U.S. patent number 3,791,769 [Application Number 05/043,519] was granted by the patent office on 1974-02-12 for magnetic heart pump.
Invention is credited to Stephen G. Kovacs.
United States Patent |
3,791,769 |
Kovacs |
February 12, 1974 |
MAGNETIC HEART PUMP
Abstract
A magnetically driven heart pump wherein relative movement
between opposing magnetic fields induce pump piston motion, which
simulates the pulsatile pumping action of a natural heart. The
heart pump has two separate parts. The first part comprises the
pumping and valve chambers, and is adapted to be imbedded within
the chest cavity. The second part, adapted to be strapped to the
exterior of the chest wall, carries the magnet and mechanical
linkage. The motion of the exterior magnet induces pump piston
motion within the pumping chamber.
Inventors: |
Kovacs; Stephen G. (Clearwater
Beach, FL) |
Family
ID: |
21927567 |
Appl.
No.: |
05/043,519 |
Filed: |
June 4, 1970 |
Current U.S.
Class: |
417/417; 623/3.1;
417/413.1 |
Current CPC
Class: |
A61M
60/40 (20210101); F04B 53/1022 (20130101); F04B
17/042 (20130101); A61M 60/258 (20210101); A61M
60/122 (20210101); A61M 60/894 (20210101) |
Current International
Class: |
A61M
1/10 (20060101); F04B 17/03 (20060101); F04B
53/10 (20060101); F04B 17/04 (20060101); A61M
1/12 (20060101); F04b 017/04 () |
Field of
Search: |
;3/1,DIG.2 ;310/80,103
;417/410,413,415-417,470 |
References Cited
[Referenced By]
U.S. Patent Documents
Primary Examiner: Husar; C. J.
Attorney, Agent or Firm: Stein, Orman & Fisher
Claims
What is claimed is:
1. A device for pumping fluids comprising a pumping chamber having
a magnetically responsive first piston disposed therein, said first
piston having a first and second position, a first pressure
responsive free floating shuttle valve having a first and second
position, said first pressure responsive free floating shuttle
valve communicating with said chamber such that when the ambient is
greater that the internal pressure of said pumping chamber said
first shuttle valve is in first position allowing fluid to flow
into said chamber and when said internal pressure is greater than
said ambient pressure said first pressure responsive free floating
shuttle valve is in said second position to seal said pumping
chamber, a second pressure responsive free floating shuttle valve
with said chamber, said second pressure responsive free floating
shuttle valve having a first and second position, said second
pressure shuttle valve being in said first position when the
ambient pressure is greater than the internal pressure of said
pumping chamber to seal said chamber and in said second position
when the ambient pressure is less than the internal pressure of
said pumping chamber to allow fluid to flow from said chamber,
means to generate a magnetic field, said magnetic field generating
means arranged relative to said first piston to generate a variable
magnetic field thereon, said magnetic field generator means and
said first piston being mechanically free to move said first piston
from said first position to said second position to generate a
pressure change within said pumping chamber, piston return means to
return said piston to said first position to cause said pressure
within said pumping chamber to vary first above and then below said
ambient pressure whereby fluid within said pumping chamber is
caused to flow respectively out of and into said pumping chamber
through said first and second valves to substantially exhaust fluid
from said chamber, said axis of translation of said first piston,
first pressure responsive free floating shuttle valve and said
second pressure responsive free floating shuttle valve being
parallel.
2. The device of claim 1 wherein variable magnetic field means
comprises a magnet external to said pumping chamber, mechanical
reciprocating means adapted to move said second magnet
alternatively from a remote to a proximate and return to a remote
location from said magnetically responsive first piston.
3. The device of claim 2 wherein said mechanical reciprocating
means comprise a cam rotating means to rotate a cam, a cam riser
arm attached to one end of a pivoted throw arm and pivotally
connected at the distal end to said magnet, said mechanical
reciprocating means operatively secured to frame means which are
adapted to be portably secured to the chest of the user.
4. The device of claim 1 wherein said piston return means comprise
a non-reactive spring.
5. The device of claim 2 wherein said magnetically responsive
piston is axially aligned and coextensive with said magnet.
