U.S. patent number 3,911,273 [Application Number 05/439,612] was granted by the patent office on 1975-10-07 for x-ray diagnostic apparatus for preparing x-ray exposures including an automatic illuminating device and automatic adjustment of the exposure voltage.
This patent grant is currently assigned to Siemens Aktiengesellschaft. Invention is credited to Kurt Franke.
United States Patent |
3,911,273 |
Franke |
October 7, 1975 |
X-ray diagnostic apparatus for preparing x-ray exposures including
an automatic illuminating device and automatic adjustment of the
exposure voltage
Abstract
An automatically illuminatable X-ray diagnostic apparatus which,
in comparison with the state of the technology is considerably
simplified with respect to its operation by avoiding the need for
adjustment of the X-ray tube voltage. The X-ray tube voltage
therein automatically adjusts itself in conformance with a
preselected contrast. The X-ray tube voltage is automatically
lowered by means of adjusting means for commencing an exposure
within a short period as compared with the shortest exposure time,
from a maximum initial value corresponding to the largest patient
bulkiness, and in which the adjusting means is controllable by a
comparator element having introduced at one input thereof a
differential quotient of a proportional value of the dosage load
measured behind the patient in the direction of the X-rays pursuant
to the X-ray tube voltage at the instantaneous X-ray tube voltage
as the actual value, while at the other input thereof there is
provided a reference value signal corresponding to the desired
contrast and which conveys a signal to the adjusting means for
maintaining the X-ray tube voltage as soon as both input signals
are equal. The reference value signal herein is a percentage figure
of a differential quotient of the dosage load behind the patient,
and corresponding to the desired contrast, pursuant to the X-ray
tube voltage at a relative reference X-ray tube voltage of
proportional value.
Inventors: |
Franke; Kurt (Erlangen,
DT) |
Assignee: |
Siemens Aktiengesellschaft
(Erlangen, DT)
|
Family
ID: |
5879492 |
Appl.
No.: |
05/439,612 |
Filed: |
February 4, 1974 |
Foreign Application Priority Data
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|
|
|
|
Apr 27, 1973 [DT] |
|
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2321448 |
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Current U.S.
Class: |
378/97;
378/108 |
Current CPC
Class: |
H05G
1/32 (20130101); H05G 1/44 (20130101) |
Current International
Class: |
H05G
1/32 (20060101); H05G 1/44 (20060101); H05G
1/00 (20060101); G03B 041/16 () |
Field of
Search: |
;250/320,322,401,402,403,408,409,410,413,414,416 |
References Cited
[Referenced By]
U.S. Patent Documents
Primary Examiner: Willis; Davis L.
Attorney, Agent or Firm: Waters, Schwartz & Nissen
Claims
What is claimed is:
1. In an X-ray diagnostic apparatus having an X-ray tube for the
making of X-ray exposures of a patient; including an automatic
exposure timer means for automatically switching off the X-ray tube
upon an X-ray film being subject to a predetermined dosage of rays;
and means for automatically adjusting the voltage of the X-ray
tube, the improvement comprising; said voltage adjusting means
being adapted to automatically lower the X-ray tube voltage at the
initiation of each exposure during a small time interval in
comparison with the shortest exposure time of said apparatus from a
maximum initial value, equal for all examinations, and based on a
largest patient bulk; and comparison circuit means operatively
connected to said voltage adjusting means and adapted to control
the latter, said comparison circuit having a first input receiving
a signal as an actual value proportionate to a differential
quotient of the X-ray dosage quantity measured behind the patient
in the direction of the X-rays pursuant to the X-ray tube voltage,
and a second input receiving a reference value signal corresponding
to a desired image contrast; and means transmitting a signal from
the output of said comparison circuit means to said voltage
adjusting means for maintaining the X-ray tube voltage constant
upon said first and second input signals being equal.
2. An apparatus as claimed in claim 1, said reference value signal
at the second input of said comparison circuit means being in
correspondence with the desired image contrast, a percentage of a
signal proportional to the differential quotient of the dosage
quantity measured behind the patient in the direction of the X-rays
pursuant to an X-ray tube voltage.
