U.S. patent number 3,927,670 [Application Number 05/321,140] was granted by the patent office on 1975-12-23 for automatic respiratory gas monitoring system.
Invention is credited to John W. Ashworth, III, Walter Blumenfeld, R. Adams Cowley, Charles McCluggage, Stephen Z. Turney, Samuel Wolf.
United States Patent |
3,927,670 |
Turney , et al. |
December 23, 1975 |
Automatic respiratory gas monitoring system
Abstract
An automated system monitors and records vital signs and
respiratory gases of each of several patients in an intensive care
center by time-sharing the use of a mass spectrometer and hybrid
instrumentation under control of an electronic programmable
calculator. Automatic measurement is performed and recorded on high
and low levels corresponding to inspiratory and peak expiratory
values of O.sub.2 and peak expiratory CO.sub.2. Sampled gas
waveforms are counted for respiratory rate and the respiratory
quotient is computed for each patient. Respiratory gas flow is
automatically measured and CO.sub.2 production and O.sub.2
consumption are computed and recorded. This invention is equally
applicable to analysis of gases other than respiratory gases.
Inventors: |
Turney; Stephen Z.
(Lutherville, MD), Blumenfeld; Walter (Bowie, MD),
Cowley; R. Adams (Baltimore, MD), Wolf; Samuel
(Baltimore, MD), McCluggage; Charles (Baltimore, MD),
Ashworth, III; John W. (Towson, MD) |
Family
ID: |
23249345 |
Appl.
No.: |
05/321,140 |
Filed: |
January 5, 1973 |
Current U.S.
Class: |
600/532;
73/23.3 |
Current CPC
Class: |
A61B
5/08 (20130101); A61B 5/083 (20130101); A61B
5/082 (20130101) |
Current International
Class: |
A61B
5/083 (20060101); A61B 5/08 (20060101); A61B
005/08 () |
Field of
Search: |
;128/2.07,2.08,2.1R,2C,DIG.29 ;73/23.1,421.5R,422,423 |
References Cited
[Referenced By]
U.S. Patent Documents
Other References
Osborn, J. J. et al., Surgery, December 1968, Vol. 64, No. 6, pp.
1057-1070. .
Journ. of Assoc. for Advance. of Med. Instrumentation, February
1972, Vol. 6, No. 1, pp. 65-69..
|
Primary Examiner: Howell; Kyle L.
Attorney, Agent or Firm: Finch; Walter G.
Claims
What is claimed is:
1. A system for monitoring respiratory gases, which comprises:
means for withdrawing respiratory gases from the airway of at least
one patient,
means for rapidly analyzing the withdrawn gases and for developing
analog waveforms in response to the analyzation of the withdrawn
gases where the waveforms are representative of fractional
concentrations of the withdrawn gases,
means responsive to the developed analog waveforms for developing
voltage levels proportional to the maxima and minima of the
developed analog waveforms where the maxima and minima of the
waveforms are representative of monitored values of inspired and
expired respiratory gases, and
means responsive to the developed voltage levels for displaying in
visual form an indication of the maxima and minima values.
2. The monitoring system as set forth in claim 1 which further
comprises means for automatically controlling the withdrawing of
the patients respiratory gases at selected intervals.
3. The monitoring system as set forth in claim 1 wherein said
withdrawing means further comprises:
means for withdrawing the respiratory gases of a plurality of
patients to sample the respiratory gases, and
means for connecting the withdrawn gases of each patient,
independently of the withdrawn gases of the remaining patients, to
the rapid analyzing means.
4. The monitoring system as set forth in claim 3 which further
comprises means for automatically controlling the connecting means
to selectively connect the withdrawn gases of each patient to the
rapid analyzing means so that the withdrawn gases of only one
patient are connected to the rapid analyzing means at any given
instant.
5. The monitoring system as set forth in claim 4 which further
comprises means for feeding a calibrating gas to the rapid
analyzing means to calibrate the analyzing means prior to analyzing
of the respiratory gases of each patient.
