U.S. patent number 3,783,288 [Application Number 05/266,218] was granted by the patent office on 1974-01-01 for pulsed vacuum arc operation of field emission x-ray tube without anode melting.
This patent grant is currently assigned to Field Emission Corporation. Invention is credited to John P. Barbour, Francis M. Charbonnier.
United States Patent |
3,783,288 |
Barbour , et al. |
January 1, 1974 |
PULSED VACUUM ARC OPERATION OF FIELD EMISSION X-RAY TUBE WITHOUT
ANODE MELTING
Abstract
A field emission x-ray apparatus and pulsed vacuum arc method of
operation is described in which a plurality of extremely high
voltage pulses of short duration and high repetition rate are
applied between the anode and cathode of the x-ray tube to provide
an electron discharge of low energy density below about 20 joules
per square centimeter to prevent anode melting, which greatly
increases the useful lifetime of such tube. For example, with a
tube having a conical anode of tungsten having a surface area of
1.8 square centimeter, pulses of 350 kilovolts and 1,000 amperes
with a width of 30 nanoseconds, a repetition rate of 1,000 pulses
per second can be employed with an energy of 10.5 joules per pulse
to provide the tube with a useful life in excess of 200,000 pulses.
This increased tube life results from recognition and exploitation
of the fact that, at higher pulse voltages, the anode temperature
rise per pulse is reduced due to the fact that the electrons
penetrate through a thicker surface layer of the anode. The high
voltage, greater than about 250 kilovolts, of the pulses also give
improved results in radiographic apparatus, such as is employed for
x-raying the human chest, since the resulting film radiographs are
of better contrast and contain more useful diagnostic
information.
Inventors: |
Barbour; John P. (McMinnville,
OR), Charbonnier; Francis M. (McMinnville, OR) |
Assignee: |
Field Emission Corporation
(McMinnville, OR)
|
Family
ID: |
23013665 |
Appl.
No.: |
05/266,218 |
Filed: |
June 26, 1972 |
Current U.S.
Class: |
378/106;
378/122 |
Current CPC
Class: |
H05G
1/20 (20130101); H05G 1/60 (20130101); H01J
35/22 (20130101) |
Current International
Class: |
H01J
35/00 (20060101); H01J 35/22 (20060101); H05G
1/20 (20060101); H05G 1/60 (20060101); H05G
1/00 (20060101); H05g 001/32 () |
Field of
Search: |
;250/98,102,414,417
;313/309 |
References Cited
[Referenced By]
U.S. Patent Documents
Other References
"A 50 Millimicrosec. Flash x-ray Phot. System for Hyervel.
Research" Grundhauser et al. Oct. 18, 1960, .
"Fexitron" Field Emission Corp. Oct. 18, 1960,.
|
Primary Examiner: Lawrence; James W.
Assistant Examiner: Anderson; B. C.
Attorney, Agent or Firm: Stephen W. Blore et al.
Claims
We claim:
1. Pulsed x-ray apparatus comprising:
an x-ray tube including an evacuated envelope containing field
emission cathode means and an anode which emits x-rays;
a high voltage pulse generator having its output connected to said
x-ray tube;
exposure control means for triggering said pulse generator and
causing it to apply a pulse train containing a plurality of
electrical pulses between said cathode and said anode to produce a
corresponding number of x-ray pulses during one exposure time
period whose duration is determined by said control means, said
electrical pulses causing the field emission of electrons from said
cathode and the formation of a vacuum arc of vaporized cathode
material so that for each electrical pulse said anode is bombarded
with an electron discharge of extremely high voltage and high
current and emits a corresponding x-ray pulse; and
said electrical pulses having a peak voltage of at least 250
kilovolts and a narrow width so that the anode is bombarded with
electron discharge pulses each having an energy density below that
causing anode melting and the total number of pulses per exposure
and the pulse repetition rate of said pulse train is such as to
prevent the anode from being heated to a final maximum temperature
above the melting point of the anode material at the end of said
exposure period.
