U.S. patent number 3,599,244 [Application Number 04/878,484] was granted by the patent office on 1971-08-17 for dynamic action valveless artificial heart utilizing dual fluid oscillator.
Invention is credited to Donald E. Wortman.
United States Patent |
3,599,244 |
Wortman |
August 17, 1971 |
DYNAMIC ACTION VALVELESS ARTIFICIAL HEART UTILIZING DUAL FLUID
OSCILLATOR
Abstract
An artificial heart intended for supplementing or temporarily
replacing the natural heart for circulating blood through the body.
The heart relies on the dynamic flow properties of the blood for
its operation, utilizing a unique dual fluid oscillator with a
common diaphragm for providing the pulsing action to a pair of
pumps that have pressure-volume flow relationships that simulate
the natural heart.
Inventors: |
Wortman; Donald E. (Rockville,
MD) |
Family
ID: |
25372124 |
Appl.
No.: |
04/878,484 |
Filed: |
November 20, 1969 |
Current U.S.
Class: |
623/3.13;
623/3.16; 128/DIG.10; 417/350; 137/842; 600/16 |
Current CPC
Class: |
A61M
60/562 (20210101); A61M 60/122 (20210101); A61M
60/869 (20210101); Y10S 128/10 (20130101); A61M
60/50 (20210101); Y10T 137/2273 (20150401); A61M
60/205 (20210101); A61M 60/148 (20210101); A61M
60/268 (20210101) |
Current International
Class: |
A61M
1/10 (20060101); A61f 001/24 () |
Field of
Search: |
;3/1,DIG.2
;128/1,214,DIG.3,DIG.10 ;137/81.5 ;417/350 |
References Cited
[Referenced By]
U.S. Patent Documents
Other References
1 "An Ideal Heart Pump With Hydrodynamic Characteristics Analogous
To The Mammalian Heart" by G. A. Saxton et al., Trans. Amer. Soc.
Artif. Int. Organs, Vol. VI, 1960, pp. 288--291. .
2. "Progress In The Design Of A Centrifugal Cardiac Assist Pump
With Trans-cutaneous Energy Transmission By Magnetic Coupling" by
F. Dorman et al., Trans. Amer. Soc. Artif. Int. Organs, Vol. XV,
1969..
|
Primary Examiner: Gaudet; Richard A.
Assistant Examiner: Frinks; Ronald L.
Claims
I claim as my invention:
1. An artificial heart to act as a circulatory aid for the natural
heart either internally or externally of the body comprising
a. first and second pulsing means for producing first and second
pulsed flows of blood, respectively, each of said pulsing means
comprising
1. an input conduit for receiving a mainstream of blood,
2. a capacitance chamber to store said mainstream of blood until a
certain volume is attained,
3. a control conduit for transmitting the blood from said
capacitance chamber to deflect said mainstream of blood upon the
application of forcing means, said forcing means comprising a
flexible diaphragm located between and physically separating said
capacitance chambers whereby blood is ejected from one of said
capacitance chambers by a force on the diaphragm applied by the
blood that is filling the other of the said capacitance chambers,
said filling and ejecting being a continuous alternating action
whose repetition frequency is dependent upon the rate of flow of
blood through the system, and
4. an output conduit for receiving said mainstream of blood after
its deflection by the blood issuing from said control conduit;
b. first and second pumping means for receiving and pumping said
first and second pulsed flows of blood to the remainder of the
circulatory system, the output volume flow of said first and second
pumping means being directly proportional to the input pressure of
the said first and second pulsed flows of blood and inversely
proportional to the pressure against which they are pumping;
and
c. power means to drive said first and second pumping means at a
continuous and nonvarying speed.
2. The artificial heart of claim 1 wherein said first and second
pumping means each are comprised of a centrifugal pump.
3. The invention according to claim 1 wherein said first and second
pumping means are located at the inlets of said first and second
pulsing means.
Description
RIGHTS OF GOVERNMENT
The invention described herein may be manufactured, used, and
licensed by or for the United States Government for governmental
purposes without the payment to me of any royalty thereon.
BACKGROUND OF THE INVENTION
The present invention relates generally to an artificial heart and
more particularly to an electromechanical system that incorporates
the principles of fluidics to provide a device for use as a
temporary replacement for or as an aid to the heart in circulating
blood throughout the body.
Devices heretofore developed and intended for use as artificial
hearts have fallen far short of their expectations, one reason
being their inherent complexity. Earlier embodiments of artificial
hearts while attempting to simulate as closely as possible the
action of the human heart, were dependent for their operation upon
a multitude of moving parts such as valves, flexible chambers, and
displacement-type pumps, plus sophisticated synchronous control
systems and sensors for either speeding up or slowing down the
pumping action or "heartbeat." Such devices have been found to
require relatively large power supplies and to occupy large volumes
in addition to being prohibitively expensive, thus detracting from
their usefulness as an aid to the natural heart. Additionally, such
devices have not been suited for prolonged service: valves tend to
wear out, leak, lose their efficiency and promote blood clots;
pumps and collapsible chambers tend to exert large compressive
forces upon the blood to the point where the blood would become
damaged; and many other moving parts wear out or become
inefficient.