6. The monitoring system as set forth in claim 1 which further
comprises means responsive to the development of an O.sub.2
waveform from the rapid analyzing means for counting the
respiratory rate of the patient whose respiration gases are being
sampled and monitored.
7. The monitoring system as set forth in claim 1 wherein the
analyzing means is a mass spectrometer.
8. The monitoring system as set forth in claim 1 which further
comprises means for simultaneous measurement of respiratory gas
flow.
9. The monitoring system as set forth in claim 8 wherein the means
for measurement of respiratory gas flow is a pneumotachometer.
10. The monitoring system as set forth in claim 8 wherein the means
for measuring respiratory gas flow is a spirometer.
11. A gas monitoring system, which comprises:
a plurality of gas sampling lines each of which is connectable to
the airway of a respective one of a plurality of gas systems whose
gases are to be sampled, the systems being independent of each
other,
means for rapidly analyzing the sampled gases and for developing
waveforms in response to the analyzation of the sampled gases,
means connected in each of the sampling lines for opening and
closing the lines to permit and prevent, respectively, flow of the
sampled gases therethrough,
means for coupling each of the sampling lines to the analyzing
means,
means for selectively operating the opening and closing means to
permit the selective linking of each of the sampling lines with the
analyzing means independent of the remaining sampling lines,
and
means responsive to the developed waveforms for developing signal
levels porportional to and representative of monitored values of
the sampled gases.
12. A gas monitoring system as recited in claim 11, which further
comprises means responsive to the developed signal levels for
displaying in visual form an indication of such levels as a
representation of the monitored values of the sampled gases.
13. A gas monitoring system as recited in claim 11, which further
comprises means for automatically and periodically controlling the
operating means to permit automatic monitoring of each of the
plurality of gas systems independent of the remaining gas
systems.
14. A gas monitoring system as recited in claim 13 wherein the
controlling means includes:
means for selectively scanning the opening and closing means,
and
means for producing step command signals to operate the scanning
means in a predetermined manner to monitor the sampling lines as
desired.
15. A gas monitoring system as recited in claim 11, wherein the
analyzing means is a mass spectrometer.
16. A gas monitoring system as recited in claim 11 wherein the
opening and closing means includes a plurality of valves each of
which is connected serially in a respective one of the sampling
lines.
17. A gas monitoring system as recited in claim 16, wherein:
the operating means includes a plurality of solenoids each of which
is connected to a respective one of the valves, and
electrical control means for selectively operating the solenoids
independently of the remaining solenoids to permit selection of one
of the sampling lines.
18. A gas monitoring system as recited in claim 17, which further
comprises means for automatically operating the electrical control
means in a predetermined manner to selectively operate the
solenoids in a selected sequence so that sampled gases of the
plurality of systems are fed to the analyzing means in a
predetermined sequential manner.
19. A gas monitoring system as recited in claim 11 wherein the
developed waveforms are analog waveforms and the signal levels
developing means includes a plurality of analog filters which
produce steady voltage levels proportional to maxima and minima
levels of the waveforms developed by the analyzing means.
20. A gas monitoring system as recited in claim 11 wherein the
analyzing means includes means for analyzing sampled gases which
include inspired O.sub.2 gases and expired CO.sub.2 gases, and the
waveforms developed by the analyzing means are analog waveforms
representative of fractional concentrations of the inspired O.sub.2
gases and expired CO.sub.2 gases.
21. A gas monitoring system as recited in claim 20 wherein the
signal levels developing means includes a plurality of signal
conditioners which in response to the analog waveforms developed by
the analyzing means develop signals representative of fractional
concentrations of inspired O.sub.2 gases, end-expired O.sub.2 gases
and expired CO.sub.2 gases.