2. An x-ray apparatus in accordance with claim 1 in which the anode
material contains tungsten.
3. An x-ray apparatus in accordance with claim 1 in which the
electrical pulses have a peak voltage between 250 and 600 kilovolts
and the electron discharge pulses bombarding the anode have an
energy density below 20 joules per square centimeter.
4. An x-ray apparatus in accordance with claim 3 in which the
energy density is between 5 and 15 joules per square
centimeter.
5. An x-ray apparatus in accordance with claim 1 in which the field
emission cathode means includes a plurality of separate spaced
sharp emitting elements.
6. An x-ray apparatus in accordance with claim 5 in which the
emitting elements are needles.
7. An x-ray apparatus in accordance with claim 5 in which the
emitting elements are rings having sharpened inner edges
surrounding a conical anode.
8. An x-ray apparatus in accordance with claim 1 in which the pulse
rate is at least 500 pulses per second and the pulse width is less
than 200 nanoseconds.
9. An x-ray apparatus in accordance with claim 1 in which the anode
is made of tungsten, the peak voltage is between 300 and 450
kilovolts, the peak current is 1,000 amperes or more, the energy
density of the electron discharge pulses bombarding the anode is 15
joules per square centimeter or less, and the pulse width is 50
nanoseconds or less.
10. A pulsed radiograph method comprising:
producing a pulse train containing a predetermined number of
electrical pulses during one x-ray exposure time period, said
pulses being of high current of at least 500 amperes and high
voltage of at least 250 kilovolts peak voltage;
applying said electrical pulses between a field emission cathode
means and an anode of tungsten in an x-ray tube, to cause a
plurality of x-ray pulses to be emitted from said anode by a field
emission vacuum arc electron discharge operation during said
exposure time period;
transmitting said x-ray pulses through an object to form a
plurality of x-ray images of said object;
exposing a radiographic film with multiple images corresponding to
the x-ray images of said object within said exposure time period;
and
controlling the number of pulses in said pulse train, the pulse
repetition rate and pulse width so that the anode is bombarded with
electron discharge pulses having an energy density less than 20
joules per square centimeter for each pulse and the tungsten anode
is heated to a maximum temperature below its melting point.
11. A radiography method in accordance with claim 10 in which said
object is an adult human chest, the peak voltage is between 300 and
450 kilovolts and the energy density is between 5 and 15 joules per
square centimeter.
12. A radiography method in accordance with claim 10 in which the
x-ray exposure is formed by at least 10 pulses having a pulse width
of less than 100 nanoseconds and a repetition rate of at least 500
pulses per second.
Description
BACKGROUND OF THE INVENTION
The subject matter of the present invention relates generally to
pulsed field emission x-ray apparatus, and in particular to such
apparatus employing high voltage vacuum arc operation without
melting of the anode in order to increase the useful lifetime of
the x-ray tube. The x-ray apparatus of the present invention is
especially useful as a radiographic apparatus for making
radiographs of human chests at high overall voltages of about 300
kilovolts to form radiographs of higher contrast and greater
diagnostic information content. However, the present x-ray
apparatus may also be employed for industrial x-ray inspection
purposes.
Previously, when using pulsed vacuum arc field emission x-ray
tubes, high energy electrical pulses on the order of 40 joules per
square centimeter have been employed which heat the tungsten anode
of such tube above its melting point and causes evaporated cooling
of such anode, as described in U.S. Pat. No. 3,309,523 of W. P.
Dyke et al., granted Mar. 14, 1967. However, the useful lifetime of
x-ray tubes operated in this manner is severely limited. For
example, a 300 kilovolt x-ray apparatus manufactured by the
assignee of the present invention had a useful x-ray tube lifetime
of approximately 1,000 pulses for vacuum arc operation with pulse
energies of 70 joules per pulse. In addition, it has previously
been proposed to provide a radiographic x-ray apparatus employing a
pulsed field emission x-ray tube in which each x-ray exposure is
formed by a plurality of short pulses, as disclosed in U.S. Pat.
