Positron CT apparatus and a timing correction method

Patent metadata

Field	Value
Publication number	US-9360569-B2
Application number	US-201013698971-A
Country	US
Kind code	B2
Filing date	May 18, 2010
Priority date	May 18, 2010
Publication date	Jun 7, 2016
Grant date	Jun 7, 2016

Abstract

A PET apparatus and a timing correction method of this invention select two target gamma-ray detectors which count coincidences, select a reference detector which is one detector out of the two selected gamma-ray detectors, select a gamma-ray detector different from the other, opposite detector, and when repeating the selection, make a time lag histogram concerning two gamma-ray detectors selected in the past a reference, and correct a time lag histogram concerning gamma-ray detectors selected this time based on the reference. By repeating an operation to make the corrected time lag histogram concerning the two gamma-ray detectors a new reference, an optimal time lag histogram can be obtained without repeating many measurements and computations.

First claim

The invention claimed is:

1. A positron CT apparatus having a plurality of detectors for detecting radiation released from a positron-emitting radioactive drug given to a patient, comprising:
a computing device, in connection with a time lag histogram showing a count value distribution of time lag variations for each pair of detectors which count coincidences of the radiation, for:
(i) selecting a first detector as a reference detector and a second detectors as a count detector which count coincidences, to obtain a time lag histogram of the first detector and the second detector, and selecting a group of detectors including the second detector,
(ii) selecting a detector different from the second detector from the group of detectors,
(iii) correcting a time lag histogram of the first detector and the selected different detector using the time lag histogram of the first detector and the second detector,
(iv) newly selecting a detector, which has not been previously selected, from the group of detectors, and correcting a time lag histogram of the first detector and the newly selected detector using the time lag histogram of the first detector and the second detector,
(v) repeating (iv) until all of the detectors in the group of detectors are subjected to (iv), and
repeating (i)-(v) by selecting a new reference detector, a new counter detector and a new group of detectors until all of the plurality of detectors in the positron CT apparatus are subjected to the selection and correction, the new reference detector being selected from a previously selected group of detectors; and
a coincidence counting circuit for counting coincidences of the radiation based on the time lag histogram for each pair of detectors repeatedly corrected by the computing device.

2. The positron CT apparatus according to claim 1 , wherein:
a time lag at which a total count value in the time lag histogram made the reference becomes the largest is used as reference value; and
the computing device corrects time lags of the time lag histograms based on the reference value.

3. The positron CT apparatus according to claim 1 , wherein:
a time lag with a middle value between a time lag at which a total count value is the largest and a time lag at which the total count value is the second largest in the time lag histogram made the reference is used as reference value; and
the computing device corrects time lags of the time lag histograms based on the reference value.

4. The positron CT apparatus according to claim 1 , wherein:
the detector includes:
a plurality of scintillator elements which produce fluorescence upon incidence of the radiation; and
a photoelectric conversion device which detects the radiation by carrying out photoelectric conversion of light from each scintillator element; and
the detectors are DOI detectors constructed by stacking the respective scintillator elements in a depth direction of the radiation.

5. The positron CT apparatus according to claim 1 , comprising an external radiation source which emits radiation corresponding in type to the radioactive drug, or a phantom which emits, from inside, radiation corresponding in type to the radioactive drug, the time lag histograms being acquired based on the radiation from the external radiation source or the phantom.

6. The positron CT apparatus according to claim 1 , wherein the detectors have scintillator elements with self-radioactivity, the time lag histograms being acquired based on radiation from the self-radioactivity.

7. A positron CT apparatus having a plurality of detectors for detecting radiation released from a positron-emitting radioactive drug given to a patient, comprising:
a computing device, in connection with a time lag histogram showing a count value distribution of time lag variations for each pair of detectors which count coincidences of the radiation, for selecting two target detectors which count coincidences, selecting one detector out of the two selected detectors, selecting a detector different from the other detector, and when repeating the selection, making a time lag histogram concerning two detectors selected in the past a reference, correcting a time lag histogram concerning detectors selected this time based on the reference, and repeating an operation to make the corrected time lag histogram concerning the two detectors a new reference; and
a coincidence counting circuit for counting coincidences of the radiation based on the time lag histogram for each pair of detectors repeatedly corrected by the computing device, wherein:
a time lag with a middle value between a time lag at which a total count value is the largest and a time lag at which the total count value is the second largest in the time lag histogram made the reference is used as reference value, and
the computing device corrects time lags of the time lag histograms based on the reference value.

8. The positron CT apparatus according to claim 1 , wherein the new reference detector is located at an end of the previously selected group of detectors.

Assignees

• Tsuda Tomoaki
• Sato Masanobu
• Shimadzu Corp

Inventors

• Tsuda Tomoaki
• Sato Masanobu

Classifications

• G01T1/1647

  Processing of scintigraphic data (not related to a particular imaging system G01T1/2992) · CPC title

• 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

• 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

• G01T1/208

  Circuits specially adapted for scintillation detectors, e.g. for the photo-multiplier section · CPC title