22. A gas monitoring system as recited in claim 21 wherein the
signals developed by the signal conditioners are in analog form,
and which further comprises:
means responsive to the analog signals developed by the plurality
of signal conditioners for converting the analog signals to digital
signals representative of fractional concentrations of inspired
O.sub.2 gases, end-expired O.sub.2 gases and expired CO.sub.2
gases, and
means for scanning the plurality of signal conditioners and for
selectively coupling the analog signals of the signal conditioners
to the converting means.
23. A gas monitoring system as recited in claim 22, which further
comprises means for automatically controlling the operation of the
scanning and selective coupling means to permit the monitoring of
the signal conditioners in a predetermined manner.
24. A gas monitoring system as recited in claim 21 wherein each of
the plurality of signal conditioners are analog filters which
produce steady voltage levels proportional to maxima and minima
levels of the waveforms developed by the analyzing means.
25. A gas monitoring system as recited in claim 20, which further
comprises means for computing the respiratory rate of each of the
plurality of gas systems in response to the expired CO.sub.2
fractional concentration waveforms developed by the analyzing
means.
26. A gas monitoring system as recited in claim 25, wherein the
computing means includes:
a circuit operable at specific levels of each expired CO.sub.2
waveform for producing an output pulse representative of each
respiration of the gas system being analyzed,
a binary counter responsive to each pulse produced by the circuit
for producing successive counts in binary digital form, and
a summing circuit responsive to the binary digital counts of the
counter for summing the counts and developing an analog voltage
level representative of the respiratory rate of the gas system
being analyzed.
27. A gas monitoring system as recited in claim 11 which further
comprises means located in each of the sampling lines of each of
the gas systems for measuring the flow of respiratory gases through
the sampling line.
28. A gas monitoring system as recited in claim 11 which further
comprises means for indicating which sampling line is linked to the
analyzing means at any given instant.
29. A gas monitoring system as recited in claim 11 wherein the
signal levels developed by the signal levels developing means are
in analog form and which further comprises means responsive to the
developed analog signal levels for converting the analog levels to
digital signals representative of the monitored values of the
sampled gases.
Description
FIELD OF THE INVENTION
This invention relates generally to respiratory gas monitoring
systems, and more particularly it pertains to a system for
automatically monitoring the respiratory gases of each of many
patients and thereafter recording various parameters associated
with the respiratory gases and vital signs of each of the
patients.
DISCUSSION OF PROBLEM AND PRIOR ART
The monitoring of respiratory gases can be of great assistance to a
physician treating the critically ill. Unfortunately, instruments
capable of doing this job economically in clinical use have
heretofore been unavailable. Automated systems are available for
the acquisition of data from patients in intensive care units and
usually depend upon medium to large scale computers for timing,
control and computation. However, the complexity and cost of such
systems have limited their practical application.
With a rapidly increasing population and the violent complexities
encountered in life today, the number of serious and complicated
personal injuries requiring treatment are increasing and getting
worse. In many instances, a number of such injured patients require
constant surveillance and attention simultaneously. The cost for a
medical team and equipment that would be required for each such
seriously injured patient would be prohibitive.
Consequently, there is a need for a simplified, economical system
which will permit a reasonably limited number of medical personnel
to monitor the vital signs and respiratory gases of a number of
critically ill patients at frequent intervals.
SUMMARY OF THE INVENTION
It is an object of this invention, therefore, to provide a system
for economically and automatically monitoring respiratory
gases.
Another object of this invention is to provide a system for
monitoring the vital signs of several patients with a time-shared
system.
To provide a simplified system for economically monitoring
respiratory gases of several patients on a time-shared basis and
thereafter recording data of vital signs is yet another object of
the invention.
