Method for producing a detector module and radiation source module for use in such a method

Abstract

The invention relates to a method for producing a detector module comprising e. Firstly providing (S1) a stack arrangement comprising a detection element (1) and an anti-scatter grid (3), wherein a radiation-curing adhesive (5) is present at least partially on a surface of the detection element (1) facing the anti-scatter grid (3), which is in contact with both the anti-scatter grid (3) and the detection element (1), f. Second provision (S2) of a radiation source module (7) comprising a planar radiation source (9) and a collimation unit (11) arranged parallel thereto, wherein the collimation unit (11) is divided into a plurality of sub-regions (12), each of which extends over a partial surface area of the radiation source (9), and wherein each of the partial regions (12) of the collimation unit (11) is designed to collimate radiation (13) emitted by the partial surface area of the radiation source (9) assigned to it, g. Positioning (S3) the radiation source module (7) relative to the stack arrangement on a side of the anti-scatter grid (11) facing away from the detection element (1), h. Exposing (S4) the stack arrangement by means of the radiation source module (7) and thus curing the radiation-curing adhesive (5) so that an adhesive-based connection is produced between the anti-scatter grid (3) and detector element (1).

Description

The invention relates to a method for producing a detector module from a stack arrangement comprising a detection element and a scattering radiation grating, wherein a radiation source module is provided for exposing the stack arrangement and thus curing a radiation-curing adhesive, which has a planar radiation source and a collimation unit arranged parallel thereto. The invention also relates to a radiation source module for use in such a method.X-ray imaging apparatuses (X-ray apparatuses for short) usually have an X-ray source and an X-ray detector (X-ray detector for short), which are arranged in a manner opposite one another. During operation of the X-ray device, the X-ray radiation emitted by the X-ray source and, if appropriate, partially attenuated by an examination object, for example a patient and / or a patient and / or an examination phantom and / or a workpiece, is detected by means of the X-ray detector. The X-ray detector is configured to output a (measurement) signal corresponding to the intensity of the incident X-ray radiation. In particular, the X-ray detector has a plurality of image points, in particular pixels and / or voxels, which serve for the two-dimensionally resolved detection of the intensity distribution of the incident X-ray radiation.During operation of the X-ray device, the X-ray radiation emitted by the X-ray radiation source is not only attenuated to different extents by the examination object, but is also partially scattered at an angle to the original radiation direction, which usually runs radially with respect to the X-ray radiation source. These scattered rays ("scattered rays") cause, when incident on the X-ray detector, distortion of the image reconstructed from the intensity distribution on account of their superposition with the (main) X-rays incident in the original radiation direction. In particular, these stray beams result in a reduction in the contrast of the reconstructed image.In order to reduce the effects of scattered radiation, an X-ray detector is frequently assigned a so-called anti-scatter grid (also referred to as an "anti-scatter grid" or anti-scatter filter), which is connected upstream of the X-ray-sensitive elements of the X-ray detector in the radiation direction. Such scattered radiation grids usually have a grid-like structure formed by X-ray absorbing walls arranged crosswise and X-ray transmissive channels formed thereby, wherein each grid opening, i.e. each channel, forms a type of radiation channel which runs in the direction of the main X-rays. Scattered radiation, on the other hand, is absorbed by the X-ray absorbing walls. In most cases, each radiation channel is assigned to an individual pixel or a small number of pixels of the detector. The filtering effect of the anti-scatter grid with respect to the scattered radiation increases with the height of the X-ray-absorbing walls in the direction of radiation incidence and the smaller the distance between them is formed (= aspect ratio of a channel of the anti-scatter grid).Such an X-ray detector can be formed from one or also a plurality of detector modules each comprising a stack arrangement of a detection element, configured for detecting the X-ray radiation, and a scattered radiation grating. During assembly of the stack assemblies, these must be assembled precisely and with sufficient stability. In this case, inter alia, adhesive connections between anti-scatter grids and detection element are also used, in particular also using radiation-curing adhesives.However, one difficulty arises from the fact that the radiation for curing such a radiation-curing adhesive must reach the joint location between the anti-scatter grid and the detection element. Lateral accessibility is often only possible to a limited extent or not at all, so that an exposure through the anti-scatter grid may be necessary. However, the function of the scattered radiation grating in the module is, as described above, to absorb scattered radiation, that is to say radiation which does not impinge in parallel. Light sources for curing adhesives (such as mercury vapor lamps or LEDs) usually emit uncollimated light which is largely absorbed by the anti-scatter grid and is then accordingly no longer available for curing the adhesive. This results in long exposure times which extend further with increasing aspect ratio of the anti-scatter grid, which is associated with disadvantages for the process time in production, or else necessary high output intensities. Both furthermore result in a higher heat input into the anti-scatter grid or the stack arrangement, which can have a negative effect on the positioning accuracy of the anti-scatter grid relative to the detection element, but also on the anti-scatter grid itself. With particularly high aspect ratios of the anti-scatter grid, curing of the adhesive with uncollimated light is even often not possible at all. The use of individual spotlights or laser-based light sources as alternative, directed exposure possibilities is generally associated with an insufficient size of the exposed region and long exposure durations, which leads to uncertainties with regard to a sufficient curing and / or to long process durations.The document DE 198 52 048 A1 discloses a radiation detection device for receiving radiation, in particular X-ray radiation, comprising a digital radiation detector, wherein a scattered radiation grid consisting of a silicon carrier with absorption elements supported thereon and projecting from the carrier on one side is directly glued to the side having the absorption elements on the radiation detector.The publication DE 10 2011 079 410 A1 discloses methods for fixing at least one component on a carrier, wherein an alternative method comprises the following steps: positioning the component at a predefined distance from the carrier forming a gap; filling the gap without any projection with a dual-cure adhesive, which can be cured both with UV light and with elevated temperature; laterally irradiating the gap filled with the dual-cure adhesive with UV light until the adhesive in the region of the side surfaces of the gap is cured to such an extent that the component is fixed on the carrier; and curing the dual-cure adhesive by means of elevated temperature.The publication DE 10 2004 061 867 A1 discloses an adhesive and an X-ray detector produced using the adhesive, wherein it is proposed to add a powder 5 produced from a material having a refractive index of at least 1.8 and an average grain size of less than 100 nm to the adhesive in order to increase the sensitivity of the X-ray detector.It is an object of the invention to provide a method for producing a detector module which permits improved exposure of a radiation-curing adhesive used, and a radiation source module for use in such a method.The object is achieved according to the invention by the subject matter of the independent claims. Advantageous embodiments with expedient refinements are the subject matter of the dependent claims. Regardless of the grammatical sex of a certain term, individuals with male, female or other sex identity are included.The invention relates to a method for producing a detector module comprising a first provision of a stack arrangement consisting of a detection element and a scattered radiation grating, wherein a radiation-curing adhesive is at least partially present on a surface of the detection element facing the scattered radiation grating, said radiation-curing adhesive being in contact both with