No. 3,256,439 of W. P. Dyke et al. granted June 14, 1966. However,
in this prior radiographic apparatus, electrical pulses of lower
voltage and lower energy per pulse were employed of, for example,
135 kilovolts and 4 joules in order to prevent destruction of the
tube anode, which are not fully satisfactory for chest x-ray
surveys since the limited energy per pulse leads to undesirably
long exposure time while at the same time the limited voltage leads
to excessive x-ray absorption in bony structures, hence to an
underexposed low contrast radiograph in several areas, particularly
the mediastinum. As a result, several radiographs must be taken
from different directions in order to obtain all of the necessary
diagnostc information.
It has been found that both of these problems of short tube life
and low local contrast radiographs can be solved by increasing the
pulse voltage to a value greater than about 250 kilovolts and
reducing the energy density per pulse to a value below about 20
joules per centimeter while also controlling the total number of
pulses per exposure so that the anode is not heated above its
melting point. Thus, one embodiment of the pulsed x-ray apparatus
of the present invention operated with pulses of 350 kilovolts and
1,000 amperes, a pulse width of 30 nanoseconds energy per pulse of
10.5 joules, and a pulse repetition rate of 1,000 pulses per second
which results in a useful lifetime of the tube of greater than
200,000 pulses and in chest radiographs of excellent overall
contrast and high diagnostic information content.
These improved results are achieved, in part, because of the
discovery that there is a reduction of anode temperature rise when
a higher pulse voltage is used. This is due to the deeper
penetration of the electrons into the anode surface. Thus, the
tendency of increased heating due to the higher voltage of the
electrons is more than offset by the thicker surface layer and
correspondingly greater volume of anode material being heated
during the pulse. It has been calculated that the depth of electron
penetration in the surface of a tungsten anode for a 350 kilovolts
pulse is four times that of a 135 kilovolts pulse, while the
increase in electron energy for a 350 kilovolts pulse is only 2.6
times that of a 135 kilovolts pulse. As a result, the maximum anode
temperature rise is much less for the 350 kilovolts pulse than for
the 135 kilovolts pulse. For example, when employing pulses of 135
kilovolts and 4 joules energy with a pulse width of 30 nanoseconds,
the maximum anode temperature rise per pulse is approximately
2,150.degree. Kelvin, compared with a temperature rise of only
600.degree. Kelvin for purposes of 350 kilovolts, but otherwise of
similar characteristics.
As a result of the reduction in temperature rise, it is possible to
increase the energy per pulse to 10.5 joules for the 350 kilovolt
pulses and still produce a maximum anode temperature rise of
approximately 1,050.degree. K per pulse which is still lower than
that for pulses of 135 kilovolts and 4 joules. The maximum
temperature at the end of a 50 pulse exposure is still under
3,000.degree. K or well below the melting point of tungsten of
3,640.degree. K even when the temperature rises of such pulses are
added to the initial room temperature value of approximately
300.degree. K to determine the final temperature of the anode. Of
course, by increasing the energy per pulse, the total number of
pulses to provide an adequate exposure is reduced, which is
extremely important in chest x-rays to prevent movement of the
heart and other organs from "blurring" the radiograph.
It is, therefore, one object of the present invention to provide an
improved pulsed field emission vacuum arc x-ray apparatus of longer
useful tube life.
Another object of the invention is to provide such an x-ray
apparatus in which electrical pulses having a peak voltage of at
least 250 kilovolts and an energy of less than 20 joules per square
centimeter are applied to the x-ray tube to prevent its anode from
being heated above the melting point of the anode material.
A further object of the invention is to provide such an x-ray
apparatus as part of an improved high voltage radiographic
apparatus for making x-ray radiographs of higher overall contrast
and greater diagnostic information content.
Still another object of the invention is to provide such a
radiographic apparatus in which each exposure is formed by a
plurality of x-ray pulses whose number and repetition rate are such
that the exposure time is short enough to prevent motion blur in
the radiograph and the maximum anode temperature at the end of the
exposure does not exceed the melting point of such anode.
