Scatter and random coincidence rejection

Patent metadata

Field	Value
Publication number	US-11707243-B2
Application number	US-202117230499-A
Country	US
Kind code	B2
Filing date	Apr 14, 2021
Priority date	Apr 14, 2021
Publication date	Jul 25, 2023
Grant date	Jul 25, 2023

Abstract

Multiple interactions, such as Compton scattering, inside a PET detector are used to predict an incident photon's direction for identifying true coincidence events versus scatter/random coincidence events by creating a cone shaped shell projection defining a range of possible flight directions for the incident photon. The disclosed techniques can be used as prior information to improve the image reconstruction process. The disclosed techniques can be implemented in a LYSO/SiPM-based layer stacked detector, which can precisely register multiple interactions' 3D position.

First claim

The invention claimed is:

1. A nuclear medical diagnostic apparatus, comprising:
first and second gamma ray detectors for detecting first and second annihilation gamma rays, respectively;
processing circuitry configured to
identify a possible coincidence event between the first gamma ray detector and the second gamma ray detector;
estimate a range of possible flight directions for the first annihilation gamma ray detected by the first gamma ray detector based on a Compton scatter event, which is detected by the first gamma ray detector, wherein the possible coincidence event includes the Compton scatter event detected by the first gamma ray detector;
determine whether the second gamma ray detector is located within the estimated range of possible flight directions; and
count the possible coincidence event as a true coincidence event when determining that the second gamma ray detector is located within the range of possible flight directions, and not count the possible coincidence event as a true coincidence event when determining that the second gamma ray detector is not located within the range of possible flight directions.

2. The apparatus of claim 1 , wherein the processing circuitry is further configured to estimate the range of possible flight directions for the first annihilation gamma ray detected by the first gamma ray detector based on a location of the Compton scatter event in the first gamma ray detector, an energy of the Compton scatter event in the first gamma ray detector, a location of a second event, and an energy of the second event, wherein the second event is caused by the Compton scatter event.

3. The apparatus of claim 2 , wherein the range of possible flight directions estimated by the processing circuitry comprises flight directions based on a variability of the energy of the Compton scatter event and the energy of the second event, the variability being caused by a limited energy resolution of the nuclear medical diagnostic apparatus.

4. The apparatus of claim 2 , wherein the range of possible flight directions estimated by the processing circuitry comprises flight directions based on a variability of the location of the Compton scatter event and the location of the second event, the variability being caused by a limited spatial resolution of the nuclear medical diagnostic apparatus.

5. The apparatus of claim 2 , wherein the range of possible flight directions estimated by the processing circuitry corresponds to a cone-shaped shell projection, the cone-shaped shell projection having an apex point at the location of the Compton scatter event, an axis in line with the location of the Compton scatter event and the location of the second event, and a half angle based on the energy of the Compton scatter event and the energy of the second event.

6. The apparatus of claim 1 , wherein the nuclear medical diagnostic apparatus is a layer stacked PET detector.

7. The apparatus of claim 1 , wherein the first gamma ray detector and the second gamma ray detector comprise lutetium yttrium oxyorthosilicate.

8. The apparatus of claim 1 , wherein the first gamma ray detector and the second gamma ray detector comprise one or more silicon photomultipliers.

9. A method for collecting coincidence data in a nuclear medical diagnostic apparatus having a first and second gamma ray detector for detecting first and second annihilation gamma rays, respectively, the method comprising:
identifying a possible coincidence event between the first gamma ray detector and the second gamma ray detector;
estimating a range of possible flight directions for the first annihilation gamma ray detected by the first gamma ray detector based on a Compton scatter event, which is detected by the first gamma ray detector, wherein the possible coincidence event includes the Compton scatter event detected by the first gamma ray detector;
determining whether the second gamma ray detector is located within the estimated range of possible flight directions; and
counting the possible coincidence event as a true coincidence event when determining that the second gamma ray detector is located within the range of possible flight directions, and not counting the possible coincidence event as a true coincidence event when determining that the second gamma ray detector is not located within the range of possible flight directions.

10. The method of claim 9 , wherein the estimating the range of possible flight directions comprises estimating the range of possible flight directions for the first annihilation gamma ray detected by the first gamma ray detector based on a location of the Compton scatter event in the first gamma ray detector, an energy of the Compton scatter event in the first gamma ray detector, a location of a second event, and an energy of the second event, wherein the second event is caused by the Compton scatter event.

11. The method of claim 10 , wherein the range of possible flight directions estimated in the estimating step comprises flight directions based on a variability of the energy of the Compton scatter event and the energy of the second event, the variability being caused by a limited energy resolution of the nuclear medical diagnostic apparatus.

12. The method of claim 10 , wherein the range of possible flight directions estimated in the estimating step comprises flight directions based on a variability of the location of the Compton scatter event and the location of the second event, the variability being caused by a limited spatial resolution of the nuclear medical diagnostic apparatus.

13. The method of claim 10 , wherein the range of possible flight directions estimated in the estimating step corresponds to a cone-shaped shell projection, the cone-shaped shell projection having an apex point at the location of the Compton scatter event, an axis in line with the location of the Compton scatter event and the location of the second event, and a half angle based on the energy of the Compton scatter event and the energy of the second event.

14. The method of claim 9 , wherein the nuclear medical diagnostic apparatus is a layer stacked PET detector.

15. The method of claim 9 , wherein the first gamma ray detector and the second gamma ray detector comprise lutetium yttrium oxyorthosilicate.

16. The method of claim 9 , wherein the first gamma ray detector and the second gamma ray detector comprise one or more silicon photomultipliers.

17. A non-transitory computer-readable medium including computer-readable instructions that, when executed by a computing system, cause the computing system to perform a method comprising:
identifying a possible coincidence event between a first gamma ray detector for detecting a first annihilation gamma ray and a second gamma ray detector for detecting a second annihilation gamma ray;
estimating a range of possible flight directions for the first annihilation gamma ray detected by the first gamma ray detector based on a Compton scatter event, which is detected by the first gamma ray detector, wherein the possible coincidence event includes the Compton scatter event detected by the first gamma ray detector;
determining whether the second gamma ray detector is located within the estimated range of possible flight directions; and
counting the possible coincidence event as a true coincidence event when determining that the second gamma ray detector is located within the range of possible flight directions, and not counting the possible coincidence event as a true coincidence event when determining that the second gamma ray detector is not located within the ra

Assignees

• Canon Medical Systems Corp

Inventors

• Cai Liang
• Qi Wenyuan
• Lai Xiaochun
• Peng Peng

Classifications

• G06T12/10

  Image preprocessing, e.g. calibration, positioning of sources or scatter correction · CPC title

• A61B6/5205 Primary

  involving processing of raw data to produce diagnostic data · CPC title

• A61B6/037 Primary

  Emission tomography · CPC title

• G01T1/172

  with coincidence circuit arrangements (G01T1/178 takes precedence {; combination of detectors, see G01T1/1603, G01T1/30}) · CPC title

• G01T1/248

  Silicon photomultipliers [SiPM], e.g. an avalanche photodiode [APD] array on a common Si substrate · CPC title