3. An apparatus as claimed in claim 1, comprising differentiating
means for generating a signal conforming to the formation of change
in the dosage quantity measured behind the patient in the direction
of the X-rays; and dose rate meter means connected to said
differentiating means for measuring voltage proportional to the
dosage quantity.
4. An apparatus as claimed in claim 3, said differentiating means
having an output signal adapted to generate one of the input
signals of said comparison circuit means.
5. An apparatus as claimed in claim 1, comprising means for fixedly
programming the function of the reducing rate of the X-ray tube
voltage.
6. An apparatus as claimed in claim 4, said programming means
linearly reducing said X-ray tube voltage as a function of time.
Description
FIELD OF THE INVENTION
The present invention relates to an X-ray diagnostic apparatus for
the preparation of X-ray exposures, including an automatic exposure
timer device for the automatic switching off of the X-ray tube upon
a predetermined ray dosage being received by the X-ray film, and
including automatic adjusting means for the X-ray tube voltage.
DISCUSSION OF THE PRIOR ART
In known X-ray diagnostic apparatus having automatic exposure timer
devices, adjustment must be provided for the X-ray tube voltage.
The switching off of the X-ray tube, in effect, the completion of
an exposure, is obtained the required X-ray dosage predetermined
for optimum film darkening has been imparted to the film. The X-ray
tube voltage must, in that instance, be adjusted in dependence upon
the object being penetrated by the rays, so as to provide an
optimum picture contrast. The adjustment of the X-ray tube voltage
is effected by means of tables, or based on the experience of the
examining person.
Through German Pat. No. 1,227,570 there has become known
automatically illuminated X-ray diagnostic apparatus having
adjusting means for the X-ray tube voltage and the X-ray tube
current, including an overload protective device for indicating and
adjusting the limiting time in dependence upon the preadjusted
X-ray tube load by means of the X-ray load nomograph or computing
chart, as well as through an X-ray dosage load measuring device
located behind the object being X-rayed. In this X-ray diagnostic
apparatus there is provided a control arrangement, which upon an
adjustment of the overload protective device, located on the basis
of the preadjusted value of the existent tube load presently lies
at a predetermined breakage point below the limiting load of the
X-ray tube, then raises the X-ray tube voltage during the first
exposure phase until it attains the limiting load limit of a
permissible magnitude, when the predetermined dosage load
measurement commenced with exposure initiation indicates that the
required X-ray dosage for the desired film darkening cannot be
attained with the preadjusted dosage load within the set time
limit. In this X-ray diagnostic apparatus there is achieved an
automatic correlation between the X-ray tube voltage and the bulk
of the patient. Also attainable is a predetermined degree of
automation of the adjustment of the X-ray tube voltage. However,
the initial value of the X-ray tube voltage must always be selected
in conformance with the body portion or organ which is to be
X-rayed. Additionally, for the exposure of a predetermined body
portion or organ there are only two different X-ray tube voltages
available, so that correlation to the varied constitutions of
patients is only roughly obtained. Consequently, also this X-ray
diagnostic apparatus, not always can there be obtained an optimum
illumination time at the lowest possible ray load on the patient
and at an optimum image contrast.
SUMMARY OF THE INVENTION
It is, accordingly, an object of the present invention to provide
an X-ray diagnostic apparatus of the type described, in effect, an
automatically illuminatable X-ray diagnostic apparatus which, in
comparison with the state of the technology is considerably
simplified with respect to its operation, inasmuch as there is no
longer a need for adjustment of the X-ray tube voltage. The X-ray
tube voltage therein automatically adjusts itself in conformance
with a preselected contrast.
