X-ray system and ct system

Abstract

The invention relates to an X-ray system for inspecting N objects (O), in particular N battery modules for quality control, having the following features: a linear accelerator (1), which is designed to emit X-rays (R) with an energy ≥ 1 MeV at a conical radiation angle (8); N X-ray detectors (13a, 13b, 13c, 13d), which are each designed to detect the X-rays (R) in a partial cone (8a, 8b, 8c, 8d) of the conical radiation angle (8); N axes of rotation (12a, 12b, 12c, 12d) and (4a, 4b) for N objects (O), which are each assigned to a partial cone (8a, 8b, 8c, 8d) and are arranged in each of them; a collimator (3, 3'), which is designed with two stages, wherein a first stage defines the conical radiation angle (8) at which the X-rays (R) are emitted, and wherein a second stage (10) defines the N partial cones (8a, 8b, 8c, 8d).

Description

[0001] X-ray system and CT system

[0002] Description

[0003] Embodiments of the present invention relate to an X-ray system and a CT system. Further embodiments relate to a method for operating the X-ray system and a method for operating the CT system. Further embodiments relate to a corresponding computer program. In general, the embodiments of the invention lie in the field of high-throughput computed tomography for quality assurance of vehicle battery modules. Preferred embodiments provide an X-ray system or computed tomography system with a linear accelerator and a multi-beam arrangement.

[0004] The production of battery modules for electromobility applications places high demands on the quality of the internal module structure. Therefore, during the development of such energy storage systems, computed tomography examinations are performed, which visualize the internal structure and thus allow the detection of various quality parameters. These CT procedures are generally based on an X-ray tube and a planar X-ray detector that captures the X-ray shadow cast by the battery module under investigation. The battery module is rotated in the beam using a rotation axis and thus captured from a variety of viewing angles. Following the scan, the projection data obtained in this way are calculated into a volume using a mathematical reconstruction operation, which enables the module quality to be assessed.

[0005] The X-ray technology used for this purpose usually has only limited radiation energy, which often leads to inadequate image quality in the reconstructed volume and thus limits the reliability of the assessment. In general, the costs of quality assurance are extremely high when high reliability is required. Therefore, there is a need for an improved approach.

[0006] The object of the present invention is to create a concept that creates an improved compromise between high reliability in the quality assurance of battery modules in combination with high cost efficiency.

[0007] The problem is solved by the subject matter of the independent patent claims.

[0008] FH230704PDE-2024196511. DOCX Embodiments of the present invention provide an X-ray system for examining N objects, such as battery modules. N battery modules can thus be examined for quality control using the X-ray system. The X-ray system comprises a linear accelerator configured to emit X-rays with an energy of > 1 MeV at a conical radiation angle, e.g., 25° or 180°, and generally any angle. Furthermore, the X-ray system has N X-ray detectors, each configured to detect the X-rays in a partial cone of the conical radiation angle. One of at least N axes of rotation for the at least N objects is assigned to each of the partial cones and is also arranged in each partial cone.According to embodiments, the arrangement of the rotation axis, which may include an object holder for the at least N objects, is arranged between the linear accelerator and the respective one of the N X-ray detectors. Furthermore, the X-ray system has a collimator that is designed in two stages, with a first stage forming or defining the conical radiation angle and a second stage defining the N partial cones.

[0009] Embodiments of the present invention are based on the finding that by using N X-ray detectors, N objects can be examined or x-rayed in N separate partial cones, e.g., for quality assurance purposes. The N partial cones result from a conical X-ray spectrum emitted by a linear accelerator. The separate examination or subsequent simultaneous examination of the N objects is achieved by providing each object with its own axis of rotation. The advantage of this arrangement is that the most cost-intensive component can be used not only for x-raying one object, but for x-raying a series of objects or, in general, for multiple objects. This increases throughput and thus also the investment costs per object to be examined.The collimator, which divides the X-ray radiation into the partial cones, advantageously images the high-energy X-ray radiation > 1 MeV in such a way that there are no disadvantages compared to the emission of only one entire cone.

