Abstract: A digital radiographic detector includes redundant bonding pads formed on the array substrate and electrically connected to the array of photosensors. A plurality of COFs are each electrically connected to one of the bonding pads. A repair may be performed by removing a bond pad and reconnecting a corresponding COF to a redundant bond pad. A PCB including array read out electronics is electrically connected to the plurality of COFs.

Abstract: A digital radiographic detector uses an IGZO active layer in the switching element for each imaging pixel in a two-dimensional array of imaging pixels. Each imaging pixel has a photo-sensitive element and the switching element. Read-out circuits electrically connected to the two-dimensional array generate a radiographic image by reading out image data by switching on and off the switching elements. The IGZO active layer may be formed having a thickness less than about 7 nm.

Abstract: A radiographic energy detecting pixel generates charges in a photosensor in response to photon impacts. A switch electrically connected to the photosensor selectively transmits collected charges to a data line. A sensing circuit electrically connected to the photosensor detects a rate of accumulation of the charges in the photosensor.

Abstract: A digital radiographic detector uses an IGZO active layer in the switching element for each imaging pixel in a two-dimensional array of imaging pixels. Each imaging pixel has a photo-sensitive element and the switching element. Read-out circuits electrically connected to the two-dimensional array generate a radiographic image by reading out image data by switching on and off the switching elements. The IGZO active layer may be formed having a thickness less than about 7 nm.

Abstract: A digital radiographic detector uses an IGZO active layer in the switching element for each imaging pixel in a two-dimensional array of imaging pixels. Each imaging pixel has a photo-sensitive element and the switching element. Read-out circuits electrically connected to the two-dimensional array generate a radiographic image by reading out image data by switching on and off the switching elements. The IGZO active layer may be formed having a thickness less than about 7 nm.

Abstract: A radiographic energy detecting pixel generates charges in a photosensor in response to photon impacts. A switch electrically connected to the photosensor selectively transmits collected charges to a data line. A sensing circuit electrically connected to the photosensor detects a rate of accumulation of the charges in the photosensor.

Abstract: A digital radiographic detector uses an IGZO active layer in the switching element for each imaging pixel in a two-dimensional array of imaging pixels. Each imaging pixel has a photo-sensitive element and the switching element. Read-out circuits electrically connected to the two-dimensional array generate a radiographic image by reading out image data by switching on and off the switching elements. The IGZO active layer may be formed having a thickness less than about 7 nm.

Abstract: Embodiments of radiographic imaging systems; radiography detectors and methods for using the same; and/or fabrication methods therefore can include radiographic imaging array that can include a plurality of pixels that each include a photoelectric conversion element coupled to a thin-film switching element. In certain exemplary embodiments, thin-film switching element is a metal oxide (e.g., a-IGZO) TFT manufactured using a reduce photolithography mask counts. In certain exemplary embodiments, the thin-film switching element is a metal oxide (e.g., a-IGZO) TFT that includes reduced lower alignment tolerances between TFT electrodes. In certain exemplary embodiments, the thin-film switching element is a metal oxide (e.g., a-IGZO) TFT including a reduced thickness active layer.

Abstract: A digital radiographic detector uses predetermined calibration information corresponding to a first operating temperature of the detector. The calibration data is accessible by the detector to compensate a radiographic image captured by the detector at a second operating temperature different than the first operating temperature. The operating temperature of the detector is monitored at approximately the time at which the radiographic image is captured at the second temperature.

Abstract: A two dimensional array of digital imaging pixels each include a photo-sensing element and a readout element. A test element within the two-dimensional array, a column of test elements peripheral to the array, or test monitoring circuits peripheral to the array are constructed using the same process as the readout elements. The test element within the array and the column of test elements are connected to a first and second external voltage sources. The test element within the two-dimensional array and the column of test elements may be connected to a test data line or to a data line used by the imaging pixels.

Abstract: Described is a scintillator screen that includes a supporting layer having a phosphor dispersed in a polymeric binder disposed on the supporting layer and a barrier layer disposed on the polymeric binder. The barrier layer includes a non-moisture absorbing polymer selected from the group consisting of polyethylene terephthalate, cellulose diacetate, ethylene vinyl acetate and polyvinyl butyraldehyde. The barrier layer has a thickness of less than 1 micron. An antistatic layer is disposed on the barrier layer. The antistatic layer includes poly(3,4-ethylenedixythiophene)-poly(styrene sulfonate) (PEDOT/PSS) dispersed in a polymer selected from the group consisting of a polyester and a polyurethane. The antistatic layer has a transparency of greater than 95 percent at a wavelength of from about 400 nm to 600 nm.