the scattered radiation grating and with the detection element.The method further comprises a second provision of a radiation source module, having a planar radiation source and a collimation unit arranged parallel thereto, wherein the collimation unit is divided into a plurality of partial regions which each extend over a partial surface region of the radiation source, and wherein each of the partial regions of the collimation unit is configured in such a way as to collimate radiation which is emitted by the partial surface region of the radiation source assigned to it.Furthermore, the method according to the invention comprises positioning the radiation source module relative to the stack arrangement on a side of the anti-scatter grid facing away from the detection element and exposing the stack arrangement by means of the radiation source module and thus curing the radiation-curing adhesive, such that an adhesive-based connection is produced between the anti-scatter grid and detector element.The detector module can be, in particular, a detector module for X-ray radiation and can be provided for use in an X-ray detector. For example, the X-ray detector can be a detector for a CT device, a C-arm or also another X-ray-based imaging device. The detection element is then in particular configured to convert incoming X-ray radiation into an electrical signal. The detection element can comprise a direct-converting or an indirect-converting converter material. The X-ray radiation or the X-ray photons can be converted into electrical signals in a direct-converting detection element by a suitable converter material. As converter material, for example, CdTe, CZT, CdCdTeSe, CdTeSe, CdCdTe, InP, TIBr2, Hgl2, GaAs, or others can be used. The X-ray radiation or the photons can be converted in an indirect converting detection element by a suitable converter material into light and into electrical pulses by means of optically coupled photodiodes, in particular a photodiode array. Scintillators, for example GOS (Gd2O2S), CsJ, YGO or LuTAG, are frequently used here as converter material. The detection element can in particular have a planar extent along two directions running perpendicular to the stacking direction of the stack arrangement. Expressed in reverse, this means that the stacking direction of the stack arrangement of the detection element and the anti-scatter grid arranged parallel thereto runs substantially perpendicular to the planar extents of the detection element and of the anti-scatter grid. The detection element can be formed in one piece or can be composed of a plurality of converter elements which are positioned next to one another along the planar extent. Indirectly converting detection elements can be used in particular advantageously in the method according to the invention, since these are generally mechanically more robust than directly converting detection elements and thus adhesion between detection element and scattered radiation grid present in a stack arrangement is advantageously made easier.The scattered radiation grating present in a stack arrangement with respect to the detection element is then, as already described above, provided for reducing the influence of scattered radiation when the detector module is used in an X-ray detector in that scattered radiation which occurs is absorbed by the scattered radiation grating before it impinges on the detection element. Thus, essentially only radiation provided for the detection by means of the detector module can pass from the main incident direction through the anti-scatter grid to the detection element. For this purpose, the scattered radiation grating can have a crosswise arrangement of X-ray-absorbing walls and X-ray-transmissive channels formed thereby. This advantageously allows filtering of scattered radiation along two directions. However, other arrangements are also possible, for example, X-ray absorbing walls arranged only along a direction parallel to one another. The X-ray absorbing walls can each be arranged parallel to the stacking direction of the stack arrangement or can also have an inclination thereto. The inclination can comprise an inclination of up to 10 degrees, in particular less than 5 degrees, for example 3 degrees. The inclination of the X-ray-absorbing walls can vary depending on the location within the scattering radiation grating. In particular, the X-ray radiation-absorbing walls and thus the X-ray-transmissive channels formed by them can be inclined such that they are aligned with a focal point of an X-ray source arranged for the exposure of the detector module when used in an X-ray detector.The X-ray absorbing walls of the scattered radiation grating preferably comprise a material which absorbs X-ray radiation in such a way that a suppression of scattered radiation which occurs during an exposure and transmission of an object in an imaging application is ensured to a sufficient extent. The X-ray-absorbing walls comprise in particular a material which strongly absorbs X-rays, i.e. has a high absorption coefficient for X-rays, for example a higher absorption coefficient than bone tissue. In particular, the X-ray-absorbing walls of the anti-scatter grid can comprise a metallic material. Preferably, the X-ray absorbing walls comprise tungsten. The plurality of X-ray absorbing walls may also comprise lead, molybdenum, zinc or another material or composite material.Radiation-curing adhesives, in particular UV-radiation-curing adhesives, generally have an advantageously rapid curing time, a high strength, a good media resistance, and a good dosability. The radiation-curing adhesive in the method according to the invention can serve for prefixing the anti-scatter grid relative to the detection element. This comprises that for an arrangement of the anti-scatter grid relative to the detection element, a further fixing possibility is provided, for example by means of a further adhesive joint between the detection element and the anti-scatter grid, such as a thermosetting adhesive, or else a different mechanical fixing of the anti-scatter grid, for example by means of fixing means, such as screws, relative to a carrier element. This further fixing can be carried out, for example, following a prefixing. In the case that a further adhesive joint is provided, the further adhesive can already be present between the anti-scatter grid and the detection element during the prefixing, wherein a curing, which may take a longer time or may necessitate other environmental conditions, can then take place subsequently. In this case, the radiation-curing adhesive can therefore also be in contact with the detection element, and the detection element can already have a layer of another adhesive, for example based on an epoxy resin or acrylic resin. The further fixing possibility can ensure a mechanically more robust connection, which can be necessary for secure use of the detector module in the X-ray detector. The radiation-curing adhesive present according to the invention can, however, also be provided to serve as sole or at least principal fixing between anti-scatter grid and detection element.The radiation-curing adhesive can be present only at one or more limited and separated locations on the surface of the detection element, for example as adhesive spot(s) or linear adhesive bead(s). In particular in the case of prefixing, this can provide a sufficient connection, wherein at the same time advantageously little adhesive material has to be used. For example, 4, 6, 8 or 10 spots of glue may be present. For example, 2, 3, 4 or 5 adhesive beads may be present. Other numbers are also possible. However, the radiation-curing adhesive can also be applied in a planar manner, i.e. it can cover the entire surface or at least a large part of the surface of the detection element. This can advantageously ensure a more robust connection between the anti-scatter grid and the detection element. The latter is particularly advantageous if the radiation-curing adhesive is provided as the sole or at least principal fixing.The radiation-curing adhesive is designed to cure upon exposure to radiation, in particular radiation in the UV range. For example, the radiation-curing adhesive can cure upon exposure to light having a wavelength between 350 nm and 460 nm, in particular between 380 nm and 420 nm. In particular, the adhesive is matched to the emitted radiation of the radiation source module used according to the invention. This means, conversely, that the emitted radiation of the radiation source module according to the invention is matched with respect to its wavelength to the radiation-curing adhesive and in this case in particular to the absorption range of the initiator used in the adhesive in each case. The radiation-curing adhesive can be based, for example, on an acrylate, such as epoxy, polyester, polyether or silicone acrylate, in particular urethane acrylate, to which photoinitiators are added. In