[0010] According to embodiments, the N X-ray detectors are designed as line detectors or, preferably, as area detectors. Each of the N X-ray detectors can, according to embodiments, have its own detector electronics. According to further embodiments, it would also be conceivable for the electronics of at least two of the N detectors to be combined. It would also be possible for two adjacent X-ray detectors to overlap one another, namely in such a way that the electronics form an overlap and thus the rear electronics are protected from the projection of the X-ray radiation by the front electronics. The advantage of this is that the electronics are X-ray sensitive and thus separate means for protecting the electronics from X-ray radiation, at least for the rear electronics, can be dispensed with. According to embodiments, the electronics have means for protection against X-ray radiation, such as, for example,an absorber arranged upstream of the X-ray cone. According to alternative embodiments, the electronics are arranged in an area protected from the X-ray radiation. According to advantageous embodiments, such an area can be formed by a shadow cone. For example, the electronics of the N X-ray detectors can be arranged between the partial cones. Alternatively, it would also be conceivable for the electronics to be arranged in an area shielded by one or more shielding elements. The one or more shielding elements can be arranged between the partial cones. According to further embodiments, it would also be conceivable for the electronics to be shielded by a respective shielding element that is either part of the collimator (i.e., in an area between the linear accelerator and the object) and / or is provided as a dedicated shielding element in an area between the object and the detector.According to further embodiments, the collimator can be designed to create a shadow cone between the partial cones. The electronics, for example, can be positioned in this shadow cone.

[0011] According to embodiments, the N X-ray detectors can be arranged linearly, circularly, or elliptically (around the linear accelerator or the center of the conical radiation angle). Overlap can also be provided in both the linear and circular arrangements. As already explained above, the overlap can be provided particularly in the electronics area of ​​the respective detector elements.

[0012] According to embodiments, the axis of rotation between the linear accelerator and the detector is arranged at a distance ratio of the distances from the linear accelerator to the axis of rotation and the axis of rotation to the X-ray detector such that at least 75% or at least 95% of the object can be detected simultaneously. If, for example, a possible object size of 10x10 cm or 50x20 cm is assumed, this results in the appropriate arrangement and dimensioning of the object holder on the axis of rotation. According to a further embodiment, it would also be conceivable to provide a lifting movement in addition to the rotating movement. In this respect, the axis of rotation can be extended by an additional lifting axis so that, in addition to the rotating movement, a lifting movement of the object also occurs, either together or independently of one another.

[0013] Another embodiment provides a CT system comprising an X-ray system as described above and a CT calculation unit. This CT calculation unit performs reconstruction for the N objects independently of one another.

[0014] Further embodiments relate to a method for operating the X-ray system. The core element of the method is the formation of N partial cones for irradiating N objects. According to embodiments, the formation can be achieved by the collimator, and in particular by the second stage of the collimator.

[0015] Another embodiment provides a method for operating the defined CT system. The method comprises a step of processing a plurality of radiographs per object, assigned to the different rotation angles, in order to obtain, for example, a CT reconstruction for each object. The method can be computer-implemented according to embodiments.

[0016] Embodiments of the present invention are explained with reference to the accompanying drawings. They show:

[0017] Fig. 1 is a schematic representation of an X-ray system according to a basic embodiment;

[0018] Fig. 2 is a schematic representation of an X-ray system according to an extended embodiment; and

[0019] Fig. 3 is a schematic representation of an X-ray system according to the prior art.

[0020] Before exemplary embodiments of the present invention are explained below with reference to the accompanying drawings, it should be noted that elements and structures with the same function are provided with the same reference numerals, so that the description of them is applicable to one another or interchangeable.

[0021] Before embodiments of the present invention are explained, the prior art is explained with reference to Fig. 3.