Abstract: A digital radiographic detector uses predetermined calibration information corresponding to a first operating temperature of the detector. The calibration data is accessible by the detector to compensate a radiographic image captured by the detector at a second operating temperature different than the first operating temperature. The operating temperature of the detector is monitored at approximately the time at which the radiographic image is captured at the second temperature.

Abstract: A digital radiographic detector uses predetermined calibration information corresponding to a first operating temperature of the detector. The calibration data is accessible by the detector to compensate a radiographic image captured by the detector at a second operating temperature different than the first operating temperature. The operating temperature of the detector is monitored at approximately the time at which the radiographic image is captured at the second temperature.

Abstract: Described is a scintillator screen that includes a supporting layer having a phosphor dispersed in a polymeric binder disposed on the supporting layer and a barrier layer disposed on the polymeric binder. The barrier layer includes a non-moisture absorbing polymer selected from the group consisting of polyethylene terephthalate, cellulose diacetate, ethylene vinyl acetate and polyvinyl butyraldehyde. The barrier layer has a thickness of less than 1 micron. An antistatic layer is disposed on the barrier layer. The antistatic layer includes poly(3,4-ethylenedixythiophene)-poly(styrene sulfonate) (PEDOT/PSS) dispersed in a polymer selected from the group consisting of a polyester and a polyurethane. The antistatic layer has a transparency of greater than 95 percent at a wavelength of from about 400 nm to 600 nm.

Abstract: A projection radiographic imaging apparatus includes a scintillator and an imaging array. The imaging array includes a plurality of pixels formed directly on a side of the scintillator. Each of the pixels includes at least one photosensor and at least one readout element.

Abstract: Embodiments relate to detector imaging arrays with scintillators (e.g., scintillating phosphor screens) mounted to imaging arrays or radiographic detectors using the same. For example, the detector imaging arrays can include a scintillator, an imaging array comprising imaging pixels, where each imaging pixel comprises at least one readout element and one photosensor; and a first dielectric layer formed between the scintillator and the imaging layer, wherein the dielectric constant of the insulating layer is very low. Embodiments according to the application can include a second dielectric layer formed over at least a portion of the non-photosensitive regions of the array and/or a first dielectric layer, each with a dielectric constant.

Abstract: A two dimensional array of digital imaging pixels each include a photo-sensing element and a readout element. A test element within the two-dimensional array, a column of test elements peripheral to the array, or test monitoring circuits peripheral to the array are constructed using the same process as the readout elements. The test element within the array and the column of test elements are connected to a first and second external voltage sources. The test element within the two-dimensional array and the column of test elements may be connected to a test data line or to a data line used by the imaging pixels.

Abstract: A wireless X-ray detector for a digital radiography system with remote detection of impinging radiation from the system X-ray source onto a sensor panel having amorphous or crystalline silicon photodiodes or metal insulated semiconductor (MIS) sensors. Certain exemplary embodiments described herein can provide a digital radiography detector including a housing having first and second spaced members and side walls defining a cavity; a radiographic image detector assembly mounted within the cavity for converting a radiographic image to an electronic radiographic image, wherein the detector assembly includes a scintillator screen and a detector imaging array; and a light guiding element positioned proximate the radiographic image detector assembly to detect a start of exposure, a termination of the exposure, dose for the exposure or rate of dose for the exposure using light generated by the scintillator screen.

Abstract: Embodiments of methods/apparatus can transition a DR detector imaging array to low power photosensor mode where a first voltage is applied across the photosensors. Embodiments of methods/apparatus can provide an area radiographic imaging array including a plurality of pixels arranged in a matrix at the imaging array where each pixel can include at least one electrically chargeable photosensor and at least one transistor, row address circuits, signal sensing circuits, and photosensor power control circuitry to maintain a first voltage across photosensors of the portion of the imaging array when the detector is between imaging operations. In one embodiment, photosensor power control circuitry can maintain the first voltage across the photosensors when a power consumption of the signal sensing circuits is less than 1% of the power consumption of the signal sensing circuits during readout of a signal from the portion of the imaging array.

Abstract: A projection radiographic imaging apparatus includes a scintillator and an imaging array. The imaging array includes a plurality of pixels formed directly on a side of the scintillator. Each of the pixels includes at least one photosensor and at least one readout element.