Computer tomography apparatus using image intensifier detector

• US 5,692,507 A
• Filed: 12/07/1994
• Issued: 12/02/1997
• Est. Priority Date: 07/02/1990
• Status: Expired due to Fees

• Current Assignee: Varian Medical Systems Incorporated (Siemens AG)
• Original Assignee: Varian Associates, Inc.
• Inventors: Seppi, Edward J., Anderson, Robert L., Shapiro, Edward G.
• Primary Examiner(s): Lateef, Marvin M.
• Assistant Examiner(s): SHAW, SHAWNA JEANNINE
• Application Number:
  US08/352,269
• Time in Patent Office: 1,091 Days
• Field of Search: 364/413.13, 364/413.15, 364/413.26, 250/204, 250/205, 250/214 G, 378/14, 378/16, 378/19, 378/65, 378/98.7, 378/98.8, 128/653.1
• US Class Current: 600/407
• CPC Class Codes: A61B 6/032 Transmission computed tomography [CT]
• CPC Class Codes: A61B 6/548 Remote control of the apparatus or devices
• CPC Class Codes: A61B 6/583 using calibration phantoms
• CPC Class Codes: H04N 5/32 Transforming X-rays cameras or camera modules for generating image signals from X-rays H04N23/30; circuitry of SSIS for transforming X-rays into image signals H04N25/30
• CPC Class Codes: H05G 1/64 Circuit arrangements for X-ray apparatus incorporating image intensifiers
• CPC Class Codes: Y10S 128/92 Computer assisted medical diagnostics

Abstract

Disclosed is a low cost computer tomographic (CT) scanner system specifically designed for radiation therapy treatment planning. A 512-channel photo-diode array with digitizing electronics converts image intensifier optical projection data directly into digital signals and has a dynamic range on the order of 100,000:1. The new simulator includes a rotating gantry, an X-ray generator with radiographic and fluoroscopic modes and a therapy style patient support assembly. Results on head and body size phantoms indicate that the simulator X-ray generator and image intensifier tube (IIT) with multi-channel photo-detector can produce photon statistic limited CT images. Software and hardware compensation methods are described which minimize geometrical distortions. Low noise, high input impedance electronics are employed which are phase-locked to the line frequency. A dual sample interval method is employed which effectively increases the range of the digital signal produced by the front-end electronics by three additional bits.

Claims

1. A radiation therapy X-ray simulator having an X-ray source providing a fan beam, a gantry to support the X-ray source, a couch to support a patient and an image forming system including a computer for fan beam reconstruction without reordering, wherein the simulator is constructed such that the X-ray source is positioned relative to the couch in a geometry essentially identical to the geometry of the same elements of a target radiotherapy machine,

the improvement comprising:

said image forming system includes a first X-ray detector being an image intensifier (IIT) for converting X-rays from said source to electrons after said X-rays have passed through a patient, and for accelerating said electrons to an output phosphor screen to provide visible light, said first X-ray detector having a first quantum efficiency;

a photo diode linear array detector, said photo diode linear array detector replacing a TV camera, a plurality of photo diodes in said photo diode linear array detector having a second quantum efficiency of approximately 0.6 or more electrons per photon and a dynamic range on the order of 35,000 to 1, said photo diode linear array detector providing an electrical signal the amplitude of which is responsive to the intensity of said visible light;

a lens means, said lens means being interposed between said output phosphor screen and said photo diode detector for coupling visible radiation from said image intensifier to said photo diode detector, said lens means having a third quantum efficiency;

wherein an X-ray beam from said X-ray source becomes reduced in intensity as it passes through a portion of a patient and impinges upon said X-ray detector of said IIT at a first point and causes the emission of a visible light ray having an intensity which corresponds to the intensity of the impinging ray and spatially corresponds to said first point, and where said visible light ray passes through said lens means and intersects said photo diode detector at a second point, which second point spatial position and intensity correspond to the spatial position and intensity of said first point; and

wherein the product of said first, second and third quantum efficiencies is greater than unity.