It is therefore an object of the present invention to provide an
artificial heart that is capable of temporarily replacing or aiding
the natural heart by completely or partially taking over the
operation of pumping blood through the circulatory system.
It is another object of the present invention to provide an
artificial heart that is inherently pressure sensitive and thus
does not require any external regulating mechanism for long term
use.
It is an additional object of the present invention to provide an
artificial heart which will be chemically inert and which will not
destroy or be destroyed by the blood which it pumps.
A further object of the present invention is to provide a greatly
simplified artificial heart that simulates the action of the
natural heart to a high degree and yet is valveless and contains no
collapsible chambers.
A still further object of the present invention is to provide an
artificial heart that is economical to manufacture, has very few
moving parts, and does not damage the blood in operation.
SUMMARY OF THE INVENTION
Briefly, in accordance with this invention, an artificial heart is
provided for use as either a supplement to for the natural heart to
be implanted in the chest of the user or as an external temporary
replacement during surgery or the like. The device of the present
invention is characterized by two interdependent fluid oscillators
and two free-running fluid pumps. The oscillators are separated by
a common flexible diaphragm which allows alternate pulsing to the
two pumps. The pumps are run continuously at a preselected speed
and have pressure-volume flow responses which simulate the natural
heart. The present invention provides great improvement over prior
art in that is simulates the action of the natural heart and yet
has no valves to clog the blood and no collapsible chambers to
squeeze or crush the blood thus minimizing deterioration and wear
of the device itself while allowing more efficient and dependable
operation.
BRIEF DESCRIPTION OF THE DRAWING
The specific nature of the invention as well as other objects,
aspects, uses, and advantages thereof will clearly appear from the
following description and from the accompanying drawing, in
which:
The drawing is a schematic partial cross section illustration of an
artificial heart in accordance with the present invention.
DESCRIPTION OF THE PREFERRED EMBODIMENT
A brief review of the natural heart's pumping action will
facilitate understanding of the efficiency with which the present
invention simulates the actions of the natural heart.
The heart is a muscular organ divided into four chambers. The upper
chamber on each side of the heart is called an auricle and below
each auricle is another chamber called the ventricle. Deoxygenated
blood from the body enters the right auricle of the heart through
two large veins. The blood-filled right auricle then contracts,
sending the blood into the right ventricle through the tricuspid
valve. The right ventricle then contracts, which simultaneously
closes the tricuspid valve and opens the semilunar valve leading to
the lungs via the pulmonary artery. From the lungs, oxygen-enriched
blood flows into the left auricle through the pulmonary vein. The
filled left auricle contracts, forcing blood through the mitral
valve into the left ventricle which in turn will contract and force
the blood through another semilunar valve into the aorta which is
the main artery to the body.
It is evident that an artificial heart built to the above
specifications to operate over an extended period of time would
encounter many mechanical difficulties due to inevitable
deteriorations of its numerous valves, chambers and contraction
apparatus. The present invention, while efficiently aiding the
final result of the natural heart, does not attempt to duplicate
its actions. Rather it employs well-known fluidic principles in a
unique dual fluid oscillator that provides alternate pulsing to a
pair of fluid pumps that respond to pressure input variations as
would the natural heart.
The drawing illustrates the artificial heart of the present
invention, showing a cross-sectional view of a preferred embodiment
of the dual fluidic oscillator and a schematic representation of
the pumps and associated hardware. The dual fluidic oscillator is
comprised of two back-to-back RCR
(resistance-capacitance-resistance) fluid oscillators shown at 10
and 12 and internally separated by a flexible diaphragm 18 which is
made of a suitable nonporous material such as silicone rubber. The
two oscillators 10 and 12 provide a pulsed flow of blood to two
fluid pumps 14 and 16 by way of the conduits 44 and 46,
respectively. The input to oscillators 10 and 12 is received from
conduits 20 and 22, respectively, and proceeds to travel the RCR
flow paths in each oscillator as defined by resistance conduits 28
and 30, capacitance tanks 32 and 34 and resistance conduits 40 and
42, before exiting to pumps 14 and 16 by way of conduits 44 and 46,
respectively. The oscillators 10 and 12 alternately oscillate at a
frequency that varies directly as the flow of blood through the
body varies, When the body is at rest, there exists a low blood
flow and the frequency of oscillation will automatically lower.
