U.S. patent number 3,682,166 [Application Number 05/059,206] was granted by the patent office on 1972-08-08 for emergency percutaneous trans-tracheal high flow oxygen catheter-type resuscitator for restoration of breathing in non-breathing patients.
Invention is credited to Harvey Barry Jacobs.
United States Patent |
3,682,166 |
Jacobs |
August 8, 1972 |
EMERGENCY PERCUTANEOUS TRANS-TRACHEAL HIGH FLOW OXYGEN
CATHETER-TYPE RESUSCITATOR FOR RESTORATION OF BREATHING IN
NON-BREATHING PATIENTS
Abstract
An emergency percutaneous trans-tracheal high flow oxygen
resuscitator of the catheter type which restores breathing to a
non-breathing patient comprising a soft plastic catheter molded
from non-pyrogenic thermoplastic material such as polyethylene,
polytetrafluorethylene, polypropylene, polycarbonate or other
readily sterilized, orientable material which is precurved at its
long tubular bottom portion for proper positioning in the median
axis of the trachea after straight insertion by means of a
cooperating, interiorly positioned hypodermic needle through the
crico-thyroid membrane of the patient. The catheter has outwardly
projecting wing portions at the top collar portion, the collar
accommodating a suction tube or an oxygen tube after the needle is
removed. Suction aids in the exhale phase of ventilating the lungs.
Ventilating apparatus is provided for connection to the catheter.
The apparatus comprises cyclically operated valve means for
selectively connecting the catheter to a source of compressed
oxygenated gas or to a source of vacuum for inflation and deflation
in the breathing cycle. Other valve means are provided to vary the
ratio of inflation and deflation phases during a cycle. The
cyclically operated valve means are driven by air motor means
powered by the compressed gas. Another set of valves is provided
whereby the cyclically operated valve controlled conduit system is
bypassed and the catheter may be selectively connected to the
oxygenated gas or to the suction source by a manually operated
valve in accordance with the requirements of the condition of the
patient.
Inventors: |
Jacobs; Harvey Barry (Reston,
VA) |
Family
ID: |
22021484 |
Appl.
No.: |
05/059,206 |
Filed: |
July 29, 1970 |
Current U.S.
Class: |
128/205.19;
128/205.24; 128/207.29; 128/205.12; 128/207.14 |
Current CPC
Class: |
A61M
16/0465 (20130101); A61M 25/0606 (20130101); A61M
16/16 (20130101); A61M 25/00 (20130101); A61M
16/0452 (20140204); A61M 25/04 (20130101); A61M
16/00 (20130101); A61M 25/0668 (20130101); A61M
16/0472 (20130101) |
Current International
Class: |
A61M
16/00 (20060101); A61M 25/04 (20060101); A61M
16/04 (20060101); A61M 25/06 (20060101); A61M
25/02 (20060101); A61M 16/16 (20060101); A61M
16/10 (20060101); A61M 25/00 (20060101); A62b
007/00 () |
Field of
Search: |
;128/145.8,145.5,145.6,145.7,140,145R,142.2,142.3,142.4,351,305 |
References Cited
[Referenced By]
U.S. Patent Documents
Foreign Patent Documents
Other References
Pekkasoila, "Preparation & Use of Polytetrafluorethylene
Catheters & Crannulae in Diagnostic Radiology," Acta
Radiologica, Vol. 57, May, 1962, pp. 218-226..
|
Primary Examiner: Gaudet; Richard A.
Assistant Examiner: Mitchell; J. B.
