U.S. patent number 3,707,960 [Application Number 05/069,191] was granted by the patent office on 1973-01-02 for balloon cardiac assisting pump having intraaortic electrocardiographic electrodes.
Invention is credited to Paul S. Freed.
United States Patent |
3,707,960 |
Freed |
January 2, 1973 |
BALLOON CARDIAC ASSISTING PUMP HAVING INTRAAORTIC
ELECTROCARDIOGRAPHIC ELECTRODES
Abstract
An intra-arterial cardiac assisting pump is provided with
intraaortic electrocardiographic electrodes to improve the
signal-to-noise ratio of the electrocardiogram and the reliability
of trigger signal for phase-shift pumping.
Inventors: |
Freed; Paul S. (Brooklyn,
NY) |
Assignee: |
|
Family
ID: |
22087324 |
Appl.
No.: |
05/069,191 |
Filed: |
September 3, 1970 |
Current U.S.
Class: |
600/381; 604/914;
600/18 |
Current CPC
Class: |
A61B
5/283 (20210101); A61B 5/6853 (20130101); A61M
60/40 (20210101); A61M 2205/33 (20130101); A61M
60/50 (20210101); A61M 2205/3303 (20130101); A61M
60/135 (20210101); A61M 60/871 (20210101) |
Current International
Class: |
A61B
5/042 (20060101); A61B 5/0408 (20060101); A61M
1/10 (20060101); A61b 005/04 () |
Field of
Search: |
;128/1R,2.5R,2.6E,2.1E,DIG.4 |
References Cited
[Referenced By]
U.S. Patent Documents
Primary Examiner: Kamm; William E.
Claims
What is claimed is:
1. In an intra-arterial cardiac assisting pump comprising: a hollow
elongated arterial catheter having an outer diameter sufficiently
small to permit insertion thereof into an artery, and having a
perforated portion; a thin-walled cylindrical, inflatable balloon
surrounding the perforated portion of said catheter and in
gas-sealing relationship therewith; and pumping means for
periodically feeding gas to said balloon through said catheter in
response to an electrocardiographic signal, the improvement
comprising
means connected to said pumping means for simultaneously
controlling balloon pumping and obtaining an electrocardiographic
signal, comprising a pair of intracorporeal electrodes along the
outer surface of said intraarterial pump in the vicinity of said
balloon, and an electrical lead extending from each said electrode
along the length of said catheter, wherein one said intracorporeal
electrode is located at the leading end of said catheter adjacent
the leading end of said balloon, and the other said intracorporeal
electrode is located at the caudal end of said balloon.
2. A device in accordance with claim 1 wherein said arterial
catheter is formed of a flexible mesh-material and wherein said
leads from said electrodes are woven in said mesh.
3. A device in accordance with claim 2 wherein said electrodes
consist essentially of a plastic material filled with electrically
conductive particles.
4. A device in accordance with claim 3 wherein said electrically
conductive particles consist of carbon black.
Description
The present invention relates to the provision of intraortic
electrocardiographic electrodes for use in conjunction with driving
a cardiac assisting balloon pump and, more particularly, to an
auto-synchronous intra-arterial balloon pump incorporating
intracorporeal electrodes for improving the reliability of the
trigger signal for the balloon pumping.
As indicated in copending application Ser. No. 710,596, filed Mar.
5, 1968, now U.S. Pat. No. 3,585,983, a vital need has existed for
quickly combating profound cardiogenic shock in those who suffer
from acute myocardial infarction. The provision of intra-arterial
balloon pumping has provided great promise in this area.
Among such devices has been described the phase-shift balloon
pumping system of U.S. Pat. No. 3,585,983, for providing such
circulatory assistance. In using such balloon pumps, it is
conventional to obtain the electrocardiographic signal, used to
control the phase-shift pumping procedure, from conventional
electrocardiographic skin electrodes. The use of such conventional
skin electrodes, however, has a number of disadvantages, one of the
most important of which is the undesirably low signal-to-noise
ratio. The low signal-to-noise ratio decreases the reliability of
the triggering signal for phase-shift pumping, and this in turn
reduces the reliability of the regulation of the inflation,
deflation cycle of the balloon pumping chamber.
