in fig1 , 2 is a scintillation crystal , 4 indicates a bundle of light guides , and 6 is a detector . a beam of high - energy radiation is indicated by 8 , while 10 designates an object , experimental animal or human to be examined , hereinafter usually indicated as “ object ” for the sake of brevity . it should be noted that fig1 , and the others in this drawing are schematic and not necessarily to scale . the camera shown is of the transmissive type , in which usually parallel radiation from a separate source passes through the object and subsequently impinges on the detector . in the camera shown , a beam of high - energy radiation , for example x - ray or gamma radiation is supplied , parallel in this case , to an object 10 to be examined , for example a laboratory mouse . having passed through the object , the unabsorbed fraction of the radiation will hit a scintillation crystal in which the radiation incident thereon is ( partially ) converted into optical radiation which is carried via the bundle of light guides 4 to a detector 6 which is sensitive to that optical radiation . the scintillation crystal 2 in this case is a homogenous unit of an iodide , a tungstate , a plastic or the like . here the shape is that of a block , with top and bottom faces parallel , so as to provide constant thickness . the bundle of light guides 4 is shown as a parallel bundle of guides of equal thickness , such as optical fibres of , for example , glass . the alignment of the light guides 4 is drawn as being parallel to the beam 8 . the positional information is obtained by virtue of optical radiation which enters a light guide 4 remaining captive therein and propagating in a parallel manner until it is fed to the detector 6 . if the detector 6 is capable of position - sensitive measurements , as is the case , for example , for a ccd or cmos device or an arrangement of photomultiplier tubes , the detection as a whole is position - sensitive . an apparatus of this type can have a number of pixels or subdetectors which matches the desired resolving power . similar considerations obviously also apply to the number of light guides 4 in the bundle but these details will not be addressed further hereinafter . fig2 shows a detail of the camera of fig1 , with a beam path therein . here , 4 - 1 , 4 - 2 and 4 - 3 are a first , second and third light guide , respectively , and 14 - 1 , 14 - 2 and 14 - 3 are the corresponding first , second and third collection cones of directions from where optical radiation can be collected , each having an apex angle a . a first and a second gamma ray are indicated by 12 ′ and 12 ″ respectively . the collection cones 14 - 1 etc . can be determined in a simple manner on the basis of the numerical aperture ( na ) of the light guides 4 , according to na = sine ( apex half - angle of the collection cone ). therefore a light guide having an na of 0 . 1 , such as a single - mode optical fibre , has an apex half - angle of the collection cone of a mere 5 . 7 °, whereas a light guide having an na of 0 . 8 has an apex half - angle of 53 ° which therefore will have far greater overlap but on the other hand will collect more light . the desired na depends , inter alia , on the thickness of the scintillator layer 2 and the desired resolving power . for a thickness of 1 mm and a resolving power at that face of the scintillator layer which faces away from the detector of 250 μm , the required half - na =( 0 . 25 mm / 2 )/ 1 mm = 0 . 125 , which does not constitute a problem . for that matter , overlap will still be able to occur , but image processing employing weighting can correct a great deal . moreover , it is possible to opt for making the spacing between the separate light guides sufficiently large for there to be just about no overlap , everything being in geometric proportion to the thickness of the scintillator material . it can be seen that the first gamma ray 12 ′ comes in into the collection cones 14 - 1 and 14 - 3 . this means that optical radiation generated as the ray 12 ′ passes through the scintillation material 2 , will arrive in part in the third light guide 4 - 3 and in part in the first light guide 4 - 1 , in this case , as seen statistically , in equal proportions in both . this means in turn that the corresponding gamma flash has a width of precisely two light guides . this in turn implies that the flash must have occurred at the interface of the two light guides 4 - 1 and 4 - 3 . it should be noted here that the gamma flash in question will of course radiate in all directions , but only that radiation which falls within a collection cone will be capable of being picked up and carried within a light guide . the remaining radiation will be lost . it can also be seen that the second gamma ray 12 ″ predominantly comes in into the collection cone 14 - 1 of light guide 4 - 1 . only a small fraction of the optical radiation generated thereby falls outside , in collection cones 14 - 2 and 14 - 3 . thus the detector ( not shown here ) will be capable of clearly locating this gamma flash at light guide 14 - 1 , possibly on the basis of weighting the intensity of the signals from light guides 14 - 1 , 14 - 2 and 14 - 3 . fig3 shows a schematic second embodiment of a scintillation camera , in operation . here , as in the other figures of the drawings , similar elements are indicated by corresponding reference numerals . the camera