U.S. patent number 3,738,370 [Application Number 05/107,312] was granted by the patent office on 1973-06-12 for method of defibrillating a malfunctioning heart by means of electrodes located within the atrium.
Invention is credited to Bernard L. Charms.
United States Patent |
3,738,370 |
Charms |
June 12, 1973 |
METHOD OF DEFIBRILLATING A MALFUNCTIONING HEART BY MEANS OF
ELECTRODES LOCATED WITHIN THE ATRIUM
Abstract
A bi-polar coaxial cable or catheter is passed transvenously
into the right atrium or auricle of the heart, and the electrodes
or poles of the cable are so positioned within the atrium and
exposed to the interior of the atrium that when the cable is
connected to a defibrillator unit, direct current shocks of very
low energy or intensity may be transmitted by said unit through the
cable to effect defibrillation, without causing pain or appreciable
discomfort to the patient undergoing defibrillation.
Inventors: |
Charms; Bernard L. (Shaker
Heights, OH) |
Family
ID: |
22315989 |
Appl.
No.: |
05/107,312 |
Filed: |
January 18, 1971 |
Current U.S.
Class: |
607/5 |
Current CPC
Class: |
A61N
1/3956 (20130101); A61N 1/056 (20130101) |
Current International
Class: |
A61N
1/375 (20060101); A61N 1/39 (20060101); A61N
1/05 (20060101); A61N 1/372 (20060101); A61n
001/36 () |
Field of
Search: |
;128/419D,419P,419R,421,422 |
References Cited
[Referenced By]
U.S. Patent Documents
Other References
Hopps et al., "Surgery", Vol. 36, No. 4, Oct. 1954, pp. 833-849
(only pp. 834 & 841 relied on).
|
Primary Examiner: Kamm; William E.
Claims
Having thus described my invention, I claim:
1. In a method of defibrillating a malfunctioning heart, the steps
of introducing a pair of electrical conductors transvenously into
the right atrium of the heart, positioning said conductors within
the atrium in widely spaced relation to each other, to thereby
provide spaced poles located entirely within the atrium generating
electrical impulses of an intensity of from 1 to 10 watt seconds
sufficient to cause defibrillation of the heart, and delivering
said impulses to said poles for a period of from 3 to 100
milliseconds.
2. The method, as defined in claim 1, wherein said poles are
disposed adjacent the wall of the atrium.
3. The method, as defined in claim 1, wherein said poles are
disposed at diametrically-opposite sides of the atrium.
4. The method, as defined in claim 1, wherein said impulses are
direct current impulses.
5. The method, as defined in claim 1, wherein said electrical
impulses or shocks are generated externally of the body of the
person who is being defibrillated.
6. The method, as defined in claim 1, wherein said electrical
impulses or shocks are generated within the body of the person who
is being defibrillated.
7. The method, as recited in claim 1, wherein said placement of the
poles is effected by coiling the leading portions of said
conductors about the atrium in closely spaced relation to the inner
wall of the atrium.
Description
The human heart beats about 70 times a minute, and while all of the
fine mechanisms and forces that trigger the heartbeat are not known
with precision, a small knot of tissue known as the pacemaker or
sinus node is a vital spark plug. It is located in the upper part
of the heart near where great veins enter the right auricle. It
consists of specialized nerve and muscle cells which ignite a wave
of muscle contraction in the heart. This wave spreads over
auricular muscles and, although there is no direct connection,
appears to travel from auricles to ventricles and muscles of the
heart valves over a bridge, the auricular-ventricular or A-V
node.
The electrical nature of impulses that spark the heartbeat is shown
by the success of artificial pacers in triggering normal rhythms in
some forms of heart disease. These artificial pacers are
battery-powered devices, worn over the shoulder like a camera or
implanted under the skin, which are connected to electrodes in
heart tissue, and which feed tiny jolts of electric current to a
faulty heart, to spark its beat and keep it running
rhythmically.
An implantable cardiac Pacemaker is described in Greatbatch U.S.
Pat. No. 3,057,356, this pacer permitting innocuous, painless, long
term cardiac stimulation at low power levels by utilizing a small,
completely implanted transistorized, battery operated Pacemaker,
connected via flexible electrode wires directly to the myocardium
or heart muscle. A subsequent Chardack U.S. Pat. No. 3,198,195, was
an improvement, in that it taught variable Pacemaker controls,
adjustable from outside the body by a percutaneous needle, to
change Pacemaker rate and/or output level.
In a more recent Greatbatch U.S. Pat. No. 3,478,746, a cardiac
implantable demand Pacemaker is described, consisting of a
portable, self-contained device including circuitry which senses
each natural heartbeat and resets the Pacemaker pulse generator
timing in response to it. This device stimulates only skipped beats
and does not compete with natural beats, the first generated
impulse after a natural beat occurring after a preset time interval
longer than the natural interval unless another natural beat has
intervened. When a natural beat intervenes, the Pacemaker timer is
coordinated with it.
