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BACKGROUND OF THE INVENTION
This invention relates to cardiovascular monitoring and, more particularly,
to an absorption spectroscopic catheter for the in vivo measurement of
blood gas partial pressures as well as blood pressure and pulse rate.
Pressure transducer catheters are well-known (References 1, 2), as are
electrolytic type catheters for determining blood gases (3). Various
optical catheters have been conceived for the measurement of gas content
in blood (4-9) and for providing both blood gases and pressure-pulse rate
data (8). Some of such systems utilize fiber optic technology to introduce
light in the red-visible region of the spectrum into the bloodstream which
is reflected by blood molecules. The reflected light is then
colorimetrically analyzed to determline blood color from which information
pertaining to oxygen saturation can be derived. This information, however,
is actually a ratio of the number of oxygenated hemoglobin molecules to
non-oxygenated hemoglobin molecules, and does not provide data in terms of
the partial pressure of oxygen which is a vital parameter vis-a-vis the
life of the catheterized patient. Another disadvantage of colorimetric
systems is that carbon dioxide content in the blood is not directly
obtainable.
Other catheter systems utilizing the arts of gas chromotography (10) or
mass spectrometry (11) have been devised to measure cardio-vascular
functions. Such systems, however, generally require the removal of a blood
sample from the body before analysis can take place. The analytical
components are very large and are usually located in laboratories which
are often far removed from the operating room. Once the blood reaches the
laboratory the analysis response time of such systems is typically slow.
Delay is a primary disadvantage of mass spectrometric and gas
chromotographic systems. Expense is a further disadvantage.
The principles of absorption spectrometry are well-known and find
application in a number of analytical systems, procedures and devices.
These principles, however, have not been applied to the rapid and accurate
in vivo analysis of dissolved gases in blood. Briefly, and in a very much
simplified manner, the principle of operation of the present absorption
spectrometry catheter system is described as follows.
Each atom or molecule absorbs and radiates electromagnetic radiation in
discrete quantitative increments at a number of discrete levels of energy.
In the present instance, the electro-magnetic energy is in the energy
range referred to as "light," including both the visible and the invisible
infrared and ultra-violet regions of the light spectrum. When a light beam
of a specific energy level, i.e. wavelength, preferably of only one
wavelength, i.e. monochromatic light, is passed through a chamber
containing a specific substance which absorbs at that wavelength, the
amount of absorbed light, and hence the reduction in the intensity of the
light beam, is proportional to the number of atoms or molecules of the
substance in the chamber which interact with the incident radiation. The
ratio of intensity incident light, I.sub.o, to the intensity of the exit
light, I.sub.f, is a measure of the absorbed light and, therefore, a
measure of the amount of the substance in the absorption chamber.
Actually, any given substance will absorb light of many differnt energy
levels (wavelengths), some wavelengths being strongly absorbed and others
much less strongly absorbed. This variation in amount of absorption with
wavelength is referred to as the absorption spectrum of the particular
material.
When the substance to be measured is a gas, such as oxygen or carbon
dioxide, it is convenient to measure the amount of the gas present in a
chamber of defined dimensions. According to the gas law, the pressure of
the gas in such a chamber is directly proportional to the amount, or
number of molecules, of gas in the chamber. Thus, it is possible to
measure directly the pressure of a given gas in the chamber simply by
measuring the total amount of the gas in the chamber. Where more than one
gas is present the pressure contribution of each constituent gas is
referred to as the "partial pressure" of that gas.