The foregoing task is inventively solved in that the X-ray tube
voltage is automatically lowered by means of adjusting means for
commencing an exposure within a short period as compared with the
shortest exposure time, from a maximum initial value corresponding
to the largest patient bulkiness, and in which the adjusting means
is controllable by a comparator element having introduced at one
input thereof a differential quotient of a proportional value of
the dosage load behind the patient pursuant to the X-ray tube
voltage at the instantaneous X-ray tube voltage as the actual
value, while at the other input thereof there is provided a
reference value signal corresponding to the desired contrast and
which conveys a signal to the adjusting means for maintaining the
X-ray tube voltage as soon as both input signals are equal. The
reference value signal herein is a percentage figure of a
differential quotient of the dosage load behind the patient, and
corresponding to the desired contrast, pursuant to the X-ray tube
voltage at a relative X-ray tube voltage of proportional value. In
the inventive X-ray diagnostic apparatus there is no longer a
requirement for the adjustment of the X-ray tube voltage. It is
merely necessary to select the desired image contrast. This
selection sequence, however, is only to be relatively seldomly
required. Within the scope of the invention, the desired image
contrast may also be fixedly adjusted when a contrast variation is
not considered to be needed. The operation of the inventive X-ray
diagnostic apparatus thus becomes extremely simple, inasmuch as
practically no exposure data need be selected. Consequently, a
fully automatic operation of the apparatus becomes possible.
Within the framework of the invention there may be, on the one side
conveyed to a differentiating element, for the formation of a value
proportional to a differential quotient of the dosage quantity
behind the patient in the direction of teh X-rays according to the
X-ray tube voltage, a voltage of the automatic exposure timer
device which is proportional to the instantaneous dosage, and, on
the other side, a voltage which is proportional to the
instantaneous X-ray tube voltage. The automatic exposure timer
device herein is employed for the generation of switching off
signal for the X-ray tube, as well as for adjustment of the X-ray
tube voltage. Consequently, there is provided thereby an extremely
simple construction.
A particularly simple construction is achieved when the reduction
of the X-ray tube voltage for commencement of the exposure from the
maximum initial value thereof is effected in a time-proportional
manner. In that instance it is not required to actually determine
the X-ray tube voltage. It is much more adequate that the
differentiating element timewise differentiates a voltage from the
automatic exposure timer device proportional to the instantaneous
dosage.
A further embodiment of the invention consists of in that the X-ray
tube voltage, through there is imparted the required differential
quotient for the formation of the reference value, is also switched
over in dependence upon the selected contrast, and wherein the
maximum initial value of the X-ray tube voltage for initiating the
exposure lies only a small amount above the present X-ray tube
voltage effective for the differential quotient.
BRIEF DESCRIPTION OF THE DRAWINGS
Further advantages of the present invention may be now ascertained
from the following detailed description of an exemplary embodiment
thereof, taken in conjunction with the accompanying drawings, in
which:
FIG. 1 is a graphical representation of the relationship of the
dosage load at various X-ray tube voltages with respect to the
dosage load at a predetermined maximum X-ray tube voltage for
various patient bulks;
FIG. 2 illustrates differential quotients of the dosage load behind
the patient (DL) according to the X-ray tube voltage in dependence
upon the X-ray tube voltage, as obtained from the curves in FIG. 1,
regulated for these differential quotients at a maximum X-ray
voltage (U.sub.RMax) for various patient bulks;
FIG. 3 illustrates a circuit diagram for an X-ray diagnostic
apparatus according to the present invention;
FIG. 4 graphically illustrates a sequence for the X-ray tube
voltage in the X-ray diagnostic apparatus of FIG. 3; and
FIG. 5 shows circuit details of the circuit diagram of FIG. 3.
DETAILED DESCRIPTION
Referring now to the drawing, in FIG. 1 the X-ray tube voltage is
designated by U.sub.R. The curve 1 relates to a thin patient,
whereas curve 4 relates to a bulky patient. The curves 2 and 3
correspondingly relate to intermediate values of patient bulks.
The image contrast K of an X-ray exposure remains, not-withstanding
variations in the bulk D of a patient, approximately constant when
the X-ray tube voltage U.sub.R is adjusted in a manner in which the
quotient Q remains constant from the differential quotient of the
dosage quantity behind the patient pursuant to the X-ray tube
voltage at the location U.sub.1 (exposure voltage) and the
differential quotient of the dosage quantity behind the patient
pursuant the X-ray tube voltage at the location of a suitable X-ray
tube voltage U.sub.RMax which is larger than U.sub.1.
