Radiation detector, particularly for a computed tomography...

Details Radiation detector, particularly for a computed tomography... Radiation detector, particularly for a computed tomography...

1999-09-08

2002-03-26

Hannaher, Constantine (Department: 2878)

Radiant energy

Invisible radiant energy responsive electric signalling

With or including a luminophor

C250S370110, C378S019000

Reexamination Certificate

active

06362480

ABSTRACT:

BACKGROUND OF THE INVENTION
1. Field of the Invention
The present invention is directed to a radiation detector of the type having a scintillator as well as a photodiode array, whereby an electrical connection is provided from the photodiode array to measuring electronics.
2. Description of the Prior Art
A radiation detector of the above type is disclosed in German OS 197 27 219.
FIG. 1
herein as well as
FIGS. 2 and 3
herein, which are taken from German OS 197 27 219 are used below for explaining problems addressed by the subject matter of the present invention.
The computed tomography apparatus shown in
FIG. 1
has a measuring unit composed of an x-ray source ray I that emits a fan-shaped x-ray beam
2
and a radiation receiver
3
that is composed of a series of individual detectors, for example of 512 individual detectors. The focus is referenced
1
1
. The patient
4
to be examined lies on a patient bed
5
. For scanning the patient
4
, the measuring unit
1
,
3
is rotated around a measuring field
9
, in which the patient
4
lies by 360° . The rotational axis is referenced
10
. The x-ray source
1
that is supplied by a voltage generator
6
is operated to emit pulsed or continuous radiation. Given predetermined angular positions of the measuring unit
1
,
3
, sets of data are generated that are supplied from the radiation receiver
3
to a computer
7
that calculates the attenuation coefficients of predetermined picture elements from the generated data sets and visually reproduces these on a viewing monitor
8
. Accordingly, an image of the transirradiated slice of the patient appears on the viewing monitor
8
.
FIG. 1
also shows a gantry
14
on which the x-ray source I and the radiation receiver
3
are mounted. The rotation of the x-ray beam
2
ensues by means with of a drive mechanism
15
which engages the gantry
14
.
The radiation receiver
3
is only schematically shown in FIG.
1
.
FIGS. 2 and 3
show the structure thereof in greater detail. As can be seen in
FIG. 2
a number of individual detectors
16
are held in a formed part
17
composed of plastic, preferably an injection molded part, having a surface on which interconnects
18
are applied at both sides. Detector arrays can also be provided. Further, electronic components
19
(for example, ICs) are mounted on the formed part
17
, these being electrically connected to one another by interconnects
18
. The individual detectors
16
are also electrically connected to the electronic components
19
by the interconnects
18
on the formed part
17
. The formed part
17
accordingly serves the purpose of holding the components
16
,
19
and for their electrical connection.
As can be seen in
FIGS. 1 and 3
the radiation receiver
3
is subdivided into individual detectors transversely relative to the rotational axis
10
as well as in the direction thereof, so that the simultaneous scanning of a number of slices of the patient
4
is enabled. The individual detectors
16
are connected to the interconnects
18
on the formed part
17
by contacts
20
. A scintillator
21
for the conversion of the x-rays into visible light lies in front of the individual detectors
16
, this visible light being converted into corresponding electrical signals by the individual detectors
16
, fashioned as semiconductor detectors.
As can be seen from
FIG. 2
the radiation receiver
3
is constructed of a number of modules
22
, each module thereof comprising a formed part
17
with the components
16
,
19
. For example sixteen individual detectors
16
can thereby be provided per module, with a total number of, for example,
512
individual detectors being provided by thirty-two such modules
22
. The modules
22
can be electrically connected to one another via cables
23
that are connected to molded plugs
24
.
FIG. 3
, which shows a view in the direction of the arrow III in
FIG. 2
, shows that the formed parts
17
are angled, with the individual detectors
16
mounted at the outside on the upper leg, and the electronic components
19
mounted in the inside of the angle. Some of the electronic components
19
are arranged on an inward projection
25
. The angle is thereby closed by a covering
26
, so that a box-shaped overall profile is produced (in cross-section) for the acceptance of the electronic components
19
. A carrier plate
27
carries the modules
22
which are held thereon by catches
28
. An adjustment (shim) fit pin
29
serves the purpose of aligning the shaped parts
17
to the focus
11
of the x-ray source
1
.
SUMMARY OF THE INVENTION
An object of the present invention is to provide a radiation detector of the type initially described which can be economically manufactured while still achieving reliable electrical connections between the photodiode
3
and the measuring electronics.
This object is inventively achieved in a radiation detector having a scintillator and a photodiode array wherein a transparent film with interconnects is arranged between the scintillator and the photodiode array for the electrical connection of the photodiode array to a measuring electronics. As a result, particularly good electrical connections can be effected in a very tight space.
It is especially advantageous for the transparent film to be placed into connection with the measuring electronics via contact pads, since the photodiode array then can be electrically tested independently of the measuring electronics.
It is also advantageous for the transparent film with the contact pads to be placed into connection with the contacts of the measuring electronics by at least one resilient biasing element, since an easier replacement of the photodiode array as well as replacement of the measuring electronics are thus possible.
When photodiode arrays are arranged in a number of lines, then a number of slices can be scanned given a single transirradiation of an examination subject. Preferably, the scintillator has a ceramic substrate, particularly when the scintillator is a scintillating ceramic, and advantageously this scintillating ceramic carrier has individual tiles that are arranged in at least one row. Cross-talk, i.e. the transfer of light from one tile to another tile, is thus reduced, and as a result the resolution of the radiation detector is increased. In order to suppress the cross-talk, a reflector can be disposed between the tiles.


REFERENCES:
patent: 5917878 (1999-06-01), Peter
patent: 6091795 (2000-07-01), Schafer et al.
patent: 7-333348 (1995-12-01), None

Affiliated with

Also associated with

Rating

Radiation detector, particularly for a computed tomography... does not yet have a rating. At this time, there are no reviews or comments for this patent.

If you have personal experience with Radiation detector, particularly for a computed tomography..., we encourage you to share that experience with our LandOfFree.com community. Your opinion is very important and Radiation detector, particularly for a computed tomography... will most certainly appreciate the feedback.

Rate now

Comments { 0 }

Profile ID: LFUS-PAI-O-2857921