CA1093713A - Radiographic normalizing system - Google Patents
Radiographic normalizing systemInfo
- Publication number
- CA1093713A CA1093713A CA291,891A CA291891A CA1093713A CA 1093713 A CA1093713 A CA 1093713A CA 291891 A CA291891 A CA 291891A CA 1093713 A CA1093713 A CA 1093713A
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- CA
- Canada
- Prior art keywords
- signals
- activity
- camera
- address
- event
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Expired
Links
- 230000000694 effects Effects 0.000 claims abstract description 18
- 230000002285 radioactive effect Effects 0.000 claims abstract description 12
- 230000008878 coupling Effects 0.000 claims description 3
- 238000010168 coupling process Methods 0.000 claims description 3
- 238000005859 coupling reaction Methods 0.000 claims description 3
- 230000004044 response Effects 0.000 claims description 3
- 238000005259 measurement Methods 0.000 claims description 2
- 230000011664 signaling Effects 0.000 claims description 2
- 230000015654 memory Effects 0.000 description 36
- 230000000875 corresponding effect Effects 0.000 description 10
- 240000007320 Pinus strobus Species 0.000 description 3
- 150000002500 ions Chemical class 0.000 description 2
- 238000009740 moulding (composite fabrication) Methods 0.000 description 2
- 206010028980 Neoplasm Diseases 0.000 description 1
- 241000505673 Scintilla Species 0.000 description 1
- 230000003750 conditioning effect Effects 0.000 description 1
- 230000006870 function Effects 0.000 description 1
- 238000005286 illumination Methods 0.000 description 1
- 230000010354 integration Effects 0.000 description 1
- 230000000873 masking effect Effects 0.000 description 1
- 239000000463 material Substances 0.000 description 1
- 238000012986 modification Methods 0.000 description 1
- 230000004048 modification Effects 0.000 description 1
- 239000012857 radioactive material Substances 0.000 description 1
- 229920003987 resole Polymers 0.000 description 1
- 238000007493 shaping process Methods 0.000 description 1
- 230000007781 signaling event Effects 0.000 description 1
- 125000006850 spacer group Chemical group 0.000 description 1
Classifications
-
- G—PHYSICS
- G01—MEASURING; TESTING
- G01T—MEASUREMENT OF NUCLEAR OR X-RADIATION
- G01T1/00—Measuring X-radiation, gamma radiation, corpuscular radiation, or cosmic radiation
- G01T1/16—Measuring radiation intensity
- G01T1/161—Applications in the field of nuclear medicine, e.g. in vivo counting
- G01T1/164—Scintigraphy
- G01T1/1641—Static instruments for imaging the distribution of radioactivity in one or two dimensions using one or several scintillating elements; Radio-isotope cameras
- G01T1/1642—Static instruments for imaging the distribution of radioactivity in one or two dimensions using one or several scintillating elements; Radio-isotope cameras using a scintillation crystal and position sensing photodetector arrays, e.g. ANGER cameras
Abstract
Abstract of the Disclosure A system for portraying data obtained by a radiographic camera, such as an Anger camera, which signals the occurrences of radioactive events and the addresses of locations of the events. Data is obtained from a reference subject and a liv-ing subject. The activity of events of the reference subject is stored as a function of event location and is utilized as scale factors for scaling the relative energies of event sig-nals obtained from the living subject, whereby data of the living subject is normalized relative to the reference subject.
Description
~0~7~
~ackground of ~he Invention A radiographic camera such as the Anger camera dis-closed in the United States Patent No. 3,011~057 which issued in the name of H. O. Anger on November 28, 1961 and in the United States Patent No. 3,914,611 which issued in the name of K. J. Stout on October 21, 1975, is often uti-lized for obtaining a radiographic image of a radioactive subject. Such a camera includes a scintillator viewed by a set of scintillation detectors or photomultiplier tubes pro-viding signals which are combined, typically, by a resistormatrix to provide a Z-axis signal which signals the presence of a radioactive even~ in the sub~ect. Resistor matrices also combine the detector signals to provide coordinate axes signals, Cartesian coordinates having X and Y signals being readily implemented, to serve as an address for locating the radio-active event.
A problem arises in that the many photomul~iplier tubes utilized in present day cameras are subject to individual drift-ing which varles the locations and, hence, the density of the apparent locations of the radioactive events as provided by the coordinate axes signals. Regions of increased event den-sity in the image of the subject appear to a clinician viewing the image as regions of greater intenslty. As a result, a clinican viewing the image produced by the camera perceives regions of varying intensity which may be incorrectly diagnosed as a tumor or malady.