[0022] Fig. 3 shows an X-ray system with the central components radiation source 1 and detector 2. The radiation source can be a conventional X-ray tube or - according to embodiments of the invention - a linear accelerator designed to emit X-ray radiation R along an X-ray cone 8. The X-ray cone 8 can be limited or defined by means of a collimator 3 - and this is how it is used in embodiments of the invention explained below. The X-ray radiation is emitted by the radiation source 1 along the central plane 7 so that a detector 2 (the housing of the detector is illustrated schematically here) can receive the X-ray radiation R. For this purpose, the X-ray detector has an X-ray-sensitive layer 6, but can also be implemented differently, e.g., using a scintillator.

[0023] A turntable is arranged between the X-ray source 1 and the X-ray detector 2. The turntable functions as an object holder. According to exemplary embodiments, the turntable can have an object holder. The turntable or the object holder is designed to hold the object O and rotate it during the recording in order to perform radiographic images from multiple object angles for a CT reconstruction. Consequently, the turntable 4 or the rotation axis 4 is designed to rotate, e.g., by 360°. With regard to its dimensions, the turntable is adapted to the object O. According to preferred applications, the object O is a battery, for example, with dimensions of 10x10 or 50x50, in a format with different lengths.

[0024] Battery modules have a high density, so it was recognized that a special combination of radiation source 1 and radiation detector 2 is advantageous. The following was recognized through exemplary embodiments: Due to the high density of battery modules O, a linear accelerator with energies above 1 MeV is useful for optimal fluoroscopy. Due to the very high acquisition and operating costs (expenses for regular inspections, for example) of a linear accelerator, sufficiently good imaging quality can be achieved, but the above-defined goal of cost-effectiveness is missed.

[0025] Embodiments of the present invention are based on the finding that, especially for applications on battery modules with typical volume cross-sections between 10 x 10 cm and 50 x 20 cm and different lengths, profitability can be significantly increased by introducing additional beam axes, also called beamlines. These beam axes, or beam axes, consist, according to embodiments, of a dedicated X-ray detector and one or more rotation axes in the cone beam of the linear accelerator. This optimally utilizes the beam cone / beam cone spanned by the linear accelerator. This concept is explained below using Fig. 1.

[0026] Fig. 1 shows an X-ray system with a radiation source 1, a collimator 3 and two detectors 13a and 13b.

[0027] The collimator 2, on the one hand, limits the beam cone 8 in its outer contour and divides the beam cone 8 into two partial cones 8a and 8b. The beam cone 8a is received by the detector 13a, while the beam cone 8b is received by the detector 13b. In each beam cone 8a and 8b, a respective turntable 4a or 4b is provided for the corresponding objects O. With regard to the geometry, it should be noted that, according to exemplary embodiments, the turntables 4a and 4b are arranged in the respective beam cones 8a and 8b, specifically in the area between the radiation source 1 or collimator 2 and the respective X-ray detector 13a or 13b. The image scale of the object O can be determined by the distance ratio of the distances between the radiation source 1 and the object holder 4a / 4b and between the object holder 4a / 4b and the detector 13a and 13b. The image scale is selected according to embodiments so that a complete image of the object O is possible.Now that the structure has been explained, the functionality will be explained. The linear accelerator emits X-rays R with energies above 1 MeV at a conical radiation angle (cf. beam cone 8). By rotating the objects O using the turntables 4a and 4b, several objects can be x-rayed simultaneously, i.e. parallel to one another, and from different object angles, so that CT reconstruction is possible. The x-ray images are detected by the respective detectors 13a and 13b. In this embodiment, two (N = 2) object holders or turntables 4a and 4b are provided together with two (N = 2) detectors 13a and 13b. Here, the detectors are arranged linearly next to one another, although alternatively a circular or elliptical arrangement, e.g. around the X-ray source 1 or the focal spot of the X-ray source 1, would also be conceivable.It should be noted here that the number of detectors and the number of slides do not necessarily have to be the same. For example, two slides can be used per detector.

