X-ray or gamma ray systems or devices – Electronic circuit – With display or signaling
Reexamination Certificate
2001-03-27
2002-03-19
Kim, Robert H. (Department: 2882)
X-ray or gamma ray systems or devices
Electronic circuit
With display or signaling
C378S098800
Reexamination Certificate
active
06359966
ABSTRACT:
BACKGROUND OF THE INVENTION
1. Field of the Invention
The present invention is directed to an X-ray diagnostic installation of the type having a high-voltage generator for an X-ray tube for generating an X-ray beam, an X-ray image converter that has a scintillator layer and a semiconductor layer with light-sensitive pixel elements arranged in a matrix, and a combined back light/dose measuring unit arranged therebehind in the beam direction that is formed by an array of light-emitting diodes arranged in a matrix, as backside illumination and light-sensitive sensors that acquire the X-ray dose, as sensors, with a measurement transducer for the control of the high-voltage generator being connected thereto.
2. Description of the Prior Art
German OS 196 06 873 discloses an X-ray diagnostic installation of this type shown in
FIGS. 1 and 2
having an X-ray tube
2
supplied with high voltage and filament voltage by a voltage generator
1
as an X-ray unit that generates a cone-shaped beam of X-rays
3
that penetrates a patient and is incident as an X-ray image on a two-dimensional X-ray image converter
5
that is sensitive to X-rays
3
. The X-rays are incident thereon attenuated according to the transparency of the patient
4
. The X-ray image converter
5
converts the X-ray image into electrical signals that are supplied to an image system
7
as digital image data
6
. In a known way, the image system
7
can include a calculating circuit, filter circuits, converters, image memories and processing circuits, these not being shown. For playback of the acquired X-ray images, it is connected to a monitor
8
. Control elements
9
are connected to the remaining components of the X-ray diagnostic installation via a system controller and communication
10
. The system controller and communication
10
also has at least one measurement transducer that is connected to the voltage generator
1
for controlling the X-ray dose.
FIG. 2
shows the known X-ray image converter
5
of
FIG. 1
in greater detail. It has a scintillator
11
onto which the X-rays
3
are incident, these being converted into a visible X-ray image according to the attenuation by the patient
4
. The scintillator
11
can be composed of cesium iodide (Csl). The visible light
12
generated by the scintillator
11
is incident onto a number of light-sensitive pixel elements, for example photodiodes
13
, that are arranged on a glass substrate
14
arranged in a pixel matrix. The semiconductor of the pixel matrix can, for example, be composed of hydrogen-doped amorphous silicon (aSi:H).
As combined back light/dose measuring unit
15
, an array of light-emitting diodes
16
and photodiodes
17
is arranged behind the X-ray image converter
5
as seen in the direction of the X-rays
3
for resetting residual charges of the pixel elements due to illumination of the semiconductor of the X-ray image converter
5
, given simultaneous measurement of the dose power or dose.
The light-emitting diodes
16
of the back light/dose measuring unit
15
generate an optical backside light
18
in order to improve the temporal signal behavior of the X-ray image converter
5
. A resetting by illumination of the pixel matrix of the photodiodes
13
of the X-ray image converter
5
ensues between two readout events. As a result, these are completely discharged and low-impedance for speed-up. Since the illumination cannot ensue line-by-line, a simultaneous, common resetting of the entire array is undertaken.
Approximately 15% of the scintillator light
12
converted by the scintillator penetrates the semiconductor layer of the pixel matrix
13
and the glass substrate
14
. This light intensity, which is a criterion for the incident dose power, is measured for the purpose of dose control. To this end, the combined back light/dose measuring unit
15
is composed of small photodiodes
15
arranged between light-emitting diodes
16
that are respectively connected to measurement transducers via switches for the selection of an arbitrary dominant in order to thus measure the X-ray dose. With the X-ray irradiation as a criterion for the accumulating X-ray dose, the ongoing radiation can be shut off by the automatic exposure unit after a prescribed value has been reached.
The electrical measured signals
19
that the photodiodes
17
generate are a criterion for the dose power or dose. The current (t) is thereby a criterion for the dose power DL(t).
The measured signals
19
of the photodiodes
17
can be used for dose control. To that end, the current is integrated up to the dose D(t
x
) at time t
x
D
(
t
x
)
∼
∫
0
t
x
I
(
t
)
ⅆ
t
The X-rays
3
are turned off at time t
x
, when the desired accumulated dose has been reached.
Since the photodiodes
17
of the combined back light/dose measuring unit
15
are arranged in the same plane as the light-emitting diodes
16
and, thus, parallel to the X-ray image converter
5
, they are also exposed to the X-radiation, so that errors in the dose measurement can occur. Further, all photodiodes cannot be employed since some are not resistant to X-radiation.
German OS 44 05 233 discloses an X-ray image device wherein a planar image converter is coupled to a luminescent screen via an optical coupling means. Further, the natural lateral light scatter of the luminescent screen is utilized by placing a light sensor of an automatic exposure unit at the narrow side.
The lateral light propagation of the luminescent screen, however, must always be minimized because of the spatial resolution, i.e. light from the central regions of interest hardly proceeds to the sensor. Further, only an integral, edge-emphasized but not a spatially resolved light measurement is possible.
SUMMARY OF THE INVENTION
An object of the present invention is to provide an X-ray diagnostic installation of the type initially described that enables a simple, fast and reliable acquisition of the X-ray dose during the irradiation with X-rays in A spatially resolved fashion, but wherein the light-sensitive pixel elements are not charged with X-rays for measurement.
This object is inventively achieved in that light waveguides are arranged in front of the light-sensitive sensors of the combined back light/dose measuring unit, the light waveguides conducting the light that proceeds from the X-ray image converter during the irradiation and that is incident onto the combined back light/dose measuring unit onto the light-sensitive sensors.
Inventively, the light-sensitive sensors can be shielded against X-rays by a covering and/or can be arranged outside the X-rays.
The homogeneity of the back side light can be improved when a diffusor layer is arranged between X-ray image converter and back light/dose measuring unit.
The precision of the measurement in the central region can be enhanced when the light entry faces of the light waveguides are arranged more densely in the center of the back light/dose measuring unit.
It has proven advantageous when the X-ray image converter is an aSi:H detector.
The measurement can ensue in arbitrary regions when the measured signals of the individual photodiodes are combined into groups to regions referred to as dominants.
The structural outlay given high precision of the measurement can be simplified when a number of light waveguides are respectively allocated to one of the photodiodes.
The light entry faces can have a uniform or non-uniform distribution, with the density of the light entry faces being higher in the middle and/or the dominant given a non-uniform distribution.
It has proven expedient in view of a compact structure for a combined back light/dose measuring unit for an X-ray diagnostic installation with light-emitting diodes as backside illumination and light-sensitive sensors as detector of the X-ray dose when the light entry faces of the light waveguides are arranged between the light-emitting diodes of the array, with the light waveguides being brought together at one side in a narrow arc toward the back and behind the array, and with the light-sensitive sensors b
Kiknadze Irakli
Kim Robert H.
Schiff & Hardin & Waite
Siemens Aktiengesellschaft
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