Claims
I claim:
1. A patient adaptor means comprising the combination of a
ventilating apparatus and a tracheotomy instrument, said
tracheotomy instrument including a catheter of plastic material
which has a plastic memory and is fabricated in a curved shape,
said catheter adapted to fit over the outside of a substantially
straight needle and be straightened out by said needle when the
needle is pushed through the catheter and penetrates into the
trachea to have the catheter therein, said material causing the
catheter to resume the original curved shape as a result of said
plastic memory within the trachea after the needle is withdrawn
therefrom, attachment means secured to said catheter near the outer
end where the needle is totally withdrawn after the catheter has
been inserted into the trachea, said attachment means adapting the
catheter to be taped, tied or fastened to the neck, and a fluid
fitting at said outer end connected to said ventilating apparatus,
said ventilating apparatus comprising a pressurized source of
oxygenated gas connected to a pressure conduit, a vacuum source
connected to a suction conduit and an output conduit connected to
said fluid fitting, valve means interconnecting said pressure,
suction and output conduits, and passage means in said valve means
to connect said pressure conduit to said output conduit and to
disconnect said suction conduit from said output conduit to provide
an inflation phase in one position and to connect said suction
conduit to said output conduit and disconnect said pressure conduit
from said output conduit to provide a deflation phase when said
valve means are in a second position, said valve means comprising
valve members cyclically operated by an air motor mechanically
connected thereto, and a throttle valve connected to said motor to
regulate the flow of control fluid thereto.
2. A patient adaptor means as claimed in claim 1, wherein the
passage means in the valve means are arranged to provide the
conduit connections of the deflation phase in at least one more or
third position of the valve means during a cycle of movement to
thereby obtain an additional deflation phase.
3. A patient adaptor means as claimed in claim 2, wherein said
valve members are rotated by said motor and the conduit connections
of the deflation phase are repeated at a third and a fourth
position during a single revolution of the valve members.
4. A patient adaptor means as claimed in claim 2, wherein the valve
means include a valve having a plurality of passages which provide
for the conduit interconnections for said first inflation phase and
said second and third deflation phases at one setting of the valve,
and when said valve is shifted to a second setting, said passages
provide the conduit interconnections for a second inflation
phase.
5. A patient adaptor means as claimed in claim 1, wherein a bypass
conduit is provided to bypass said valve means, first manually
controlled valve means to disconnect the output conduit from said
motor operated valve means and to connect the output conduit to one
end of said bypass conduit, and second manually controlled valve
means to selectively connect the other end of the bypass conduit to
either the pressure conduit for an inflation phase or to the
suction source for a deflation phase.
6. A patient adaptor means as claimed in claim 5, wherein a
throttle valve is located in the bypass conduit to control the rate
of flow of the pressurized gas.
7. A as claimed in claim 1, wherein a throttle valve is located in
the suction conduit to regulate the rate of deflation of the
patient.
8. Ventilating apparatus comprising an output conduit for
connection to the trachea of a patient requiring inflation and
deflation phases comprising a pressurized source of oxygenated gas,
a vacuum source, a pressure conduit connected to the pressurized
source, a suction conduit connected to the suction source, valve
means interconnecting said pressure, suction and output conduits,
motor means mechanically connected to said valve means for
cyclically operating said valve means to inflate positions and to
deflate positions, a reduction gear train connecting said motor
means to said valve means, and passage means in said valve means to
connect said pressure conduit to said output conduit and to
disconnect said suction conduit from said output conduit to provide
an inflation phase in one position and to connect said suction
conduit to said output conduit and disconnect said pressure conduit
from said output conduit to provide a deflation phase when said
valve means are in a second position.
9. Ventilating apparatus as claimed in claim 8, wherein said motor
means is an air motor operated by the pressurized gas, and wherein
a throttle valve is provided to regulate the flow of pressure fluid
to the motor.
10. Ventilating apparatus as claimed in claim 9, wherein the
passage means in the valve means are arranged to provide the
conduit connections of the deflation phase in at least one more or
third position of the valve means during a cycle of movement to
thereby obtain an additional deflation phase.
11. Ventilating apparatus as claimed in claim 10, wherein said
valve members are rotated by said motor and the conduit connections
of the deflation phase are repeated at a third and a fourth
position during a single revolution of the valve members.