~3~3 Summary of the Invention The foregoing problem is overcome and other advantages are provided by a radiographic system which, in accordance with the invention, compensates for variation in the locations of the camera signals slgnaling radioactive events so that a clinician views a correct image of the subject. Two subjects are utiliæed9 the first, being in the form of a uniform sheet of radioactive material 9 will be referred to hereinafter as the reference subject while the second, a living organism such as a human being, will ~e referred to hereinafter as the clinical subject. The activity of radioactive events of the reference subject is stored as a function of event location and is utilized for providing scale factors for scaling the relative energies of Z-axis signals signaling events obtained from the clinical subject whereby data of the clinical subjec~ is normalized relative to the reference subject. For convenience in explaining the invention, the afore-mentioned Z-axis signal of ~nger camera will sometimes by referred to hereinafter as a Z signal or as an event signal, while the X
and Y coordinate signals will be sometimes re~erred to hereinaf~er as the address signals. The scaling of the energies of the ~ sig-nals compensates for the variations in the density of image points on a display of the ima~e so that the clinician perceives regions o~ the image with their correct intensities.
In a preferred embodiment of the in~ention, an adder and a memory are utilized for producing summations of event signals ob-tained from the reference subject, summations of the event signals obtained from a specific location of the reference subject being stored in the memory with ~he adder being u~ilized for adding further event signals to the stored summation. The locations in 3~ the memor~ are addressed by the address signals of the camera.
~ackground of ~he Invention A radiographic camera such as the Anger camera dis-closed in the United States Patent No. 3,011~057 which issued in the name of H. O. Anger on November 28, 1961 and in the United States Patent No. 3,914,611 which issued in the name of K. J. Stout on October 21, 1975, is often uti-lized for obtaining a radiographic image of a radioactive subject. Such a camera includes a scintillator viewed by a set of scintillation detectors or photomultiplier tubes pro-viding signals which are combined, typically, by a resistormatrix to provide a Z-axis signal which signals the presence of a radioactive even~ in the sub~ect. Resistor matrices also combine the detector signals to provide coordinate axes signals, Cartesian coordinates having X and Y signals being readily implemented, to serve as an address for locating the radio-active event.
A problem arises in that the many photomul~iplier tubes utilized in present day cameras are subject to individual drift-ing which varles the locations and, hence, the density of the apparent locations of the radioactive events as provided by the coordinate axes signals. Regions of increased event den-sity in the image of the subject appear to a clinician viewing the image as regions of greater intenslty. As a result, a clinican viewing the image produced by the camera perceives regions of varying intensity which may be incorrectly diagnosed as a tumor or malady.
~3~3 Summary of the Invention The foregoing problem is overcome and other advantages are provided by a radiographic system which, in accordance with the invention, compensates for variation in the locations of the camera signals slgnaling radioactive events so that a clinician views a correct image of the subject. Two subjects are utiliæed9 the first, being in the form of a uniform sheet of radioactive material 9 will be referred to hereinafter as the reference subject while the second, a living organism such as a human being, will ~e referred to hereinafter as the clinical subject. The activity of radioactive events of the reference subject is stored as a function of event location and is utilized for providing scale factors for scaling the relative energies of Z-axis signals signaling events obtained from the clinical subject whereby data of the clinical subjec~ is normalized relative to the reference subject. For convenience in explaining the invention, the afore-mentioned Z-axis signal of ~nger camera will sometimes by referred to hereinafter as a Z signal or as an event signal, while the X
and Y coordinate signals will be sometimes re~erred to hereinaf~er as the address signals. The scaling of the energies of the ~ sig-nals compensates for the variations in the density of image points on a display of the ima~e so that the clinician perceives regions o~ the image with their correct intensities.
In a preferred embodiment of the in~ention, an adder and a memory are utilized for producing summations of event signals ob-tained from the reference subject, summations of the event signals obtained from a specific location of the reference subject being stored in the memory with ~he adder being u~ilized for adding further event signals to the stored summation. The locations in 3~ the memor~ are addressed by the address signals of the camera.
-2-~373L3 The scale factors are obtained by counting a predetermined number of event signals to obtain an average value for the summa~ions in each of the cells of the memory, this average then being divided by the value of t]le sum in each cell of the memory to obtain the scale factors corresponding to each location of the subject which is imaged by the camera. The obtaining of the scale factors com-pletes the calibration portion of the operation of the radiographic system. Thereupon, the clinical subject is imaged with the X, Y
and Z signals of the camera being utilized for presenting an image of the subject on a display, the X and Y signals serving to locate points on the display while the Z signal is scaled as described be^
low and then utilized for modulating the intensity of the display in a manner analogous to that taught by the aforementioned patents of Anger and to Stout.
In accordance with the invention, the Z-axis signal is scaled prior to its being utilized for modulating the Z-axis of the display.
The scaling is accomplished in real time, namely, at the same rates as the rate of occurences of the Z signals so that no delay in form-ing the image results from the scaling. The scaling may utilize a multiplying circuit which modulates the relative energy content of each pulse of the event signal, either by varying the amplitude of the signal or by varying the duration of each pulse whereby the product of signal amplitude times signal duration is altered.