In short form:
K .noteq. f(d), in the event U.sub.R = U.sub.1, wherein U.sub.1 is
such, that ##EQU1##
The sequence or graph of the quotient Q in dependence upon the
X-ray tube voltage U.sub.R is illustrated in FIG. 2. The curves 5
through 8 herein correspond to curves 1 through 4 in FIG. 1. In
FIG. 2 there is shown a line 9 which defines a particular
preselected contrast. From FIG. 2 it may be ascertained that in
order to obtain a contrast according to line 9 for patients
represented by curves 1 and 5, there is required an X-ray tube
voltage of approximately 70 kv, while for patients represented by
curves 4 and 8, there is required an X-ray tube voltage of
approximately 95 kv. From FIG. 2 it is ascertainable that
completely determinate X-ray tube voltage U.sub.1 =f(d) belongs to
each patient constitution, and which there is obtained a
predetermined contrast.
The invention recognizes that the image contrast, as well as the
given quotient of the differential quotients, are dependent upon
the patient bulk and the exposure voltage, and that this dependence
of the image contrast and the given quotient from the patient bulk
may be compensated for in that the exposure voltage follows the
patient's bulk in a determined function U.sub.1 = f(d), and wherein
this function U.sub.1 = f (d) is the same for the image contrast
and the quotient Q, so that it is only necessary to maintain the
X-ray tube voltage at that value which provides a preselected
quotient, in order to thereby concurrently also achieve the
associated image contrast.
An X-ray diagnostic apparatus which operates in accordance with
this principle is illustrated in FIG. 3 of the drawings. The X-ray
diagnostic apparatus according to FIG. 3 includes a rotary or
three-phase high voltage transformer 10 having a split secondary
side. Two high voltage rectifiers 11 and 12 supply an X-ray tube 13
through two conduits 14 and 15 which are positioned in the high
voltage circuit. The conduits 14 and 15 have control arrangements
or amplifers 16 and 17 associated therewith, by means of which the
anode-cathode resistance of the conduits 14 and 15, and thereby the
voltage reduction of the conduits 14 and 15, becomes adjustable.
Through the intermediary of control arrangements or amplifiers 16
and 17, the X-ray voltage tube thus may be adjusted.
The control of the control arrangements or amplifiers 16 and 17 is
effected through a function generator 18 which has an input 19, and
which maintains to final value through which it controls the
control arrangements or amplifiers 16 and 17 as soon as a signal is
generated at its input, in effect, in the conduit 19.
The conduit 19 is, at the other side thereof, connected to a
comparison circuit 20 which receives at a portion comprising a
resistance 21, as a reference value the output voltage of a sample
and hold circuit 22, and as an actual value the timewise
differentiated output voltage of a dose rate meter 25, through a
condensor 23 and resistance 24. The dose rate meter 25 is connected
with a suitable ray detector 26 which is located behind the patient
27 in the direction of the X-rays and, in FIG. 3, in front of (in
practice also possibly in back of) the X-ray film 28.
The output voltage of the dose rate meter 25, which has been
timewise differentiated by means of condensor 23 and resistance 24,
is also conveyed to the circuit 22. The differentiated output
voltage of the dose rate meter 25 which, at a particular moment
after commencement of the exposure, is present at the resistance
24, is sensed by the sample and hold 22, supplied and then
maintained at the resistance 21 for as long until a signal appears
in the conduit 19.
The output signal of the dose rate meter 25 is, in addition to the
differential components 23, 24, conveyed toward an integrator 29,
and the integrator result to a cut-off amplifier 30 which has a
reference value input 31, and which compares the integrator result
with the reference value signal at the input 31. When both of these
signals coincide, in effect, meaning when the desired optimum film
darkening has been attained, the cut-off amplifier 30 delivers at
its output 32 a cut-off signal to the function generator 18. The
switching off is effected through the closure or disconnecting of
conduits 14 and 16, but may also be effected through a switching
element located in the primary circuit of the high voltage
transformer 10 for the switching off of the X-ray tube 13.