In any system which includes gases, whether it be a gaseous system, such as
a chamber of defined proportions, or a liquid system, such as flowing
blood, each gaseous component exerts a pressure proportional to the total
amount of the gas in the system. Thus, each gas dissolved in the blood
exerts a "partial pressure" in the blood stream. If such a system having a
partial pressure of a given gas, for example blood with an oxygen or
carbon dioxide partial pressure, is placed in contact with a barrier which
is permeable to the gas but not to the blood, the gas will permeate and
diffuse through the barrier, i.e. dissolve in one side and out the other,
until the partial pressure of that gas on the other side of the barrier
equals the partial pressure of the gas in the blood stream. Actually, the
pressures on each side of the barrier need not be exactly equal since
there are permeation factors, and other factors, which effect the flow
through the barrier; however, the gas will flow through the barrier until
an equilibrium value is reached at which time the rate of diffusion
through the barrier is equal in both directions.
This principle is applied in the present invention by placing a catheter
which includes a chamber of defined dimensions in the blood stream. All or
part of the wall of the chamber is made of a barrier membrane which is
permeable to oxygen and carbon dioxide and/or selected other gases,
referred to as a semipermeable membrane. The partial pressure of a given
gas in the chamber, at equilibrium, is directly proportional to the
partial pressure of gas in the blood. Accordingly, by measuring the
partial pressure of the gas in the chamber, by measuring the total amount
present as discussed before, the partial pressure of dissolved gas in the
blood can be determined. The unique application of these principles in the
apparatus and systems and methods of this invention are an important
feature of this invention.
Absorption spectroscopy is particularly useful where emission spectra are
difficult to obtain due to the high energy levels required to achieve
electronic configurations excitations. This is especially true of
polyatomic and diotonic gases. For example, absorption spectroscopy has
been successfully employed to measure the ozone level of the atmosphere.
Since low energy radiation is sufficient for obtaining absorption spectra,
measuring systems based on this concept are very advantageous and well
suited for use in the in vivo measurement of cardiovascular functions. The
development of high infrared transmissive optical fibers has made possible
the efficient utilization of the absorption concept in blood catheters.
The use of absorption chambers in conjunction with such catheters provides
for flexible and accurate monitoring of one or a combination of several
blood gases.
The preferred embodiment of the present invention allows for the
simultaneous measurement of oxygen and carbon dioxide partial pressures,
vital indicators with respect to cardiovascular performance. Furthermore,
the same monitor is easily adapted to also measure the equally vital
overall blood pressure and pulse rate, thereby embodying a complete, yet
convenient and accurate, monitoring device. Convenience in use and
mobility of the monitor, because of its small dimensions and reduced space
requirements of the optical and electronic components, are important
features of the present invention. Use of monochromatic light of strongly
absorbed wavelength provides both accuracy and sensitivity for both gases,
with minimum effect from the presence of other gases. Response time of the
absorption catheter is very short, only about three seconds.
SUMMARY OF THE INVENTION
The present invention provides an optical catheter system, based on the art
of absorption spectroscopy, for the accurate and efficient cardiovascular
monitorization of blood gas content, as well as overall blood pressure and
pulse rate.
In general, the catheter of this invention comprises a pair of elongate
fiber optic bundles, which may be randomly mixed with each other, in an
elongate sheath of any of several biologically compatible materials. The
fiber optic bundles are adapted at the proximal end to receive incident
monochromatic radiation, I.sub.o, of known intensity and predetermined
wavelength and to transmit the incident radiation the lengths of the
catheter to an absorption chamber at the distal end of the catheter. The
absorption chamber may be of any configuration but is conveniently of
generally cylindrical shape with the fiber optic bundles at one end
directing the incident radiation the length of the chamber to a reflective
surfaced semipermeable membrane forming the other end of the chamber. In
this configuration the radiation is absorbed by gases present in the
chamber during two passes through the chamber, to the mirror and from the
mirror back to the fiber optic bundle. The remaining, or exit radiation,
is transmitted by the fiber optics back along the length of the catheter
to radiation detectors which measure the intensity of the final radiation,
I.sub.f. It is the ratio I.sub.o /I.sub.f which is proportional to the
partial pressure of the dissolved gas in the blood stream. In the
preferred form, the distal wall of the chamber serves both as a
semipermeable membrance and as a mirror, being coated with gold or some
other reflective coating to about a 50% reflectivity; however, separate
semipermeable membranes, e.g. in the cylinder walls, could be provided to
result in the same basic chamber. Similarly, the chamber may be spherical
or of some other configuration. It is intended that the specific
embodiments referred to here and hereinafter are not limiting but are
merely exemplary.