Alternatively, the scaling may involve a mathematical operation such as the raising o the Z signal to a power such as Z0 9 or zl.
in which the power is proportional to the scale factor. In the preferred embodiment disclosed hereinafter~ the Z signal is multi-plied directly by the scale factor. In particular, it is noted that in a display utilizing a cathode ray tube plus a photographic film plate for viewing the cathode-ray tube7 the intensity of an
and Z signals of the camera being utilized for presenting an image of the subject on a display, the X and Y signals serving to locate points on the display while the Z signal is scaled as described be^
low and then utilized for modulating the intensity of the display in a manner analogous to that taught by the aforementioned patents of Anger and to Stout.
In accordance with the invention, the Z-axis signal is scaled prior to its being utilized for modulating the Z-axis of the display.
The scaling is accomplished in real time, namely, at the same rates as the rate of occurences of the Z signals so that no delay in form-ing the image results from the scaling. The scaling may utilize a multiplying circuit which modulates the relative energy content of each pulse of the event signal, either by varying the amplitude of the signal or by varying the duration of each pulse whereby the product of signal amplitude times signal duration is altered.
Alternatively, the scaling may involve a mathematical operation such as the raising o the Z signal to a power such as Z0 9 or zl.
in which the power is proportional to the scale factor. In the preferred embodiment disclosed hereinafter~ the Z signal is multi-plied directly by the scale factor. In particular, it is noted that in a display utilizing a cathode ray tube plus a photographic film plate for viewing the cathode-ray tube7 the intensity of an
3'~3 image point on the film plate depends on the product o~ the magnitude of a light pulse on the face of the cathode-ray tube by the duration of said pulse.
The product of amplitude times width is proportional to the energy of an event pulse. By utilizing the aforementioned scale factors for modulating the relative energy content of the event pulses, the image of the clinical subject is normalized with respect to the reference subject with the result that ~he perceived intensities of the regions of the image become invariant with respect to drif~ing of the photomultiplier tubes.
In accordance with the invention there is provided a system for coupling a display to a radiographic camera produc;ng address signals sig-naling the locations of radioactive events, said system comprising: means coupled to said camera and responsive to said address signals for measuring the activity of event signals of said cameras wherein each of said event sig-nals represents the occurrence of a radioactive event in a subject being imaged by said camera~ said measuring means providing activity signals in-cluding addresses of respective ones of said events which signal measures of said ac~ivity; and means coupled between said camera and said mea~uring means for mathematically operating on the relative energies of respective ones of e~ent signals by corresponding ones of said activity signals, ea~h of said event signals having a co~mon address with each of said corresponding ones of said activity signals, whereby data of said subject is normalized relative to said measurement o~ said activity.
,~ ~ 4 _ ~ 3~ ~ ~
Brief Descripti~n of the Drawing The aforementioned aspects and o~her features of the in-vention are explained in the following description taken in con-nection with the accompanying drawing which shows an exploded view of a radiographic camera and its coupling to the display by electrical circuitry of the invention, the electrical circuitry being shown in block diagrammatic form.
~3rS~ ~
Description of the Preferred Embodiment -Referring now to the figure, there is seen a system 20 for obtaining radiographic images of a reference subject 22 and a clinical subject 24 by means of a radiographic camera 26 and a display 28. The camera 26 includes a collimator 30, a sointil-lator 32, an optically transparent spacer plate 34~ a set of scintillation detectors each of which incorporates a photomulti-plier 36 and a signal conditioning circuit 38, and a signal com-biner 40 which are supported by a case 42. Each signal condition-10 ing circuit 38 includes integration and pulse shaping while thecombiner 40 includes resistor matrices for forming ~he X, Y and Z axis signals in the manner such as that taught in the afore-mentioned Stout patent.
In accordance with the invention, the system 20 comprises analog-to-digital converters 44 and 46~ a timer 48, an adder 50, memories 52 and 54, a digital-to-analog converter 56, a multiplier 58, a timer 60~ an address generator 62, a counter 64, a calculator 66, a source 68, and swi~ches 70 and 72. The adder 50 and the memory 52 are utilized for providing the sums of the event signals 20 for Z axis signals identified by the letter Z in the figure, the sums being stored in the memory 52 in accordance with addresses provided by the X and Y signals from the camera 26. The counter 64 counts the total number of events~ the total number being identi-:Eied by the letter T in the figure. The average number of events per cell of the memory 52 is I7rovided by the ratio T/N where N is the number of cells in the memory 52, the number N aiso being the number of resolution elements of the image produced by the camera 26 and presented on the display 28. The scale factor is identified by the letter K in the figure, a separate value of K being produced 30 for each resolution element of the image by the calculator 66, the ~ 3 values of K being stored in the memory 54. Since the ratio T/N
is constant, the value of K is seen by the formula shown in the fi.gure for the calculator 66 to be inversely proportional to the value of B where B represents the magnitudes of the sums stored in the cells of the memory 52~ there being one ~alue of K for each value o~ B. The mutliplier 58 multiplies the relative energies of the Z axis signals~ shown in the bottom line of the graph 74 by the factor K to produce either a variation in magnitude of the Z
axis signal, as shown in the second line of the graph 74, or a ln variation in the duration of the Z axis signal as is shown in the irst line of the graph 74. The product of the multiplicatlon, identified in the figure by the symbol KZ, is applied to the dis-play 28.