BRIEF DESCRIPTION OF DRAWINGS
Other objects and advantages of the present invention will be
apparent from the following description of a preferred embodiment
thereof and from the attached drawings of which:
FIG. 1 is a schematic diagram of one embodiment of a pulsed field
emission x-ray apparatus in accordance with the present invention
with one suitable x-ray tube shown in cross section;
FIG. 2 is a perspective view of another embodiment of an x-ray tube
which can be employed in the apparatus of FIG. 1 with parts broken
away to show internal structure;
FIG. 3 is a curve showing the maximum anode temperature rise per
pulse as a function of pulse voltage, pulse energy and target area
being held constant;
FIG. 4 is a graph showing the energy density per pulse required to
raise the surface of a tungsten anode to its melting point at
different pulse voltages;
FIG. 5 is a curve of anode temperature rise versus time after the
start of the first pulse for different pulse voltages and pulse
energies; and
FIG. 6 is a curve of the anode surface temperature produced by a
plurality of pulses in an exposure pulse train containing pulses
identical to those producing the middle curve in FIG. 5.
DESCRIPTION OF PREFERRED EMBODIMENTS
As shown in FIG. 1, one embodiment of the x-ray apparatus of the
present invention includes a field emission x-ray tube 10 including
an anode 12 of a conical shape and a field emission cathode 14 in
the form of a plurality of spaced sharpened needle shaped emitter
elements. The field emission cathode needles 14 are supported in
four radially spaced groups on a metal support sleeve 16 so that
such needles project inward toward the anode. The support sleeve 16
is attached to a metal cup member 18 enclosing one end of the tube
envelope and sealed to a tubular glass envelope portion 20 by a
suitable glass to metal seal to provide the x-ray tube with an
evacuated envelope. A thin x-ray transparent window portion 22 is
provided in the bottom of cup 18 in alignment with the anode 12 so
that x-rays 24 emitted from such anode are transmitted through such
window. When used as a radiographic apparatus, these x-rays 24 are
transmitted through the object under investigation, such as a human
chest, to expose a film within a cassette 25. The anode 12 of the
x-ray tube is mounted on a stem 26 of reduced diameter which is
attached to a support rod 28 extending through another glass to
metal seal formed between envelope portion 20 and a metal seal
member 30 provided at the other end of the envelope to enable
electrical pulses to be applied thereto through lead 32. X-ray
tubes of this construction are known and have been described in the
above-discussed U.S. Pat. No. 3,309,523 and 3,256,439 of Dyke et
al.
The cathode support cup 18 is grounded and the anode 12 is
connected through lead 32 to the output of a high voltage pulser 34
which may be a Marx surge generator but may also be of the Blumlein
field reversal type or other high voltage pulser containing storage
capacitances. The storage capacitors of the Marx surge generator
are charged in parallel and discharged in series through spark
gaps. Thus, the pulser 34 is connected to the output of a D.C.
charging current source 36 of lower voltage of, for example, about
15 kilovolts. A trigger generator oscillator 38 whose repetition
rate is set by the adjustment of a variable resistor 40 is
connected at its output to the high voltage pulser 34 for
triggering such pulser by trigger pulses 41 which cause the first
spark gap to break down. This causes the pulser to produce
corresponding high voltage output pulses 42 on conductor 32 of, for
example, 350 kilovolts peak voltage and 1,000 amperes peak current
with a pulse width of about 30 nanoseconds and a repetition rate of
about 1,000 pulses per second. This repetition rate may be varied
between about 500 and 4,000 pulses per second, depending upon the
setting of resistor 40. An exposure control circuit 44 including a
variable resistor 46 of variable resistance is connected at its
output to the trigger oscillator 38 to control the number of
trigger pulses 41 and the corresponding number of high voltage
output pulses 42 per exposure. Thus, the control circuit 44 applies
an enabling signal 48 to the trigger oscillator 38 to cause it to
produce trigger pulses so that the duration of the enabling signal
48 determines the total exposure time, and such duration is
adjusted by the setting of variable resistor 46.