BRIEF DESCRIPTION OF THE DRAWINGS
Other objects and attendant advantages of this invention will
become more readily apparent and understood from the following
detailed specification and accompanying drawings in which:
FIG. 1 is a diagrammatical representation of the floor plan layout
of a multi-bed intensive care unit with respiratory gas monitoring
facilities;
FIG. 2 is a block diagram of the various component parts of an
automatic respiratory gas monitoring system embodying certain
principles of the invention;
FIG. 3 is a view showing a facility for sampling respiratory gases
of a patient;
FIG. 4 is a view showing alternate embodiments of endotracheal
attachment devices for obtaining the sampling of respiratory
gases;
FIG. 5 is a schematic of a solenoid system which forms a portion of
a gas sampling manifold and is used for selectively connecting
patient respiratory-gas and calibration-gas lines to the monitoring
and recording system of FIG. 2;
FIG. 6 is a schematic of a relay and switch which also forms a
portion of the gas sampling manifold and is used for selective
control of the solenoid system of FIG. 5;
FIG. 7 is a schematic of a hybrid circuit which forms a portion of
the system of FIG. 2 and which counts the CO.sub.2 waveforms as a
measure of respiratory rate;
FIG. 8 is a graph of the frequency distribution of the absolute
value of the rate of change of the alveolar-arterial O.sub.2
gradient with respect to time; and
FIG. 9 is a graph of the frequency distribution of the absolute
value of the rate of change of the arterial-alveolar CO.sub.2.
DETAILED DESCRIPTION
Referring to FIG. 1, there is illustrated an intensive care unit or
trauma center 21 which includes a plurality of patient-bed
locations numbered bed No. 1 through bed No. 12. The bed locations
are disposed about a centrally located monitoring station 22 which
includes the necessary facilities for monitoring respiratory gas
samples of patients in the bed locations.
The monitoring facilities include a gas sampling manifold 23 which
is linked to each patient-bed location by gas sampling lines 24
located in conduits beneath the floor of the trauma center 21. A
data acquisition unit 25 controls the gas sampling manifold 23 to
feed respiratory gases of successively sampled patients to a mass
spectrometer 26 which rapidly analyzes the waveform of the gas
samples and develops analog waveforms in response thereto. The mass
spectrometer 26 is a rapid gas analyzer such as, for example, a
model MMS-8 available from Scientific Research Instruments
Corporation of Baltimore, Md.
The analog waveforms from the mass spectrometer 26 are conditioned
by analog filters for high and low levels corresponding to
inspiratory and peak expiratory values of O.sub.2 and peak
expiratory values of CO.sub.2. CO.sub.2 waveforms are counted for
respiratory rate and the respiratory quotient is computed.
Respiratory gas flow is measured by an electronic air flow
transducer 52 (FIGS. 3 and 4) situated at the patients airway, such
as a Fleisch pneumotachometer or an ultrasonic spirometer. The
combined data from the mass spectrometer 26 and air flow transducer
52 enables a digital calculator 40 (FIG. 2) to automatically
compute CO.sub.2 production and O.sub.2 consumption.
The waveforms developed by the mass spectrometer 26 are ultimately
coupled to the data acquisition unit 25 which controls central
physiologic monitors to display, for visual observation, the key
recorded information relating to respiratory gases and vital signs
of the patients in bed No. 1 through bed No. 12.
A nurses' station is located amongst the sampling, analyzing and
monitoring facilities to permit a limited number of medical
personnel to maintain the trauma center 11.
Referring to FIG. 3, the airway of an intubated patient is
connected to a respirator 27 by use of a linking section 28 and an
endotracheal tube 29. A sample port 30 is connected to the linking
section 28 and facilitates the sampling of the respiratory gases
necessary for the monitoring procedure. A vinyl tube 31 of
capillary size is connected between the sample port 30, at one end
thereof, and one end of a copper tube 32 at the other end thereof.
The vinyl tube 31 and the copper tube 32 combine to form the gas
sampling line 24. The other end of the copper tube is connected to
the gas sampling manifold 23. The copper tube 32 is 1/8 inch O.D.
and is about 50 feet in length. The vinyl tube 31 is about 6 feet
in length. The lengths of the tubes 31 and 32 and the fittings used
to make the various interconnections are designed to provide
optimum results in a smooth flow of the sampled gases therethrough.
A similar arrangement attaches to a mouth piece or face mask to
facilitate measurements of extubated patients.