12. Ventilating apparatus as claimed in claim 10, wherein the valve
means include a valve having a plurality of passages which provide
for the conduit interconnections for said first inflation phase and
said second and third deflation phases at one setting of the valve,
and when said valve is shifted to a second setting, said passages
provide the conduit interconnections for a second inflation
phase.
13. Ventilating apparatus as claimed in claim 9, wherein a bypass
conduit is provided to bypass said valve means, first manually
controlled valve means to disconnect the output conduit from said
motor operated valve means and to connect the output conduit to one
end of said bypass conduit, and second manually controlled valve
means to selectively connect the other end of the bypass conduit to
either the pressure conduit for an inflation phase or to the
suction source for a deflation phase.
14. Ventilating apparatus as claimed in claim 13, wherein a
throttle valve is located in the bypass conduit to control the rate
of flow of the pressurized gas.
15. Ventilating apparatus as claimed in claim 14, wherein all the
claimed valve means and valves, and the drive motor and the conduit
are housed in a carrier case and wherein the throttle valves and
the first and second manually operated valve means are provided
with handle means protruding from the case for access thereof to
the operator.
Description
The present invention relates to an emergency tracheotomy
instrument and ventilating apparatus for restoring breathing to
non-breathing patients due to tracheal obstructions and pulmonary
complications, which is also useful for aiding ventilation for
bronchoscopy and during general anesthesia. The ventilator of the
invention permits closer control of oxygen inflation to provide
adequate ventilation and oxygenation, especially with poor risk
patients (heart condition, lung disease, etc.) for whom general
anesthesia may be contraindicated but who must have upper abdominal
or lower chest surgery. In such surgery, a high spinal or epidural
anesthesia is done, but this paralyzes the abdominal and lower
chest muscles which assist respiration. The diaphragm is spared
because the phrenic nerve originates from the cervical area in
embryology and descends, so the diaphragm is able to be voluntarily
moved but respirations are depressed.
The instrument of the present invention is an improvement over the
prior art instruments represented by the "Tracheotomy Instrument"
of U. S. Pat. No. 2,991,767 to Shelden et al. The improved
instrument comprises a soft plastic catheter which is precurved at
its long tubular bottom portion and an interiorly positioned
hypodermic needle. The catheter is provided with a hub portion for
connection to suction or vacuum and wings which anchor the
instrument after insertion into the trachea. The instrument is
inserted into the trachea through the crico-thyroid membrane(after
local (novacaine) anesthesia is used to anesthesize the skin, after
the needle enters the trachea and novacaine or xylocaine is
injected to anesthesize the trachea and tracheo-bronchial tree only
in non-comatose patients). The catheter is advanced and the needle
removed and the catheter is taped in place. Then the spinal or
epidural anesthesia is given and following this, the device is
connected to the tracheal catheter and the patient's respirations
are assisted. As long as assistance is in rhythm with the patient's
own rate, it is tolerated well; oxygen, compressed air or
anesthetic gas can be given via this catheter. When the patient is
comatose, no anesthesia is needed and if there is an emergency,
anesthesia is not needed before insertion. If the patient is not
breathing, the ventilator controls the ventilation.
A further object of this invention is to provide a ventilating
apparatus comprising a source of oxygenated gas (air, oxygen, etc.)
under the catheter selectively to the pressure gas source or
suction source. The system provides automatic operation of the
valve means by a motor means, preferably driven by the pressure
gas, whereby inflation and deflation phases are automatically timed
during a breathing cycle. The apparatus also includes a valve
whereby the ratio of inflation and deflation phases during a cycle
may be varied.
Another object is to provide a valve and conduit system for the
above apparatus whereby the cyclically operated system may be
bypassed to connect the catheter selectively to the pressure source
or to the suction by means of a manually controlled valve. Thus,
inflation and deflation phases may be carried out in accordance
with the judgment of the operator as he observes the condition of
the patient.