The storing of the sums of the event signals in the memory 52 during the calibration of the system 20 is accomplished as follows.
First~ the reference subject 22 is placed in front of the camera 26. The reference subject 22 is typically in the form of a flat sheet uniformly inpregnated with a r~adioactive material for uni-formly illuminating the fron~ face o-f the collimator 30. The switch 72 is manually set in the calibrate position as shown in the figure.
I`he counter 64 is manually reset to zero by the reset button 76.
In the reset condition of the counter 64, the counter 64 provides a logic s~ate of zero on ].ine 78 under which condition the switch 70 has the position as shown in the figure.
In response to the illumination provided by the reference subject 22 9 scintilla~ions appear on the scintillator 32, the scintillations being converted by the pho~omultipliers 36.and the signal combiners 40 to pulse signals which are coupled via the li.nes 8Q to the signal combiner 40 which combines the signals on the lines 80 to produce the X, Y and Z sigllals which are seen to fan into the line 82. The X and Y signals of line 82 are coupled to the conver~ers 44 and 46 which convert the X and Y signals from an analog format to a digita:L format, the digital formated signals being seen to fan into line 84. The Z, or event, is coupled via the line 82 to the timer 48, the adder 50 and the counter 64. In re-sponse to each strobing of the timer 48 by the Z signal, the timer 48 provides clock signals on line 86 for operating the converters 44 and 46, the timer 48 also providing clock pulses, identified by the legend Cl, which are seen to fan into the line 84 for operat-ing the memory 52 to store digital numbers at locations corre-sponding to the address of the X and -the Y signals.
In response to the clock signals Cl, the contents of a cell of the memory 52 is incremented upon the occurences of successive events at the address of the cell. The contents of the cell is coupled along line 88 from the output terminal of the memory 52 via the switch 70 to an input terminal of the adder 50 to be summed with the Z signal. The resulting sum ~rom the adder 50 is coupled via the line 84 and the switch 70 back to the same cell of the memory 52~ this cell being addressed by the X and the Y signals of the converter 44 and 46. With each appearance of a Z signal in combination with a specific address of the X and the Y signals, the memory 52 makes available to the adder 50 the previously stored sum at that address, the adder 50 then incrementing that sum by a count of 1 corresponding to ~he one even~ signaled by the Z axis signal. In this way, each cell of the memory 52 stores a count of the number of radioactive events from the reference subject 22 which have appeared at the image location corresponding to the address of that cell of the memory 52.
l~hen the counter 64 attains a count of T events, this being a predetermined number to which the counter 64 is preset 9 the 7~
counter 64 provides a logic level of 1 on line 78 which serves as a strobe signal for operating the switch 70 to its alternate po-sition whereupon the line 84 is disconnected from the memory 52.
There~pon, no new data enters the memory 52. The si~nal on :line 78 also strobes the timer 60 to operate the memor~ 52 in a read-only mode via clock pulses C2. In addition, the timer 60 strobes the address generator 62 which sequentially addresses each cell o~
the memory 52 by means of X and Y signals generated by the gener-ator 62. Signals are coupled from the output terminal of the memory via line 88 and the swi~ch 70 ~o the B input terminal of the calculator 66. The timer 60 also provides timin~ signals C3 for operating the calculator 66 to perform the calculation in accordance with the formula shown on the figure in the block identi-fying the calculator 66. Thus, for each sum B coupled from a cell of the memory 52 to the calculator 66, the calculator 66 provides electrical signals in a digital format representing a value of the scale factor K, these electrical signals being cou~led via the switch 72 to the memory 54 and representing a measure of the activity of radioac~ive events at a specific location of the reference sub-ject. The clock pulses C2 and ~he address signals of the generator62, which are .seen to fan into the line 90 and be coupled via the switch 70 to the memory 52, are also cou~led via the switch 72 to the memory 54 for strobin~ and addressin~ the memory 54 in accordance with the strobing and addressing of the memory 52. Thereby, the memory 54 stores a set of scale factors K at locations corresponding to the resolution elements of the image corresponding to the X and Y coordinate locations of the resol.ution elements.
During ~he second phase of the operation of the system 20, the switch 72 is manually positioned in the run position and the reference subject 22 is replaced with the clinical subject 24. Thereupon, the camera 26 and the display 28 are operated to produce an image on the display 28 in the manner commollly employed in hospitals, as disclosed in the aforementioned Stout patent except that, in ac-cordance with the invention~ each Z axis signal which signals a radivactive event is moclified by the multiplier 58 before being applied to the Z axis terminal of the display 28.