Referring to FIG. 4, there is illustrated two embodiments 28a and
28b of the linking section 28 (FIG. 3) which are somewhat similar
except in the portion which is connected directly to the respirator
27 (FIG. 3). The embodiment 28a has a forked ventilator. The
embodiment 28b has a single opening for receiving a continuous flow
of O.sub.2 and air and also is formed with a valveless port. Each
embodiment 28a and 28b has a pneumotachometer, such as the
transducer 52, attached thereto to measure the flow rate of gas
passing therethrough.
As illustrated in FIG. 5, the gas sampling manifold 23 includes 16
input lines, 12 of which are linked to the bed locations of bed No.
1 through bed No. 12. Three additional lines are connected to other
locations in the hospital for sampling gases from a hyperbaric
unit, a cardiac catheterization laboratory and a trauma operating
suite. The remaining input is connected to a gas calibration
facility 33 which includes a supply 34 of calibration gas (5%
CO.sub.2, 50% O.sub.2, 45% N.sub.2), a solenoid controlled shut-off
valve 35 and an open sample chamber 36.
Each of the 16 input lines to the manifold 23 is connected to a
three-way, solenoid-controlled valve 37. A normally open port of
each of the solenoid-controlled valves 37 is connected, for
cleaning purposes, to a hospital vacuum through an H.sub.2 O trap
38. The remaining valve arrangement permits selective passage of
sampled respiratory gases through the manifold 23 to the
spectrometer 26. The vacuum bypass feature also reduces the time
required for stabilization to new gas values when switching from
patient to patient during the gas sampling period.
Referring to FIG. 2, there is illustrated a block diagram of an
automatic respiratory gas monitoring system 39 embodying certain
principles of the invention. The system 39 includes a digital
calculator 40, such as, for example, a model 370 programmable
digital desk calculator available from Wang Laboratories of
Tewksbury, Mass. The calculator 40 is equipped with eight program
card readers which provide the necessary instructions for operating
the system 39.
The command signals are fed from the calculator 40 to an interface
41, such as, for example, a model 379-8 digital interface also
available from Wang Laboratories, which then disperses the command
signals to the selected facilities of the system 39.
The system 39 also includes the gas sampling manifold 23, which is
illustrated in FIG. 5, with manual selecting controls and
identified as unit 42. A bed scanner 43 responds to step commands
from the calculator 40 and interface 41 to select the particular
solenoid-controlled valve 37 (FIG. 5) and, therefore, a particular
gas sampling line 24. Instructions for the gas calibration
procedure come directly from the interface 41 to the unit 42.
Special sample and calibrate gas lines are also coupled to the unit
42 for purposes previously explained.
The sampled gases are fed to the spectrometer 26 for rapid
analyzing. The O.sub.2 and CO.sub.2 analog waveforms developed in
response thereto are fed to a hybrid waveform analyzer 44 where the
analog waveforms are conditioned for ultimate feeding to the
calculator 40. A high point signal conditioner 45 selects the peak
of a fractional concentration of the sampled O.sub.2 waveform
(FO.sub.2) and develops a signal which represents a fractional
concentration of the inspired O.sub.2 (FIO.sub.2).
A fractional concentration of the "valley" of the O.sub.2 waveform
(FO.sub.2) is fed to a low point signal conditioner 46 which
develops a signal corresponding to an approximation of end-expired
O.sub.2 fractional concentration (FAO.sub.2). Similarly, the peak
value of expired CO.sub.2 (FACO.sub.2) is measured by a high point
signal conditioner 47.
The signal conditioners 45, 46 and 47 are, for example, analog
filters available from Statham Instruments, Inc., of Oxnard, Calif.
The analog filters produce relatively steady voltage levels
proportional to the maxima and minima of the output waveforms of
the mass spectrometer 26.
The respiratory rate (R.R.) is computed by a tachometer or hybrid
circuit 48 in response to receiving a fractional concentration of
CO.sub.2 (FCO.sub.2). The circuit 48 is shown in detail in FIG.
