reference will now be made in detail to the preferred embodiments of the claimed subject matter , a method and system for the use of a reputation service provider , examples of which are illustrated in the accompanying drawings . while the claimed subject matter will be described in conjunction with the preferred embodiments , it will be understood that they are not intended to be limit to these embodiments . on the contrary , the claimed subject matter is intended to cover alternatives , modifications and equivalents , which may be included within the spirit and scope as defined by the appended claims . furthermore , in the following detailed descriptions of embodiments of the claimed subject matter , numerous specific details are set forth in order to provide a thorough understanding of the claimed subject matter . however , it will be recognized by one of ordinary skill in the art that the claimed subject matter may be practiced without these specific details . in other instances , well known methods , procedures , components , and circuits have not been described in detail as not to unnecessarily obscure aspects of the claimed subject matter . some portions of the detailed descriptions which follow are presented in terms of procedures , steps , logic blocks , processing , and other symbolic representations of operations on data bits that can be performed on computer memory . these descriptions and representations are the means used by those skilled in the data processing arts to most effectively convey the substance of their work to others skilled in the art . a procedure , computer generated step , logic block , process , etc ., is here , and generally , conceived to be a self - consistent sequence of steps or instructions leading to a desired result . the steps are those requiring physical manipulations of physical quantities . usually , though not necessarily , these quantities take the form of electrical or magnetic signals capable of being stored , transferred , combined , compared , and otherwise manipulated in a computer system . it has proven convenient at times , principally for reasons of common usage , to refer to these signals as bits , values , elements , symbols , characters , terms , numbers , or the like . it should be borne in mind , however , that all of these and similar terms are to be associated with the appropriate physical quantities and are merely convenient labels applied to these quantities . unless specifically stated otherwise as apparent from the following discussions , it is appreciated that throughout the present claimed subject matter , discussions utilizing terms such as “ storing ,” “ creating ,” “ protecting ,” “ receiving ,” “ encrypting ,” “ decrypting ,” “ destroying ,” or the like , refer to the action and processes of a computer system or integrated circuit , or similar electronic computing device , including an embedded system , that manipulates and transforms data represented as physical ( electronic ) quantities within the computer system &# 39 ; s registers and memories into other data similarly represented as physical quantities within the computer system memories or registers or other such information storage , transmission or display devices . accordingly , embodiments of the claimed subject matter provide a method and system for building a high quantum efficient imager . the quantum efficiency , which represents the percentage of photons that interact with the imager of a conventional mv imager is around 2 %. in one embodiment of this invention , the goal is to improve the quantum efficiency significantly . fig1 represents a typical digital imaging system 100 which may be used to capture images to assist a physician in making accurate diagnoses . digital imaging systems such as those depicted in fig1 may include one or more radiation sources . as depicted , the digital imaging system 100 of fig1 depicts a kv radiation source 110 and an mv radiation source 120 , with corresponding detectors ( detectors 130 , 140 , respectively ). in alternate embodiments , one or more of the radiation sources may be operable to generate both kv and mv radiation . likewise , a single detector may be used to receive radiation from both sources . according to these embodiments , one or more of the radiation and / or detectors may not be present . in still further embodiments , the imaging system 100 may also include a communicatively coupled computing device 150 for processing images and / or controlling and manipulating the device 100 . radiation energy , such as x - rays , produced by the radiation source 110 , 120 travel through an volume to be imaged and are detected ( i . e ., received ) by a detector 130 , 140 . a corresponding image processing system obtains image data from the detector and prepares a diagnostic image on a display corresponding to the arrangement of the detection sites in the imager . the images may also be used for verifying and / or adjusting patient positioning on a therapy machine , for example . additionally , the imaging system may also be used as a 2 - dimensional dose measuring device ( dosimetry ), which allows the verification of the accurate dose delivery of the therapy machine . in even more advanced applications the captured signals by the imaging system can be used to calculate the dose deposited in the patient . fig2 depicts a block diagram of the electronic portion of an image processing system in a digital imaging system . according to one embodiment , the digital imaging system may include a detector ( e . g ., detector 130 , 140 of fig1 ) for receiving a plurality of incident particles , such as the x - ray particles from a radiation beam . the detector