addition to purely radiation-curing adhesives, dual-curing adhesives can also be used, i.e. adhesives having more than one curing mechanism, for example those whose curing, in addition to radiation, is also based on heat input. In preferred variants, the radiation-curing adhesive is also selected such that this has little effect on radiation used for exposure when the detector module is used in a detector. In advantageous variants, the radiation-curing adhesive chosen is substantially X-ray transparent. In other words, in advantageous embodiments, the radiation-curing adhesive absorbs less than 5%, more preferably less than 3%, of an amount of radiation which, after passing through the anti-scatter grid, would be incident on the detection surface of the detector element without adhesive bonding present or would be detected by the detector element. By exposing and thus curing the radiation-curing adhesive, an adhesive-based fixing of the anti-scatter grid relative to the detection element is ensured. The detector module can then be supplied to further process steps.The radiation source module provided according to the invention is used for the exposure of the radiation-curing adhesive in the stack arrangement of the detector module. For this purpose, the radiation source of the provided radiation source module is configured planar according to the invention. This comprises in particular that the radiation source is designed to emit radiation over a flat region. This advantageously allows a large surface of the stack arrangement and thus all regions provided with adhesive to be exposed and cured simultaneously. In advantageous embodiments, the planar region of the radiation source extends at least over the surface of the detection element on which radiation-curing adhesive is provided. In particularly advantageous embodiments, the planar region of the radiation source extends at least over a large part or over the entire region of the planar extent of the stack arrangement perpendicular to the stacking direction. In this way, positioning of the radiation source module relative to the stack arrangement is possible in a simple manner and without great uncertainties. Moreover, uncertainties in the position of the radiation-curable adhesive areas can thus be compensated. In particular, if the entire surface or at least a major part of the surface of the detection element is covered with the radiation-curing adhesive, the planar region of the radiation source advantageously extends at least over the entire region of the planar extent of the stack arrangement.The planar radiation source can be composed of a plurality of individual sources. For example, the planar radiation source can have a plurality of individual sources arranged in a plane in a matrix-like manner, wherein each individual source emits radiation at least over a partial surface region of the planar radiation source. The planar region of the planar radiation source can then be composed of the entirety of the partial surface regions. The number and arrangement of the individual sources are in particular matched to the desired surface of the planar region of the radiation source. In particular, the planar radiation source can be formed from a plurality of LEDs arranged in a matrix-like manner. This corresponds to a configuration which is advantageously simple to implement and cost-effective. In addition, the use of LEDs makes it possible to keep a heat input into the stack arrangement low. Such a configuration is also referred to as an LED planar emitter or an LED array. In other embodiments according to the invention, the planar radiation source can also be designed differently. In particular, the planar radiation source, as already described above, is matched to the adhesive used and is preferably designed to emit UV radiation in a planar manner.In the method according to the invention, the radiation source module comprising the planar radiation source is positioned relative to the stack arrangement on a side of the anti-scatter grid facing away from the detection element in order to enable exposure and thus curing of the radiation-curing adhesive. That is, the radiation emitted by the radiation source module exposes the radiation curing adhesive through the radiation transmissive channels of the anti-scatter grid. In order to now prevent a large part of the radiation emitted by the radiation source module from being absorbed unused in the scattering radiation grating, the radiation source module used according to the invention comprises the collimation unit arranged parallel to the planar radiation source. This is arranged on a side of the radiation source module which, when used in the production method according to the invention, faces the anti-scatter grid. The collimation unit according to the invention can be formed in one part or in multiple parts.In particular, the collimation unit is also planar overall and can cover the planar region of the radiation source completely, but at least for the most part, in advantageous embodiments. However, according to the invention, the collimation unit is divided into partial regions which each extend over a partial surface region of the radiation source and are designed to collimate the radiation emitted by the associated partial surface region. If the planar radiation source is composed of a plurality of individual sources, in particular LEDs, each partial region of the collimation unit can be assigned to one of the individual sources, in particular LEDs. This comprises in particular that each partial region of the collimation unit is assigned to an individual source of the radiation source in a one-to-one relationship. Each partial area of the collimation unit and its collimation effect can advantageously be matched as well as possible to the individual source assigned to it or to the partial surface area assigned to it.Collimating here means that the radiation emitted by a partial surface region or an individual source, in particular / as a rule uncollimated and thus divergently, of the planar radiation source of the radiation source module is guided to an increased extent parallel relative to the state emitted by the radiation source after passing through the collimation unit. In this way, it is achieved that more radiation from the planar radiation source, without being absorbed, can pass through the anti-scatter grid to the joint location. This means that the collimation unit advantageously increases the proportion of the emitted radiation that is available for the exposure of the radiation-curing adhesive in the stack arrangement, and thus the light power at the joining location, relative to an application without collimation unit. However, this does not necessarily mean that complete parallel guidance has to be achieved or radiation absorbed in the anti-scatter grid is completely avoided. Even with an increased parallel guidance of the radiation in the direction of the detection element, i.e. along the stacking direction, an improved light output can advantageously be associated with the radiation-curing adhesive. The degree of collimation, which leads to particularly advantageous results by the collimation unit, can be dependent on the scattered radiation grating used, in particular its aspect ratio. The greater the aspect ratio, the smaller the acceptance angle opened by the X-ray-transmissive channels, within which an increased light output can be achieved particularly advantageously by means of the collimation unit. That is, the higher the aspect ratio and smaller the acceptance angle, the more advantageous is a high degree of collimation to reduce absorption of radiation in the anti-scatter grid. The acceptance angle can be between 2° and 10°, for example, depending on the configuration of the anti-scatter grid. The mean direction of the radiation emitted by a partial surface region or an individual source after passage through the collimation unit can also be referred to below as the collimation direction. This corresponds substantially to the propagation direction of an ideally collimated, i.e. ideally parallel-guided, beam.An advantageous design of the collimation unit can be determined in advance, for example empirically or else by simulations. For example, by means of simulation, for example by means of ray tracing, depending on the configuration of the collimation unit and the specific configuration of the planar radiation source, in particular its emission profile, the achievable light power after passing through an provided anti-scatter grid and / or also an expected heat input into the anti-scatter grid can be estimated and correspondingly optimized. A simulative estimation has the advantage that a plurality of configurations of the collimation unit and / or also different anti-scatter grids can be viewed relatively easily and quickly. If the radiation source module is to be used for a plurality of anti-scatter grids with different aspect