7.
The respiratory airflow transducer 52 could be, for example an
ultrasonic spirometer model 1007 or model 1009, available from
Statham Instruments, Oxnard, Calif. It could also be, for example,
a Fleisch pneumotachometer which is also available from Statham
Instruments, Oxnard, Calif.
Under the control of step command signals from the interface 41, a
parameter scanner 49 scans the conditioners 45, 46 and 47 and the
hybrid circuit 48 to feed the respiratory rate, FACO.sub.2,
FAO.sub.2, and FIO.sub.2 signals to the interface. These analog
signals are then fed to a digital voltmeter 50 where
analog-to-digital conversion of the signals is accomplished. The
voltmeter 50 could be, for example, a model 4432 digital voltmeter
available from Dana Laboratories, Inc., of Irvine, Calif.
The digital signals are then fed through the interface 41 to the
digital calculator 40 whereat calculations are made of various
respiratory and vital signs information. This information is
displayed on a typewriter 51 for monitoring observations by the
medical team attending the trauma center 11.
The unit 42 includes a control circuit, as illustrated in FIG. 6,
for manual or automatic selection of the solenoid-controlled valves
37 (FIG. 5). A relay coil RI.sub.7 is controlled by momentary
manual closing of normally open switch S.sub.18 to place the
associated contacts a through i in the position shown. Also, manual
lamp I.sub.18 is lit. Normally open switches S.sub.1 through
S.sub.16 (only S.sub.1 through S.sub.6 shown) can then be manually
and selectively closed to energize associated relay coils RI.sub.1
through RI.sub.16, respectively. If for example, the relay coil
RI.sub.3 is energized, the solenoid SOI.sub.3 is energized and the
related valve 37 is controlled to permit respiratory gases of the
patient in bed No. 3 to be sampled and fed to the spectrometer 26
for sample processing. The lamp I.sub.3 is also lit to identify the
selected bed.
When normally closed switch S.sub.17 is momentarily opened, the
relay coil R.sub.17 is controlled to place the associated contacts
a through i in the other position. This conditions the control
circuit of unit 42 for automatic control by calibrate and bed
select commands from the interface 41 and the bed scanner 43. The
relay coils RI.sub.1 through RI.sub.16 can now be controlled
automatically and, if desired, sequentially.
The hybrid circuit 48 is illustrated in detail in FIG. 7 and
includes a Schmitt trigger which is fired at specific voltage
levels of each CO.sub.2 waveform input. The resulting pulse is fed
to the input of a binary counter composed of five J-K flip-flops.
The binary digital count is converted back to an analog voltage
level by a summing amplifier with gains proportional to the
magnitudes of the binary digits. In operation, the counter is reset
to zero, then counts expirations for 23 seconds. The count is then
read as an analog voltage and ultimately multiplied by 60/23 to
obtain breaths per minute.
The bed scanner 43 could, for example, be a multiple-deck stepping
switch with the associated stepping coil being controlled by the
calculator 40 through the interface 41. The stepping switch control
can thus facilitate the ultimate control of the solenoids SOI.sub.1
- SOI.sub.12 for the sequential gas sampling procedure through the
control circuit of FIG. 6 and the bed select commands from the
calculator 40.
The parameter scanner 49 could also be a decked stepping switch
with the associated stepping coil being controlled by the
calculator 40 through the interface 41. Four terminals of the
stepping switch are connected to the conditioners 45, 46 and 47 and
the hybrid circuit 48, respectively, to facilitate the feeding of
the various analog waveforms the digital voltmeter 50.
Each contact of one deck of the multiple deck stepping switch could
be connected to a different junction point between adjacent
series-connected resistors of a chain of series-connected resistors
which are connected to a potential source.