With respect to the multiplication by the multiplier 58~ it is noted that since the scale factors are stored in a digital format in the memory 54, the digitally formated scale factors are first con-verted to scale factors in an analog format by the converter 56 andthen apPlied to the multiplier 58. The mul~i.plier 58 may be an analog multiplier wherein the amplitude of the voltage provided by the con-verter 56 modulates the amplitude of the Z axis signals to provide the aorementioned scalin~ of the amplitude portrayed in the second line of the graph 74. Or, alterna~.ively~ the multiplier 58 may in-corporate a pulse-width modulator circuit wherein ~he amplitude of the voltage provided by the converter 56 is util.ized for varying the duration of the Z axis signal on line 92 to provide the aforemen~ioned pulse-width modula~ed si~nal on the first line of the graph 74.
Thereby, the products of the amplitudes of individual ones of the Z axis signals times the duration of the corresponding Z axis signals, this being equivalent to the relative energies in the pulses of the Z axis signals, are modula~ed to compensate for variations in the addresses of Z axis signals as may result in drifti.ng of ~he gain characteristic of individual ones of the p~otomultipliers 36. In addition, it is noted that if the reference subject 22 be provided with a design~ as by masking a portion of the reference subject 22 with a cross or a circle, the outline of the masked portion appears superposed upon an image seen on the display 28. If desired, a digital multiplier (not shown) may be utilized inlieu o~ tne , multiplier 58 in which case the converter 56 would be deleted and a pulse-width modula~or (not shown~ would be coupled between the digital multiplier and the display 28.
With reference to the calculations performecl by the calcu-lator 66, it has been found that, in an experimen~al model of the system 20 wherein the value of the total count T was held constant (7 million counts being utilized) as well as the nurnber of reso-lution elements N being held constant, the variations in the magni-tude of the sums B were sufficiently few in number such that the calculator 66 could be replaced by a read-only memory in which the memory address was supplied by the ma~ni~ude of the quan~ity B and in which the output of the memory was the desired scale factor K.
Thereby, for each value of B presented to the read-only memory, a corresponding value of K was read out of the memory~
It is understood that the above-described embodiment of the invention is illustrative only and that modifications thereof may occur to those skilled in the art. Accordingly, it is desired that this invention is not to be limited to the embodiment disclosed herein but is to be limited only as defined by the appended claims.
The product of amplitude times width is proportional to the energy of an event pulse. By utilizing the aforementioned scale factors for modulating the relative energy content of the event pulses, the image of the clinical subject is normalized with respect to the reference subject with the result that ~he perceived intensities of the regions of the image become invariant with respect to drif~ing of the photomultiplier tubes.
In accordance with the invention there is provided a system for coupling a display to a radiographic camera produc;ng address signals sig-naling the locations of radioactive events, said system comprising: means coupled to said camera and responsive to said address signals for measuring the activity of event signals of said cameras wherein each of said event sig-nals represents the occurrence of a radioactive event in a subject being imaged by said camera~ said measuring means providing activity signals in-cluding addresses of respective ones of said events which signal measures of said ac~ivity; and means coupled between said camera and said mea~uring means for mathematically operating on the relative energies of respective ones of e~ent signals by corresponding ones of said activity signals, ea~h of said event signals having a co~mon address with each of said corresponding ones of said activity signals, whereby data of said subject is normalized relative to said measurement o~ said activity.
,~ ~ 4 _ ~ 3~ ~ ~
Brief Descripti~n of the Drawing The aforementioned aspects and o~her features of the in-vention are explained in the following description taken in con-nection with the accompanying drawing which shows an exploded view of a radiographic camera and its coupling to the display by electrical circuitry of the invention, the electrical circuitry being shown in block diagrammatic form.
~3rS~ ~
Description of the Preferred Embodiment -Referring now to the figure, there is seen a system 20 for obtaining radiographic images of a reference subject 22 and a clinical subject 24 by means of a radiographic camera 26 and a display 28. The camera 26 includes a collimator 30, a sointil-lator 32, an optically transparent spacer plate 34~ a set of scintillation detectors each of which incorporates a photomulti-plier 36 and a signal conditioning circuit 38, and a signal com-biner 40 which are supported by a case 42. Each signal condition-10 ing circuit 38 includes integration and pulse shaping while thecombiner 40 includes resistor matrices for forming ~he X, Y and Z axis signals in the manner such as that taught in the afore-mentioned Stout patent.
In accordance with the invention, the system 20 comprises analog-to-digital converters 44 and 46~ a timer 48, an adder 50, memories 52 and 54, a digital-to-analog converter 56, a multiplier 58, a timer 60~ an address generator 62, a counter 64, a calculator 66, a source 68, and swi~ches 70 and 72. The adder 50 and the memory 52 are utilized for providing the sums of the event signals 20 for Z axis signals identified by the letter Z in the figure, the sums being stored in the memory 52 in accordance with addresses provided by the X and Y signals from the camera 26. The counter 64 counts the total number of events~ the total number being identi-:Eied by the letter T in the figure. The average number of events per cell of the memory 52 is I7rovided by the ratio T/N where N is the number of cells in the memory 52, the number N aiso being the number of resolution elements of the image produced by the camera 26 and presented on the display 28. The scale factor is identified by the letter K in the figure, a separate value of K being produced 30 for each resolution element of the image by the calculator 66, the ~ 3 values of K being stored in the memory 54. Since the ratio T/N
is constant, the value of K is seen by the formula shown in the fi.gure for the calculator 66 to be inversely proportional to the value of B where B represents the magnitudes of the sums stored in the cells of the memory 52~ there being one ~alue of K for each value o~ B. The mutliplier 58 multiplies the relative energies of the Z axis signals~ shown in the bottom line of the graph 74 by the factor K to produce either a variation in magnitude of the Z
axis signal, as shown in the second line of the graph 74, or a ln variation in the duration of the Z axis signal as is shown in the irst line of the graph 74. The product of the multiplicatlon, identified in the figure by the symbol KZ, is applied to the dis-play 28.