ratios, it may be advantageous to perform an optimization of the most demanding ratio in order here, too, to achieve an improved light output after passing through the anti-scatter grid. An inclination of the X-ray-absorbing walls, if provided in the anti-scatter grid, relative to the stacking direction can also be taken into account here. An optimization can in particular include an iterative procedure which takes into account, on the one hand, the light power achieved at the joint and, on the other hand, the absorption in the anti-scatter grid and thus the heat input into the anti-scatter grid or a variable dependent thereon.The positioning of the radiation source module relative to the stack arrangement can be made possible by means of a holding device, into which the stack arrangement and relative thereto the radiation source module can be arranged. The positioning may also include fixedly installing the radiation source module, the stack assembly then being disposed relative thereto. Positioning of the radiation source module and / or the stack arrangement can also be carried out automatically, for example by means of a robot.Upon exposure, the stack assembly is then exposed to radiation from the radiation source module until curing of the radiation curable adhesive is achieved. The exposure time can be, for example, between 2 and 16 s, for example 8 s or 10 s. Advantageously, however, the exposure time with the production method according to the invention and the radiation source module according to the invention can be selected to be shorter, for example by a factor of 2 to 8, than in the case of an exposure without the collimation unit according to the invention. The specific exposure time can be dependent on the radiation-curing adhesive chosen, the specific configuration of the present bond, i.e. for example the thickness of the adhesive layer, or else the ambient conditions present. In addition, the exposure time is dependent on the specific implementation of the radiation source module and the specific stack arrangement, in particular the anti-scatter grid.The method according to the invention with the radiation source module according to the invention advantageously allows a more rapid curing of the radiation-curing adhesive at the joint, since a higher intensity of radiation at the joint is ensured at the same initial intensity at the radiation source. This advantageously allows cost-effective and time-efficient production. This can also expand the pallet of possible usable adhesives. Furthermore, it can be advantageously achieved that heating of the anti-scatter grid can be reduced by the radiation source module according to the invention or is not likewise increased at least in the case of increased, achieved light power at the joint location. Reduced heating can be achieved, for example, by the primary emitted intensity of the radiation source and / or the exposure time being selected to be lower than without a collimation unit according to the invention. Similarly, an input of heat by scattered radiation into the scattered radiation grating can be less. A lower heat input can advantageously benefit the accuracy of assembly and positioning, since thermal effects can play a smaller role. Furthermore, scattered radiation gratings can be used in a simplified manner, which are formed from a more thermally sensitive material, which can be deformable by a heat input or are even destroyed. In addition, the method according to the invention enables easier production of stack arrangements with stray radiation gratings which have a high aspect ratio. As the aspect ratio increases, the exposure of the adhesive at the joint location becomes increasingly challenging, as a result of which the necessary exposure time can greatly increase. Starting from a certain aspect ratio, a process-safe curing may no longer be possible. Thus, the method according to the invention can also advantageously avoid a limitation in the component design.According to an advantageous variant, the provided radiation source module comprises that each sub-region of the plurality of sub-regions of the collimation unit is of the same design. That is, each partial region of the collimation unit is substantially identical, apart from production uncertainties. This can also be referred to as a regular collimation unit. This results in a location-independent collimation effect of the subareas within the collimation unit. This advantageously corresponds to a conversion which is as simple and cost-effective as possible. In addition, this corresponds to a configuration which is as simple as possible to optimize, since the number of parameters is kept low. The use of such a regular collimation unit may be a good compromise between an improved exposure and cost-effective and time-efficient implementation. Although no possibly present location-dependently different collimation, in particular collimation direction, is achieved here within the radiation source module, for example, which would take into account a location-dependently varying inclination of the X-ray radiation-absorbing walls of the anti-scatter grid, which inclination likewise possibly exists, for example, it can nevertheless lead to an advantageously improved production process of the detector module, even in the case of cost-effective production. This also applies in particular if the same collimation unit is to be used for a plurality of different anti-scatter grids. In this case, such a regular collimation unit can be optimized in an advantageous, simple implementation to a scattered radiation grating with the highest aspect ratio, wherein it then also contributes to an improved exposure of the radiation-curing adhesive for scattered radiation gratings with a lower aspect ratio.In an alternative variant of the production method to the configuration described above, an irregular collimation unit is used. If the scattered radiation grating is formed by a crosswise arrangement of X-ray-absorbing walls and X-ray-transmissive channels formed thereby, which have a location-dependent inclination, a collimation unit is provided in this implementation variant, wherein a collimation direction of the partial regions of the plurality of partial regions of the collimation unit takes into account the inclination of the X-ray-absorbing walls or of the formed channels location-dependently. In this case, the anti-scatter grid is oriented, for example, at a focal point of an X-ray source arranged for the exposure of the detector module when used in an X-ray detector. This results in an inclination of the X-ray-absorbing walls and corresponding channels, which depends on the position (optionally both in the x- and in the y-direction) in the anti-scatter grid. In the advantageous variant described here, this inclination is then taken into account in the collimation unit in such a way that the collimation effect of the subareas of the collimation unit, i.e. here in particular the collimation direction, is matched to this location-dependent inclination in a location-dependent manner. This then results in particular in that the sub-regions of the plurality of sub-regions of the collimation unit are not of identical design, but rather in that the sub-regions vary in terms of their geometric configuration depending on the location. In particular, each sub-region of the plurality of sub-regions can be configured differently from the other sub-regions. Advantageously, a further optimization of the collimation unit with respect to an intended anti-scatter grid can thereby be achieved.Furthermore, in an advantageous variant of the method, the scattered radiation grating comprises a crosswise arrangement of X-ray-absorbing walls and X-ray-transmissive channels formed thereby, wherein each sub-region of the plurality of sub-regions of the collimation unit extends exactly over one of the X-ray-transmissive channels or an integer multiple thereof. The integer multiple is advantageously a small integer multiple, for example 2, 4 or 6, in particular less than 10.According to an advantageous variant, the collimation unit is designed as a refractive, optical element, in particular from a matrix-like arrangement of optical lenses, wherein each subregion of the plurality of subregions of the collimation unit is formed by one of the optical lenses in each case. Such a collimation unit can be embodied as a matrix-like arrangement of microlenses, a so-called micro-lens array. The aperture of a respective lens can advantageously be designed with a rectangular aperture for the planar covering. A respective partial surface area or individual source of the radiation source is then assigned to a lens in each case. The optical design of the lenses can then be carried out on the basis of the emission profile of the radiation source or of the respective individual sources and the geometric conditions on the anti-scatter grid, for example, as already described further above, by