When the body is at work and more blood flows in the system, the
oscillation will increase in frequency to pump more blood. In other
words, the operation of the system is based on the dynamic
properties of blood flow. The back-to-back fluid oscillators 10 and
12 each operate much like a standard RCR fluid oscillator but for
the addition of the flexible diaphragm 18 which separates
capacitance chambers 32 and 34 and allows the device a certain
compliance with blood pressure variations and provides the pulsing
action of the artificial heart.
Pumps 14 and 16 have the characteristics that their outputs are
directly related to their input pressure and inversely related to
the pressure head against which they are pumping. The pumps thus
respond to pressure variations at their inlets 44 and 46 and
outlets 24 and 26 in a fashion analogous to the natural heart. One
embodiment of a pump possessing such characteristics that could be
utilized in the present invention is known in the art as a
centrifugal pump. Centrifugal pumps have been shown to pump blood
in a highly efficient and nondestructive manner, as evidenced by
the F. Dorman et al. paper in Vol. XV of The Transactions of the
American Society of Artificial Internal Organs 1969, entitled
"Progress in the Design of a Centrifugal Cardiac Assist Pump with
Trans-cutaneous Energy Transmission by Magnetic Coupling." Pumps 14
and 16 are powered by a motor 48 which drives shafts 52 and 54, and
a power supply 56. Much effort has been directed towards perfecting
implantable motors and power supplies for the uses described
herein, whereas external equivalents are also well known in the
art. The entire heart can be constructed of a material that is
noncorrosive, has nonoccluding surfaces, and does not damage the
blood in any way.
In operation, consider the deoxygenated blood to be entering the
artificial heart from the body through conduit 22 to fill a nearly
empty capacitance tank 34 through resistance conduit 30. The
near-emptiness of capacitance tank 34 implies that capacitance tank
32 of oscillator 10 is nearly full and diaphragm 18 is in position
50. As tank 34 becomes filled with blood, diaphragm 18 moves from
position 50 towards position 51. The increased pressure on
diaphragm 18 from the blood in tank 34 will force the oxygen-rich
blood in nearly full tank 32 to exit through resistance conduit 40
which acts as a control jet for blood subsequently entering conduit
20 from the lungs. The control jet issuing from conduit 40 will
impinge upon the blood entering interaction region 60 and divert it
to conduit 44 which leads to pump 14 which pumps the oxygen-rich
blood out conduit 24 to the body. This action continues until tank
32 is nearly empty and diaphragm 18 is fully in position 51, which
would imply a nearly full supply of deoxygenated blood in tank 34.
Once the diaphragm is in position 51, no force is exerted on the
blood remaining in tank 32 and thus the control jet will cease to
issue from conduit 40. Part of the blood entering along conduit 20
will then reattach to resistance conduit 28 and begin to fill tank
32 once more. As tank 32 fills with blood, diaphragm 18 will move
towards position 50 and exert pressure on the blood in nearly
filled tank 34 forcing the blood to exit through resistance conduit
42 which now acts as a control jet to impinge upon the main stream
of blood entering conduit 22 from the body. The main stream
entering conduit 22 is thus deflected and attaches to conduit 46
which leads to pump 16, which pumps the deoxygenated blood out
conduit 26 to the lungs. Once the blood has been nearly emptied
from tank 34 and diaphragm 18 is in position 50, the control jet
from conduit 42 will slow to a trickle and eventually cease. Part
of the blood subsequently entering conduit 22 will reattach along
conduit 30 and the above cycle will repeat itself. The foregoing
description encompasses one cycle in the operation of the
artificial heart; i.e. one pulse has issued from each oscillator to
each pump. The duration of a single cycle is controlled in part by
the dimensions of the resistance conduits and the capacitance tanks
which can be varied for each patient's needs by the positioning of
the partitions 36 and 38.
During the alternate pulsing of oscillators 10 and 12, pumps 14 and
16 are running continuously and at the same speed. The pumps will
pump only that blood that is present at their inlets. Thus if the
blood pressure increases or decreases and forces the frequency of
oscillation to do likewise, the pumps would automatically adjust to
the change in pulsatile flow.
From the foregoing it is apparent that I have provided a greatly
improved artificial heart capable of assisting the natural heart by
complete implantation within the body or for use as an external
temporary aid to circulation. The device heretofore described is
simple and uncomplicated, relying on the dynamic flow properties of
the blood for its operation. No valves or collapsible chambers are
used, which makes the device less susceptible to wear and tear
while insuring further that the blood remains undamaged. The entire
apparatus can be constructed with a material that is noncorrosive
and easily adaptable to the use intended.
I wish to be understood that I do not desire to be limited to the
exact details of construction shown and described, for obvious
modifications will occur to a person skilled in the art. For
example, the positions of the pumps and oscillators could be
interchanged if greater compliance with the circulating system
could be attained.
* * * * *