as shown here is sometimes referred to as a pinhole camera . again , it comprises a scintillation crystal 2 and a bundle of light guides 4 on a detector 6 . an antireflective layer is indicated by 24 . gamma radiation now comes from the object 10 , e . g . as a result of radioisotopes being used , and passes through an opening ( pinhole ) 22 in a wall 20 . since the wall 20 is substantially opaque to the gamma radiation , for example because it is made of lead , a beam 8 is provided as a cone fanning out from opening 22 . the beam 8 first passes through antireflective layer 24 . since this is substantially transparent to gamma radiation , the latter will pass through unhindered and arrive in scintillation crystal 2 . there , scintillation causes optical radiation to be generated , some of which finds its way to the light guides 4 . it should be noted that the bundle of light guides in this case points to one spot , substantially the opening 22 . as a result , each gamma ray will generate , from the opening 22 , scintillations in the smallest possible number of collection cones ( not shown separately , but cf . fig2 ). this will have a beneficial effect on the resolving power of the camera . for comparison , if a gamma ray is obliquely incident with respect to the axis of the light guides , said ray will intersect a plurality of adjoining collection cones , which means that scintillation radiation will arrive in a plurality of adjoining light guides 4 . whilst this effect can be reduced to some extent by means of weighting , the alignment of the light guides according to fig3 will provide an optimal result in this case . moreover , the use of non - aligned light guides of scintillation material would ensure that even the gamma ray would fall into a plurality of light guides and generate optical radiation therein , which will significantly impair the resolving power . alignment of the light guides is therefore even more important if these too are fabricated from a scintillation material . it should be noted that this is based on the assumption that the refractive indices , for the optical radiation , of the scintillation crystal 2 and of the material of the light guides 4 are substantially equal . if the refractive indices differ , refraction of the optical radiation at the interface between the two materials should be taken into account . likewise , the direction of the end face of the light guide and its position with respect to the axis of the light guide should also be taken into account . if each end face is perpendicular to the axis of the light guide and to the gamma rays , in other words is directed towards opening 22 , refraction need not be taken into account , given the vertical incidence of the optical radiation . if the end face is not perpendicular to the axis or not perpendicular to the gamma rays , a simple optical calculation should be performed in order to obtain the correct collection cone and consequently the corresponding alignment of the light guides . the camera shown is of the emissive type , in which an image of the object to be examined is formed on the detector via a pinhole ( or collimator ). usually , the object to be examined is itself the source of high - energy radiation , for example via the administration of radionuclides which are distributed in the object . the object will then radiate , from each part , in all directions . each time , a fraction of the radiation will be able to pass the pinhole and thus form the image . this is an alternative to the transmission scintillation camera as shown , for example , in fig1 and 4 , which does require a separate source of high - energy radiation . it should be noted that as a result of the type of the light guides and light transport by virtue of total internal reflection , the alignment far away from the interface with the scintillation material is irrelevant . furthermore , it is also possible , within certain limits , to achieve correct alignment of the collection cones with substantially parallel light guides by means of an advantageous choice , in each case , of the position of the end face of the light guide , utilizing the refraction at said end face . one condition in this last - mentioned situation is of course that a difference in refractive index exists between the material of the scintillation crystal 2 and the light guides 4 . the antireflective layer 24 , which could also be called absorption layer , serves to absorb optical radiation incident thereon in the scintillation crystal 2 or to prevent it in some other way from returning in the direction of the light guides 4 . as a result , the detected background signal will decrease , and the signal - to - noise ratio will be improved . in essence , any material can be used for this purpose which absorbs the generated optical radiation but is itself transparent to the high - energy radiation , for example pigmented plastics etc . the thickness of the layer 24 as shown is exaggerated , incidentally . for that matter , an optically retroreflective layer such as scotchlite ™ can be used as an alternative instead of layer 24 . in a favourable case , the intensity of the detector improves by a factor of 2 . fig4 a and b show a third and fourth embodiment of a scintillation camera according to the invention , in operation . here , the light guides 4 in fig4 a point in a raywise manner towards the source 22 of