means of simulation. For example, such a collimation unit can be designed as a one-piece body for an advantageously simple handling, wherein the matrix-like arrangement of the lenses is formed at least on one surface of the body.The collimation unit, in particular a microlens array described above, can comprise a plastic. For example, the collimation unit can be manufactured from an optical plastic with a high transmission at the wavelength of the radiation emitted by the planar radiation source. For example, a cycloolefin polymer, an amorphous thermoplastic polymer, can be used. A plastic enables an advantageously cost-effective production, in particular in the case of a high number of pieces, for example by means of injection molding. Production by means of milling can also be used. In other embodiments, the collimation unit can also be made glass-based. This can advantageously represent a more robust variant.According to a further advantageous variant of the method according to the invention, a collimation unit is used, wherein the collimation unit is designed as an adaptable collimation unit, wherein each subregion of the plurality of subregions of the collimation unit is designed as a non-rigid, optical beam shaping element which can be switched over at least between two states. Suitable for this purpose are, for example, reflective beam profile shaping via so-called "deformable mirrors" (dt: deformable mirrors) or refractive beam shaping via controllable lenses. Advantageously, an adaptation of the collimation unit to different existing stack arrangements is possible after production of the collimation unit.According to a further advantageous variant of the method according to the invention, a collimation unit is used, wherein the collimation unit itself is formed from a plurality of collimating walls arranged in a cross-wise manner, which are configured to absorb the radiation from the planar radiation source, and transmissive collimating channels lying therebetween, wherein each sub-region of the plurality of sub-regions of the collimating unit comprises in each case one of the transmissive collimating channels. Such a collimation unit resembles a scattered radiation grating of the detector module that is used in the stack arrangement. Such a collimation unit correspondingly achieves its collimation effect by absorbing the radiation deviating from the collimation direction specified by the collimation walls. The arrangement of the collimation walls of the collimation unit is advantageously matched to the arrangement of the X-ray-absorbing walls of the anti-scatter grid. In this way, it is achieved that after passage through the collimation unit the absorption of the radiation in the anti-scatter grid is reduced as much as possible. It is particularly advantageous to match the distances between the respective walls, i.e. the distances and arrangement of the collimation walls correspond to the distances and arrangement of the X-ray absorbing walls of the anti-scatter grid. In addition, the higher the collimation walls are made, the greater the collimation effect increases. Such a collimation unit comprises in particular a material which well absorbs the emitted radiation of the planar radiation source and is not impaired by the heat input by the absorbed radiation. The material can comprise, in particular, a metal. Advantageously, it has good heat conduction and poor reflection, or is coated accordingly in order to optimize the properties. For example, the collimation unit can comprise a black-anodized aluminum, tungsten or copper.According to an advantageous method variant, the radiation-curing adhesive covers a large part of the detection element. This includes the radiation curable adhesive covering the entire surface. Such a configuration advantageously makes it possible to use the radiation-curing adhesive as the sole joint connection between the anti-scatter grid and the detection element in a simplified manner without providing a further fixing, for example a thermally curing further adhesive bond. The use of a radiation source module according to the invention advantageously enables such a conversion to be implemented in a process-safe manner, since efficient illumination and thus safe curing can be achieved here over a larger area. Advantageously, process steps relating to a further fixing could be dispensed with.According to a further process variant, the radiation-curing adhesive is a dual-curing adhesive, i.e. an adhesive having more than one curing mechanism. In particular, such a dual-curing adhesive can also enable thermal curing in addition to curing by means of radiation. A dual cure adhesive may combine the benefits of a radiation curable adhesive with the benefits of the second curing mechanism. In particular in shaded zones, improved curing may be possible, for example. An overall more robust connection can also optionally be present. The curing of such dual-curing adhesives generally requires higher doses of radiation than is known from purely radiation-curing adhesives. The use of a radiation source module according to the invention also advantageously enables such a conversion to be implemented in a process-safe manner here. The invention thus opens up the possibility of using dual-curing adhesives for this application. In this case, it would also be possible to dispense with a further fixing, for example by means of a further thermally curing adhesive, and thus an additional process step. Such a dual-curing adhesive can be based on an acrylate, an epoxy resin or also on other chemistries, for example on a modified polycarboxylic acid derivative.The invention also relates to a radiation source module having a planar radiation source and a collimation unit arranged parallel thereto, wherein the collimation unit is divided into a plurality of subareas which each extend over a subarea of the radiation source, and wherein each of the subareas of the collimation unit is designed to collimate radiation emitted by the subarea of the radiation source assigned to it, for use in a method and its variants as described above.The advantages of the proposed radiation source module substantially correspond to the advantages of the proposed production method for a detection element using such a radiation source module and its variants as described above. Features, advantages or alternative embodiments mentioned here can likewise also be transferred to the radiation source module.Exemplary embodiments of the invention are illustrated in the drawings and described in more detail below. In different figures, the same reference numerals are used for the same features. The following are shown: FIG. 1 shows a schematic block diagram of a method sequence according to the invention for producing a detector module, FIG. 2 shows a schematic illustration of an arrangement of a radiation source module relative to a stack arrangement comprising a scattered radiation grating and a detection element, FIG. 3 shows a schematic illustration of the stack arrangement from FIG. 2 in a plan view, FIG. 4 shows a further schematic illustration of an arrangement of a radiation source module relative to a stack arrangement comprising a scattered radiation grating and a detection element according to one variant, FIG. 5 shows a schematic illustration of a stack arrangement comprising a scattered radiation grating and a detection element according to one variant, FIG. 6 shows a schematic illustration of a section of an exemplary embodiment variant of a radiation source module, FIG. 7 shows a schematic illustration of a detail of an exemplary embodiment variant of a radiation source module according to a further variant, and FIG. 8 shows a schematic illustration of an arrangement of a radiation source module relative to a stack arrangement comprising a scattered radiation grating and a detection element according to a further variant.FIG. 1 shows a schematic block diagram of a method sequence according to the invention for producing a detector module comprising the stepsa) First providing S 1 a stack arrangement comprising a detection element 1 and a scattered radiation grating 3, wherein a radiation-curing adhesive 5 is at least partially present on a surface of the detection element 1 facing the scattered radiation grating 3, said adhesive being in contact both with the scattered radiation grating 3 and with the detection element 1,b) Second provision S 2 of a radiation source module 7, having a planar radiation source 9 and a collimation unit 11 arranged parallel thereto, wherein the collimation unit 11 is divided into a plurality of subareas 12 which each extend over a subarea region of the radiation source 9, and wherein each of the subareas 12 of the collimation unit 11 is designed in such a way as to collimate radiation 13 which is emitted by the subarea region of the radiation source 9 assigned to it,a) positioning S 3 of the radiation source module 7 relative to