The number of junction points corresponds to the number of bed
locations with a different analog potential appearing at each
junction point to identify the selected bed location for patient
gas sampling. A single-pole, double-throw switch is connected
between each terminal of the stepping switch and the associated
junction point so that the terminal can be selectively connected to
ground if there is no patient located at the particular bed
location. The particular analog potential can be fed to the
calculator 40 for printout on the typewriter 51 to identify from
which patient the sampled gases are taken.
Other decks of the multiple deck switch could be connected to
transducers at bedside to pick up the patient's temperature, pulse
and other vital intelligence. This information is selectively fed
to the calculator 40 by use of additonal terminals on the parameter
scanner 49 and ultimately appears on the printout of the typewriter
51.
Under the automatic control of the program, the calculator 40 each
hour enters a sequence wherein the spectrometer 26 is placed in an
"operate" mode for a 2-minute warmup and stabilization period. Each
occupied bed is sampled sequentially for 20 seconds at 1 -minute
intervals. Prior to each bed reading, the calibrating gas is read
and corrections made for changes in calibration. Readings from the
analog signal conditioners 45, 46 and 47 and the hybrid circuit 48
which functions as the respiratory rate counter. Calculations are
made and printed out along with time, hour and minute, and bed
identification number.
The print-out includes:
a. maximum FCO.sub.2 (PACO.sub.2 and FACO.sub.2)
b. minimum FO.sub.2 (PACO.sub.2 and FAO.sub.2)
c. maximum FO.sub.2 (FIO.sub.2)
d. respiratory rate (R.R.), and
e. respiratory exchange ratio (R.sub.E),
where ##EQU1## f. tidal volume (V.sub.t) g. minute ventilation
(Ve)
h. CO.sub.2 production (VCO.sub.2)
i. O.sub.2 consumption (VO.sub.2)
In the above print-out display,
Fco.sub.2 is a fractional concentration of CO.sub.2 ;
Paco.sub.2 is the pressure of peak expired CO.sub.2 ;
Faco.sub.2 is the fractional concentration of peak expired CO.sub.2
;
Fo.sub.2 is a fractional concentration of O.sub.2 ;
Pao.sub.2 is the pressure of peak expired O.sub.2 ;
Fao.sub.2 is the fractional concentration of peak expired O.sub.2
;
Fio.sub.2 is the fractional concentration of peak inspired O.sub.2
; and
Pio.sub.2 is the pressure of peak inspired O.sub.2.
At the completion of the sampling sequence, the spectrometer 26 is
placed on standby status.
As previously noted, the calculator 40 may be overridden manually
by switch S18 which energizes relay coil R17 so that the switches
S.sub.1 through S.sub.16 can control the individual solenoid valves
SOI.sub.1 through SOI.sub.16, respectively, may be actuated at any
time for any length of time.
The calculator programming permits spot readings of any selected
sample line 24 at 1-minute intervals at the option of clinical
staff, in addition to automatically initiated hourly readings from
all patients in the unit. The data obtained in this spotreading
made is still automatically calibrated, calculated and printed as
in the hourly sequence.
There is shown in FIG. 8 the frequency distribution of the absolute
value of the rate of change, with respect to time, of the
alveolar-arterial oxygen (A-aO.sub.2) gradient which has a distinct
relationship to PAO.sub.2, as would be anticipated in patients with
large intrapulmonary shunts. This distribution was tabulated from
137 pairs of sequential measurements in 16 patients. The data were
restricted to sequential measurements such that PAO.sub.2 was not
altered more than 100 mm. Hg. during the interval between
measurements.
There is shown in FIG. 9 the frequency distribution of the absolute
value of rate of change in the arterial-alveolar CO.sub.2
(a-ACO.sub.2) gradient. The distribution is of a sample of 203
sequential pairs of readings from 15 patients. The data were
restricted to samples measured not more than 24 hours apart. A
large CO.sub.2 gradient is seen primarily with a large alveolar
dead space.
Obviously many modifications and variations of the present
invention are possible in light of the above teachings. It is,
therefore, to be understood that within the scope of the appended
claims the invention may be practiced otherwise than as
specifically described.
* * * * *