In accordance with the preferred embodiment of this invention, the blood
partial pressures of two gases, oxygen and carbon dioxide, are
concurrently measured and displayed. Where two gases are present in the
chamber, each will absorb light passed through it, to one degree or
another, depending upon the wavelength of the incident light rays. Thus,
the absorption by both gases will contribute to the decrease in intensity
of the incident light, that is, I.sub.o less I.sub.f, thereby making
inaccurate the measurement of either one of the two gases. It is therefore
necessary for the measurement of a first gas, to supply light to the
chamber of a wavelength at which absorption by that particular gas is very
high, and at which absorption by the other gas present is very low.
Similarly, absorption analysis of the second gas should utilize light of a
wavelength at which absorption by that gas is high and at which absorption
by the first gas is very low, or negligible.
The present invention accomplishes this objective by utilizing light with a
predeterined wavelength of approximately 7596 angstroms for the absorption
analysis of oxygen, and of approximately 2 microns for the measurement of
carbon dioxide. At these wavelengths, the respective absorption by carbon
dioxide and oxygen, as well as other gases present, water vapor and
nitrogen will be negligible. The optical fibers employed by the present
invention are unique in that they exhibit high transmissive qualities,
that is, above 30%, of light in the infrared region.
Two distinct light sources, one visible and one infrared, are provided for
the production of light beams of these wavelengths. The visible source in
the preferred embodiment is a laser, well-known for the coherent and
monochromatic nature of its light rays (22-24). Dual detectors, responsive
to light in the visible and infrared regions of the spectrum,
respectively, are also provided.
Light from the two sources is alternately pulsed by the use of an optical
multiplexer, referred to as a "chopper," towards the incidence channel of
the fiberoptical system for transmission to the chamber. Pulsing is
necessary not only because there are two light sources and only a single
incidence channel, but also because a continous beam of light falling on
the detectors substantially dampens its sensitivity and reduces the signal
to noise ratio. The chopper herein employed, however, is novel in that it
not only produces the necessary pulsation of light, but also
simultaneously synchronizes the alternate pulsation of light from two
light sources, and the alternate detection of reflected light rays by two
detectors.
A further advantage of the present invention is that it provides for the
measurement of gases present in the blood stream, other than oxygen and
carbon dioxide. The structure and concept of this invention allows the
absorption analysis of one or a combination of several gases.
Finally, besides the measurement of blood gas partial pressures, the
present invention is capable of simultaneous monitoring of overall blood
pressure and pulse rate. The semipermeable window contained in the
absorption chamber is made of a flexible substance which allows it to
deflect in response to blood pressure and pulse rate. These responsive
deflections are transmitted to the light by the window at the point of
reflection, and are exhibited by the reflected light in the form of
amplitude modulations. These modulations are sensed by the detectors which
generate electronic signals in response thereto. These signals can then be
properly converted and visually displayed to provide the instantaneous and
complete monitorization of cardiovascular functions, including blood gas
partial pressures, overall blood pressure and pulse rate.
These and other advantages of the present invention are readily apparent by
reference to the drawings in which:
FIG. 1 is a perspective drawing of the Cardiovascular Monitor including
digital display of oxygen and carbon dioxide partial pressures, blood
pressure and cardiacrate, detectable optical catheter chambered sensor end
tip;
FIG. 2 is a perspective and schematic diagram optical multiplexing system
and fiber optics of the preferred embodiment of the present invention;
FIG. 3 is a section view, taken along lines 3--3, of the sensor end tip
showing absorption chamber and peripheral sensor construction;
FIG. 4 is a block diagram illustrating the electronic analog to digital
conversion of the output signals; and
FIGS. 5 and 6 are signal output waveforms.
DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENT
Shown in FIG. 1 is an exemplary cardiovascular moniter with catheter
attachment, indicated generally at 10 and 12, respectively, which embody
the present invention. Other forms of equipment of like function, e.g.
using a strip chart display are obviously within the scope of this
invention. Moniter 10 provided for the visual digital display of blood
pressure 14, both systolic and diastolic, cardiac rate 16, pulse rate
indicator light 18, and partial blood pressures of oxygen and carbon
dioxide, 20 and 22, respectively. On/off switch 24 and power light
indicator 26 are also shown.
Housed within monitor 10 is the optical multiplexing system of the present
invention, including light sources, detectors and rotary multiplexor, as
well as the electronic analog-to-digital conversion system, necessary for
the processing and display of the cardiovascular data. This mode of
housing and display is, however, merely a preferred example. In many cases
it may be desirable to record, by means of a strip chart for example, the
signals corresponding to the above data.
The monitor face is provided with input/output connection 28, which
receives dual jacks 30 of the bifurcated optical catheter 12. Incidence
channel 32 and reflection channel 34 combine to form catheter body 36, the
former for transmitting light to sensor end tip 38 and the latter for
return transmission of reflected light. The construction of the bifurcated
fiber optical system will be dealt with in more detail below.
FIG. 2 illustrates the primary components of the preferred embodiment, the
optical multiplexing system 40, fiber optical catheter 12, and the sensor
end tip 38 and the manner in which these systems interface. Sensor 38 is
generally defined as a cylindrical housing 46, fitted at one end with a
semipermeable window 48. The sensor housing can be constructed of
stainless steel, or of less rigid materials such as nylon, ABS or of any
of the well-known biologically acceptable materials. Its diameter is
approximately 2 mm and measures about 4 mm in overall length.
The window material must be flexible, so as to be sensitive to blood
pressure and cardiac rate, and also permeable, in the preferred
embodiment, to oxygen and carbon dioxide. Sylastic brand (General
Electric) silicon rubber of thickness about 10 microns is generally
accepted as a biologically compatible semipermeable membrane material and
is quite satisfactory.
A circular light aperture 50 generally defines the proximal end of housing
46 and receives the non-bifurcated end of fiber optic bundle 53, thereby
allowing the entrance and exit of light into and out of sensor end tip 38.
The detailed construction of the sensor end tip 38 is shown in FIG. 3.
Sensor housing 46 narrows at its proximal end to facilitate attachment to
the optical catheter body 36. Window 48 is affixed to the housing using an
autoclavable epoxy glue. The deflection of the window 48, shown in phantom
line 56, is due to the pressure of the blood on its exterior surface,
indicated by the arrows 58, the frequency of such deflections being
dependent upon the rate of heartbeat. In addition to flexing in response
to blood pressure and pulse rate, the window is permeable to oxygen and
carbon dioxide molecules dissolved in the blood.
Gas molecules 60 diffuse through the window membrane into the absorption
chamber 54 until equilibrium is reached. At this point, the partial
pressures of O.sub.2 +CO.sub.2 inside chamber 54 will equal, or at least
be directly proportional, to the surrounding partial pressure of these
gases in the bloodstream. A reflective coating 62 is applied to the
interior surface of the window using conventional vacuum deposit or
evaporational techniques. The coating material can be gold or aluminum and
is applied so as to exhibit an optical density of about 46%, not opaque
enough to reduce to any substantial degree the permeability of the window
and yet sufficient to allow for reflection of incident light rays, as
shown by arrows 64 and 66.
Body 36 of optical catheter 12 is comprised of a sheathing material such as
flexible polyvinyl chloride, nylon, Tygon, chlorinated rubber, or other
biocompatible material. The body is, conveniently, shrink molded for
attachment to housing 46 of sensor end tip 38.
