U.S. patent number 3,858,573 [Application Number 05/377,758] was granted by the patent office on 1975-01-07 for alveolar gas trap and method of use.
This patent grant is currently assigned to SAID Ryan, by said Williams. Invention is credited to Donald F. Ryan, Allan N. Williams.
United States Patent |
3,858,573 |
Ryan , et al. |
January 7, 1975 |
ALVEOLAR GAS TRAP AND METHOD OF USE
Abstract
An alveolar gas trap includes a small tubular reservoir having
check valves at opposite ends and a mouthpiece so that when a
person exhales through the mouthpiece, the exhalation gasses pass
through the reservoir to the ambient with the last or alveolar gas
being collected in the reservoir.
Inventors: |
Ryan; Donald F. (Lombard,
IL), Williams; Allan N. (Griffith, IN) |
Assignee: |
SAID Ryan, by said Williams
(N/A)
|
Family
ID: |
23490405 |
Appl.
No.: |
05/377,758 |
Filed: |
July 9, 1973 |
Current U.S.
Class: |
600/543;
73/863.71; 73/863.86; 128/205.12 |
Current CPC
Class: |
A61B
5/097 (20130101); G01N 33/497 (20130101) |
Current International
Class: |
A61B
5/097 (20060101); A61B 5/08 (20060101); G01N
33/483 (20060101); G01N 33/497 (20060101); A61b
010/00 (); G01n 001/22 () |
Field of
Search: |
;128/2R,2C,2.07,2.08
;73/421.5R,23 ;23/254R |
References Cited
[Referenced By]
U.S. Patent Documents
Foreign Patent Documents
Primary Examiner: Gaudet; Richard A.
Assistant Examiner: Cohen; Lee S.
Attorney, Agent or Firm: Patnaude; Edmond T.
Claims
What is claimed is:
1. An alveolar gas trap for obtaining a sample of alveolar gas from
a person, comprising
means defining a gas reservoir having a volume equal to no greater
than one hundred cubic centimeters,
a mouthpiece for disposition in said person's mouth,
a first one-way check valve mounted in proximity to said mouthpiece
and connected between said mouthpiece and said reservoir,
said means defining a gas reservoir being mounted directly to said
mouthpiece with said check valve opening directly into said
reservoir so that all of the gas passing through said check valve
enters said reservoir,
a second one-way check valve connected between said reservoir and
the ambient for passing gas from said reservoir to the ambient,
said valves being self biased into a closed position with a
sufficiently low force so as to be opened by the normal exhalation
pressure of said person,
a sampling port opening into said reservoir between said check
valves, and
a valve connected to said port for controlling the removal of gas
from said reservoir.
2. An alveolar gas trap, according to claim 1, wherein said means
defining said reservoir comprises
a tube, and
said check valves are positioned at respectively opposite ends of
said tube, whereby air flow is through said tube from one end to
the other during exhalation.
3. An alveolar gas trap, according to claim 2, wherein said check
valves open at a pressure differential of less than one centimeter
of water.
4. An alveolar gas trap according to calim 1 wherein said reservoir
has a volume no greater than about 50 cubic centimeters.
5. An alveolar gas trap according to claim 1, wherein
said means defining said reservoir is a straight, transparent
tube,
said mouthpiece is a tubular member aligned with said transparent
tube and to which said transparent tube is mounted,
said check valves being positioned at opposite ends of said tube,
and
said valve being mounted directly on said tube.
Description
The present invention relates in general to an apparatus and method
of collecting alveolar gas samples from human beings and to the
normal use of such samples for making cardiopulmonary analyses.
Prior to the present invention, it had been both difficult and
costly to collect a sample of alveolar air, and the samples
actually collected did not result in accurate measurements. One
such attempt to obtain an alveolar air sample employed a Douglas
bag in which the expired gas over a number of breaths was
collected. However, anatomical variances between individuals make
it impossible to determine the actual alveolar gas concentration
from the mean expired sample so collected. Another method which has
been used in the prior art employs a servo-electric valve which
operates on a fixed time basis to select the alveolar gas from the
total expired gas in a single breath. Not only is such equipment
costly, but since any change in the ratio of inspiratory to
expiratory time changes the sample, the sample is easily taken at
the wrong point in the breathing cycle with resulting erroneous
readings.