the stack arrangement on a side of the anti-scatter grid 3 facing away from the detection element 1, andb) exposing S 4 the stack arrangement by means of the radiation source module 7 and thus curing the radiation-curing adhesive 5, so that an adhesive-based connection is produced between the anti-scatter grid 3 and detector element 1.FIG. 2 shows, by way of example, a schematic illustration of such a positioning of a radiation source module 7 according to the invention relative to a stack arrangement comprising an anti-scatter grid 3 and a detection element 1 according to a variant, wherein the stack arrangement is exposed to radiation 13 of the planar radiation source 9 collimated by means of the collimation unit 11 and the radiation-curing adhesive 5 present is thus cured. The positioning S 3 of the radiation source module 7 relative to the stack arrangement can be made possible by means of a holding device, not shown here, in which the stack arrangement and relative thereto the radiation source module 7 can be arranged. The positioning may also include the radiation source module 7 being fixedly installed, the stack assembly then being disposed relative thereto. Positioning of the radiation source module 7 and / or of the stack arrangement can also be carried out automatically, for example by means of a robot.The detection element 1 can comprise, for example, as an indirect or direct-converting detection element 1 designed for X-ray radiation, and for example GOS (Gd2O2S), CsJ, YGO or LuTAG or CdTe, CZT, CdMnTeSe, CdTeSe, CdMnTe, InP, TIBr2, Hgl2, GaAs, as converter material.The scattered radiation grating 3 in the form of an arrangement of X-ray absorbing walls comprising a material having a high absorption coefficient for X-ray radiation, for example a metal such as tungsten, lead, molybdenum or the like, forms X-ray transmissive channels 2. In particular, the scattered radiation grating 3 is present as a crosswise arrangement of the X-ray-absorbing walls. This is also illustrated in FIG. 3, which shows a plan view of the stack arrangement from FIG. 2 comprising the anti-scatter grid 3 and the detection element 1. However, other arrangements of X-ray absorbing walls are also possible. The X-ray-absorbing walls of the scattered radiation grating 3 are arranged here by way of example parallel to the stacking direction of the stack arrangement of detection element 1 and scattered radiation grating 3. In other embodiments, however, these may also have an inclination relative to the stacking direction. The inclination can also vary locally within the anti-scatter grid 3. A tilt can result from the fact that the X-ray-absorbing walls and thus the X-ray-transmissive channels 2 of the anti-scatter grid 3 formed by them are aligned with a focal point of an X-ray source arranged for the exposure of the detector module when used in an X-ray detector.In the exemplary case shown in FIGS. 2 and 3, the radiation-curing adhesive 5 is present in the form of adhesive spots. The presence of 4 adhesive spots 5 is chosen here purely by way of example; more or fewer adhesive spots can likewise be present. Likewise, a linear application of one or more adhesive beads or else a planar presence of an adhesive layer is conceivable. The latter is illustrated, for example, in FIG. 5. In FIG. 5, the adhesive 5 present in a planar manner extends over the entire surface of the detection element 1, but in other variants it can also only partially cover the surface. The presence of adhesive 5 at one or more limited and separated points on the surface of the detection element 1 in the form of, for example, adhesive spots or linear adhesive beads can advantageously save material and in particular, but not exclusively, enable sufficient fixation in the case of prefixing. A more flat application, on the other hand, as illustrated by way of example in FIG. 5, can possibly ensure a more robust connection between the detection element 1 and the anti-scatter grid 3. If the radiation-curing adhesive 5 is used merely as prefixing, then for an arrangement of the anti-scatter grid 3 relative to the detection element 1, a further fixing possibility can be provided, for example by means of a further adhesive joint between the detection element 1 and the anti-scatter grid 3, such as a thermosetting adhesive, or else a different mechanical fixing of the anti-scatter grid 3, for example by means of fixing means, such as screws, relative to a carrier element. In the case that a further adhesive joint is provided, the further adhesive can already be present between the anti-scatter grid 3 and the detection element 1 during the prefixing.The radiation-curing adhesive 5 is designed to cure upon exposure to radiation 13 from the radiation source module 7, in particular radiation in the UV range. For example, the radiation-curing adhesive 5 can cure upon exposure to light having a wavelength between 350 nm and 460 nm, in particular between 380 nm and 420 nm, for example 390 nm + / - 10 nm or 405 nm + / - 10 nm. In particular, the adhesive is matched to the emitted radiation 13 of the radiation source module 7 used according to the invention or vice versa. The radiation-curing adhesive 5 can be based, for example, on an acrylate, such as epoxy, polyester, polyether or silicone acrylate, in particular urethane acrylate, to which photoinitiators are added. In addition to purely radiation-curing adhesives 5, dual-curing adhesives can also be used, i.e. adhesives having more than one curing mechanism, for example those whose curing is based not only on radiation but also on heat input. Radiation-curing adhesives, in particular UV-radiation-curing adhesives, generally have an advantageously rapid curing time, a high strength, a good media resistance, and a good dosability. A dual cure adhesive may combine the benefits of a radiation curable adhesive with the benefits of the second curing mechanism. Furthermore, the adhesive 5 is advantageously selected in such a way that this has a slight effect on radiation used for exposure when the detector module is used in a detector, i.e. it only absorbs it to a slight extent.The radiation source 9 of the radiation source module 7 is configured to emit radiation 13 for the exposure of the radiation-curing adhesive 5 via a planar region, and is correspondingly configured planar. In the schematic example shown here, the planar region extends over the entire planar extent of the stack arrangement perpendicular to the stacking direction. However, other configurations are also possible, for example those in which only a large part of the surface is over-stretched. In advantageous embodiments, the planar region extends at least over the surface of the detection element 1, on which radiation-curing adhesive 5 is present, so that simultaneous and thus time-efficient exposure can be achieved.The planar radiation source 9 can be constructed composed of a plurality of individual sources 15, as illustrated exemplarily and schematically in FIGS. 4, 6 and 7. Each individual source 15 can then emit radiation 13 at least over a partial surface area of the flat radiation source 9. Thus, the planar radiation source 9 can have a plurality of individual sources 15 arranged in a matrix-like manner in a plane. The number and arrangement of the individual sources 15 are in particular matched to the desired surface of the planar region of the radiation source 9. 10x10, 12x12, 14x14 or 20x20 or else a different number of individual sources can be provided, for example. Thus, planar radiation sources with 3x30, 6x17 or 15x23 individual sources can be present in the same way. The planar radiation source 9 is particularly advantageously designed as a so-called LED planar emitter or LED array.The collimation unit 11 according to the invention advantageously extends over the flat region of the radiation source 9, from which radiation 13 is emitted. Indicated in FIG. 2 is the subdivision according to the invention of the collimation unit 11 into partial regions 12 which are each designed to collimate the radiation 13 emitted by the respectively assigned partial surface region of the radiation source 9. If the planar radiation source 9 is composed of a plurality of individual sources 15, in particular LEDs, each partial region 12 of the collimation unit 11 can be assigned to one of the individual sources 15, in particular LEDs. This includes, in particular, that each partial region 12 of the collimation unit 11 is assigned to an individual source 15 of the radiation source 9 in a one-to-one relationship, as is illustrated by way of example in FIGS. 4, 6 and 7. In this way, it can be achieved that the respective partial region 12 of the collimation unit 11 and its collimation effect are each matched to an individual source 15.The collimation unit 11 has the effect that the radiation 13 of the planar radiation source 9 of the radiation source module 7, emitted by a partial surface region or an individual source 