As shown in FIG. 2, the x-ray tube 10 of the apparatus of FIG. 1
can be replaced by modified tube 10' which is similar, but is
provided with a different field emission cathode means 14'. The
cathode 14' is in the form of three or more annular rings 50 having
their inner edges 52 provided as sharpened emitting elements which
surround the conical anode 12 extending coaxially through such
rings. The cathode rings 50 are mounted in a modified support
sleeve 16' so that they project inward and are longitudinally
spaced along the anode.
Both the tube 10 of FIG. 1 and the modified tube 10' of FIG. 2 are
provided with a vacuum arc field emission operation in which the
electrical pulses 42 applied to the anode cause the field emission
of electrons from the sharpened emitter elements of the cathode.
These elctrons are accelerated by the high pulse voltage to the
anode where they bombard the anode surface and cause x-rays to be
emitted therefrom. The anode 12 may be made of tungsten or tungsten
containing alloy, as well as other refractory metals including
molybdenum, and the cathode emitting elements may be made of a
similar material. During vacuum arc operation, a portion of the
cathode material is vaporized to produce positive ions of cathode
material which neutralize the negative space charge ordinarily
surrounding the cathode and thereby greatly increase the electron
discharge current to provide a current on the order of 1,000
amperes during the brief time period of pulses 42. This vacuum arc
field emission operation produces an intense x-ray pulse of short
duration for each electrical pulse 42, as described in the
above-mentioned patents.
As shown in FIG. 3, a curve 54 of the maximum anode temperature
rise in degrees Kelvin for different pulse voltages in kilovolts
shows that as the voltage increases the anode temperature rise
decreases. This is surprising, because one would ordinarily think
that the increase in electron energy due to the greater pulse
voltage would cause a corresponding increase in anode temperature.
However, it has been found that this increase in beam voltage
causes the electrons to penetrate through a thicker surface layer
of the anode, thereby increasing the effective volume of anode
material in which the heat energy is dissipated during each pulse.
For example, at 350 kilovolts, the effective depth of penetration
of the electrons in a tungsten anode is approximately 17.6 microns,
while the effective depth of penetration of electrons at 135
kilovolts is only about 4.4 microns. Thus, it can be seen that the
thickness of the anode surface layer in which the heat is
dissipated for the 350 kilovolt electron beam is four times that of
the 135 kilovolt beam, while the increase in electron energy is
only 2.6 times that of the 135 kilovolt electrons. The result is a
net decrease in anode temperature with increases in pulse voltage
and this decrease in temperature follows along the curve 54 for a
pulse energy of 5 joules per square centimeter. This effect is more
fully discussed hereafter with respect to FIG. 5.
FIG. 4 shows a curve 56 of the energy density in joules per square
centimeter per pulse at different pulse voltages in kilovolts
required to increase the temperature of the tungsten anode surface
to its melting point. While the values used in FIG. 4 are
calculated values and the actual energy density is lower because of
the finite rise time and fall time of the pulse, it can be seen
that for a beam of 150 kilovolts, the energy density is about 5
joules per square centimeter to cause anode melting, while at a
higher voltage of 350 kilovolts approximately 18 joules per square
centimeter are required for melting. Here again, the greater energy
density required for anode melting with higher voltage pulses is a
result of the increased surface penetration of the electrons which
increases the effective volume of anode material available for heat
dissipation during each pulse. Thus, the energy density required
for melting actually increases with increases in beam voltage.