We have recognized, however, that if a true alveolar air sample
could be derived from the gas exhaled by the patient,
cardiopulmonary analyses could be greatly expedited with minimum
body invasion, and could provide accurate cardiopulmonary
measurements not heretofor obtained except over long periods of
time with substantial patient duress. At the present time, such
measurements, as for example, cardiac output, oxygen consumption,
carbon dioxide production and respirartory quotient can only be
determined with the use of expensive, complicated and sophisticated
equipment.
OBJECTS OF THE INVENTION
Therefore, a principal object of the present invention is to
provide a new and improved method and means for obtaining an
alveolar gas sample from respiratory gasses.
Another object of this invention is to provide a new and improved
method of making cardiopulmonary measurements using alveolar gas
samples.
A further object of this invention is to provide a new and improved
method for determining the overall efficiency of a patient's
cardiopulmonary system.
SUMMARY OF THE INVENTION
Briefly, there is provided in accordance with one aspect of the
present invention, a device through which a patient exhales and
which automatically separates and traps a sample of the alveolar
gas from the total respiratory gasses. The device incorporates a
relatively small gas reservoir on opposite sides of which low
pressure, positive sealing check valves are located. As the patient
exhales through the device, the respiratory gasses pass directly
through the device to the ambient, with the final small amount of
the expired gas being trapped in the reservoir compartment. Since
the alveolar air is the last to leave the lungs during normal
exhalation, the gas which is trapped in the reservoir is an
accurate sample of alveolar air from which the oxygen and carbon
dioxide pressures can be readily determined in a conventional
blood-gas analyzer. As is explained in greater detail hereinafter,
these partial pressures in combination with samples of arterial and
venous blood taken substantially simultaneously with the alveolar
gas sample permit the rapid calculation in a normal manner of
oxygen consumption and carbon dioxide production as well as what we
term the "Index number of cardiopulmonary disability." In addition,
calculations of shunt ratio, cardiac output, physiological dead
space, respiratory quotient, ventilation perfusion ratio, mitral
valve flow, alveolor ventilation and total blood volume can be
readily performed using the alveolar air sample. Using the method
and apparatus of the present invention, all of these measurements
can be completed within about fifteen minutes, as compared to the
previous minimum of about two to three days if the physiological
condition of the patient would actually permit it.
Further objects and advantages and a better understanding of the
invention may be had from the following detailed description taken
in connection with the accompanying drawings, wherein:
FIG. 1 is an elevational view of the alveolar gas trap of the
invention in use; and
FIG. 2 is a longitudinal section of the alveolar gas trap shown in
FIG. 1.
DETAILED DESCRIPTION OF THE INVENTION
Referring now to the drawing, and particularly to FIG. 1 thereof,
an alveolar gas trap 10 is there shown with the mouthpiece portion
11 in the mouth of a patient 12. The trap is both small in size and
light in weight so as not to be uncomfortable to the patient who
simply breathes in the normal manner, inhaling through the nostrils
and exhaling through the mouth and thus through the alveolar gas
trap 10.
As best shown in FIG. 2, the gas trap 10 includes the tubular
mouthpiece 11 in which a check valve 13 is mounted. The valve 13 is
a light, flexible disc 14, suitably formed of rubber and overlying
an annular valve seat 15 mounted to the mouthpiece tube 11. The
disc 14 has a centrally disposed post 16 which is secured in a
mounting ring 17 connected to the main body of the seat member 15
by a spider made up of a plurality of spaced apart radial arms
18.
The mouthpiece tube 11 sealably extends into one end of a
transparent plastic tube 19 and an exhaust tube 22 sealably extends
into the other end of the tube 19. A check valve 23 is mounted in
the tube 22 and is identical in construction to the inlet check
valve 13 and includes a flexible valve disc 24 overlying an annular
valve seat 25. The valves 13 and 23 should operate at low pressure
differentials of less than one centimeter of water pressure and
must provide a good hermetic seal at a substantial zero pressure
differential. We have found that a light silicone spray applied to
the valving surfaces of the rubber discs 14 and 24 provides
satisfactory results.
