Koninklijke Philips Corporation N.V.

John Vesel

Jinghan Ye

Michael J Petrillo

Frank P DiFilippo

Steven E Cooke

David Sowards-Emmerd

Lingxiong Shao

Jens Wiegert

Paul M Hug

Matthias Bertram

Mahmoud Janbakhsh

Rizwan Syed Hassan

Jody L Garrard

Hongjie Liang

Sorin V Cora

Ian Farmer

Joseph J Stefan

Marc A Huber

Micheal J Petrillo

Michael J Petrilo

Sanyi Tseng

A method and apparatus of image reconstruction attenuation correction in PET or SPECT cardiac imaging is provided. A volumetric attenuation imaging scan by an X-ray source may be used to generate a gamma ray attenuation map. The volumetric attenuation imaging scan may be randomized, and may be performed while the imaged subject is breathing.

Method and apparatus for attenuation correction

When generating a 3D image of a subject or patient, a cone beam X-ray source () is mounted to a rotatable gantry () opposite an offset flat panel X-ray detector (). A wedge-shaped attenuation filter () of suitable material (e.g., aluminum or the like) is adjustably positioned in the cone beam to selectively attenuate the beam as a function of the shape, size, and density of a volume of interest () through which X-rays pass in order to maintain X-ray intensity or gain at a relatively constant level within a range of acceptable levels.

Movable wedge for improved image quality in 3D X-ray imaging

When performing nuclear (e.g., SPECT or PET) and CT scans on a patient, a volume cone-beam CT scan is performed using a cone-beam CT X-ray source () and an offset flat panel X-ray detector (). A field of view of the X-ray source overlaps a field of view of two nuclear detector heads (), and the offset of the X-ray detector () minimizes interference with nuclear detector head movement about a rotatable gantry (). Additionally, a locking mechanism () provides automatically locking of the X-ray detector () in each of a stowed and operation position, improving safety and CT image quality.

Nuclear medicine SPECT-CT machine with integrated asymmetric flat panel cone-beam CT and SPECT system

A computed tomography acquisition geometry provides an increased field of view (). A radiation source () such as an x-ray source and a radiation detector () are displaced from the imaging center (). In one implementation, the central ray () of a radiation beam () is parallel to the plane of the detector () at the detector midpoint (), but is displaced from the imaging center.

Computed tomography image acquisition

A radiation detector package includes a radiation-sensitive solid-state element () having a first electrode () and a pixelated second electrode () disposed on opposite principal surfaces of the solid-state element. An electronics board () receives an electrical signal from the solid-state element responsive to radiation incident upon the radiation-sensitive solid-state element. A light-tight shield (') shields at least the radiation-sensitive solid-state element from light exposure and compresses an insulating elastomer and metal element connector () between the pixilated electrode () and contact pads () on the electronics board.

Solid state detector packaging technique

A nuclear camera system includes a detector ( ) for receiving radiation from a subject ( ) in an exam region ( ). The detector ( ) includes a scintillation crystal ( ) that converts radiation events into flashes of light. An array of sensors ( ) is arranged to receive the light flashes from the scintillation crystal ( ). Each of the photomultiplier sensors ( ) generates a respective sensor output value in response to each received light flash. A processor ( ) determines when each of the radiation events is detected. At least one of an initial position and an energy of each of the detected radiation events is determined in accordance with respective distances (d . . . d ) from a position of the detected event to the sensors ( ). An image representation is generated from the initial positions and energies.

Event localization and fall-off correction by distance-dependent weighting

A nuclear medicine imaging device includes a radiation camera ( ) including a plurality of photo multiplier tubes ( ). Each photo multiplier tube ( ) is configured with an analog to digital converter ( ) which converts a detected scintillation event ( ) to sampled digital values. A storage device ( ) is preloaded with an estimator function which can be derived from a calibration scintillation events. A processor ( ) in communication with both the camera ( ) and the storage device ( ), detects an event and combines the digital values which are sampled together to arrive at a total area or energy of the scintillation event. Alternately, if a second pulse ( ) is detected before the first scintillation event ( ) has ended, the area combining (A ) of the first event is stopped and a pulse tail is estimated (A ) from the estimator functions stored. This estimated tail is then added to the combined data values taken until the time of pile-up. Additionally, the estimated tail (A ) is subtracted from the combined data values for the second scintillation event ( ).

Method and apparatus for improved estimation of characteristics of pulses detected by a nuclear camera

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Kirtland, OH, United States of America

John Vesel