A further object is to house the apparatus in a carrying case for
portability. The various control valves are provided with handle
means extending through suitable openings in the case for selected
manual manipulation of the valves. The conduit means to be
connected to the catheter, pressure source and suction source also
extend from the case and are provided with conventional terminal
fittings for easy connection to the catheter and sources.
Further objects and advantages will be apparent from the following
description accompanying drawings, wherein:
FIG. 1 is a cross-sectional view of the instrument;
FIG. 2 is a perspective view of the catheter in its free state;
FIG. 3 illustrates the position of the instrument in relation to
the trachea;
FIG. 4 illustrates the position of the free catheter in the
trachea, the catheter having assumed its normal curved shape;
FIG. 5 is a diagrammatic layout of the conduit, the valve means and
the valve operating means of the ventilating apparatus, the valves
being in the position for the automatic mode of operation;
FIG. 6 is a partial view of FIG. 5 with the valves in the position
for the manual mode of operation;
FIG. 7 is a perspective view of the carrying case housing the
several devices of FIG. 5, and illustrating the access to the
handle means of the control valves;
FIG. 8 is a top view of a portion of a valve illustrating the
configuration of the port of a valve passage;
FIG. 9 illustrates the inflation and deflation phases of the valve
in its other position;
FIGS. 10a, 10b and 10c illustrate the positions of the automatic
valve means at 90.degree., 180.degree. and 270.degree., of
rotation, respectively, during a revolution of the cyclically
operated valve means, with the inflation and deflation phases of
the control valve set for one inflation phase followed by three
deflation phases;
FIGS. 11a, 11b and 11c are similar to FIGS. 10a, 10b and 10c,
respectively, but with the inflation and deflation phases of the
control valve moved to a position to obtain two inflation phases
followed by two deflation phases; and
FIG. 11d is similar to FIG. 11c, but showing the valve means in the
position of 0.degree. to 360.degree. of rotation.
FIG. 1 illustrates the assembled instrument 1 ready for use. It
comprises a hollow needle 2 of suitable gauge which may be a large
No. 14 or 16 for the average patient with a soft plastic catheter 3
fitting snugly outside the needle. Point 4 of the needle projects
beyond the catheter, the adjacent end 6 of the catheter being
shaped to form a gradual reduction in its cross-section to
facilitate its insertion in the trachea.
Catheter 3 is molded of a soft plastic to assume a desired
curvature suitable for movement within the trachea and at the
proper angle. Preferably, the plastic is of the type that
incorporates a "memory" therein to resume its molded shape after
needle 2 is pulled out therefrom.
The type of soft plastic material which will provide the plastic
memory when molded and which is non-pyrogenic has been used in
plastic catheters in the prior art and such polymer materials as
polyethylene, polytetrafluorethylene, polypropylene, polycarbonate,
vinyl chloride resins, vinyl chloride ethylene copolymer resins and
the like may be used, these polymers being readily sterilized and
being inert.
A wing formation 7 is secured to catheter 3 near its other end 8
whereby the catheter may be fastened to the skin of the neck of the
patient by adhesive tape. This tape may be an integral part of the
wing. Also a ribbon may be used to hold it tied around the neck.
End 8 terminates in a fitting arrangement whereby the interior of
catheter 3 may be connected to a ventilating or resuscitating
means, or to medicine administering means. End 8 may be provided
with a threaded flange 9 to be screwed to the desired connecting
tubing or socket formation means 11 for cooperation with a mating
plug on the connecting tubing.
As shown in FIG. 2, it is convenient to mark the device at the wing
with an arrow 10 which points in the direction which the precurved
soft catheter will assume after the needle is removed from the
catheter.
The end of needle 2 is connected by fitting 12 to the discharge end
of a syringe device 13. Syringe 13 is used to move air through the
inserted needle and catheter to indicate free flow through the
trachea and thereby control the movement and location of the needle
catheter. The syringe may also be used as a suction device for
removing obstructing matter in the trachea. It may also be used for
forcing air, medicine or any other desired and necessary fluid into
the trachea after the insertion of the catheter.