It has been found that high voltage pulses in the range of 250 to
600 kilovolts, and preferably between about 300 and 450 kilovolts,
give greatly improved x-ray radiographs of higher overall contrast
and greater diagnostic information content, especially when
employed for human chest x-rays. Thus, the x-ray pulses produced at
these higher voltages penetrate through the spine and rib bones in
the chest to expose organs positioned behind such bones, which is
extremely advantageous, especially in the study of the lungs whose
outer periphery is frequently hidden in radiograph by the x-ray
image of the ribs. It should be noted that at extremely high
voltages, greater than 600 kilovolts, x-ray scattering becomes a
problem which cannot be solved by conventional Bucky grid type
collimators. Previous chest x-ray radiographic apparatus have
operated at approximately 150 kilovolts and because of the low
contrast several radiographs must be taken from different angles to
obtain the same information which can be obtained in a single
radiograph taken by a multiple pulse exposure at the high voltage
level of, for example, 350 kilovolts in the manner of the present
invention.
When a pulsed vacuum arc field emission x-ray tube is operated at
this high voltage of about 350 kilovolts and high current of about
1,000 amperes, the tube life is ordinarily severely limited due to
melting of the anode. Thus, in one such apparatus manufactured by
the assignee of the present application, the tube life was only
about 50 pulses. This problem has been overcome in the x-ray
apparatus of the present invention by reducing the energy per pulse
and increasing the number of pulses per exposure. Thus, it has been
found that for voltages greater than 250 kilovolts, the energy
density per pulse should be less than 20 joules per square
centimeter, and preferably is about 8 joules per square centimeter
or less at 350 kilovolts for a typical multiple pulse exposure of
15 pulses or more. Also, the pulses should have a pulse width less
than 100 nanoseconds, or preferably about 30 nanoseconds, and a
pulse repetition rate greater than 500 pulses per second, or
preferably 1,000 pulses per second to give satisfactory exposure
time and total energy per exposure without anode melting. Thus, for
chest x-rays, the exposure time must be less than about
one-fiftieth of a second to prevent motion blur in the radiograph
due to, among other things, heart and lung movement. Also, for a
normal chest x-ray, a pulse train of approximately 20 pulses of the
preferred values given above is sufficient for a proper exposure of
about 20 millirads for a patient six feet from the x-ray source
when the x-ray cassette 25 contains Kodak RP54 film and two
fluorescent intensifier screens on opposite sides of such film.
As shown in FIG. 5, a curve 58 of anode temperature rise in degrees
Kelvin versus time after the start of the first pulse for 135
kilovolt pulses, shows that the temperature rise is a maximum of
2,150.degree. K at peak point 60 corresponding to the end of the
first pulse. After the pulse terminates, the temperature rise
gradually reduces by heat diffusion into the anode material below
the bombarded surface layer to an equilibrium temperature of about
22.degree. K. This curve 58 is for pulses of 135 kilovolts and 4
joules energy with a pulse width of 30 nanoseconds and an effective
anode area of one square centimeter. However, a second curve 62 of
anode temperature rise versus time for a 350 kilovolt pulse of the
same energy and other characteristics shows a peak temperature rise
64 at the end of the first pulse of only about 600.degree. K. Thus,
the maximum temperature rise for the 350 kilovolt pulse is over
1,500.degree. less than the temperature rise produced by the 135
kilovolt pulse. This dramatically illustrates the reduction in
anode temperature rise resulting from increased pulse voltage that
was previously referred to in FIG. 3. It should be noted that the
curve 62 closely follows the curve 58 after the time of
10.sup.-.sup.5 second, since the total energy for both of the
corresponding pulses is the same. However, by increasing the amount
of pulse energy to 10.5 joules for the 350 kilovolt pulse, a third
curve 66 results which has a peak temperature rise 68 at the end of
the first pulse of about 1,050.degree. K. This peak temperature
rise 68 for the 350 kilovolts, 10.5 joule pulse is still much lower
than the peak temperature 60 of the 135 kilovolt curve 58, even
though the third curve 64 is produced by a pulse of over twice the
energy. Thus, as a result of the reduction in temperature, it is
possible to greatly increase the energy of the 350 kilovolt pulse
without causing anode melting, which reduces the number of pulses
required for the necessary total exposure energy.