The above problem is increased in patients in whom the R-wave
voltage, as recorded through the skin electrodes, is reduced. Most
patients in cardiogenic shock have had myocardial infarctions,
which generally are associated with reduced voltage of the R-wave.
In addition, pulmonary edema, pericarditis, and other conditions
which further reduce the amplitude of the R-wave are relatively
frequent in patients in whom balloon pumping is performed.
It is, accordingly, an object of the present invention to overcome
the above and other deficiences of the prior art.
It is another object of the present invention to provide for
intra-arterial cardiac assistance in a new, improved and unobvious
manner and to provide a novel intra-arterial cardiac assisting
balloon pump.
It is another object of the present invention to provide for
intracorporeal electrodes in a phase-shift balloon pumping system
to improve the signal-to-noise ratio of the electrocardiogram, and
thereby, the reliability of the trigger signal for phase-shift
pumping.
It is another object of the present invention to provide an
improvement on previous intracorporeal balloon pump units.
These and other objects and the nature and advantages of the
instant invention will be more apparent from the following detailed
description of an exemplification of the invention taken in
conjunction with the drawing wherein:
The FIGURE is a perspective view, partly broken away, of an
intracorporeal balloon pump unit.
An intra-arterial assisting device in which the present improvement
is used comprises, in general, two major components, namely an
extra-corporeal unit (not shown) such as that provided and
described in U.S. Pat. No. 3,585,983, and an intracorporeal balloon
pump unit 10. Briefly, the intracorporeal unit comprises the
balloon pump portion including a hollow elongated arterial catheter
14, an inflatable non-elastic balloon portion 16, and a perforated
reinforcing portion 18 which constitutes an extension to the
elongated arterial catheter portion 14.
The extra-corporeal unit includes, very generally, a source of gas
under pressure, valve means for periodically feeding the gas used
to inflate the balloon portion 16 to the intracorporeal unit 10
through the hollow catheter 14, and suitable electronic means for
receiving a signal from the body in which the intra-arterial
cardiac assisting device has been placed (such as an ECG signal)
and using such signal for the opening and closing periodically of
the valve means. In the past such signal has been provided from
conventional electrocardiographic skin electrodes.
In the preferred embodiment of the present invention, the
intracorporeal unit 10 is very similar to that disclosed in U.S.
Pat. No. 3,585,983 in its details of construction. Among the
important features of such a device is the provision of an arterial
catheter 14 and perforated portion 18 of sufficiently small outer
diameter to permit insertion thereof into an artery. The balloon
16, which surrounds the perforated portion 18 of the catheter in
gas-sealing relationship therewith, is of cylindrical configuration
and is preferably very thin-walled; it is preferably formed of a
non-elastic and very strong material, such as polyurethane rubber.
The perforated reinforcing portion 18 preferably comprises a
flexible braided tube of metal wires, such as copper braid,
conventionally used as electrical shielding.
The intracorporeal unit 10 of the present invention differs from
prior balloon pumps in the provision of intracorporeal electrodes
and suitable leads to provide the electrocardiographic signal
utilized in the extracorporeal unit to drive the balloon pump.
While such electrodes and leads may be provided in various ways, it
is preferred that the electrodes be primarily non-metallic. In the
illustrated embodiment a first electrode 20 is provided at the
leading end of the balloon pump and a second electrode 22 is
located at the caudal end of the balloon 16, in use preferably
downstream from the balloon in the aorta. A first lead 201 passes
from the first electrode 20 and a second lead 221 passes from the
second electrode 22, both along the length of the catheter 14 and
to the extracorporeal unit.
