Abstract: The present discussion relates to the design fabrication and use of synthetic scaffold structure for bone growth. In certain implementations the scaffold structures are comprised of a plurality of repeating structures each defined by a local topology. The local topologies are defined at a subset of points in their respective volumes by various parameters including, but not limited to, shape index, curvedness, mean curvature, and Gauss curvature.

Abstract: Various embodiments discussed herein utilize a C-shaped imager to provide images with a minimal footprint, such as may be suitable in a surgical context. In addition the systems and methods described herein allow for suitable angular (i.e., azimuthal) scan coverage about the patient. To provide real-time 3D imaging, multiple X-ray tubes or a distributed X-ray source may be employed, coupled with an extended detector or multiple detectors. To reconstruct high-quality volumes, in some implementations reconstruction techniques may be employed that utilize pre-operative (pre-op) computed tomography (CT), magnetic resonance imaging (MRI), ultrasound (U/S), or other suitable modality images or data as prior information.

Abstract: Various embodiments discussed herein utilize a C-shaped imager to provide images with a minimal footprint, such as may be suitable in a surgical context. In addition the systems and methods described herein allow for suitable angular (i.e., azimuthal) scan coverage about the patient. To provide real-time 3D imaging, multiple X-ray tubes or a distributed X-ray source may be employed, coupled with an extended detector or multiple detectors. To reconstruct high-quality volumes, in some implementations reconstruction techniques may be employed that utilize pre-operative (pre-op) computed tomography (CT), magnetic resonance imaging (MRI), ultrasound (U/S), or other suitable modality images or data as prior information.

Abstract: Various embodiments discussed herein utilize a C-shaped imager to provide images with a minimal footprint, such as may be suitable in a surgical context. In addition the systems and methods described herein allow for suitable angular (i.e., azimuthal) scan coverage about the patient. To provide real-time 3D imaging, multiple X-ray tubes or a distributed X-ray source may be employed, coupled with an extended detector or multiple detectors. To reconstruct high-quality volumes, in some implementations reconstruction techniques may be employed that utilize pre-operative (pre-op) computed tomography (CT), magnetic resonance imaging (MRI), ultrasound (U/S), or other suitable modality images or data as prior information.

Abstract: Exemplary embodiments are directed to imagining detectors and methods of fabricating the imagining detectors for use in medical imagining systems. In exemplary embodiments, a detector for an imaging device include a continuous unpatterned photoelectric material that forms a portion of a photosensor and an electrode disposed with respect to the photoelectric material to form an anode or cathode of the photosensor. Data readout lines connected to the outputs of transistors of the detector can be susceptible electronic noise from capacitive coupling between the electrode of the photosensor. In exemplary embodiments of the present disclosure, a lateral offset and/or vertical offset between the electrode and the data readout lines can be formed to control the capacitive coupling between the electrode and the data readout line.

Abstract: A process for fabricating an organic x-ray detector is presented. The process includes forming a layered structure that includes disposing a first electrode layer on a thin film transistor array, disposing an organic photoactive layer on the first electrode layer and disposing a second electrode layer on the organic photoactive layer. The organic photoactive layer includes a fullerene or a fullerene derivative having a carbon cluster of at least 70 carbon atoms. The process further includes disposing a scintillator layer on the layered structure at a temperature greater than 50 degrees Celsius. An organic x-ray detector fabricated by the process is further presented. An x-ray system including the organic x-ray detector is also presented.

Abstract: A process for fabricating an organic x-ray detector is presented. The process includes forming a multilayered structure that includes disposing a first electrode layer on a thin film transistor array, disposing an organic absorber layer on the first electrode layer, and disposing a second electrode layer on the organic absorber layer. The process further includes disposing a scintillator layer on the second electrode layer and thermally treating the multilayered structure after the step of disposing the second electrode layer. An organic x-ray detector fabricated by the process is further presented. An x-ray system including the organic x-ray detector is also presented.

Abstract: An organic x-ray detector and a method of making the organic x-ray detector are disclosed. The x-ray detector includes a TFT array disposed on a substrate, an organic photodiode layer disposed on the TFT array, a barrier layer disposed on the photodiode layer, and a scintillator layer disposed on the barrier layer, such that the barrier layer includes at least one inorganic material.

Abstract: An organic charge integrating device is presented. The organic charge integrating device includes a thin film transistor (TFT) array, a first electrode layer disposed on the TFT array, an organic photoactive layer disposed on the first electrode layer, and a second electrode layer disposed on the organic photoactive layer. The organic photoactive layer has a thickness in a range from about 700 nanometers to about 3 microns. An organic x-ray detector is presented. An imaging system including the organic x-ray detector is also presented.

Abstract: A process for fabricating an organic x-ray detector is presented. The process includes forming a layered structure that includes disposing a first electrode layer on a thin film transistor array, disposing an organic photoactive layer on the first electrode layer and disposing a second electrode layer on the organic photoactive layer. The organic photoactive layer includes a fullerene or a fullerene derivative having a carbon cluster of at least 70 carbon atoms. The process further includes disposing a scintillator layer on the layered structure at a temperature greater than 50 degrees Celsius. An organic x-ray detector fabricated by the process is further presented. An x-ray system including the organic x-ray detector is also presented.