The storing of the sums of the event signals in the memory 52 during the calibration of the system 20 is accomplished as follows.
First~ the reference subject 22 is placed in front of the camera 26. The reference subject 22 is typically in the form of a flat sheet uniformly inpregnated with a r~adioactive material for uni-formly illuminating the fron~ face o-f the collimator 30. The switch 72 is manually set in the calibrate position as shown in the figure.
I`he counter 64 is manually reset to zero by the reset button 76.
In the reset condition of the counter 64, the counter 64 provides a logic s~ate of zero on ].ine 78 under which condition the switch 70 has the position as shown in the figure.
In response to the illumination provided by the reference subject 22 9 scintilla~ions appear on the scintillator 32, the scintillations being converted by the pho~omultipliers 36.and the signal combiners 40 to pulse signals which are coupled via the li.nes 8Q to the signal combiner 40 which combines the signals on the lines 80 to produce the X, Y and Z sigllals which are seen to fan into the line 82. The X and Y signals of line 82 are coupled to the conver~ers 44 and 46 which convert the X and Y signals from an analog format to a digita:L format, the digital formated signals being seen to fan into line 84. The Z, or event, is coupled via the line 82 to the timer 48, the adder 50 and the counter 64. In re-sponse to each strobing of the timer 48 by the Z signal, the timer 48 provides clock signals on line 86 for operating the converters 44 and 46, the timer 48 also providing clock pulses, identified by the legend Cl, which are seen to fan into the line 84 for operat-ing the memory 52 to store digital numbers at locations corre-sponding to the address of the X and -the Y signals.
In response to the clock signals Cl, the contents of a cell of the memory 52 is incremented upon the occurences of successive events at the address of the cell. The contents of the cell is coupled along line 88 from the output terminal of the memory 52 via the switch 70 to an input terminal of the adder 50 to be summed with the Z signal. The resulting sum ~rom the adder 50 is coupled via the line 84 and the switch 70 back to the same cell of the memory 52~ this cell being addressed by the X and the Y signals of the converter 44 and 46. With each appearance of a Z signal in combination with a specific address of the X and the Y signals, the memory 52 makes available to the adder 50 the previously stored sum at that address, the adder 50 then incrementing that sum by a count of 1 corresponding to ~he one even~ signaled by the Z axis signal. In this way, each cell of the memory 52 stores a count of the number of radioactive events from the reference subject 22 which have appeared at the image location corresponding to the address of that cell of the memory 52.
l~hen the counter 64 attains a count of T events, this being a predetermined number to which the counter 64 is preset 9 the 7~
counter 64 provides a logic level of 1 on line 78 which serves as a strobe signal for operating the switch 70 to its alternate po-sition whereupon the line 84 is disconnected from the memory 52.
There~pon, no new data enters the memory 52. The si~nal on :line 78 also strobes the timer 60 to operate the memor~ 52 in a read-only mode via clock pulses C2. In addition, the timer 60 strobes the address generator 62 which sequentially addresses each cell o~
the memory 52 by means of X and Y signals generated by the gener-ator 62. Signals are coupled from the output terminal of the memory via line 88 and the swi~ch 70 ~o the B input terminal of the calculator 66. The timer 60 also provides timin~ signals C3 for operating the calculator 66 to perform the calculation in accordance with the formula shown on the figure in the block identi-fying the calculator 66. Thus, for each sum B coupled from a cell of the memory 52 to the calculator 66, the calculator 66 provides electrical signals in a digital format representing a value of the scale factor K, these electrical signals being cou~led via the switch 72 to the memory 54 and representing a measure of the activity of radioac~ive events at a specific location of the reference sub-ject. The clock pulses C2 and ~he address signals of the generator62, which are .seen to fan into the line 90 and be coupled via the switch 70 to the memory 52, are also cou~led via the switch 72 to the memory 54 for strobin~ and addressin~ the memory 54 in accordance with the strobing and addressing of the memory 52. Thereby, the memory 54 stores a set of scale factors K at locations corresponding to the resolution elements of the image corresponding to the X and Y coordinate locations of the resol.ution elements.