Referring again to FIG. 2 the bifurcated construction of the fiber optical
catheter 12 is shown. Ten fibers, in a typical structure, each constitute
the incidence and reflection channels 32, 34 of the catheter, to form the
20-fiber, randomly mixed bifurcated bundle, shown in section at 68.
Corning fiber optics No. 44-49016-1499 is a presently preferred fiber
optic material.
The optical multiplexing system, indicated generally at 40, consists
essentially of red visible and infrared light sources 70 and 72, visible
and IR detectors 74 and 76, and an optical multiplexer 78, referred to as
a "chopper." The rotary chopper 78 is powered by motor 80. Visible source
70 is a laser which produces light with an approximate wavelength of 7596
angstroms and intensity of 5-10 mw, e.g. Spectraphysics Model 142 or Model
335 used for the absorption analysis of oxygen. A laser source is
preferred because of the characteristically coherent and monochromatic
narrow beam produced thereby. A further advantage is the reduced size of
the source optics required, providing for a monitor of reduced dimensions.
The infrared source 72 is a standard incandescent reflective source for the
absorption measurement of carbon dioxide. For the reasons discussed above,
a carbon dioxide laser is a desirable source but cost considerations
presently suggest the use of conventional IR source. The wavelength of
light produced by the IR source is approximately 2 microns and has an
intensity of 250-300 watts.
The visible detector 74 consists of a silicon phototransistor, peaked for
detection via narrow band filters of light wavelengths of around 7596
angstroms. Texas Instruments Co. Model TIL 78 is an example of such a
detector. While a silicon phototransistor could be utilized as the IR
detector 76, a triglycine sulfate crystal detector is preferred because of
its proper gain special frequency and time response. The IR detector is
selected and adjusted to sense light wave lengths of around 2 microns.
Narrow band filters of, respectively, 7596 angstroms and 2 microns with a
band width of 1/2A are part of the detector and not depicted separately.
It is well-known that a continuous beam of light falling upon an optical
detector will substantially dampen its response, and that pulsation of the
incident light is therefore necessary. Optical chopper 78 accomplishes
this result, as well as the multiplexing of two discrete light rays down a
single fiber optical channel. As shown in FIG. 2, each 90.degree. rotation
of the chopper wheel 78 allows light procuded by the visible source 70 to
be reflected by one of its four prisms 82 towards the incidence channel 32
of fiber optic catheter 12. Instantaneously, the incident light ray will
be reflected by window 48 for return transmission via reflection channel
34, whereupon it impinges upon another prism located on the chopper
180.degree. from the first. Turning of the visible beam at the locations
shown in FIG. 2 is provided for by totally reflective optical flats 84.
With each 45.degree. rotation of the chopper, the infra-red light produced
by IR source 72 is allowed to pass through and enter the incidence channel
32 for transmission to the absorption chamber 54. Reflected IR light will
similarly pass through the chopper for direct sensing by IR detector 76.
The electrical output signals produced by the sensors, indicated generally
at 100, in response to reflected light rays are processed in accordance
with the analog/digital conversion electronics system shown in FIG. 4. The
analog signal first undergoes pre-calibration in a conventional scaler
amplifier 102 where it is scaled to correspond to the voltage input limits
of the microprocessor.
