Abstract: A position-signal processing method for flat panel gamma imaging probe includes a modeling phase and a use phase. In the modeling phase, a weight direction for an imaging detector is defined, position centers and weight ratios of the imaging detector in the weight direction are utilized to obtain a distribution graph of the weight ratios to the position centers, and curve fitting is performed upon the distribution graph to obtain a position estimation curve. In the use phase, the position estimation curve is utilized to derive a position estimation value of a probe trigger event in a 2D crystal diagram, a position value of the probe in the 2D crystal diagram with respect to the position estimation value of the probe trigger event is obtained, and a crystal code is located in a crystal code look-up table for the position value of the probe in the 2D crystal diagram.

Abstract: A position-signal processing method for flat panel gamma imaging probe includes a modeling phase and a use phase. In the modeling phase, a weight direction for an imaging detector is defined, position centers and weight ratios of the imaging detector in the weight direction are utilized to obtain a distribution graph of the weight ratios to the position centers, and curve fitting is performed upon the distribution graph to obtain a position estimation curve. In the use phase, the position estimation curve is utilized to derive a position estimation value of a probe trigger event in a 2D crystal diagram, a position value of the probe in the 2D crystal diagram with respect to the position estimation value of the probe trigger event is obtained, and a crystal code is located in a crystal code look-up table for the position value of the probe in the 2D crystal diagram.

Abstract: An energy-resolved X-ray image detector includes a scintillation crystal layer, a photon detector layer and an optical layer. The scintillation crystal layer includes a plurality of scintillation crystals. The photon detector layer includes a plurality of photon detector elements. The optical layer is disposed between the scintillation crystal layer and the photon detector layer. The optical layer includes a plurality of optical elements having different light transmittances. The scintillation crystal is used for converting the X-ray beams into scintillation lights, and, when each scintillation light injects the corresponding optical elements, the light transmittances of the optical elements determine whether the scintillation lights can pass through the respective optical elements. The photon detection element then detects the scintillation lights passing through the corresponding optical elements to discriminate the energy of the X-ray beams.

Abstract: An energy-resolved X-ray image detector includes a scintillation crystal layer, a photon detector layer and an optical layer. The scintillation crystal layer includes a plurality of scintillation crystals. The photon detector layer includes a plurality of photon detector elements. The optical layer is disposed between the scintillation crystal layer and the photon detector layer. The optical layer includes a plurality of optical elements having different light transmittances. The scintillation crystal is used for converting the X-ray beams into scintillation lights, and, when each scintillation light injects the corresponding optical elements, the light transmittances of the optical elements determine whether the scintillation lights can pass through the respective optical elements. The photon detection element then detects the scintillation lights passing through the corresponding optical elements to discriminate the energy of the X-ray beams.

Abstract: A method for determining three dimensional locations and energy of gamma incidence events includes the steps of: providing a multi edge-read imaging probe, the multi edge-read imaging probe detecting scintillating photons generated by a gamma incidence event and obtaining a plurality of reaction locations corresponding to the scintillating photons; performing a location-judging process; performing a process for screening valid events; performing an energy-correction process upon the valid events; and, performing a process of energy calculation so as to obtain a total energy value for the gamma incidence event.

Abstract: The present invention based on not changing hardware design, which means that each imaging detector keep independent considerations, the weighted value of the circuit to be pushed back the weight of the original signal, and then estimate the amount of the original signal in a virtual cascade circuit to renew weighted signal; this estimation process through simplification, only simple addition and multiplication calculations on real numbers need to be implemented. Advantage of the present invention is that the signal data through a simple operation will complete the estimate. Executing the estimate in hardware without increasing storage capacity of the rear-end list mode data, and also to achieve a continuous and effective imaging area to expand and enhance the probe's sensitivity and keep a higher signal to noise ratio (S/N ratio).

Abstract: The present invention based on not changing hardware design, which means that each imaging detector keep independent considerations, the weighted value of the circuit to be pushed back the weight of the original signal, and then estimate the amount of the original signal in a virtual cascade circuit to renew weighted signal; this estimation process through simplification, only simple addition and multiplication calculations on real numbers need to be implemented. Advantage of the present invention is that the signal data through a simple operation will complete the estimate. Executing the estimate in hardware without increasing storage capacity of the rear-end list mode data, and also to achieve a continuous and effective imaging area to expand and enhance the probe's sensitivity and keep a higher signal to noise ratio (S/N ratio).

Abstract: A composite crystal array for a pixelated gamma camera and a method of making thereof, which are adapted to a photoelectric matrix that consists of position sensitive photomultiplier elements, in which the photoelectric matrix is divided into sensible and non-sensible areas with a geometric distribution, so as to set a ratio of a segmented region; a configuration detail of a partial optical splitting crystal array and a configuration detail of a whole optical splitting crystal array are set according to the ratio of the segmented region; and the partial optical splitting crystal array and the whole optical splitting crystal array are made according to the two configuration details, and two kinds of crystal arrays are combined to form a whole crystal array for the pixelated cameras according to the segmented region, so that the effective area of the pixelated camera is kept continuous and the resolution thereof is kept uniform.

Abstract: The present invention provides a method for identifying a 3-D event location of a gamma interaction for enhancing the precision of event location determination and improving the practicability of an edge-on ends-read imaging detector. The method establishes two expected photopeak relations and a mapping table for every unit in the sensor array before imaging. In real practice, two sensing values with respect to the energy of scintillation photons generated during the detection on an event are obtained by the edge-on ends-read imaging detector. Furthermore, two energy windows corresponding to each sensing value are determined according to the corresponding expected photopeak relations. If both the two sensing values fall within the corresponding energy windows respectively, the event location along the long axis of sensor array is determined according to the sensor values with respect to the mapping table mentioned above.

Abstract: The present invention provides a method for identifying a 3-D event location of a gamma interaction for enhancing the precision of event location determination and improving the practicability of an edge-on ends-read imaging detector. The method establishes two expected photopeak relations and a mapping table for every unit in the sensor array before imaging. In real practice, two sensing values with respect to the energy of scintillation photons generated during the detection on an event are obtained by the edge-on ends-read imaging detector. Furthermore, two energy windows corresponding to each sensing value are determined according to the corresponding expected photopeak relations. If both the two sensing values fall within the corresponding energy windows respectively, the event location along the long axis of sensor array is determined according to the sensor values with respect to the mapping table mentioned above.

Abstract: A method for making isolating plates for imaging array of crystal lattices, which comprises steps of: providing a substrate; coating a mirror film on the substrate by evaporation so as to form a mirror substrate; and, forming a comb-like isolating plate by the formation of a plurality of notches on the mirror substrate. By assembling a plurality of the comb-like isolating plates to form an array with a plurality of isolated spaces. After inserting a scintillator segment in each of those isolated spaces, an imaging array of crystal lattices for gamma ray detection in nuclear medicine can be manufactured. The imaging device of the invention is preferred since it is easy to assemble, inexpensive, and exhibits desirable imaging and light condensing effects.