FIG. 5 diagrammatically illustrates the ventilating or resusciating
system, which system employs oxygenated gas sources such as
compressed air, pure oxygen, atmospheric air and a vacuum source.
The system comprises a source of gas under pressure 15. This source
may be compressed air, pure oxygen or air fortified with a higher
percentage of oxygen than normal atmospheric air. The source 15 is
connected by conduit means 16 and 16' to a sputum trap 17. From
sputum trap 17, a conduit means 18 extends to the patient where it
is connected to catheter 3.
Conduit means 16-16' has a series of three-way valves 21, 22 and 23
inserted therein. While the valves are shown as plug valves, such
showing is merely for illustration. The valves may be of any type,
such as piston valves, poppet valves, disc valves or combinations
of other types. Valve 21 has a handle means 24 to move it to a
selected position. While valves 22 and 23 are shown
diagrammatically as two separate plug means, their passages may be
incorportated in a single plug valve device at axially spaced
planes. To illustrate the unitary operation of valves 22 and 23, a
handle 25 is provided for each valve, the handle being connected
for joint movement by a connecting link means 26. Valves 22 and 23
rotate in opposite 90.degree. directions.
Suction or vacuum source 27 may be of any conventional type. It
comprises a container connected to a conventional vacuum producing
means, such as an air blower, a jet pump, a Venturi device, etc.
Conduits 28 and 29 extend from source 27. Conduit 29 is connected
to deflate valve means 30, and conduit 28 extends to valve 21.
A two-way valve means 31 is located between conduits 16 and 16' and
functions as an inflate valve. For illustrative purposes, valves 30
and 31 are shown as separate valves; however, they work in unison
by connecting means 32 which connects them to reduction gear drive
33. Valves 30 and 31 may be a single valve device with passages to
perform the valving functions to be described herebelow. Such valve
device may assume any conventional valve configuration, such as
piston, poppet, plug, disc, etc. as long as it performs the
required valving function. It is preferable that the outlet ports
34a of the several passages 34 in valves 30 and 31 be of a
configuration illustrated in FIG. 8. Outlet port 34a is elongated
in the direction of valve movement and may be of elliptical or
diamond configuration whereby the flow from the valve to the
conduits connected thereto is gradually initiated and gradually cut
off. The duration of time of fluid flow may be regulated by the
length of the longer axis of the port configuration.
Reduction gear device 33 may be driven by any type of motor or
mechanical driving means. Preferably, it is driven by fluid motor
35, which may be a conventional air motor, connected by conduit 36
to conduit 16 and thus to source 15. The use of an air motor in
lieu of, say, an electric motor permits a self-contained
ventilating unit which may be used where no electricity is
available, or with a source of compressed gas and never needs a new
battery, and its power medium is source 15, which is part of the
system.
The speed of motor 35 is regulated by an adjustable throttle valve
means 37 inserted in line 36, which valve is diagrammatically
illustrated as an adjustable choke valve.
A three way valve 40 is connected by conduit 41 to valve 30 and by
a conduit to valve 31. The function of valve 40 is to control the
ratio of inflation pulses or phases to deflation phases during a
revolution of valves 30-31. It may be termed an inflation and
deflation phase control valve. A conduit 42 connects valve 30 to
conduit 16'. A branch conduit 43 connects conduit 42 to valve 40. A
conduit 45 connects valves 22 and 23.
To control the rate of flow of the oxygenated gas in accordance
with the age and size of the patient, throttle or choke valve 47 is
inserted in line 16 upstream of valve 31 and a similar valve 47a is
inserted in conduit 45. Valve 47 controls the rate of flow when the
system operates automatically. Valve 47a controls the rate of flow
during manual control of ventilation, as will be described
herebelow. The rate of flow of deflation gas from the patient may
be controlled by throttle valve 48 inserted in suction line 29.