During ~he second phase of the operation of the system 20, the switch 72 is manually positioned in the run position and the reference subject 22 is replaced with the clinical subject 24. Thereupon, the camera 26 and the display 28 are operated to produce an image on the display 28 in the manner commollly employed in hospitals, as disclosed in the aforementioned Stout patent except that, in ac-cordance with the invention~ each Z axis signal which signals a radivactive event is moclified by the multiplier 58 before being applied to the Z axis terminal of the display 28.
With respect to the multiplication by the multiplier 58~ it is noted that since the scale factors are stored in a digital format in the memory 54, the digitally formated scale factors are first con-verted to scale factors in an analog format by the converter 56 andthen apPlied to the multiplier 58. The mul~i.plier 58 may be an analog multiplier wherein the amplitude of the voltage provided by the con-verter 56 modulates the amplitude of the Z axis signals to provide the aorementioned scalin~ of the amplitude portrayed in the second line of the graph 74. Or, alterna~.ively~ the multiplier 58 may in-corporate a pulse-width modulator circuit wherein ~he amplitude of the voltage provided by the converter 56 is util.ized for varying the duration of the Z axis signal on line 92 to provide the aforemen~ioned pulse-width modula~ed si~nal on the first line of the graph 74.
Thereby, the products of the amplitudes of individual ones of the Z axis signals times the duration of the corresponding Z axis signals, this being equivalent to the relative energies in the pulses of the Z axis signals, are modula~ed to compensate for variations in the addresses of Z axis signals as may result in drifti.ng of ~he gain characteristic of individual ones of the p~otomultipliers 36. In addition, it is noted that if the reference subject 22 be provided with a design~ as by masking a portion of the reference subject 22 with a cross or a circle, the outline of the masked portion appears superposed upon an image seen on the display 28. If desired, a digital multiplier (not shown) may be utilized inlieu o~ tne , multiplier 58 in which case the converter 56 would be deleted and a pulse-width modula~or (not shown~ would be coupled between the digital multiplier and the display 28.
With reference to the calculations performecl by the calcu-lator 66, it has been found that, in an experimen~al model of the system 20 wherein the value of the total count T was held constant (7 million counts being utilized) as well as the nurnber of reso-lution elements N being held constant, the variations in the magni-tude of the sums B were sufficiently few in number such that the calculator 66 could be replaced by a read-only memory in which the memory address was supplied by the ma~ni~ude of the quan~ity B and in which the output of the memory was the desired scale factor K.
Thereby, for each value of B presented to the read-only memory, a corresponding value of K was read out of the memory~
It is understood that the above-described embodiment of the invention is illustrative only and that modifications thereof may occur to those skilled in the art. Accordingly, it is desired that this invention is not to be limited to the embodiment disclosed herein but is to be limited only as defined by the appended claims.
Claims (6)
PROPERTY OR PRIVILEGE IS CLAIMED ARE DEFINED AS FOLLOWS:
1 A system for coupling a display to a radiographic camera producing address signals signaling the locations of radioactive events, said system comprising:
means coupled to said camera and responsive to said address signals for measuring the activity of event signals of said camera wherein each of said event signals represents the occurrence of a radioactive event in a subject being imaged by said camera, said measuring means providing activity signals including addresses of respective ones of said events which signal measures of said activity; and means coupled between said camera and said measuring means for mathematically operating on the relative energies of respective ones of event signals by corresponding ones of said activity signals, each of said event signals having a common address with each of said corresponding ones of said activity signals, whereby data of said subject is normalized relative to said measurement of said activity.
means coupled to said camera and responsive to said address signals for measuring the activity of event signals of said camera wherein each of said event signals represents the occurrence of a radioactive event in a subject being imaged by said camera, said measuring means providing activity signals including addresses of respective ones of said events which signal measures of said activity; and means coupled between said camera and said measuring means for mathematically operating on the relative energies of respective ones of event signals by corresponding ones of said activity signals, each of said event signals having a common address with each of said corresponding ones of said activity signals, whereby data of said subject is normalized relative to said measurement of said activity.
2. A system according to Claim 1 wherein said measuring means includes means responsive to address signals of said camera for storing sums of said event signals, individual ones of said sums being identified in said storing means by an address of said address signals.
3. A system according to Claim 2 wherein said operating means comprises a multiplier for multiplying said relative energies by corresponding ones of said activity signals.
4. A system according to Claim 2 wherein said measuring means further comprises an incrementing means coupled between said camera and said storing means for incrementing the sum of a previously stored sum of events.
5. A system according to Claim 4 wherein said measuring means further comprises a counter for counting the occurrences of said event signals, said storing of sums of event signals being termi-nated in response to a signal of said counter when said counter counts a predetermined number of said event signals.
6. A system according to Claim 2 wherein said measuring means further comprises means responsive to values of said stored sums of event signals for providing said activity signals, said storing means including means for storing said activity signals with each activity signal being identified by an address corresponding to the address of said address signals.
