control device (10) and the output unit (11) are designed to carry out a method according to one of claims 1 to 13. [16] Computer program which can be loaded directly into a memory of a programmable control device (10) of a combined magnetic resonance positron emission tomography device (1), with program means for carrying out all steps of the method according to one of claims 1 to 13 when the program is executed in the control device (10) of the combined magnetic resonance positron emission tomography device (1). [17] Electronically readable data carrier with electronically readable control information stored thereon, which is designed such that it carries out the method according to one of claims 1 to 13 when the data carrier is used in a control device (10) of a combined magnetic resonance positron emission tomography device (1).

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