Detector Element for Detecting Incident X-Ray Radiation

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This invention relates to an x-ray detector element designed to efficiently detect incident x-ray radiation. It uses a "sandwich" structure where a scintillation layer—containing a transparent matrix with embedded scintillator particles—converts x-rays into visible light (scintillation light). This light is then efficiently captured from both sides by thin, organic or hybrid photoactive layers (forming photodiodes), which convert the light into electrical signals. The specific structure improves sensitivity, signal quality, and fabrication flexibility compared with conventional detectors.

Use CasesContent extracted from patent full text and abstract with AI.

• Medical imaging devices such as x-ray machines and CT scanners
• Radiation dose monitoring during medical procedures to track patient exposure
• Security scanners for airports or customs inspection systems
• Industrial quality control where non-destructive x-ray testing is required
• Scientific instrumentation for materials analysis using x-ray detection

BenefitsContent extracted from patent full text and abstract with AI.

• Higher sensitivity and better signal-to-noise ratio due to increased active area and optimized light capture
• Lower required operating voltage and reduced dark current, allowing for photovoltaic (bias-free) operation in some cases
• Thin, processable layers enable flexible and cost-effective fabrication, potentially on large or curved surfaces
• Improved separation and extraction of charge carriers result in faster response and higher measurement accuracy
• Enhanced design reduces lateral light spread, minimizing cross-talk between detector pixels for higher image resolution
• Organic and hybrid materials used for absorption layers can be tailored for spectral response and may reduce manufacturing costs

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Inventors & Applicants

Patent Abstract

The invention relates to a detector element (2) for detecting incident x-ray radiation. The detector element (2) comprises a scintillation layer (4) for converting the x-ray radiation into scintillation light and a photoactive element (6) for converting the scintillation light into an electric signal. The photoactive element (6) comprises a first photoactive absorption layer (8a) contacted by an electrode (12), and a second photoactive absorption layer (8b) contacted by a counter electrode (14). Here, the scintillation layer (4) is arranged between the first photoactive absorption layer (8a) and the second photoactive absorption layer (8b).