At the output of the dose rate meter 25 there is formed a voltage
which is proportional to the measured dosage quantity in back of
the patient 27 in the direction of the X-rays. The resistance 24 is
small in comparison with the fraction T.sub.O/C in which
T.sub.O> T.sub.M (see FIG. 4) for that time, within which the
X-ray tube voltage, for commencing the exposure at a suitably high
value, reaches its correct value U.sub.1, and in which C is the
capacity of condensor 23. The voltage at the resistant 24 is
defined by the following equation: ##EQU2## wherein U.sub.K is the
voltage at the resistance 24, i is the current flowing through this
resistance, and R the resistive value of this resistance. C is the
capacity of the condensor 23, U.sub.DL is the output voltage
proportionate to the dosage quantity DL of the dose rate meter 25,
t the time, and c' is a constant.
In the exemplary embodiment according to FIG. 3 it is basic that
the X-ray tube voltage drops linearly with time. For the foregoing,
the following equation defines the X-ray tube voltage: ##EQU3## in
which K* is a constant. In order to obtain a linear dropping off of
the X-ray tube voltage, the function generator 18 is programmed in
a manner so that this linear reduction is effected for as long as
the voltage at the resistance 24 is larger than the voltage at the
tap-off for resistance 21, in effect meaning, as long as no signal
is transmitted from the comparison circuit 20 to the conduit
19.
If dt with respect to the relationship for the X-ray tube voltage
U.sub.R is introduced in the relationship for the voltage U.sub.K
at the resistance 24, then the following equation is obtained for
the voltage U.sub.K : ##EQU4##
In this equation the differential quotient of the dosage quantity
is obtained pursuant to the X-ray tube voltage. Based on the prior
assumption that the X-ray tube voltage drops off linearly with
time, then the voltage U.sub.K in the embodiment of FIG. 3 may be
utilized for obtaining the quotient Q, as follows: ##EQU5##
The operation of the X-ray diagnostic apparatus of FIG. 3 is as
follows, having reference to FIG. 4:
The X-ray tube voltage U.sub.R, after commencement of the X-ray
exposure, jumps to a suitable maximum value U.sub.RMax. This is
retained until time point T.sub.M, and then drops linearly.
At the resistance 24 there appears a voltage impulse in conformance
with the sudden occurrence of the dosage. After the voltage impulse
has reduced prusuant to T.sub.M, and the voltage U.sub.K is now
proportional to the differential quotient d (DL)/d U.sub.R, then
U.sub.K = (U.sub.K) at U.sub.RMAX is sensed and supplied or
energized.
(U.sub.K) at U.sub.RMax then appears at the output of circuit or
unit 22. Through the intermediary of resistance 21, a predetermined
portion (percentage) corresponding to the desired image contrast is
transmitted to the comparison circuit 20, as represented by:
Q .sup.. (U.sub.K) at U.sub.RMax mit Q < 1
At t.sub.o, or respectively, at U.sub.R = U.sub.1, the following
pertains:
Q .sup.. (U.sub.K) at U.sub.RMax = (U.sub.K) at U.sub.1 ;
##EQU6##
For U.sub. 1 there results for various patient bulks, from exposure
to exposure, always a different value, and namely the X-ray tube
voltage which independently of the patient's bulk always constantly
provides the same contrast. At the time point T.sub.O there is
accordingly maintained the X-ray tube voltage at the value U.sub.1
, and the X-ray exposure is prepared at the voltage U.sub.1 up to
the time point T.sub.1, at which the cut-off amplifier 30
terminates the exposure. After the time point T.sub.1, the X-ray
tube voltage drops exponentially toward zero. The slope or degree
of drop-off of the X-ray tube voltage for initiating the exposure
is so selected, that the dosage which is produced in the time
T.sub.O is also at the lowest occurring X-ray tube voltage small in
comparison with the dosage between the time T.sub.O and the minimum
employed exposure time T.sub.1, so that during the largest portion
exposure time there provided at the X-ray tube an X-ray tube
voltage corresponding to the optimum contrast.