Other irregularities of the heart beat, or arrhythmias, include
atrial fibrillation, found most often with rheumatic valvular
disease (chiefly mitral stenosis), thyroid overactivity, or
coronary disease with congestive failure, as well as a far more
serious and often fatal disturbance of rhythm, known as ventricular
fibrillation, in which condition the ventricle is not pumping, and
which is rapidly fatal unless the heart can be "defibrillated" by
means of electrical machines which shock the heart out of its
dangerous standstill. Ventricular fibrillation occurs most commonly
in acute coronary attacks, and during cardiac surgery, although it
may unexpectedly occur during other forms of surgery.
Such "defibrillators" are described, by way of example, in U.S.
Pat. Nos. 3,211,154; 3,258,013; 3,389,704; 3,442,269; 3,454,012;
3,518,997 and 3,527,229.
The methods described in these patents and others, for the most
part, employ electrical shocks applied to the external surface of
the heart with the chest open, or through the chest wall.
In U.S. Pat. No. 3,442,269, for example, reference is made to the
fact that in closed chest utilization of the defibrillator, one of
the electrodes is placed on the right border of the sternum just
below the sternal notch, while the other electrode is placed on the
mid-clavicular line near the fifth interspace, with the heart
approximately midway therebetween, while for internal use,
following thoracetomy, the electrodes may be applied directly
across the heart itself.
Due to the high electrical resistance of the skin and other tissues
between the heart muscle and the electrodes, and the distance of
the electrodes from the heart, large or high electrical voltages
are necessary to overcome this resistance. Shocks incident to the
use of such high voltages, produce pain, and anesthesia is required
to eliminate or lessen this pain, so that the shocks cannot be
repeated at frequent intervals. Moreover, burns of the skin are
frequently produced, and recurrence of the abnormal rhythm within a
matter of weeks, is common.
For example, conversion of atrial fibrillation to normal rhythm by
direct current countershock through the chest wall requires from
100 to 400 watt seconds of electrical energy, usually delivered
very rapidly, i.e., for periods of 3-4 milliseconds.
In artificial pacers, to which reference has hereinbefore been
made, it has been proposed, as in Chardack U.S. Pat. No. 3,348,548,
to provide an implantable bi-polar electrode which is inserted
through a vein, one of the jugular veins, for example, and brought
to lie in contact with the inner lining of the heart. However, in
such a pacer, in common with all pacers, small electrical impulses
are delivered to the electrode, that is to say, impulses of the
order of 1 to 5 milliamps at 6 volts, and at a frequency of 50 to
100 per minute. Such impulses are effective to stimulate the
ventricle to beat, but are far too small to be used with any useful
effect for defibrillation.
I have discovered that by proper placement of a bipolar coaxial
cable, of novel or unique construction, in the right atrium, and
inserted transvenously, as through the jugular vein, I can quickly
convert a rapid irregular rhythm to a normal rhythm, by the
administration of direct current shocks, of the same duration as
those delivered through the chest wall, but of very low energy or
intensity, i.e., 1 to 10 watt seconds.
I have further found that the closer the two electrodes are to each
other, the greater the electrical energy that is required to
accomplish the defibrillation, and that the distance between the
two electrodes should ideally be that equivalent to one-half the
circumference of the right atrium.
I have further noted that a the delivery time or period of 3-4
milliseconds, sufficient insulation for the bipolar coaxial cable
to prevent shocking the body generally must be provided, because
the voltage and amperage levels required may reach 1,000 volts and
70 amperes. However, as previously shown by others, successful
defibrillation by countershock, up to 100 milliseconds in duration
can be accomplished. With the longer duration, lower voltages and
amperages can be used, avoiding the problem of overall shocks, and
reducing the requirements for insulation. This also makes possible
the permanent implantation of a self-contained power unit attached
to the cable positioned in the right atrium. Such a unit could be
set to determine the presence of a too rapid or irregular heart
rate and deliver a shock synchronized with the next intrinsic heart
beat. The energy required for such a unit can be derived from an
inductively rechargable battery source connected to a series of
condenser plates for storage of the charge, as described, for
automatic internal defibrillation. The small energies required
should permit miniaturization of the unit sufficient for practical
permanent implantation in the body. Moreover, the cable could be
interchangeably connected to a conventional pacer, so as to become
usable for ordinary pacer purposes, thereby providing a complete
control for all cardiac rhythm disturbances, whether too fast or
too slow.
