Self-aligning scintillator-collimator assembly

• US 7,177,387 B2
• Filed: 10/12/2004
• Issued: 02/13/2007
• Est. Priority Date: 11/29/2003
• Status: Expired due to Fees

• Current Assignee: General Electric Company
• Original Assignee: General Electric Company
• Inventors: Schweinert, Gerhardt E., Graves, Brian, Yasunaga, Takashi
• Primary Examiner(s): Ho; Allen C.
• Application Number:
  US10/711,890
• Publication Number:
  US 20050117697A1
• Time in Patent Office: 854 Days
• Field of Search: 378/19, 378/98.8, 378/147, 378/149, 378/154, 250/370.09
• US Class Current: 378/19
• CPC Class Codes: A61B 6/032 Transmission computed tomography [CT]
• CPC Class Codes: A61B 6/4035 the source being combined with a filter or grating
• CPC Class Codes: G01T 1/1648 Ancillary equipment for scintillation cameras, e.g. reference markers, devices for removing motion artifacts, calibration devices adapted for flow studies G01T1/1647
• CPC Class Codes: H01L 27/14658 X-ray, gamma-ray or corpuscular radiation imagers measuring X-, gamma- or corpuscular radiation G01T1/00

Abstract

The present invention is directed to scintillator module for a CT detector as well as an apparatus and method of manufacturing the same. The scintillator module is comprised of a scintillator array having a plurality of scintillators aligned in parallel with respect to one another. A collimator assembly includes a comb having a number of teeth and a plurality of collimator plates positioned proximate to the scintillator array. The scintillator array includes at least one indexing pin extending therefrom. The indexing pin engages the comb and is constructed to improve alignment of the scintillator array relative to the collimator plates.

Claims

1. A CT detector comprising:

a scintillator module including at least one scintillator configured to be impinged with radiographic energy from a radiographic energy source;

at least one indexing pin connected to the scintillator module; and

a collimator assembly having a plurality of collimator elements and a plurality of teeth configured to define a relative position of the plurality of collimator elements and a portion of the plurality of teeth configured to engage the at least one indexing pin, and wherein at least two of the plurality of teeth are constructed to flank an indexing pin.

2. The CT detector of claim 1 wherein the at least one scintillator includes a plurality of scintillators uniformly arranged in a scintillator array.

3. The CT detector of claim 1 further comprising at least one photodiode configured to detect illumination of the at least one scintillator.

4. The CT detector of claim 1 incorporated into a rotatable gantry of a CT imaging system.

5. A scintillator-collimator combination comprising:

a plurality of collimator elements configured to collimate x-rays projected thereat;

a scintillator module having a scintillator pack formed of a material configured to illuminate upon reception of x-rays;

a comb having a plurality of teeth constructed to align the plurality of collimator elements and constructed to engage the collimator module and align the scintillator module relative to the plurality of collimator elements; and

wherein the scintillator module further comprises a locating pin constructed to snuggly engage a recess of the comb, wherein the recess is defined between two of the plurality of teeth.

6. The scintillator-combination of claim 5 wherein the locating pin is configured to align the scintillator pack with respect to the plurality of collimator elements such that the scintillator module does not overlap two collimator elements spaced apart from one another a distance equal to a width of the scintillator module.

7. The scintillator-collimator combination of claim 5 configured to be optically coupled to a photodiode array and configured to detect illumination from the scintillator pack and output electrical signals responsive thereto.

8. The scintillator-collimator combination of claim 5 incorporated into a CT imaging system designed to acquire diagnostic data of a medical patient.

9. A CT system comprising:

a rotatable gantry having a bore centrally disposed therein;

a table movable fore and aft through the bore and configured to position a subject for CT data acquisition;

a high frequency electromagnetic energy projection source positioned within the rotatably gantry and configured to project high frequency electromagnetic energy toward the subject; and

a detector array disposed within the rotatably gantry and configured to detect high frequency electromagnetic energy projected by the projection source and impinged by the subject, the detector array including;

a plurality of scintillator modules, each having a scintillator array and an indexing pin;

a collimator assembly having a plurality of collimator plates; and

a detector support having at least one comb of alignment teeth, the alignment teeth constructed to align the plurality of collimator plates and engage an indexing pin to align a scintillator array with the plurality of collimator plates.

10. The CT system of claim 9 wherein the alignment teeth define a uniform spacing between collimator plates of the plurality of collimator plates.

11. The CT system of claim 9 wherein the indexing pin laterally extends beyond an end of a respective scintillator array.

12. A method of manufacturing a CT detector comprising the steps of:

providing a scintillator away having at least one locator extending beyond the scintillator array;

providing a comb having a plurality of teeth constructed to define a spacing between collimating elements of a collimator; and

positioning the at least one locator between at least two of the plurality of teeth.