high - energy radiation 8 , a homogenous layer of scintillation material 2 being located on the end faces . this layer may have been deposited by being grown thereon or be attached separately after having been given the correct shape , for example by grinding or the like . in this arrangement , the scintillation material can , if required , be joined , for example , to the light guides 4 with the aid of an optical bonding medium such as cement having a suitable refractive index . the source 22 can be an x - ray tube , for example . it should be noted that the bundle of light guides 4 fanning out in a raywise manner need no longer be aligned in such a way at some distance from the scintillation material . at a distance , for example , of several cross sections of the light guides , the bundle can alternatively continue in a parallel arrangement , to avoid unduly large dimensions of the bundle . it is also to be noted that the alignments shown in fig3 and 4 a relate to so - called convergent alignments , in which the point where the directions of the high - energy rays converge is situated in front of the camera . they form an enlarged image of the object 10 . another convergent option , used far more often in practice , for fig4 b is an object 10 which is itself a source , for example by injection of radioisotopes , a pinhole 28 being used to form images . a convergent collimator is positioned close to or on scintillation material 2 , the channels therethrough having an alignment which corresponds to that of the light guides 14 . both parts , collimator and light guides , then point to the virtual source ( pinhole 28 ) of high - energy radiation . also existing are , for example , divergent collimators , which form a reduced image . in these collimators , the convergence point of the directions in which the high - energy rays propagate is situated behind the camera . here , again , the light guides accord with the alignment of the channels through the collimator , the bundle 14 being divergent , in contrast . in general it is the case that the light guides 14 , in terms of their alignment , agree with the alignment of the channels of the collimator . fig5 shows a fifth embodiment of a scintillation camera according to the invention , in operation . this relates to a configuration involving two subcameras , each of them being emission scintillation cameras . the camera as a whole comprises two scintillation crystals 2 ′ and 2 ″, and two corresponding bundles of light guides 4 ′ and 4 ″ and two detectors 6 ′ and 6 ″, the latter being linked to a processing unit 24 . reference numerals 26 ′ and 26 ″ indicate two beam formers , each having an opening ( pinhole ) 28 ′ and 28 ″, respectively . reference numeral 10 ′ indicates an experimental animal from which a beam of gamma radiation 30 emanates . the system as shown in fact comprises two cameras according to the invention . this allows two views of the experimental animal to be detected simultaneously . the assumption here is that the source of the high - energy radiation in this case is a radioisotope distributed within the experimental animal . the pinhole camera is able to project an image of the distribution onto the detector via the pinhole , obviously via the scintillation material and the light guides . obviously , the position of the experimental animal 10 ′ can be adjusted with respect to the camera , for example rotated in order to obtain further views . the number of cameras is obviously not limited to two but can in fact be any desired number , such as three , four or even several tens . furthermore , the space between the cameras could be constructed as an enclosed chamber ( not shown in this example ) so as to define more closely the position of the animal 10 ′. the beam formers 26 ′ and 26 ″ shown herein , with their pinholes 28 ′ and 28 ″, make the ( two ) cameras shown into pinhole cameras . this is again a typical example of an emission scintillation camera , an image being made of a source and imaging being performed by means of a pinhole . the pinhole is , as it were , the camera optics . the pinholes become virtual sources which appear to emit radiation , which does now , however , contain positional information from the original extended source . the light guides and their end faces in the bundles 4 ′ and 4 ″ are directed in such a way that within the scintillation crystals 2 ′ and 2 ″ the collection cones of the light guides are directed towards the pinholes 28 ′ and 28 ″, respectively . if the material of the light guides and the scintillation material have matching refractive indices , it is sufficient for the ends of the light guides to be directed towards the pinholes . alternatively or complementarily , the ( sub ) cameras can also comprise a collimator which then have a series of openings in an opaque wall with corresponding transmission directions . the ( collection cones of the ) light guides can then each be in line with one of the transmission directions of the collimator . the schematically depicted processing unit 24 can comprise , for example , a computer with image processing software , as well as , for example , a monitor for visual assessment of the detected images , a data storage device etc . the specific embodiments shown here are to be understood merely as a non - limiting explanation of the invention , whose scope is defined by the appended claims .