The invention may be explained with reference to the accompanying
drawings, wherein
FIG. 1 is a cut-away view, somewhat diagrammatic in nature, showing
the blood circulation of a normal heart, and showing, also, the
manner in which the coaxial cable of the present invention is
introduced into the right atrium or auricle of the heart, as well
as the optimum or desired placement of the electrodes;
FIG. 2 is a cross-sectional view, on an enlarged scale, taken on
the line 2--2 of FIG. 1;
FIG. 3 is a cross-sectional view, on an enlarged scale, taken on
the line 3--3 of FIG. 1; and
FIG. 4 is a cross-sectional view, on an enlarged scale, taken on
the line 4--4 of FIG. 1.
Referring more particularly to the drawings, reference numeral 1
designates the left atrium or auricle of the heart, 2, the left
ventricle, 3, the right ventricle, 4, the right atrium or auricle,
5, the aorta, 6, the pulmonary artery, 7, the superior vena cava,
and 8, the inferior vena cava.
For purposes of effecting defibrillation, a coaxial cable or
"catheter," generally indicated by reference numeral 9, is
used.
The coaxial cable consists of a lead wire 10, insulation 11
surrounding this lead wire, a tubular lead wire 12 surrounding the
insulation 11, and a covering insulation 13 surrounding the lead
wire 12.
The wires 10 and 12 may be made of any metal which has excellent
electrical transmitting properties, and which is completely
compatible with body fluids while the insulation 11 and 13 may be
any electrically-insulative inert material which has good
insulating properties, such, for example, as Teflon, and which is
also completely compatible with body fluids.
The cable 9 is passed transvenously through the body, and caused to
enter the right atrium or auricle in the manner depicted in FIG. 1,
that is to say, the leading portion of the cable is coiled within
the atrium, so as to lie closely adjacent the inner wall or
endocardium of the atrium. Before this is done, however, portions
of the insulation are removed to expose the wire 10 at the point
10a, and the wire 12 at the point 12a, these points thus becoming
the electrodes or poles of the cable. These poles are, of course,
completely insulated from each other.
It is to be noted that the poles or electrodes 10a and 12a are
located at diametrically-opposite sides of the atrium, that is to
say, at points which are at a maximum distance from each other
diametrically of the atrium cavity or chamber. With the poles or
electrodes thus positioned, the electrical countershock, i.e.,
defibrillation shock, passed between the poles or electrodes,
traverses the entire atrium, and exerts a maximum defibrillatory
action, covering the entire chamber wall. If the poles or
electrodes are located closer to each other, shocks of greater
intensity would have to be administered to effect the desired
results.
The distance between the poles 10a and 12a will vary in accordance
with the size of the atrium.
The inner and outer leads of the cable are then connected to a
defibrillator machine or unit, indicated generally by reference
numeral 14 in FIG. 1. This unit is a source of direct current
shocks of very low energy or intensity, i.e., from 1 to 10 watt
seconds, and is so designed as to administer countershocks having a
time duration of 3 to 50 milliseconds.
This time duration of the countershocks will depend on the
thickness and qualities of the insulation provided in the cable,
and, in some cases, countershocks up to 100 milliseconds in
duration can be used to successfully accomplish defibrillation
while avoiding the problem of overall shock, to which reference has
previously been made.
The defibrillator unit 14 may be a portable DC defibrillator unit,
such as described in Druz U.S. Pat. No. 3,258,013, to which
reference has been made. Synchronization may be effected by an
automatic selector of the type described in the Tischler U.S. Pat.
No. 3,135,264, which is designed for ratios too slow for the
purposes of the present invention, but which can be adapted for
ratios which are too fast. A unit such as described in the
McLaughlin U.S. Pat. No. 3,527,228 could also be adapted for use in
the present invention, and a synchronizer such as described in the
Berkovits U.S. Pat. No. 3,345,990 could be adapted to show R-R
intervals. In this connection, the curves shown in FIGS. 2a, 2b,
2c, 2d and 3 of the above Druz patent are of interest.
By reducing the requirements for insulation, it becomes possible to
utilize a permanently-implantable self-contained power unit, which
could be set to determine the presence of a too-rapid or irregular
heart beat and deliver a shock synchronized with the next intrinsic
heart beat. The energy required for such a unit can be derived from
an inductively rechargable battery source connected to a series of
condenser plates for storage of the charge.
Although the invention has been described with particular reference
to the use of a bi-polar coaxial cable, it is to be understood that
any cable containing two wires in parallel spaced arrangement with
each other, but fully insulated from each other, may be used, or,
for that matter, insulated wires which are entirely separated from
each other may be used, the important desideratum being the
placement of the wire or wires in the atrium, and the spacing of
the poles, electrodes or terminals of the wires in the atrium
chamber or cavity.
It is to be understood that various changes in the method and
apparatus which has been described may be made without departing
from the spirit of the invention and the scope of the appended
claims.
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