A calibration source 104, which may be any of a large number of stable
signal generators of conventional design, is selectively fed to the scaler
amplifier 102 to ensure electronic stability. The sensor output also
triggers the syncronization detector 106 which, along with syncronization
driver 108, generates a sync pulse to ensure proper syncronization in the
input multiplexer 110 and the output multiplexer 112. The processed signal
from the multiplexer 110 is processed by a peak detector 114 which senses
the maximum amplitude of each peak of the alternating signal resulting
from the optical multiplexer. An automatic gain control amplifier 116
receives an output signal from the peak detector and feeds the scaler
amplifier 102 to ensure proper voltage input to the multiplexer 110. The
peak detector output is an analog signal which is converted to a digital
signal for further processing by a conventional analog to digital
converter 118 which feeds the digital signal to the output multiplexer 112
where the signal is processed for individual display and may then be
displayed as a digital signal by means of counters 120, catch decoder
drivers 122 over predetermined time intervals controlled by the update
clock 124 and then visually presented by displays 126 which may be
conventional neon glow tube devices of any design, or any other digital
signal responsive display device. A plotter or printer could, for example,
be used in lieu of the neon glow tubes of the exemplary embodiment
depicted in FIG. 1. In addition, or alternatively, the processed signal
may be converted by a conventional digital to analog converter 128 to be
displayed by an analog display device 130, such as a conventional strip
chart recorder.
No novelty or unique features reside in the electronic circuits; indeed,
all electronic circuits and signal handling devices and displays are
well-known and generally used thoughout the electronics and instrument
industries and are described in numerous standard texts and other
publications. See, for example, Brophy, J. J., 1972, Basic Electronics for
Scientists, 2nd Ed., McGraw-Hill, New York; Offner, F. F., 1967,
Electronics for Biologists, McGraw-Hill, New York; Vassos, B. H. and
Ewing, G. W., Analog and Digital Electronics for Scientists, 1972,
Wiley-Interscience, New York. Off-the-shelf electronic signal processing
instruments which are adaptable for producing suitable readout of the
signals are available from a number of instrument manufacturers.
In use, the optical catheter 12 is inserted into the bloodstream such that
sensor end tip 38 is in the desired location. Carbon dioxide and oxygen
molecules dissolved in the blood diffuse across the permeable window 48
and occupy absorption chamber 54. The systolic and diastolic pressures of
the blood produce corresponding deflections in window 48 which occur at
the frequency of the pulse rate. The rotary action of the chopper 78
multiplexes alternate light rays of known intensities down incidence
channel 32 of the optical catheter 12 to chamber 54. As shown in FIG. 3,
incident light rays 64 pass through the chamber, and are reflected by the
reflective coating 62 of window 48 back through the chamber, whereupon the
reflected rays 66 enter one of the fibers constituting reflection channel
34 for transmission to the detectors. The reflected light pulse is
amplitude modulated at the point of reflection by the deflections of
window 48, resulting from pulsing of the blood and the average blood
pressure. Calibration of each catheter, or selection of like-sensitivity
catheters, is required for quantitization of the signal output; however,
it will be apparent from the geometry of the sensor chamber that an
increase in blood pressure, either long term or transitional, will cause
distension of the membrane and will result in greater scattering of the
light thus reducing the proportion of the light reflected to the
reflecting channel optical fiber bundle. This phenomenon, in itself, is
known (8) and therefore, no detailed discussion is required.
The light of each frequency, in addition, undergoes two absorptions by the
respective gas to which each corresponds. For example, light from the
visible source 70, having a predetermined wavelength of about 7596 A,
precedes the pulse of light from the IR source 72 down the incidence
channel to the chamber. As this pulse of light twice traverses the
chamber, its energy is absorbed by the oxygen molecules present. CO.sub.2
and other gases, on the other hand, will absorb only a negligible amount
of energy. Therefore, the intensity of the reflected visible beam, as
determined by the visible detector 74, when compared to the known
intensity of the incident beam, will correspond accurately to the partial
pressure of oxygen in the absorption chamber and bloodstream. Partial
pressure of gases is displayed or recorded in units of mmHg.
The output signals of the detectors will contain information relating not
only to the intensities of reflected light, but also to blood pressure and
pulse rate. These data then enter the electronic processing system,
illustrated in FIG. 4, previously described.