2. The improved apparatus of claim 1, wherein the photo diode detector means includes

a plurality of photo diodes each of which convert the visible radiation impinged thereon into a quantity of charge;

means for integrating the quantity of charge from each of, said photo diodes wherein the integrating means has low noise and high input impedance; and

means for resetting the integrating means in preparation for receipt of a subsequent detector signal wherein the means for integrating includes

a low noise, high input-impedance amplifier having an output, an inverting input to which the quantity of charge is supplied, and a non-inverting input which is coupled to a system common point;

capacitor means coupled between the output and the inverting input of the amplifier for accumulating the applied quantity of charge; and

further wherein the resetting means includes

first switch means coupled in parallel with the capacitor means for controllably discharging the capacitor means in preparation for receipt of a subsequent quantity of charge; and

second switch means coupled between the output of the amplifier and the system common point for clamping the output of the amplifier to system common whenever the first switch means is controlled to discharge the capacitor means.

3. The improved apparatus of claim 1 where said photo diode detector means includes

a main array of photodiodes positioned to receive the visible radiation coupled by the lens means and providing an output signal;

and

an extension detector array positioned to receive X-rays and providing an output signal.

4. The improved apparatus of claim 3, wherein the extension detector array comprises a plurality of detectors, each of which comprises

a body of scintillating crystal material providing visible light photons over a range of the visible light spectrum in proportion to a intensity of the impinging X-rays;

and

a photodiode optically coupled to said body, having a response characteristic which is compatible with the range of the visible light spectrum provided by said body, and providing a current which is proportional to the visible light photons received from said body.

5. The improved apparatus of claim 3, wherein said photo diode detector means includes means for accommodating a wide range of output signal magnitudes from the main array of photodiodes and the extension detector array.

6. The improved apparatus of claim 14 wherein said means for accommodating a wide range of detector signal magnitudes includes means for measuring the photo diode outputs from the main array and the extension detector array over a long sample interval and a short sample interval and for selecting the sample which most accurately represents the magnitude of the X-ray photons impinging on the image intensifier and the extension detector array.

7. The improved apparatus of claim 5 including digitizing means wherein said digitizing means includes a 16 bit analog-to-digital converter and means for transforming the 16 bits of data from the 16 bit analog-to-digital converter into an effective 19 bit signal when a predetermined sample interval is used to sample the photo diode detector means.

8. The improved apparatus of claim 12 where said photo diode detector means includes means for background noise correction.

9. The improved apparatus of claim 1 wherein said photo diode detector means includes means for accommodating a wide range of detector signal magnitudes including means for measuring the electrical signals from the image intensifier over a long fixed sample interval and a short fixed sample interval, wherein photodiodes of the photo diode detector array means accumulate charge when the visible radiation impinges upon them, and further wherein the means for measuring said long and a short sample interval are in communication with the photodiodes of the photo diode detector array means.

10. The improved apparatus of claim 9, wherein in operation of the simulator a plurality of scans are obtained, and a plurality of projections within each of the plurality of scans is obtained, and further wherein all photo diodes in said photodiode linear array detector are each sampled over said long time interval and over said short time interval during each of said plurality of projections.

11. The improved apparatus of claim 9, wherein the electrical signals from the photo diode detector means have an expected range of magnitudes, and further wherein the long time interval samples are selected as the electrical signal to be used in constructing a tomographic X-ray image when the detector signal magnitude is below a transition range of magnitudes;

and further wherein the short time interval samples, multiplied by a scaling factor, are selected as the electrical signal to be used in constructing the tomographic X-ray image when the detector signal magnitude is above the transition range of magnitudes, and a weighted combination of the long interval samples and the scaled short interval samples are selected as the detector signal to be used in constructing the tomographic X-ray image when the electrical signal magnitude falls within the transition range of magnitudes.

12. The improved apparatus of claim 11, wherein the photo diodes of the photo diode detector means are characterized by a series of calibrating signals which are measured using a long sample interval and a short sample interval, and further wherein the scaling factor is determined by comparing the long sample interval calibrating signal measurements to the short sample interval calibrating signal measurements, multiplied by the scaling factor, over a predetermined range of magnitudes, and adjusting the scaling factor to obtain the most accurate sealing factor using a least squares curve fitting criteria.

13. The improved apparatus of claim 12, wherein the calibrating signals measurements have a range from zero counts to 500,000 counts, and the predetermined range of magnitudes over which the long and short sample interval calibrating signals measurements are compared is approximately 44,000 to 62,000 counts.

14. The improved apparatus of claim 13, wherein the scaling factor is approximately equal to nine and said fixed long time interval is nine times the period of said fixed short time interval.