DMW:df
DMW:df
Applications Claiming Priority (2)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| US05/752,650 US4093857A (en) | 1976-12-20 | 1976-12-20 | Radiographic normalizing system |
| US752,650 | 1976-12-20 |
Publications (1)
| Publication Number | Publication Date |
|---|---|
| CA1093713A true CA1093713A (en) | 1981-01-13 |
Family
ID=25027193
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CA291,891A Expired CA1093713A (en) | 1976-12-20 | 1977-11-28 | Radiographic normalizing system |
Country Status (7)
| Country | Link |
|---|---|
| US (1) | US4093857A (en) |
| JP (1) | JPS5378694A (en) |
| CA (1) | CA1093713A (en) |
| DE (1) | DE2756780A1 (en) |
| DK (1) | DK152232C (en) |
| GB (1) | GB1545408A (en) |
| IL (1) | IL53541A0 (en) |
Families Citing this family (13)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US4281382A (en) * | 1977-12-21 | 1981-07-28 | Medtronic, Inc. | Radiation signal processing system |
| US4212061A (en) * | 1977-12-21 | 1980-07-08 | Medtronic, Inc. | Radiation signal processing system |
| US4817038A (en) * | 1977-12-21 | 1989-03-28 | Siemens Gammasonics, Inc. | Radiation signal processing system |
| US4386404A (en) * | 1979-12-03 | 1983-05-31 | Medtronic, Inc. | Radiation signal processing system |
| JPS5759183A (en) * | 1980-09-26 | 1982-04-09 | Toshiba Corp | Scintillation camera and its adjusting method |
| US4566074A (en) * | 1981-10-08 | 1986-01-21 | Tokyo Shibaura Denki Kabushiki Kaisha | Scintillation camera |
| US4514632A (en) * | 1981-11-24 | 1985-04-30 | The United States Of America As Represented By The Department Of Health And Human Services | Modular scintillation camera |
| US4611283A (en) * | 1981-12-30 | 1986-09-09 | Raytheon Company | Radiographic imaging apparatus and methods for operating such apparatus |
| JPS59162A (en) * | 1982-06-25 | 1984-01-05 | Sharp Corp | Synchronizing method of image formation on photoreceptor |
| US4527240A (en) * | 1982-12-29 | 1985-07-02 | Kvitash Vadim I | Balascopy method for detecting and rapidly evaluating multiple imbalances within multi-parametric systems |
| US5321261A (en) * | 1992-09-10 | 1994-06-14 | Packard Instrument Company, Inc. | Normalization technique for photon-counting luminometer |
| US5500886A (en) * | 1994-04-06 | 1996-03-19 | Thermospectra | X-ray position measuring and calibration device |
| BR9510290A (en) * | 1994-12-23 | 1997-11-11 | Digirad | Semiconductor gamma ray camera and medical imaging system |
Family Cites Families (8)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US3732420A (en) * | 1971-06-25 | 1973-05-08 | Picker Corp | Automatic calibration system for a scintillation device |
| US3878373A (en) * | 1971-06-30 | 1975-04-15 | Alvin Blum | Radiation detection device and a radiation detection method |
| US3745345A (en) * | 1971-11-09 | 1973-07-10 | Nuclear Chicago Corp | Radiation imaging device |
| US3916198A (en) * | 1973-06-01 | 1975-10-28 | Westinghouse Electric Corp | Amplified-scintillation optical-coded radioisotope imaging system |
| JPS5035435A (en) * | 1973-07-28 | 1975-04-04 | ||
| US3988585A (en) * | 1974-06-11 | 1976-10-26 | Medical Data Systems Corporation | Three-dimensional rectilinear scanner |
| FR2286393A1 (en) * | 1974-09-27 | 1976-04-23 | Labo Electronique Physique | AUTOMATIC PERMANENT CALIBRATION SYSTEM FOR SCINTILLATION CAMERA |
| US4020348A (en) * | 1975-05-12 | 1977-04-26 | G. D. Searle & Co. | Gantry scanning camera |
-
1976
- 1976-12-20 US US05/752,650 patent/US4093857A/en not_active Expired - Lifetime
-
1977
- 1977-11-28 CA CA291,891A patent/CA1093713A/en not_active Expired
- 1977-12-05 IL IL53541A patent/IL53541A0/en not_active IP Right Cessation
- 1977-12-19 DK DK566177A patent/DK152232C/en not_active IP Right Cessation
- 1977-12-20 JP JP15349377A patent/JPS5378694A/en active Granted
- 1977-12-20 GB GB53026/77A patent/GB1545408A/en not_active Expired
- 1977-12-20 DE DE19772756780 patent/DE2756780A1/en active Granted
Also Published As
| Publication number | Publication date |
|---|---|
| JPS5378694A (en) | 1978-07-12 |
| DK152232C (en) | 1988-07-04 |
| DK152232B (en) | 1988-02-08 |
| DE2756780A1 (en) | 1978-06-22 |
| DK566177A (en) | 1978-06-21 |
| GB1545408A (en) | 1979-05-10 |
| US4093857A (en) | 1978-06-06 |
| DE2756780C2 (en) | 1992-05-07 |
| IL53541A0 (en) | 1978-03-10 |
| JPS5640309B2 (en) | 1981-09-19 |
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