FIG. 5 depicts, in a very general fashion, the gross signal that may be
obtained from an oxygen sensor of the type described, the ordinate
indicating increasing dissolved oxygen, partial pressure, in the blood,
increasing upwardly, the abscissa indicating time, from an arbitrary zero
starting point, in seconds, increasing to the right. As the partial
pressure of oxygen in the blood increases (in the course of graph of FIG.
5 the increase being very rapid simply to illustrate the type of signal
output) the absorption by the oxygen in the sensor chamber increases, thus
decreasing the intensity of the output signal. This gross decrease in
signal is depicted by the sharp downward turn of the output signal curve,
followed by a levelling as the oxygen partial pressure stabilizes and then
by a sharp decrease accompanied by a rapid, shallow pulse at the right of
the figure. The pulse rate and pressure is carried on the signal in the
form of a more rapid amplitude modulation component which is effectively
averaged electronically when considering the oxygen partial pressure
signal. The relative magnitude of the pulse and partial pressure signals
depends upon the geometry of the sensor and may be predetermined at any
desired ratio by making the chamber longer and the membrane smaller to
increase the partial pressure to pulse signal ratio or by making the
membrane larger and the chamber smaller to increase the pulse to partial
pressure signal ratio.
FIG. 6 is short time period depiction of a signal of the type depicted in
FIG. 5 except that the pulse to partial pressure ratio is very much higher
than that ratio in FIG. 5, simply to illustrate the manner in which the
pulse rate-blood pressure data are carried by the signal. In FIG. 6, the
partial pressure component is ignored because of the short time duration,
the entire figure representing only about two seconds, and to focus upon
the pulse rate-blood pressure data. The signal is in the form of a
modulated AC, the AC component resulting from the optical multiplexer, the
amplitude modulation resulting from the distension of the membrane by the
pulsation pressure in the blood vessel in which the catheter dwells during
use. In practice, the pulse rate is read directly, e.g. 83 pulses per
minute, and the pressure is converted electronically to correspond to the
blood pressure as determined by the conventional sphygmometer, e.g.
130/95, the conversion factor being determined empirically.
As pointed out before, the invention resides in the application of
absorption spectrometry to the in vivo determination of oxygen and carbon
dioxide, or other gases, in blood and, more particularly in the design and
operation of the catheter and optical system and not in the manner or
means for electronically processing and displaying the output signal.
Considerable variation in the precise manner and apparatus in which the
invention is embodied is contemplated without departing from the concept
of the invention of the scope of the invention as defined in the claims,
it being immaterial to the invention that any particular method or means
of electronic signal processing and display is used. It is, accordingly,
the intent that the claims which follow be read in light of and
consistently with the scope and nature of the inventive concept and the
manner in which that concept is utilized and not upon the merely exemplary
embodiment by which the invention is depicted and described hereinbefore.
REFERENCES CITED IN THE SPECIFICATION
The following references, and those specifically referred to in the
specification, are incorporated herein as if fully set forth.
1. U.S. Pat. No. 3,249,105, Polanyi, May 3, 1966.
2. U.S. Pat. No. 3,273,447, Frank, Sept. 20, 1966.
3. U.S. Pat. No. 3,791,376, Rybak, Feb. 12, 1974.
4. U.S. Pat. No. 3,123,066, Brumley, Mar. 3, 1964.
5. U.S. Pat. No. 3,136,310, Meltzer, June 9, 1964.
6. U.S. Pat. No. 3,498,286, Polanyi et al, Mar. 3, 1970.
7. U.S. Pat. No. 3,814,081, Mori, June 4, 1974.
8. U.S. Pat. No. 3,822,695, Takayama, July 9, 1974.
9. U.S. Pat. No. 3,847,483, Shaw et al, Nov. 12, 1974.
10. U.S. Pat. No. 3,983,864, Sielaff et al, Oct. 5, 1976.
11. U.S. Pat. No. 3,952,730, Key, Apr. 27, 1976.
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