In summation, it may be readily ascertained that in the X-ray
diagnostic apparatus according to FIG. 3 there is no requirement
for an adjustment of the X-ray tube voltage. Since the X-ray tube
current may also be rigidly programmed pursuant to the loading
nomograph of the X-ray tube, the operation and manipulation of this
X-ray diagnostic apparatus is considerably simplified, inasmuch as
practically no exposure data need be adjusted. The desired contrast
may singly be adjusted for a plurality of exposures at the
resistance 21, and the correlation with the employed X-ray film
similarly fillows for a plurality of exposures at a single instance
through generation of a corresponding signal at the input 31 of the
cut-off amplifier 30. The X-ray diagnostic apparatus according to
FIG. 3 consequently is completely automatedly exposed, and in which
the adjusting sequence for the X-ray tube voltage is incorporated
in the automation thereof.
The embodiment according to FIG. 3 is particularly simple since the
X-ray tube voltage drops off linearly with time, and consequently
no particular evaluation of the X-ray tube voltage changes need be
effected through corresponding measuring elements. Within the
framework or scope of the invention, the reduction or dropping off
of the X-ray tube voltage may also follow in conformance with
another function. If this function is fixedly programmed in the
function generator 18, then also in this instance no measurement of
the particular actual value of the X-ray tube voltage change is
required, but merely the differentiation cannot be effected by
means of the RC-element 23, 24, and a more suitable differentiator
must be introduced. Within the scope of the invention it is also
possible, to ascertain the dosage quantity change, as well as the
X-ray tube voltage change be ascertained through corresponding
measuring elements, and to form the differential quotient ##EQU7##
by means of a differentiating element. It is always important for
the invention that a signal be transmitted to the comparison
circuit 20 which is proportional to the differential quotient of
the dosage quantity pursuant to the X-ray tube voltage, and in
which the signal is compared with a signal proportional to the
reference value of the contrast corresponding percentage value Q of
a differential quotient of the dosage quantity pursuant to the
X-ray tube voltage at a reference X-ray tube voltage, and upon the
balancing of the signals the X-ray tube voltage is maintained.
The construction of the function generator 18 is described in
greater particularity in FIG. 5 of the drawings. From FIG. 5 it is
ascertained that the function generator 18 includes a condensor 33
which is dischargeable through a discharge resistance 34, as well
as through a relay contact 35. The relay contact 35 is actuatable
by means of a relay 36 which is controlled by the cut-off amplifier
30. The switching-in of the discharge resistance 34 at the
condensor 33 is effected through a circuit switch 37 and a relay
contact 38, whose relay 39 is controlled by the signal in the
conduit 19.
Prior to commencing an exposure, the exposure switch 37 is opened
and the condensor 33 is charged. In order to initate an exposure,
the switch 37 is closed. The condensor 33 discharges approximately
linearly through resistance 34 up to the time point T.sub.O. Since
the X-ray tube voltage corresponds to the condensor voltage, the
X-ray tube voltage also drops linearly up to time point T.sub.O
pursuant to FIG. 4. The control voltage for the conduits or triodes
14 and 15 namely corresponds with the voltage in the conduit 40,
which is amplified through the control amplifiers 16 and 17.
At the time point T.sub.O, the voltage U.sub.1 is attained in the
X-ray tube, and the comparison circuit 20 transmits a signal to
conduit 19, which causes the relay 39 to open its contact 38 and
interrupt the discharge of condensor 33. The condensor voltage
thereby remains constant up to time point T.sub.1, whereby the
X-ray tube voltage also maintains the value U.sub.1 up to time
point T.sub.1. At time point T.sub.1 there is effected the
termination of the exposure by means of the output signal of the
cut-off amplifier 30, which causes the excitation of relay 36.
Relay 36 closes its contact 35 and completely discharges condensor
33. The condensor voltage, and therewith the X-ray tube voltage,
extend herewith from time point T.sub.1 on, pursuant to the graph
in FIG. 4, until reaching zero value. Prior to initiating a new
exposure, the relay 36 is again de-energized so that the contact 35
is opened. Furthermore, the exposure switch 37 is again opened
prior to initiating an exposure, and for the making of a new
exposure, closed again. The above-described sequences are then
repeated.
While there has been shown what is considered to be the preferred
embodiment of the invention, it will be obvious that modifications
may be made which come within the scope of the disclosure of the
specification.
* * * * *