[0028] According to embodiments, the detectors can be flat panel detectors that can simultaneously detect the majority of the battery module O. The detection range is adjusted, as already explained above, via the distance ratio of the object carrier 4a or 4b relative to the two elements 1 and 13a / 13b.

[0029] According to exemplary embodiments, each X-ray detector 12a and 12b can have the sensitive detector surface 6 and corresponding detector electronics 5. In the present case, the beam cone 8 is divided into two parts by the line 7 (central beam plane). Since the detector surface 6 does not extend across the full width of the detector 13a or 13b, according to exemplary embodiments, the rotation axis 4a or 4b can also be arranged decentrally in the respective partial cone 8a and 8b. Here, each is displaced slightly towards the central beam plane 7. According to exemplary embodiments, with n = 2, the detector electronics 5 can be arranged in the edge region of the X-ray beam cone 8 (outer edge of the X-ray beam cone 8 defined by the beam collimator 3).According to further embodiments, it would also be conceivable for the beam collimator 3 to further restrict the aperture angle of the X-ray beam cone 8, so that the electronics 5 are arranged in a sealed-off area, i.e., protected from the X-ray radiation R. According to further embodiments, it would also be conceivable for a so-called shielding block to be provided to protect the detector electronics 5 from the X-ray radiation R. This shielding block is provided, for example, in the area of ​​the electronics 5 of the X-ray detector 13a and is provided with the reference numeral 9.

[0030] With reference to Fig. 2, a further embodiment is explained in which again N X-ray detectors 13a-13d and N rotation axes 4a-4d are provided in combination with the radiation source 1 or the collimator 3'. In this embodiment, N = 4, i.e. four objects O can be x-rayed simultaneously using the four detectors 13a-13d. The four objects O are arranged on the respective rotation axes 4a-4d. According to one embodiment, the detectors 13a and 13b are designed to partially overlap, as are the detectors 13c and 13d. The detector electronics 5 is provided in the overlap region, while the sensitive surface 6 is provided in the non-overlapping region. According to one embodiment, precisely this overlap region, which overlaps in alignment as seen in the direction of the X-ray radiation, is provided with a specially shaped shielding block 11.This shielding block, for example, has a shape adapted to the angle of incidence (e.g., a cone shape). According to exemplary embodiments, the thickness depends on the expected energy of the X-ray radiation R and on the selected shielding material of the shielding block 11. In this exemplary embodiment, two shielding blocks 11 are provided, namely one in the overlapping area 13a and 13b and one in the overlapping area 13c and 13d.

[0031] Additionally or alternatively, the collimator 3' can also be expanded by an additional collimator for limiting the cone beam to the additional detectors. This element is provided with the reference numeral 11 and forms a shadow cone 10k between the partial cones 8a, 8b, 8c, and 8d. As can be seen, the shadow cone 10k is only provided between the cones 8a and 8b and between the cones 8c and 8d. According to preferred embodiments, the electronics 5 of the detector elements 13a, 13b, 13c, and 13d are arranged precisely in this shadow cone 10k or in alignment with this shadow cone 10k. The additional collimator element 10 can also be combined with the shielding block 11 according to embodiments. With regard to their dimensions, these can be adapted to one another according to embodiments.

[0032] This means that, according to exemplary embodiments, one stage of the collimator divides the X-ray cone into several partial cones 8a, 8b, 8c, and 8d, and in doing so inserts one or more shadow cones 10k between two partial cones 8a and 8b. Advantageous here is, on the one hand, the good separation of the beam cones, so that mutual interference during simultaneous measurement can be excluded, and, on the other hand, the possibility of positioning the electronics in this shadow cone, as already mentioned. At this point, it should be noted that the element 10 for limiting the cone beam 8 can be referred to as the second stage of the collimator 3'. The first stage of the collimator limits the cone beam to the sides, while the second stage of the collimator 10 subdivides the cone beam into partial cone beams.With regard to the combination of collimator 3' with additional collimator element 10, it should be noted that this creates a special beam collimator that defines an optimal beam field for each detector axis pair.