The space within the tube 19 between the valves 13 and 23 thus
constitutes a reservoir in which the alveolar gas is trapped. While
the size of the reservoir is not critical, it must have a
substantially smaller volume than that of a normal exhalation tidal
volume. In a normal adult person, there is between 100 and 200 cc
of alveolar air in the lungs upon inhalation. We have successfully
used a reservoir size of thirty-one cubic centimeters. Since the
normal tidal volume for an adult is in the range of about 400 cc to
800 cc, the gas trapped in the reservoir is less than the last ten
percent of the expired gas, and less than one-third of the alvoelar
air. Since the gas passing through the tube 19 makes a
substantially clean sweep, there is only a negligible amount of
turbulence and mixing of the earlier expired gas from the
anotomical dead spaces with the alveolar gas.
A sampling valve assembly 28 is mounted to the tube 19 and is used
for extracting a gas sample from the reservoir in the tube 19. The
assembly 28 includes a tubular body 29 having a necked down end
portion 30 which extends a short distance into the tube 19 through
a hole 31 in the wall thereof. The end portion 30 is suitably
sealed to the tube 19 to prevent escape or contamination of the gas
trapped in the reservoir. A valve member 33 is rotatably mounted in
the body 29 and has a flat 34 provided on one side for opening an
outlet port 35 in the side of the body 29. A flexible tube is
connected to the outlet port 35 for coupling it to a bloodgas
analyzer. A knob 38 is provided at the distal end of the valve
member 33 for rotating it between the open position shown in FIG. 2
wherein the flat 34 is opposite the port 35 and a closed position
wherein the member 33 sealably engages the wall portion of the body
29 surrounding the port 35 to close it. The position of the valve
member 33 is indicated by an elongated, pointed flange 39 which is
aligned with the flat 34. A pair of spring fingers 40 depend from
the flange and fit under an annular flange at the top of the body
29 to hold the valve member in place therein.
OPERATION OF GAS TRAP
In use, the patient is asked to breath normally by inhaling through
the nose and exhaling through the mouth. With the valve 28 closed,
the mouthpiece 11 of the trap is then placed in the patient's mouth
as shown in FIG. 1 and breathing continued with the patient's lips
sealingly engaging the mouthpiece so that the entire respiratory
breath passes into the trap. The exhaust gas pressure is sufficient
to open both the inlet and exhaust check valves until exhalation
ceases, at which time both valves close to trap the last or
alveolar portion of the exhaust gasses from the lungs. Because of
the construction of the trap 10, there is little turbulence in the
reservoir which could cause mixing of the alveolar gas and the
previously exhaled gasses from the anotomical dead space and other
areas of the lungs. Moreover, since the capacity of the reservoir
is but a small fraction of the tidal volume, i.e. quantity of gas
exhaled in each breath, the gas thus trapped in the reservoir is,
for all practical purposes, only alveolar gas.
A small portion of say one-half a cubic centimeter of the trapped
sample is pumped from the reservoir through the valve 28 at a
pressure less than the biasing forces on the inlet and outlet
valves and is supplied to any suitable device, such for example, as
a blood gas analyzer to measure the partial pressures of the oxygen
and carbon dioxide in the alveolar gas sample.
Since, in order to maintain a steady state within the respiratory
system, oxygen consumption must be equal to oxygen uptake and
carbon dioxide production must be equal to carbon dioxide release,
these values may be calculated by taking arterial and venous blood
samples substantially simultaneously with the taking of the
alveolar gas sample. We have determined that the blood samples
should be taken at as nearly the same time as the alveolar gas
sample is obtained, but at least within one minute thereafter.