FIG. 5 illustrates the positions of the several valves in the
system for automatic operation of the ventilating means. Air under
suitable pressure flows from source 15 through conduits 16 and 16'
and through the connecting passages in valves 21, 22, 31 and 23 to
sputum cup and from there, by conduit means 18, to catheter 3.
Thus, air with the proper, selected percentage of oxygen flows to
the patient at a rate controlled by throttle valve 47.
At this phase of the cycle, valve 30 cuts off the several
connecting conduits and valve 40 from suction conduit 29.
Valve means 31 and 30 are continuously rotated in the direction of
the arrows 49 at the proper desired speed by air motor 35. Assuming
the setting of the valves in FIG. 5 to be 0.degree., at 90.degree.
of rotation, as illustrated in FIG. 10a, valve 31 blocks flow from
conduit 16 to conduit 16', and valve 30 connects suction source 27
and conduit 29 to conduit 41 and through valve 40 to conduits 43,
42 and 16' and thereby the catheter is connected to the suction
source whereby deflation or exhalation of the patient is aided. At
180.degree. of rotation, as illustrated in FIG. 10b, valve 31 still
blocks air flow to 16', and valve 30 connects conduit 42 to conduit
29 and therethrough to suction source 27. At 270.degree. of
rotation, as illustrated in FIG. 10c, valve 31 still blocks flow to
conduit 16' and valve 30 still connects conduit 42 to conduit 29.
At 360.degree. of rotation, valves 30 and 31 again assume the
positions of FIG. 5 and air is again delivered to the patient to
aid in the inhalation phase of breathing.
Thus, a single cycle or rotation of valve means 30 and 31 results
in one inflation and three deflation phases. Under certain
conditions, it may be desirable to have the same extent of
inflation and deflation. Inflation and deflation phases control
valve 40 is provided for such operation. If valve 40 is moved by
its handle 50 to the position illustrated in FIGS. 9, 11a to 11d,
the following connections occur during a single cycle or rotation
of valve means 30 and 31. At 0.degree., illustrated in FIG. 11d,
valve 31 connects conduits 16 and 16' and suction conduit 29 is cut
off from all connection by valve 30. At 90.degree. or rotation in
the direction of arrows 49, illustrated in FIG. 11a, valve 31
disconnects conduits 16 and 16' and connects conduit 16 and 41; and
through the passages in valve 40 conduits 41', 43, 42 and 16' are
interconnected, for a second inflation phase, while deflation
(suction) is blocked. At 180.degree. of rotation, as illustrated in
FIG. 11b, conduit 16 is cut off from the other conduits by valve
31. Suction conduit 29 is connected by valve 30 to conduits 42,
16', and 18 to catheter 3 for the deflation phase. At 270.degree.
of rotation, as illustrated in FIG. 11c, valve 31 still cuts off
flow from conduit 16 and valve 30 connects conduits 29, 42 and 16'
for a second deflation phase. At 360.degree. of rotation, the
valves assume the position illustrated in FIG. 11d, that is, the
0.degree. position, in which an inflation phase is initiated.
Thus, with valve 40 in the position of FIG. 9, there are two
inflation and two deflation phases during a cycle or a revolution
of the valve means 30 and 31.
The tapered configurations of outlet ports 34a of the valve
passages 34 gradually throttle the flow of the fluid between the
valve passages and the conduits during the continuous rotation of
valves 30 and 31. The long dimension of the configuration
determines the time duration of a phase.
Air motor 35 is always connected to source 15. By manipulating
valve 37, the speed of rotation of valve means 30 and 31 may be
controlled to vary the phases, of inflation and deflation, per
unit-time in accordance with the observed condition of the patient.
It is to be understood that the operator of the device is
constantly observing the ventilation, blood pressure and other
vital conditions of the patient.