may comprise a plurality of pixels arranged in a matrix ( e . g ., two dimensional array ). pixels of images generated by the detector may correspond to the plurality of pixels of the detector . in one embodiment , the particles received in the detector 130 , 140 generate electron - hole pairs in an array of photo - diodes 210 , accumulating charge which is stored in an intrinsic capacitor of the photo diodes 210 . the accumulated charge may be subsequently transferred into a read out circuit 220 ( e . g ., fed pixel by pixel ). at a basic level , the presence and absence of photons ( and in turn light ) is detected by either the presence or absence of a flow of current in the photodiode . such a pixel based electric behavior is subsequently received in the image processing subsystem 230 , via an electronic interface 240 communicatively coupling the read out circuit 210 and the image processing subsystem 230 , for example . the data received by the image processing subsystem 230 may be thereafter processed and used to generate an image of objects disposed in the path of the radiation . according to some embodiments , the detector 130 , 140 may be an amorphous silicon ( a - si ) panel detector . amorphous silicon is a type of silicon that is not crystalline in structure . pixels which constitute the generated image may correspond to the pixels of the detector 130 , 140 . the detector pixels may be formed from amorphous silicon photodiodes which are connected to switches on the flat panel . since photodiodes react to light photons , a scintillator is placed in front of the flat panel detector . in typical embodiments , the scintillators act as an absorber of x - rays and convert the x - ray radiation particles to visible light photons at energies that a layer of sensors is able to convert to charge carriers . in some embodiments , the sensors may be comprised of amorphous silicon ( a - si ) photo - diode arrays . alternatively , the sensors may be implemented as photo - diode arrays based on organic semiconductors , which convert the light photons into electron hole - pairs . in still further embodiments , the layer of sensors may also include amorphous silicon ( a - si ) or organic semiconductor thin film transistors which enable the measurement of the charge corresponding to the electron hole - pairs in a readout circuit , such as an application specific integrated circuit ( asic ). each pixel of the detector 130 , 140 then , may comprise both a photo - diode as well as a thin film transistor . for high energy photons , a build - up plate consisting of , for example , copper is used to enhance the detective quantum efficiency ( dqe ) of the detector . fig3 depicts an illustration of an image detector signal sequence 300 , in accordance with embodiments of the present invention . in one embodiment , the scintillator 304 receives x - rays from an x - ray source 301 and emits light of an intensity related to the amount of x - rays absorbed . x - ray source 301 sends a beam of x - ray photons through an object 302 . x - ray photons 303 that are not absorbed by the object 302 , strike a layer of scintillating material 304 that converts the x - ray photons into visible light photons 305 . these photons then strike an array of photo - diodes 306 in a sensor layer , which converts the photons into electrons 307 that are stored in the intrinsic capacitance of the pixels in a layer of amorphous silicon 309 . according to some embodiments , the sensor layer may include an amorphous silicon ( a - si ) thin film transistor ( tft ) array . the activated pixels generate electronic data that is transferred through the tft array to a computing device , which can convert the transferred charge into a high quality image of the target 308 . the image may be subsequently displayed on a computer monitor , or stored in memory or on a tangible computer readable medium . as illustrated in fig4 , a detector comprising a paired scintillator 401 and an array of a - si photo - diodes 402 is depicted . generally , the detective quantum efficiency ( dqe ) of an imager is generally dependent on the energy of the radiation . when the radiation is high energy , the dqe of the imager falls . in one embodiment , the dqe of a mv imager may be 2 %. in order to increase the efficiency , the scintillation material has to be made thicker . with a lower dqe , higher doses of source radiation have to be applied to get a set quality of image . however , a higher radiation dose to a patient may be detrimental and is typically not preferred . typically , that a patient be exposed to as little dose of radiation as possible is desired . thus , increasing the dqe of the imager achieves the goal of maintaining image quality while reducing the radiation received by a patient , or alternatively , improves and increases image quality without exposing a patient to increased levels of radiation . an exemplary embodiment of the design of a detector according to the present invention is presented in fig5 . in one embodiment of this invention , multiple layers of the imager ( scintillator 504 and photo - diode array 502 ) are built on top of each other . in one embodiment , x - rays 501 are received incident to the top layer of the imager and travel through a series of scintillator and photo - diode pairs , thereafter allowing for image capture processing . in an alternative embodiment , layers of the pixel matrix with different resolutions ( e . g ., a higher or lower density of pixels ) may be used . for instance , the top layer could have double the resolution ( 502 ). according to an alternate embodiment , an imager is provided with multiple layers having different energy