Ordinarily, there is substantial pain associated with the taking of
the arterial blood sample, and since a person's reaction to pain
affects the alveolar gas, it is important that the gas sample not
be taken after the arterial blood sample is taken, or the data will
be erroneous. Other well-known and easily measured factors, such as
tidal volume, respiratory rate, approximate anatomical dead space
and barometric pressure are also used in these calculations. The
various cardiopulmonary measurements or indices, referred to above
may be readily calculated from the equations given below wherein
the following well-known terms are used:
Q.sub.t " cardiac output (ml/min)
Q.sub.s = pulmonary physiological shunt (ml/min)
P.sub.e 0.sub.2 = expired alveolar oxygen tension (mm Hg)
P.sub.e C0.sub.2 = expired alveolor carbon dioxide tension (mm
Hg)
P.sub.a 0.sub.2 = arterial blood oxygen tension (mm Hg)
P.sub.a C0.sub.2 = arterial blood carbon dioxide tension (mm
Hg)
P.sub.v 0.sub.2 = mixed venous blood oxygen tension (mm Hg)
P.sub.v C0.sub.2 = mixed venous blood carbon dioxide tension (mm
Hg)
P.sub.i 0.sub.2 = inspired air oxygen tension (mm Hg)
P.sub.i C0.sub.2 = inspired air carbon dioxide tension (mm Hg)
C'.sub.c 0.sub.2 = alveolar oxygen content per 100 ml
C.sub.v 0.sub.2 = mixed venous oxygen content per 100 ml
C.sub.a 0.sub.2 = arterial oxygen content per 100 ml
S.sub.e 0.sub.2 = alveolar oxygen saturation
S.sub.a 0.sub.2 = arterial oxygen saturation
S.sub.v 0.sub.2 = mixed venous oxygen saturation
Vo.sub.2 = oxygen consumption (ml/min)
Ads = anatomical dead space
Tv = average tidal volume
F = respiratory rate
P.sub.b = barometric pressure
V.sub.c O.sub.2 = CO.sub.2 production
R = respiratory quotient
V.sub.a = alveolar ventilation (1/min)
F.sub.a CO.sub.2 = concentration of CO inalveolar gas
Q.sub.c = blood flow through pulmonary capilaries
CvCO.sub.2 = CO.sub.2 concentration in venous blood
C.sub.c CO.sub.2 = CO.sub.2 concentration in alveolar air
C.sub.a O.sub.2 = O.sub.2 concentration in arterial blood
Mvf = mitral valve flow
The following equations are used to calculate the various
measurements or indices used in making a cardiopulminary
diognosis.
Shunt equation
q.sub.s /Q.sub. t = C'cO.sub.2 - C.sub.a O.sub.2 /C' cO.sub.2 -
C.sub.v O.sub.2
O.sub.2 consumption
vo.sub.2 = (p.sub.i O.sub.2 - PAO.sub.2 /P.sub.b - 47) .times. (TV
- ADS) .times. F
Cardiac output
q.sub.t = 100 VO.sub.2 /C.sub.a O.sub.2 - C.sub.v O.sub.2
Physiological deadspace
v.sub.d = V.sub.t (P.sub.a CO.sub.2 - P.sub.a CO.sub.2 /P.sub.a
CO.sub.2)
Co.sub.2 production
co.sub.2 = (p.sub.a co.sub.2 - p.sub.i CO.sub.2 /P.sub.b - 47) (TV
- ADS) (F)
Respiratory quotient
r = vco.sub.2 /vo.sub.2
alveolar ventilation
v.sub.a = vco.sub.2 /faco.sub.2
approximate effective blood volume
bv = vo.sub.2 /(c.sub.a O.sub.2 - C.sub.v O.sub.2) .times. 100
Ventilation/perfustion ratio
v.sub.a /q.sub.c = R.sub.x 0.863 (C.sub.A O.sub.2 - C.sub.vo2)
/P.sub.A CO.sub.2
Mitral valve flow
mvf = cardiac output (cc)/Rate (Min) .times. average duration of
diastole (sec)
In order to provide a repeatable measurement of the cardiopulminary
disability of a patient, we have found that the "Index Number of
cardiopulminary disability" is quickly and easily determined from
the true alveolar gas sample. The following equation may be used to
calculate this number:
I = C.sub.a CO.sub.2 - C'.sub.c CO.sub.2
Extensive testing of patients having healthy and impaired
cardiopulminary systems indicated that an Index Number of about two
or less indicates a normal cardiopulminary function with the degree
of impairment increasing in proportion to the value of the index
number over two. For example, an index number of 13 or more shows
extremely poor cardiopuliminary function with a consequent life
expectancy of a few months or less.
While the present invention has been described in connection with a
particular embodiment thereof, it will be understood that those
skilled in the art may make many changes and modifications without
departing from the true spirit and scope thereof. Accordingly, the
appended claims are intended to cover all such changes and
modifications as fall within the true spirit and scope of the
present invention.
* * * * *