Under certain conditions, the patient cannot be subject to the
automatic inflation and deflation and the operator must manipulate
the inflation and deflation phases in accordance with the abnormal
conditions of the patient. FIG. 6 illustrates the valve settings
for the manual mode. Valves 21, 22 and 23 are shifted by means of
their handles from their positions of FIG. 5 to the positions of
FIG. 6. Valves 30 and 31 are rendered inoperative by shutting off
flow to motor 35 by either valve 37 or by a conventional shut off
valve located in conduit 36. Thus, in the positions of FIG. 6,
valves 22 and 23 interconnect conduit 16 to conduit 16' at sputum
cup 17 by means of conduit 45 which bypasses the valve means 30, 31
and 40, and their interconnected conduits.
Valve 21 is then manipulated by the operator from one position to
another by handle 24. The position shown in solid lines is the
inflate position wherein oxygenated pressure gas, regulated by
throttle valve 47a flows from source 15 to conduits 16, 45, 16', 18
to catheter 3. When deflation is desired, valve 21 is moved
anticlockwise 90.degree., to the dotted line positions of handle
24, and the valve passage means. In this deflate position, suction
source 27 is connected by the valve means to conduits 16, 45, 16',
18 and catheter 3. The duration of the inflation and deflation
phases will be regulated by the operator in accordance with the
requirements of the patient which is under his visual
observation.
When the patient has reached the state at which automatic
ventilation may take place, valves 21 and 22-23 are returned to
their "automatic" position (FIG. 5), and motor 35 is started and
its speed regulated by throttle valve 37. The rate of flow of gas
is controlled by throttle valve 47, since regulation by valve 47a
will effect the flow of pressure fluid to motor 35.
The above system is adapted to be placed in a carrying case. FIG. 7
illustrates a preferred embodiment of packaging the system in a
case. Case 53 may be of metal or plastic and has a conventional
hinged cover. The several conduits may be in the form of rubber or
plastic hose means of sufficient strength and rigidity to withstand
the pressure and vacuum conditions during operation. Motor 35, gear
drive 33 and valves 30 and 31 may be a unitary assembly fastened to
the walls or bottom of the case. Handle 24 of valve 21, handle 25
of interconnected valves 22 and 23 and handle 50 of valve 40
protrude from one end of case 53 for manipulation by the operator.
It should be understood that FIG. 7 is somewhat diagrammatic and
the handles and knobs shown may be members which are mechanically
or electrically linked to the valve means within the case to move
them from one position to the other position, as described
above.
Conduit means 16, 18 and 29 may extend from the other end of the
case, or be connected from within the case, each hose having a
conventional terminal fitting or plug for easy connection to the
catheter and the source of air, oxygen, vacuum, etc.
PROCEDURE OF OPERATION
The article by R. D. Sanders, "Two Ventilating Attachments for
Bronchoscopes". Delaware Med. Journ. 39:170 1967, describes an
injector device for high flow of oxygen through a bent thin tube,
down a bronchoscope to which it attaches at the top, to inflate the
lungs of paralyzed, anesthetized patients undergoing bronchoscopy
(a 2 foot tube passed between the vocal cords and down into the
bronchi in the lungs used for inspection and biopsy). A venturi
tube (high pressure air jet) helps to inflate the lungs, but the
tube does not go through the skin and only attaches to the outside
end of the bronchoscope.
The patient lying on his back, has his neck minimally straightened
by lifting up the chin. This makes the trachea more prominent.
Then, holding the trachea immobile, needle 2 with soft plastic
catheter 3 fitting snugly around the outside of the needle, with
arrow 10 upward, is directed down and toward the feet at
approximately a 45.degree. angle to the neck, as illustrated in
FIG. 3. The needle is inserted through the crico-thyroid membrane
(beginning of the trachea approximately one-half inch below the
vocal cords) or directly between any easily palpable space between
two tracheal cartilege rings. When the syringe 13 which is attached
to the needle aspirates air easily, the intratracheal location is
assured. Then, the previously stabilized trachea is again held as
the catheter is advanced down the trachea its entire length of 2
1/2 to 5 inches depending on the patient's size. The needle, which
has been kept stable after air is aspirated, is thereafter removed
leaving the catheter in place.