As shown in FIG. 6, when a plurality of 350 kilovolt, 10.5 joule
pulses corresponding to curve 66 of FIG. 5 are applied to the x-ray
tube at a repetition rate of 1,000 pulses per second as part of a
pulse train, the anode surface temperature increases with each
pulse due to the fact that the anode is at some higher temperature
and does not cool down to its initial temperature at the beginning
of each successive pulse. Thus, when a plurality of 350 kilovolt,
10.5 joule pulses having a repetition rate of 1,000 pulses per
second are applied to the x-ray tube, the anode is progressively
heated along a minimum anode temperature line 70 corresponding to
the envelope of the residual temperature rise at the end of each
pulse and along the maximum anode temperature line 72 corresponding
to the envelope of the peak temperature 68 of each pulse. It should
be noted that the vertical axis of the curve of FIG. 6 is in terms
of total temperature in degrees Kelvin, while the vertical axis of
FIG. 5 is in terms of temperature rise or change in temperature per
pulse in degrees Kelvin. Thus, the minimum anode temperature
envelope 70 of FIG. 6 starts at room temperature which is
approximately 300.degree. K and the maximum anode temperature
envelope 72 starts at 1,050.degree. +300.degree., or 1,350.degree.
K.
An important thing to note in FIG. 6 is that the maximum
temperature line 70 does not exceed the 3,640.degree. K melting
point 74 of the tungsten anode until after 110 milliseconds. Thus,
for the 350 killovolt, 10.5 joule pulses producing the temperature
curves 66, the maximum exposure time without anode melting is 110
milliseconds which corresponds to 110 pulses at a repetition rate
of 1,000 pulses per second. As shown in FIG. 5, on the logarithmic
time scale at this repetition rate, the second pulse indicated by
arrow 76 occurs one millisecond after the first pulse at a point 78
on the temperature curve 66 which corresponds to a temperature rise
of approximately 60.degree. K. Thus, there is a minimum anode
temperature increase along curve 70 of approximately 60.degree. K
per pulse and a corresponding increase in a maximum temperature
curve 72 of a similar amount per pulse. Of course, this is only an
approximation because by the time the fiftieth pulse occurs, as
indicated by arrow 80, the temperature curve 56 of the first pulse
has decreased to a point 82 of about 24.degree. K. From the above,
it can be seen that in order to prevent anode melting which greatly
reduces tube life, the total number of pulses per exposure and the
pulse repetition rate must be such that the maximum anode
temperature line 72 does not cross the melting point 74 of the
anode before termination of the exposure. For most chest x-rays, 50
pulses or less will be employed so that there is no danger of this
happening when using 350 kilovolt pulses of 10.5 joules energy with
a pulse repetition rate of 1,000 pulses per second and a pulse
width of 30 nanoseconds in accordance with the preferred embodiment
of the invention.
It should be noted that the tube anode on which the temperature
curve 66 was calculated had an effective area of 1.8 square
centimeters which corresponds to a conical target having a maximum
base diameter of 0.2 inch and a cone half-angle of approximately
7.degree. measured between the axis and the side surface of such
cone. This provides a small x-ray source having an effective
diameter of approximately 3 millimeters which is important for
x-ray radiography for good image resolution of small objects.
While the invention has been described with particular reference to
medical applications such as x-raying the human chest employing a
plurality of high intensity pulses of x-rays, the short duration,
high intensity x-ray pulses produced are also particularly useful
in high speed cineradiographic systems using either a high speed
pin registered framing camera and an x-ray image intensifier with
the pulses synchronized with the camera shutter or a high speed
film drum. The individual x-ray pulses are preferably less than 50
nanoseconds long so that the system has exceptional stop-motion
characteristics for high speed events and pulse rates up to 1,000
frames per second provide excellent slow motion effects.
Applications include studies of crash injuries, rocket motors,
vibrations, fast moving internal parts, etc.
It will be obvious to those having ordinary skill in the art that
many changes may be made in the details of the above-described
preferred embodiments of the present invention without departing
from the spirit of the invention. Therefore, the scope of the
present invention should only be determined by the following
claims.
* * * * *