[0033] At this point, it should be noted that due to the overlap of detectors 13a and 13b, or 13c and 13d, the distances between detector surfaces 6 and radiation source 1 may vary slightly. To ensure an image of the same size, the distance between the respective rotation axes, for example, 12c and 12d, may also vary slightly, according to embodiments.

[0034] At this point, it should be noted that, in the simplest variant, each detector can have a detector surface (line-shaped or area-shaped). In a further configuration, each detector element 13a-13d has the corresponding electronics 5. According to embodiments, electronics for two sensitive surfaces 6 can also be combined, for example, if they are arranged centrally in the shielded area / shadow cone. Furthermore, according to embodiments, each detector element 13a-13d also has a corresponding detector housing.

[0035] In the above embodiments, it was assumed that the number N for the number of rotation axes is identical to the number of detectors. According to other embodiments, the number of rotation axes can also be greater than N.

[0036] According to a further embodiment, it would be conceivable to provide a lifting axis in addition to the rotational axes 12a-12d, e.g., mounted below or on the rotational axis itself, in order to perform a lifting movement in addition to the rotational movement. This lifting movement can be performed simultaneously with the rotational movement in order to enable a helical detection of the mostly elongated battery modules O. This advantageously minimizes the so-called Feldkamp artifacts. According to a further embodiment, the movement system can of course also be different, such as having a serial movement sequence. With regard to the rotational movements of the rotational axes 12a-12d, it should be noted that these can rotate individually or synchronously.

[0037] A further embodiment relates to a CT system in which a reconstruction unit (calculation unit) is provided which carries out the CT reconstruction (volume calculation) based on the plurality of radiographs of the object O.

[0038] According to one embodiment, a method relates to operating the CT system with the central step of calculation. This method can be computer-implemented according to a preferred embodiment.

[0039] A further embodiment relates to a method for operating the X-ray device with the central step of splitting the beam cone into partial beam cones, e.g. with the aid of the collimator.

[0040] Although some aspects have been described in the context of a device, it should be understood that these aspects also represent a description of the corresponding method, so that a block or component of a device can also be understood as a corresponding method step or as a feature of a method step. Analogously, aspects described in the context of or as a method step also represent a description of a corresponding block, detail, or feature of a corresponding device. Some or all of the method steps may be performed by (or using) a hardware apparatus, such as a microprocessor, a programmable computer, or an electronic circuit. In some embodiments, some or more of the key method steps may be performed by such an apparatus.

[0041] Depending on specific implementation requirements, embodiments of the invention may be implemented in hardware or software. The implementation may be performed using a digital storage medium, such as a floppy disk, a DVD, a Blu-ray Disc, a CD, a ROM, a PROM, an EPROM, an EEPROM, or a FLASH memory, a hard disk, or other magnetic or optical storage device storing electronically readable control signals that can interact or cooperate with a programmable computer system to perform the respective method. Therefore, the digital storage medium may be computer-readable.

[0042] Some embodiments according to the invention thus comprise a data carrier having electronically readable control signals capable of interacting with a programmable computer system such that one of the methods described herein is carried out.

[0043] In general, embodiments of the present invention may be implemented as a computer program product having a program code, wherein the program code is effective to perform one of the methods when the computer program product is run on a computer.

[0044] The program code can, for example, also be stored on a machine-readable medium.

[0045] Other embodiments include the computer program for performing one of the methods described herein, wherein the computer program is stored on a machine-readable medium. In other words, one embodiment of the method according to the invention is thus a computer program that has program code for performing one of the methods described herein when the computer program is executed on a computer.