15, in particular / as a rule uncollimated and thus divergently, is guided to an increased extent parallel relative to the state emitted by the radiation source 9 after passing through the collimation unit 11. FIG. 4 schematically illustrates uncollimated emitted radiation 13 from a planar radiation source 9 constructed from a plurality of individual sources, in particular LEDs, without the collimating effect of the collimating unit 11. The uncollimated radiation 13 of the planar radiation source 9 is largely absorbed in the anti-scatter grid 3 and is accordingly no longer available for curing the radiation-curing adhesive 5. The radiation source module 7 provided comprising the collimation unit 11 now advantageously achieves the effect that the radiation emitted by the radiation source 9 or the respective individual source 15 is collimated, i.e. guided increasingly parallel, in a respective assigned partial region of the collimation unit 11, such that more radiation 13 from the planar radiation source 9 can pass through the anti-scatter grid 3 to the joint location without being absorbed. This means that the proportion of the emitted radiation 13 available for the exposure of the radiation-curing adhesive 5 in the stack arrangement, and thus the light power at the joint, is advantageously increased by the collimation unit 11, relative to an application without collimation unit 11. However, this does not necessarily mean that complete parallel guidance has to be achieved or radiation absorbed in the anti-scatter grid 3 is completely avoided. Although only parallel radiation 13 is indicated in FIG. 2, a certain opening angle of the collimated radiation 13 emerging from each partial region can also be present at the exit surface of the collimation unit 11 after passage through the collimation unit 11. Even the increased parallel guidance of the radiation 13 in the direction of the detection element 1 is advantageously associated with improved light output on the radiation-curing adhesive. The degree of collimation, which leads to particularly advantageous results by the collimation unit 11, can be dependent on the scattered radiation grating 3 used, in particular its aspect ratio. The greater the aspect ratio, the smaller the acceptance angle opened by the X-ray-transmissive channels 2, within which an increased light output can be advantageously achieved by means of the collimation unit 11. The acceptance angle can be between 2° and 10°, for example, depending on the configuration of the anti-scatter grid 3.The collimation unit 11 can be configured differently. For example, as a refractive optical element, for instance a so-called microlens array, as an adjustable collimation unit, wherein each sub-region of the plurality of sub-regions of the collimation unit is formed as a non-rigid, optical beam shaping element, or else by means of an arrangement of absorbing collimation walls. An advantageous design of the collimation unit 11 can be determined in advance, for example empirically or else by simulations. For example, by means of simulation, for example by means of ray tracing, depending on the configuration of the collimation unit 11 and the specific configuration of the planar radiation source 9, in particular its emission profile, the achievable light power after passing through an provided anti-scatter grid 3 and / or also an expected heat input into the anti-scatter grid 3 can be estimated and correspondingly optimized. An inclination of the X-ray absorbing walls relative to the stacking direction when provided in the anti-scatter grid 3 can also be taken into account in the design of the collimation unit 11. An optimization of the collimation unit 11 can in particular include an iterative procedure which takes into account, on the one hand, the light power achieved at the joint and, on the other hand, the absorption in the anti-scatter grid 3 and thus the heat input into the anti-scatter grid 3 or a variable dependent thereon.During exposure, the stack arrangement is then exposed to the radiation 13 from the radiation source module 7 until sufficient curing of the radiation-curing adhesive 5 is achieved. The exposure time can be, for example, between 2 and 20 s, for example 8 s or 10 s. Advantageously, however, the exposure time with the production method according to the invention and the radiation source module according to the invention can be selected to be shorter, for example by a factor of 2 to 10, than in the case of an exposure without the collimation unit according to the invention.The method according to the invention with the radiation source module 7 according to the invention advantageously allows a more rapid curing of the radiation-curing adhesive 5 at the joint, since a higher intensity of radiation at the joint is ensured at the same initial intensity at the radiation source 9. This can also expand the pallet of possible usable adhesives 5. Furthermore, it can be advantageously achieved that heating of the anti-scatter grid can be reduced by the radiation source module 7 according to the invention or is not likewise increased at least in the case of increased, achieved light power at the joint location. In addition, the method according to the invention enables easier production of stack arrangements with anti-scatter grids 3, which have a high aspect ratio.FIGS. 6 and 7 show two different design possibilities of the radiation source module 7 in each case in a schematic sectional view. In both variants, the planar radiation source 9 is formed from a plurality of individual sources 15, in particular LEDs, which are arranged next to one another in a matrix-like arrangement in the planar region of the radiation source 9 and each emit uncollimated radiation 13 over a partial surface region.In FIG. 6, the collimation unit 11 according to the invention is formed from a matrix-like arrangement of optical lenses, wherein each partial region 12 of the plurality of partial regions of the collimation unit 11 is formed by one of the optical lenses in each case. The collimation unit 11 is designed here as a refractive optical element, in particular as a one-piece, so-called microlens array. The collimation unit 11, for example comprising an optical plastic or a glass, has curved surfaces on a second surface here in addition to a planar first surface which faces the radiation source 9. However, the curved surfaces could also face the radiation source 9 or a different configuration could be selected. Each of the partial regions 12 of the collimation unit 11 acts as a lens, which collimates the radiation 13 impinging on it from the individual source 15 assigned to it. Optimizing such a collimation unit 11 can comprise adapting the distance d between radiation source 9 and collimation unit 11, the thickness m of collimation unit 11, and the curvatures of collimation unit 11. A distance d can be between 2 and 10 mm, for example. A thickness m can be between 2 and 15 mm, for example. Optimizing such a collimation unit 11 can comprise balancing between an optimized capturing of light and thus high intensity after the collimation unit 11, which can however be associated with a less strong collimation effect and thus increased scattering of the radiation and absorption in the scattered radiation grating, and a higher collimation and thus lower scattering, but also lower intensity after the collimation unit 11. An iterative procedure can be advantageously chosen here, wherein both the light output in the adhesion plane and a heat input into the anti-scatter grid 3 can be taken into account. This also applies to collimating units of a different design. For example, the collimation unit 11 shown here is made of an optical plastic with a high transmission at the wavelength of the radiation emitted by the planar radiation source. For example, a transmission of more than 80%, more advantageously more than 90%, should be achieved with a thickness of a few mm, for example 3 mm. For example, a cycloolefin polymer, an amorphous thermoplastic polymer, can be used. A plastic enables an advantageously cost-effective production, in particular in the case of a high number of pieces, for example by means of injection molding. Production by means of milling can also be used.FIG. 7 shows a schematic sectional view of a further possible embodiment of the radiation source module 7. the collimation unit 11 itself comprises a plurality of collimating walls arranged crosswise, which are configured to absorb the radiation 13 from the planar radiation source 9, and transmissive collimating channels located therebetween, wherein each subregion 12 of the plurality of subregions of the collimation unit 11 comprises in each case one of the transmissive collimating channels. Such a collimation unit 11 resembles a scattered radiation grating 3 of the detector module which is used in the stack arrangement. Such a collimation unit 11 correspondingly achieves its collimation effect by absorbing