The intracorporeal electrodes 20 and 22 are preferably provided by
rendering suitable components of the balloon pump electrically
conductive. As one illustration, a small amount of carbon black is
mixed with the polyurethane used for the tips of the pumping
chamber 16, either during its fabrication, or subsequently thereto
as a coating thereon. The leads are imbedded therein, respectively,
and the lead 201 is woven through the copper mesh forming the body
of the reinforcing portion 18. If the entire length of the catheter
14 is lined with the mesh material, both leads 201 and 221 may be
woven therein; if the catheter 14 is merely a hollow elongated
tube, such as one formed of vinyl plastic, the leads may be either
imbedded in the surface thereof in conjunction with a surface
coating such as of polyurethane or polytetrafluoroethylene, or such
leads may be carried within the interior of the catheter 14. In any
event, the leads 201 and 221 are brought out at the terminal end of
the catheter 14 to a suitable extracorporeal connector (not shown)
such as shown in U.S. Pat. No. 3,585,983.
It will be understood that while the carbon black impregnated
polyurethane electrodes are preferred, other electrodes may be
utilized. For example, a biologically inert metal powder, such as
titanium, stainless steel, nickel or chromium, may be used as a
filler for the plastic forming the electrodes. Alternately, the
electrodes may be formed of vacuum deposited metal of a
biologically inert nature, or the electrodes may be electro-plated
over an electroless coating in accordance with known
techniques.
As pointed out above, the electrocardiographic signal obtained from
the intracorporeal electrodes 20 and 22 are utilized in the same
manner as that from conventional skin electrodes in the phase-shift
pumping procedure. However, the signal obtained from the
intracorporeal electrodes has a number of advantages, of which the
most important is that the signal-to-noise ratio of the
electrocardiogram is substantially improved. This benefit results
from a number of factors: The cardiac voltage recorded at the sites
of the intracorporeal electrodes is greater than that recorded at
the skin. The potentials generated by movement of muscles between
the heart and the skin are eliminated from the signal. And
artifacts produced by movement of electrodes and by changes in the
conductivity of electrode jelly, used on the skin, due to
evaporation are avoided.
The improved signal-to-noise ratio in the electrocardiogram
increases the reliability of the triggering signal for phase-shift
pumping. In turn, the reliability of the regulation of the
inflation-deflation cycle of the pumping chamber, which is critical
for effective circulatory assistance, is enhanced. While these
advantages accrue in every case, they are of especial importance in
patients in whom the R wave voltage, as recorded through the skin
electrodes, is reduced, such patients including those suffering
from myocardial infarction, pulmonary edema, pericarditis, and
other conditions which reduce the amplitude of the R wave, such
patients forming a substantial portion of those in whom balloon
pumping is performed.
Beside the primary importance of the intracorporeal electrodes,
namely that they increase the capability of the system to pump with
maximal effectiveness regardless of conditions which may render the
trigger signal as recorded by external electrodes unsatisfactory,
the use of intracorporeal electrodes provides other advantages.
These include shortening the time needed to initiate balloon
pumping, since external electrodes need not be applied as a
separate step in the procedure. Furthermore, elimination of skin
electrodes reduces by three the number of external restraints on
the patient during pumping.
Also, the ability to achieve maximally effective pumping is
improved in that the effectiveness of pumping is in part dependent
upon the location of the pumping chamber in the aorta, which is
reflected by the character of the electrocardiogram recorded from
the internal electrodes; it is therefore possible to adjust the
position of the pumping chamber as soon as it has been introduced,
without waiting for X-rays to be obtained. Additionally, the
diagnosis of certain cardiac abnormalities is facilitated by the
use of internal electrodes; since the internal electrodes provide
two additional sites from which potentials can be recorded and
these locations are nearer to the heart than those of skin
electrodes, more electrocardiographic information can be obtained
than with the use of skin electrodes alone.
That other methods for incorporating electrodes in the phaseshift
balloon pumping system are possible will be evident to anyone
skilled in the art, and the scope of the present modification is
not restricted to particular methods for achieving this result. The
foregoing description of the specific embodiment will so fully
reveal the general nature of the invention that others can, by
applying current knowledge, readily modify such embodiment and/or
adapt it without departing from the generic concept and, therefore,
such adaptations and modifications should and are intended to be
comprehended within the meaning and range of equivalents of the
disclosed embodiment. It is to be further understood that the
phraseology or terminology employed herein is for the purpose of
description and not of limitation.
* * * * *