[0046] A further embodiment of the method according to the invention is thus a data carrier (or a digital storage medium or a computer-readable medium) on which the computer program for carrying out one of the methods described herein is recorded.

[0047] A further embodiment of the method according to the invention is thus a data stream or a sequence of signals that represents the computer program for carrying out one of the methods described herein. The data stream or the sequence of signals can be configured, for example, to be transferred via a data communication connection, for example via the Internet. A further embodiment comprises a processing device, for example a computer or a programmable logic component, that is configured or adapted to carry out one of the methods described herein.

[0048] A further embodiment comprises a computer on which the computer program for performing one of the methods described herein is installed.

[0049] A further embodiment according to the invention comprises a device or system designed to transmit a computer program for performing at least one of the methods described herein to a recipient. The transmission can be electronic or optical, for example. The recipient can be, for example, a computer, a mobile device, a storage device, or a similar device. The device or system can, for example, comprise a file server for transmitting the computer program to the recipient.

[0050] In some embodiments, a programmable logic device (e.g., a field-programmable gate array, an FPGA) may be used to perform some or all of the functionalities of the methods described herein. In some embodiments, a field-programmable gate array may cooperate with a microprocessor to perform any of the methods described herein. In general, in some embodiments, the methods are performed by any hardware device. This may be general-purpose hardware such as a computer processor (CPU) or method-specific hardware such as an ASIC.

[0051] The above-described embodiments are merely illustrative of the principles of the present invention. It is understood that modifications and variations of the arrangements and details described herein will be apparent to others skilled in the art. Therefore, it is intended that the invention be limited only by the scope of the following claims and not by the specific details presented in the description and explanation of the embodiments herein.

[0052] Object (O)

[0053] X-rays (R)

[0054] Linear accelerator radiation source with photon energies above 1 MeV (1)

[0055] X-ray detector outer casing (2)

[0056] Beam collimator of the linear accelerator to reduce housing transmission radiation (3, 3')

[0057] Rotation axis with battery module to be examined (4) (12a, 12b, 12c, 12d) (4a, 4b)

[0058] Detector electronics (5)

[0059] Sensitive detector surface (6)

[0060] Central ray plane (7)

[0061] Outer edge of the X-ray cone beam defined by beam collimator, radiation angle (8)

[0062] Partial cones (8a, 8b, 8c, 8d)

[0063] Shielding block to protect the detector electronics from radiation (9)

[0064] Additional beam collimators to limit the cone beam to the additional detectors, second stage (10)

[0065] X-ray detector (13a, 13b, 13c, 13d)

[0066] Specially shaped shielding blocks to protect the detector electronics when using additional

[0067] Beam axes, means of protection (11)

[0068] Additional rotary axes, each with a battery module to be measured, to increase throughput (12)

[0069] Additional detectors to increase throughput (13)

Claims

Patent claims 1. X-ray system for examining N objects (O), in particular N battery modules for quality testing, having the following features: a linear accelerator (1) designed to emit X-ray radiation (R) with an energy > 1 MeV at a conical radiation angle (8); N X-ray detectors (13a, 13b, 13c, 13d), each designed to detect the X-ray radiation (R) in one of N mutually separated partial cones (8a, 8b, 8c, 8d) of the conical emission angle (8); at least N axes of rotation (12a, 12b, 12c, 12d) and (4a, 4b) for N objects (O), each assigned to one of the N mutually separated partial cones (8a, 8b, 8c, 8d) and arranged in each; a collimator (3, 3') designed in two stages, wherein a first stage defines the conical emission angle (8) in which the X-ray radiation (R) is emitted, and wherein a second stage (10) defines the N mutually separated partial cones (8a, 8b, 8c, 8d).

2. X-ray system according to claim 1, wherein the N X-ray detectors (13a, 13b, 13c, 13d) are designed as line detectors or flat image detectors.