the radiation deviating from the collimation direction specified by the collimation walls. Such a collimation unit 11 comprises in particular a material which well absorbs the emitted radiation of the planar radiation source and is not impaired by the heat input by the absorbed radiation. For example, the collimation unit 11 can comprise a black-anodized aluminum, tungsten or copper. The arrangement of the collimation walls of the collimation unit is advantageously matched to the arrangement of the X-ray-absorbing walls of the anti-scatter grid 3. In this way, it is achieved that after passing through the collimation unit 11, the absorption of the radiation in the anti-scatter grid 3 is reduced as much as possible. An optimization of such an approach can take into account, in addition to the distances between the walls and the radiation source 9, in particular the height of the collimation walls. The higher the collimation walls, the stronger is the collimation effect, but the lower is the resulting intensity after the collimation unit 11.A further possible configuration comprises the collimation unit 11 being designed as an adjustable collimation unit, wherein each subregion 12 of the plurality of subregions of the collimation unit 11 is designed as a non-rigid, optical beam shaping element which can be switched over at least between two states. Suitable for this purpose are, for example, reflective beam profile shaping via so-called "deformable mirrors" (dt: deformable mirrors) or refractive beam shaping via controllable lenses. Advantageously, an adaptation of the collimation unit to different existing stack arrangements is possible after production of the collimation unit.In the examples shown above in FIGS. 6 and 7, each sub-region 12 of the plurality of sub-regions of the collimation unit 11 is formed identically, i.e. the collimation unit 11 is formed as a regular collimation unit. This advantageously corresponds to a conversion which is as simple and cost-effective as possible. In addition, however, it is also possible for an irregular collimation unit 11 to be implemented. This can lead to particularly advantageous results in particular if, as illustrated in FIG. 8, the scattered radiation grating 3 is formed by a crosswise arrangement of X-ray-absorbing walls and X-ray-transmissive channels formed thereby, which have a location-dependent inclination, indicated by the angles α, β, γ, δ. In the implementation variant shown here, a collimation unit 11 is now provided, wherein a collimation direction of the partial regions of the plurality of partial regions of the collimation unit (indicated by the direction of the radiation 13) takes into account the inclination of the X-ray-absorbing walls or of the channels formed depending on the location. In the advantageous variant described here, the inclination of the X-ray-transmissive channels in the collimation unit 11 is taken into account in such a way that the collimation effect of the subareas 12 of the collimation unit 11, i.e. here in particular the collimation direction, is matched to this location-dependent inclination in a location-dependent manner. This then results in particular in the fact that the sub-regions 12 of the plurality of sub-regions of the collimation unit 11 are not of identical design, but rather in the fact that the sub-regions 12 vary in terms of their geometric configuration depending on the location. In the variant shown, the collimation unit 11 is likewise designed as a microlens array. However, it could also be formed according to another variant.In particular, but not only, in connection with this variant, it is also particularly advantageous that, as schematically illustrated here, each sub-region 12 of the plurality of sub-regions of the collimation unit 11 extends exactly over one of the X-ray-transmissive channels of the anti-scatter grid 3, since the location-dependent tuning to the inclination of the individual channels of the anti-scatter grid can be taken into account in a particularly advantageous manner here. However, it can also be an in particular small, for example less than 10, integer multiple, for example 2 or 4. In a region overstretched by this, a variation of the inclination of the walls can be only slight, so that a location-dependent matching of the collimation direction can still bring advantageous results even over a plurality of channels.

Claims

Method for producing a detector module comprising a. first providing (S1) a stack arrangement of a detection element (1) and an anti-scatter grid (3), wherein a radiation-curing adhesive (5) is at least partially present on a surface of the detection element (1) facing the anti-scatter grid (3), said adhesive being in contact both with the anti-scatter grid (3) and with the detection element (1), b. second providing (S2) a radiation source module (7) having a planar radiation source (9) and a collimation unit (11) arranged parallel thereto, wherein the collimation unit (11) is divided into a plurality of partial regions (12), which each extend over a partial surface region of the radiation source (9), and wherein each of the partial regions (12) of the collimation unit (11) is configured such that radiation (13) is generated, which is emitted by the associated partial surface region of the radiation source (9), c. positioning (S3) the radiation source module (7) relative to the stack arrangement on a side of the anti-scatter grid (3) facing away from the detection element (1), d. exposing (S4) the stack arrangement by means of the radiation source module (7) and thus curing the radiation-curing adhesive (5), so that an adhesive-based connection is produced between the anti-scatter grid (3) and detector element (1).Method according to claim 1, wherein the planar radiation source (9) is formed from a plurality of individual sources, in particular LEDs (15), arranged in a matrix-like manner.Method according to claim 2, wherein each sub-region (12) of the plurality of sub-regions (12) of the collimation unit (11) is assigned to one of the individual sources (15).Method according to one of the preceding claims, wherein each sub-region (12) of the plurality of sub-regions (12) is of similar design.Method according to one of Claims 1 to 3, wherein the anti-scatter grid (3) is formed by a matrix-like / cross-wise arrangement of X-ray-absorbing walls and X-ray-transmissive channels (2) formed thereby, which have a location-dependent inclination, and wherein a collimation direction of the subareas (12) of the plurality of subareas (12) of the collimation unit (11) takes the inclination into account in a location-dependent manner.Method according to one of the preceding claims, wherein the anti-scatter grid (3) is formed by a matrix-like / cross-wise arrangement of X-ray-absorbing walls and X-ray-transmissive channels (2) formed thereby, and wherein each sub-region (12) of the plurality of sub-regions (12) of the collimation unit (11) extends exactly over one of the X-ray-transmissive channels (2) or an integer multiple thereof.Method according to one of the preceding claims, wherein the collimation unit (11) is formed from a matrix-like arrangement of optical lenses, wherein each partial region (12) of the plurality of partial regions of the collimation unit (11) is formed by one of the optical lenses in each case.Method according to one of the preceding claims, wherein the collimation unit (11) comprises a plastic or a glass.Method according to one of Claims 1 to 6, wherein the collimation unit (11) is designed as an adjustable collimation unit, wherein each subregion (12) of the plurality of subregions of the collimation unit (11) is designed as a non-rigid, optical beam shaping element which can be switched over at least between two states.Method according to one of Claims 1 to 6, wherein the collimation unit (11) is formed from a plurality of collimating walls arranged crosswise, which are designed to absorb the radiation (13) from the planar radiation source (9), and transmissive collimating channels lying therebetween, wherein each subregion (12) of the plurality of subregions of the collimation unit (11) comprises in each case one of the transmissive collimating channels.Method according to any of the preceding claims, wherein the radiation curing adhesive (5) covers a major part of the detection element (1).Radiation source module (7) having a planar radiation source (9) and a collimation unit (11) arranged parallel thereto, wherein the collimation unit (11) is divided into a plurality of partial regions (12), which each extend over a partial surface region of the radiation source (9), and wherein each of the partial regions (12) of the collimation unit (11) is designed in such a way as to collimate radiation (13) emitted by the partial surface region of the radiation source (9) assigned to it, for use in a method according to one of the preceding claims.

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