Abstract: A process for fabricating an organic x-ray detector is presented. The process includes forming a multilayered structure that includes disposing a first electrode layer on a thin film transistor array, disposing an organic absorber layer on the first electrode layer, and disposing a second electrode layer on the organic absorber layer. The process further includes disposing a scintillator layer on the second electrode layer and thermally treating the multilayered structure after the step of disposing the second electrode layer. An organic x-ray detector fabricated by the process is further presented. An x-ray system including the organic x-ray detector is also presented.

Abstract: An organic x-ray detector is presented. The organic x-ray detector includes a layered structure. The layered structure includes a thin-film transistor (TFT) array disposed on a substrate, an organic photodiode disposed on the TFT array, and a scintillator layer disposed on the organic photodiode. The organic x-ray detector further includes an encapsulation cover at least partially encapsulating the layered structure; and an oxygen getter layer disposed between the organic photodiode and the encapsulation cover, wherein the oxygen getter layer includes an ether-containing material. X-ray system including the organic x-ray detector is also presented.

Abstract: There is set forth herein a method for making an apparatus for use in X ray detection comprising fabricating a first layered assembly 10 comprising a scintillator and first electrode layer, and laminating the first layered assembly 10 onto a second layered assembly 20 wherein the second layered assembly has a thin film transistor (TFT) array, wherein the TFT array includes a second electrode layer, wherein at least one of the first layered assembly and the second layered assembly includes an organic photodiode (OPD) absorber layer and wherein the laminating is absent use of an adhesive.

Abstract: An organic photodiode is presented. The organic photodiode includes a first electrode; an organic absorber layer disposed on the first electrode; a second electrode disposed on the organic absorber layer; and a first charge blocking layer including a metal fluoride disposed between the organic absorber layer and one of the first electrode or the second electrode. The metal fluoride comprises lithium, sodium, potassium, rubidium, cesium, berrylium, magnesium, calcium, strontium, barium, iron, yttrium, ytterbium, or combinations thereof. The charge blocking layer is substantially free of an electrically conductive material, and the thickness of the charge blocking layer is greater than about 10 nanometers. A method of making an organic photodiode and an organic x-ray detector are also presented.

Abstract: An organic x-ray detector is presented. The organic x-ray detector includes a layered structure. The layered structure includes a thin-film transistor (TFT) array disposed on a substrate, an organic photodiode disposed on the TFT array, and a scintillator layer disposed on the organic photodiode. The organic x-ray detector further includes an encapsulation cover at least partially encapsulating the layered structure; and an oxygen getter layer disposed between the organic photodiode and the encapsulation cover, wherein the oxygen getter layer includes an ether-containing material. X-ray system including the organic x-ray detector is also presented.

Abstract: There is set forth herein a method for making an apparatus for use in X ray detection comprising fabricating a first layered assembly 10 comprising a scintillator and first electrode layer, and laminating the first layered assembly 10 onto a second layered assembly 20 wherein the second layered assembly has a thin film transistor (TFT) array, wherein the TFT array includes a second electrode layer, wherein at least one of the first layered assembly and the second layered assembly includes an organic photodiode (OPD) absorber layer and wherein the laminating is absent use of an adhesive.

Abstract: An organic x-ray detector and a method of making the organic x-ray detector are disclosed. The x-ray detector includes a TFT array disposed on a substrate, an organic photodiode layer disposed on the TFT array, a barrier layer disposed on the photodiode layer, and a scintillator layer disposed on the barrier layer, such that the barrier layer includes at least one inorganic material.

Abstract: An x-ray imaging system includes an organic x-ray detector having a layered structure composed of a scintillator layer disposed on a first electrode layer and an absorber layer sandwiched between the first electrode layer and a second electrode layer. The second electrode layer is disposed on a TFT array and the TFT array is disposed on a substrate. The absorber layer includes a donor material and an acceptor material, and the donor material contains a low bandgap polymer.

Abstract: Exemplary embodiments are directed to imagining detectors and methods of fabricating the imagining detectors for use in medical imagining systems. In exemplary embodiments, a detector for an imaging device include a continuous unpatterned photoelectric material that forms a portion of a photosensor and an electrode disposed with respect to the photoelectric material to form an anode or cathode of the photosensor. Data readout lines connected to the outputs of transistors of the detector can be susceptible electronic noise from capacitive coupling between the electrode of the photosensor. In exemplary embodiments of the present disclosure, a lateral offset and/or vertical offset between the electrode and the data readout lines can be formed to control the capacitive coupling between the electrode and the data readout line.

Abstract: The present approach involves a radiation detector module with increased quantum efficiency and methods of fabricating the radiation detector module. The module includes a scintillator substrate and a photodetector fabricated on the scintillator substrate. The photodetector includes an anode, active organic elements, and a cathode. The module also includes a pixel element array disposed over the photodetector. During imaging, radiation attenuated by an object to be imaged may propagate through the pixel element array and through the layers of the photodetector to be absorbed by the scintillator which in response emits optical photons. The photodetector may absorb the photons and generate charge with improved quantum efficiency, as the photons may not be obscured by the cathode or other layers of the module. Further, the module may include reflective materials in the cathode and at the pixel element array to direct optical photons towards the active organic elements.