3. X-ray system according to one of the preceding claims, wherein each of the N X-ray detectors (13a, 13b, 13c, 13d) has an electronics (5) or wherein at least two of the N detectors have a common electronics (5).

4. X-ray system according to claim 3, wherein the electronics (5) is designed with means for protection (11) against X-ray radiation (R) and / or wherein the electronics (5) is arranged in an area protected against X-ray radiation (R).

5. X-ray system according to claim 3 or 4, wherein the N X-ray detectors (13a, 13b, 13c, 13d) are designed to overlap; or wherein the N X-ray detectors (13a, 13b, 13c, 13d) are designed to overlap and the electronics (5) of the N X-ray detectors (13a, 13b, 13c, 13d) are arranged in an overlap region.

6. X-ray system according to one of claims 3, 4 or 5, wherein the electronics (5) of the N X-ray detectors (13a, 13b, 13c, 13d) are arranged between the partial cones (8a, 8b, 8c, 8d) and / or in a region shielded by one or more shielding elements (10, 11), wherein the one or more shielding elements (10, 11) are arranged between the partial cones (8a, 8b, 8c, 8d); and / or wherein the electronics (5) is shielded by a shielding element (10, 11) that is either part of the collimator (3, 3') and / or is provided as a dedicated shielding element (10, 11) in a region between the object (O) and the detector.

7. X-ray system according to one of the preceding claims, wherein the collimator (3, 3') is designed to generate a shadow cone between the partial cones (8a, 8b, 8c, 8d) or to generate a shadow cone for the arrangement of an electronics (5) between the partial cones (8a, 8b, 8c, 8d).

8. X-ray system according to one of the preceding claims, wherein the axis of rotation (12a, 12b, 12c, 12d) and (4a, 4b) between the linear accelerator (1) and the respective detectors is arranged in a distance ratio of the distances from the linear accelerator (1) to the axis of rotation (12a, 12b, 12c, 12d) and (4a, 4b) and the axis of rotation (12a, 12b, 12c, 12d) and (4a, 4b) to the X-ray detector (13a, 13b, 13c, 13d) such that at least 75% or at least 95% of the object (O) can be detected simultaneously.

9. X-ray system according to one of the preceding claims, wherein the N X-ray detectors (13a, 13b, 13c, 13d) are arranged linearly or circularly or linearly overlapping or circularly within the conical radiation angle (8).

10. X-ray system according to one of the preceding claims, wherein the rotation axes (12a, 12b, 12c, 12d) and (4a, 4b) are designed to be rotated individually and / or synchronously.

11. X-ray system according to one of the preceding claims, wherein the rotation axes (12a, 12b, 12c, 12d) and (4a, 4b) are extended by an additional lifting axis, so that a lifting movement of the object (O) can take place together with or independently of a rotational movement.

12. X-ray system according to one of the preceding claims, wherein the N mutually separated partial cones (8a, 8b, 8c, 8d) are separated by one or more intermediate shadow cones (10k); or wherein the N mutually separated partial cones (8a, 8b, 8c, 8d) are separated by one or more intermediate shadow cones (10k), wherein in the region of the shadow cones the radiation intensity is reduced compared to the partial cones or is reduced by at least 50% 13. X-ray system according to claim 12, wherein an electronics (5) is arranged in the shadow cone (10k).

14. CT system comprising an X-ray system according to one of the preceding claims and a CT calculation unit, wherein the CT calculation unit is designed to carry out the CT reconstruction for the N objects (O) independently of one another.

15. A method for operating an X-ray system according to one of claims 1 to 14, wherein the method comprises the step of forming N partial cones (8a, 8b, 8c, 8d) for irradiating N objects (O).

16. A method for operating a CT system according to claim 15, wherein the method comprises the step of processing a plurality of radiographs per object (O) associated with different angles of rotation.

17. A computer program for carrying out the method according to claim 17 when the method runs on a CT system.

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