When catheter wing or hub 7 reaches the skin needle 2 is withdrawn
and wing 7 is taped to the skin of the neck. When the needle is
removed, catheter 3 assumes its original curved shape, as
illustrated in FIG. 4 to assure a smooth flow of fluid into and out
of the trachea passage. Conduit 16 is connected to catheter 3 at
end 8. At the option of the operator, conduit 16 may be connected
to oxygen or compressed air sources and inflation and deflation may
be carried out automatically or manually or a combination of both,
depending upon the condition and state of the patient. The number
of inflation and deflation phases during a cycle may be selected by
valve 40, by manipulating knob 50, if the ventilation is automatic.
The rate of flow of the oxygenated gas is controlled by knobs
connected to valve 47 and 47a, as indicated in FIG. 7.
If there is not complete or almost complete airway obstruction, the
exhalation phase is through the normal tracheal-pharyngeal-oral
route and suction is not mandatory, as it is in complete
obstruction, although it may be used to remove some secretions and
accelerate the exhale phase.
When used in an emergency, this allows immediate respiratory
control inserted by any trained person. Because of the soft
catheter, there is no continuing trauma to the trachea and other
contiguous organs by a sharp needle by transporting or
resuscitating the patient. Also, an endotracheal tube can be passed
with this soft catheter in place without danger of laceration of
this endotracheal tube or of its inflating balloon. The
resuscitator is turned off after the endotracheal tube is inserted
and the catheter can remain in position for future use, if needed,
such as instilling medicines directly into the tracheo-bronchial
tree.
When complete obstruction exists, a second catheter or large needle
is also inserted to act as a safety valve to insure that the
intrathoracic pressure does not continually build up to over 155 mm
Hg to begin to compromise venous blood return to the heart.
The valves of the ventilating machine of the invention adjust the
number of respirations per minute as well as the tidal volume
(volume of gas per each inflation). The statistical average minute
volume, i.e., the number of respirations per minute times the tidal
volume, is 8.4 liters per minute. In ventilating adults, the tidal
volume is increased and the respirations per minute is decreased,
while in children, the opposite is done, e.g., the tidal volume
decreased and the respirations increased. Since the volume of gas
leakage varies in each situation, the adequacy of ventilation is
judged by any or all of the following: the degree of chest
expansion, auscultation of the lungs, the color of the patient, and
the blood gas values. The valve number 40 shown in FIG. 5 allows
one to double the maximum minute volume whenever needed: a larger
than usual air leak through the pharynx or stiffer lung compliance
as in emphysema, pneumonia, or pulmonary fibrosis.
Blood gas studies were obtained on patients with different disease
processes, ages and sizes demonstrated excellent ventilation.
Controls were first obtained on other respirators, with an
endotracheal tube in place. Then blood gases were obtained after 30
minute equilibration with the apparatus of the present invention.
Oxygenation was hight and removal of waste was excellent. The blood
pH was normal. The blood carbon dioxide remained normal while the
oxygen partial pressure was markedly elevated because of the use of
100 percent oxygen. Compressed air or air-oxygen mixtures were
found also to be useful.
The chest may be opened for thoracic surgery or open cardiac
massage while the pressure device is in place.
Closed or external cardiac massage is compatible with the present
apparatus and in addition, helps to deflate the lungs to aid the
surgeon who must use cutting or clamping devices within, during
critical phases of the operation and frees his hands from
massage.
The soft intratracheal catheter, is essential rather than a stiff
needle because:
a. during resuscitation, the neck is mobile and a sharp needle
would lacerate the trachea, esophagus and nearby delicate
structures,
b. an endotracheal tube with an occluding balloon can be easily
inserted without any risk of laceration by a stiff needle, and
c. the soft catheter is unequally adapted to remain in place for
future use for long periods with absolute safety.
Although a certain preferred embodiment of the invention has been
disclosed for purposes of illustration, it will be evident that
various changes and modifications may be made therein without
departing from the scope and spirit of the invention.
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