sensitivities , respectively . for example , the top layer could be made sensitive to all energies , while the second layer could be made sensitive to a higher energy spectra by adding a filter between the two layers . processing these images allows the acquisition of images which is sensitive to the lower energy photon . the lower energy spectrum of the photons typically contains more useful image information and hence improves image quality . fig6 represents a multilayer close - up view of an imager ( e . g ., the imager described above with respect to fig5 ). x - rays 601 are received incident to the top layer . as presented , the various scintillating layers are represented in fig6 as 602 . photo - diode arrays are depicted as 603 . one scintillator and photo - diode array layer pair is depicted as 605 . photo - diodes 604 refers to peculiar diodes and may be configured to react to selected specialized particles only . in one embodiment of the invention , the multi - layer detector combines the individual efficiencies of the single scintillator photo - diode pair to add up linearly and form one high efficient detector . a multi - layer imager ( e . g ., an imager having five layers ) for example will combine the efficiency of each of the five layers to form a much more efficient composite imager . for example , a five layered imager having a 2 % efficiency per layer may have a 10 % efficiency according to embodiments of the present invention as described herein . in further embodiments , each layered scintillator and photo - diode layer may also comprise a sub - imager . according to these embodiments , in order to restore resolution when combining the images from each layer , the sub - images are re - sampled and interpolated depending on the source to imager distance to achieve a compatible pixel matrix . each sub - image from this embodiment may also optionally participate in the combination . sub - images are selectively collected across the plurality of layered scintillators and photo - diode layers based on their position in the configuration . with a digital image available from each layer , an image processing unit can appropriately processes the images to improve the resolution . in a still further embodiment of the invention , the top layer in the configuration is operable to be sensitive to light . according to this embodiment , a light field versus x - ray field verification is made possible . for example , the top layer may generate images solely from light photons . this image may be subsequently compared with the x - ray field image generated by another layer that is not light sensitive . therefore , a comparison could be made using the images acquired from a top layer and from another layer . an alternative embodiment uses a light sensitive scintillator as the top layer . the efficacy of the scintillator to generate an accurate image depends on the relational generation of light photons from radiation photons , and on light photons to strike their pixels this way the light and the x - ray image could be captured by the same a - si layer , allowing the images to be taken one after the other . the acquisition of x - ray imaging via images generated from light photons advantageously allows the simultaneous and convenient comparison of images . since the radiation dosage is often high for therapeutic sources during a radiation therapy procedure , a physician is able to cleanly delineate the exact area of exposure through benign light exposure . when the light exposure and x - ray exposure are very close , a physician can verify that the application of high doses of curative radiation will be restricted to the desired areas and is thereby able to limit the harmful effects of radiation to localized tissues with greater accuracy . while x - ray radiation has been used as an exemplary form of radiation , these procedures may be performed with and for any other source of radiation as well . in another embodiment of the invention , a plurality of anti - scatter grids could be placed in between the plurality of layers . the anti - scatter grid may be positioned between the patient and the detector , for example , and used as a method of reducing scattered radiation by absorbing a portion of the scattered radiation in its lead plates . scattering radiation generated in the target object ( e . g ., the patient ) may be collected by the anti - scatter grid . likewise , scatter produced in higher layers of the imager may also be collected by the anti - scatter grid to improve the collection of image data . while traditional solutions of having a thickened scintillator provide but one opportunity to place this anti - scatter grid , embodiments of the present invention provide almost as many opportunities for anti - scatter grid placement as the number of layers present . it must be noted by those skilled in the art that whereas this invention has been described illustratively for x - ray radiation and x - ray photons which generate light photons , an embodiment of this invention may involve a plurality of radiation particles , including but not limited to electrons , photons , protons , ions , light photons or other particles of matter subject to future discovery which may generate a plurality of particles , including but not limited to electrons , photons , protons , ions , light photons or other particles of matter subject to future discovery . nothing in the invention , as described , limits it to a particular radiation photon or striking particle . in an embodiment of the mv imager , different particles may be subject to discovery in the same imager , in different layers . in another embodiment of the invention , the layers of the mv imager may not be the same in terms of filtration , scintillation , resolution or any combination thereof . filtration changes are implemented in one embodiment by use of anti - scatter grid between layers . scintillation changes may be implemented in one embodiment as by using different types of materials , csl versus gs2o2s for example . the changes could also be implemented by using different thicknesses or any combination of the thicknesses and materials . the resolution changes may be implemented in a plurality of layers by narrowing the pixels and increasing their number or any combination thereof . such a variation could also be implemented between layers . in one embodiment , the change in resolution could be made in the direction of beam divergence . in this manner , the layers placed away from the radiation source , may be chosen to have more pixels for the same image size . in another embodiment of the invention , the number of layers may be changed for the imager to be scalar . if a higher dose is required , the number of layers may be increased by modularly adding a plurality of layered pair of scintillator and photo - diode array . similarly for a lower dose rate , the effective dqe of the imager may be reduced by modularly removing the layered pairs . in one embodiment of the invention , the same multilayer imager may be used for low dose application ( such as cone beam computer tomography ) or high dose application such as dosimetry . as presented in fig7 , an exemplary system 700 upon which embodiments of the present invention may be implemented includes a general purpose computing system environment , such as computing system 150 described above with respect to fig1 . in its most basic configuration , computing system 700 typically includes at least one processing unit 701 and memory , and an address / data bus 709 ( or other interface ) for communicating information . depending on the exact configuration and type of computing system environment , memory may be volatile ( such as ram 702 ), non - volatile ( such as rom 703 , flash memory , etc .) or some combination of the two . computer system 700 may also comprise an optional graphics subsystem 705 for presenting information to the computer user , e . g ., by displaying information on an attached display device 710 , connected by a video cable 711 . according to embodiments of the present claimed invention , the graphics subsystem 705 may be coupled directly to the display device 710 through the video cable 711 . a graphical user interface of an application for displaying images generated by a medical imaging device described above with respect to fig1 , and executing in the computer system 700 may be generated in the graphics subsystem 705 , for example , and displayed to the user in the display device 710 . in alternate embodiments , display device 710 may be integrated into the computing system ( e . g ., a laptop or netbook display panel ) and will not require a video cable 711 . in one embodiment , the processing of the image data acquired in the detectors 130 , 140 to generate an image may be performed , in whole or in part , by graphics subsystem 705 in conjunction with the processor 701 and memory 702 , with any resulting output displayed in attached display device 710 . additionally , computing system 700 may also have additional features / functionality . for example , computing system 700 may also include additional storage ( removable and / or non - removable ) including , but not limited to , magnetic or optical disks or tape . such additional storage is illustrated in fig7 by data storage device 707 . computer storage media includes volatile and nonvolatile , removable and non - removable media implemented in any method or technology for storage of information such as computer readable instructions , data structures , program modules or other data . ram 702 , rom 703 , and data storage device 707 are all examples of computer storage media . computer system 700 also comprises an optional alphanumeric input device 706 , an optional cursor control or directing device 707 , and one or more signal communication interfaces ( input / output devices , e . g ., a network interface card ) 709 . optional alphanumeric input device 706 can communicate information and command selections to central processor 701 . optional cursor control or directing device 707 is coupled to bus 709 for communicating user input information and command selections to central processor 701 . signal communication interface ( input / output device ) 709 , also coupled to bus 709 , can be a serial port . communication interface 709 may also include wireless communication mechanisms . using communication interface 709 , computer system 700 can be communicatively coupled to other computer systems over a communication network such as the internet or an intranet ( e . g ., a local area network ), or can receive data ( e . g ., a digital television signal ). in the foregoing specification , embodiments have been described with reference to numerous specific details that may vary from implementation to implementation . thus , the sole and exclusive indicator of what is the invention , and is intended by the applicant to be the invention , is the set of claims that issue from this application , in the specific form in which such claims issue , including any subsequent correction . hence , no limitation , element , property , feature , advantage , or attribute that is not expressly recited in a claim should limit the scope of such claim in any way . accordingly , the specification and drawings are to be regarded in an illustrative rather than a restrictive sense .