Method and system for PET detector efficiency normalization

Patent metadata

Field	Value
Publication number	US-11835669-B2
Application number	US-202117557710-A
Country	US
Kind code	B2
Filing date	Dec 21, 2021
Priority date	Jan 6, 2020
Publication date	Dec 5, 2023
Grant date	Dec 5, 2023

Abstract

A method of normalizing detector elements in an imaging system is described herein. The method includes a line source that is easier to handle for a user, and decouples the normalization of the detector elements into a transaxial domain and an axial domain in order to isolate errors due to positioning of the line source. Additional simulations are performed to augment the real scanner normalization. A simulation of a simulated line source closely matching the real line source can be performed to isolate errors due to physical properties of the crystals and position of the crystals in the system, wherein the simulated detector crystals are otherwise modeled uniformly. A simulation of a simulated cylinder source can be performed to determine errors due to other effects stemming from gaps between the detector crystals.

First claim

What is claimed is:

1. A positron emission tomography (PET) apparatus, comprising:
a PET detector comprising a plurality of arrayed rings in each of which a plurality of detector crystals are arrayed; and
processing circuitry configured to
acquire a first crystal efficiency for each detector crystal of the plurality of detector crystals based on a measured gamma ray emitted from a line source, a second crystal efficiency for said each detector crystal of the plurality of detector crystals, which is calculated based on a simulation assuming a gamma ray emitted from a cylinder source, and a third crystal efficiency for said each detector crystal of the plurality of detector crystals, which is calculated based on a simulation assuming a gamma ray emitted from a line source, and
calculate a fourth crystal efficiency for said each detector crystal of the plurality of detector crystals based on the first crystal efficiency, the second crystal efficiency, and the third crystal efficiency.

2. The PET apparatus according to claim 1 , wherein the processing circuitry is further configured to
count a number of single detection events detected at said each detector crystal of the plurality of detector crystals based on the measured gamma ray emitted from the line source,
determine a number of coincidence detection events for each arrayed ring, and
acquire the first crystal efficiency based on the number of the single detection events and the number of the coincidence detection events.

3. The PET apparatus according to claim 2 , wherein the processing circuitry is further configured to
determine a relative transaxial efficiency of the detector crystal based on the number of the single detection events,
determine a relative axial efficiency of the detector crystal based on the number of the coincidence detection events, and
acquire the first crystal efficiency based on the relative axial efficiency and the relative transaxial efficiency.

4. The PET apparatus according to claim 1 , wherein the processing circuitry is further configured to
acquire the second crystal efficiency based on the number of single detection events detected at said each detector crystal of the plurality of detector crystals and the number of coincidence detection events for each ring when a simulated gamma ray emitted from a simulated cylinder source is detected by a simulated PET detector, and
acquire the third crystal efficiency based on the number of single detection events detected at said each detector crystal of the plurality of detector crystals and the number of coincidence detection events for each ring when a simulated gamma ray emitted from a simulated line source is detected by the simulated PET detector.

5. The PET apparatus according to claim 4 , wherein the processing circuitry is further configured to
determine a relative transaxial efficiency of the detector crystal based on the number of the single detection events based on the simulated gamma ray emitted from the simulated line source,
determine a relative axial efficiency of the detector crystal based on the number of the coincidence detection events based on the simulated gamma ray emitted from the simulated line source, and
acquire the third crystal efficiency based on the relative axial efficiency and the relative transaxial efficiency.

6. The PET apparatus according to claim 2 , wherein the processing circuitry is further configured to correct the number of the single detection events by applying, to a distribution of the number of single detection events for said each arrayed ring based on the measured gamma ray emitted from the line source, a curve based on the distribution.

7. The PET apparatus according to claim 4 , wherein the processing circuitry is further configured to correct the number of the single detection events based on the simulated cylinder source by applying, to a distribution of the number of single detection events for said each arrayed ring based on the simulated gamma ray emitted from the simulated cylinder source, a curve based on the distribution.

8. The PET apparatus according to claim 4 , wherein the processing circuitry is further configured to correct the number of the single detection events based on the simulated line source by applying, to a distribution of the number of single detection events for said each arrayed ring based on the simulated gamma ray emitted from the simulated line source, a curve based on the distribution.

9. The PET apparatus according to claim 1 , wherein the processing circuitry is further configured to reconstruct a PET image based on a dataset normalized by using the fourth crystal efficiency.

10. A method for determining the efficiency of detector crystals in a positron emission tomography (PET) apparatus, said method to be executed by the PET apparatus comprising a PET detector comprising a plurality of arrayed rings in each of which a plurality of detector crystals are arrayed, the method comprising:
acquiring a first crystal efficiency for each detector crystal based on a measured gamma ray emitted from a line source, a second crystal efficiency for each detector crystal, which is calculated based on a simulation assuming a gamma ray emitted from a cylinder source, and a third crystal efficiency for each detector crystal, which is calculated based on a simulation assuming a gamma ray emitted from a line source; and
calculating a fourth crystal efficiency for each detector crystal based on the first crystal efficiency, the second crystal efficiency, and the third crystal efficiency.

Assignees

• Canon Medical Systems Corp

Inventors

• Qi Wenyuan
• Qiang Yi
• Asma Evren
• Li Xiaoli
• Yang Li
• Peng Peng
• Kolthammer Jeffrey

Classifications

• G01T1/2985 Primary

  In depth localisation, e.g. using positron emitters; Tomographic imaging (longitudinal and transverse section imaging; apparatus for radiation diagnosis sequentially in different planes, steroscopic radiation diagnosis); (using external radiation sources A61B6/02) · CPC title