6. The device of claim 5 wherein said magnetically responsive
piston is a permanent magnet.
7. The device of claim 1 wherein said pump chamber and valves are
constructed of lightweight, durable, non-reactive plastic material.
Description
This invention relates generally to magnetically operated pumps and
in particular to a magnetic pump for use within the chest to
simulate the rhythmic contractions of a natural heart.
In medicine today there has been much effort put toward the
development of various artificial body organs. Of all parts of the
human body, none is so simple yet so complicated as the human
heart. There are many problems inherent in the fabrication of a
mechanical heart that must be solved. For instance, the heart pump
must be lightweight, it must be of simple, rugged, dependable
construction so that the chances of breakdown or failure are
reduced to an absolute minimum. It must be relatively inexpensive
to manufacture. It must be capable of simulating the action of a
natural heart, that is, it must not damage the blood cells during
the pumping cycle while at the same time the pulsatile action of
the natural heart must be duplicated. These and other similar
problems have kept scientists and engineers from developing a
successful, practical, reliable heart pump.
It is therefore an object of this invention to provide a heart pump
which will duplicate both the pulsatile pumping action of the
natural heart together with the associated blood pressure ranges
generated in the arterial system.
Another object of this invention is to provide a heart pumping
chamber wherein damage to blood cells is kept at a minimum due to
the fact that the pumping rates correspond to normal heart
rates.
Still another object of this invention is to provide a heart pump
capable of being manually operated in the event of actuator power
failure.
A further object is to provide a pump chamber having a per beat
volume which corresponds to the average volume of blood pumped by
the human heart.
A still further object is to provide a heart pump in which the
chances of clotting within the pumping chamber are decreased.
Another object is to provide a heart pump which has a failsafe
system.
Another object is to provide a portable heart pump which is easily
strapped to the chest of the user.
Another object is to provide a heart pump of simplified
construction utilizing a minimum number of moving parts.
Another object is to provide a heart pump in which a portion of the
pump is permanently imbedded within the chest cavity of the
user.
Another object is to provide a heart pump wherein a movement of one
magnetic field induces a corresponding movement in a second
magnetic field.
Another object is to provide a pump piston which will translate in
response to varying magnetic field strength.
Another object is to provide a flow check valve for use as a
replacement for a defective natural heart valve.
Another object is to provide a flow check valve which will maintain
constant coaxial alignment regardless of relative rotational
movement.
Another object is to provide a flow check valve which permits
symmetrical flow through a valve chamber.
Another ojbect is to provide a resilient face seal which insures
uniform valve seat sealing despite surface variations on the valve
seat.
Another object is to provide a flow check valve with greater flow
rate capacity than a ball check valve having the same valve port
opening and chamber diameter.
Another object is to provide flow check valve housing guide struts
which are radially extending and insure coaxial alignment of the
valve plate with the valve seat.
Another object is to provide a flow check valve which allows
symmetrical blood flow through the chamber thereby reducing
clotting tendencies.
Another object is to provide a heart pump which is capable of
pumping rates ranging from 60 to 80 cycles per minute.
Another object is to provide a heart pump, the pulsatile action of
which is caused by an external linear reciprocating cam driven
magnetic actuator.
Another object is to provide a heart pump wherein reciprocating
motion is imparted by induction to the pump piston in the pump
chamber.
Another object is to provide a heart pump capable of producing a
rhythmic pressure gradient corresponding to the natural heart's
diastolic to systolic blood pressure range.
Other objects of the invention will in part be obvious and will in
part appear hereinafter.
The above and other objects not specifically enumerated are
efficiently obtained by providing a heart pump which duplicates
both the pulsatile pumping action of the natural heart, and the
associated blood pressure ranges generated in the arterial system.
This is accomplished by the use of high-permeability magnets. The
magnets are arranged co-axially in a pair of chambers such that
their fields tend to oppose and repel each other. The external,
actuator magnetic is cam driven by a mechanical linkage to produce
a linear reciprocating motion roughly corresponding to a normal
pulse rate. The reciprocating motion of the actuator magnetic
induces a like motion in the piston magnet located within the pump
chamber. The cyclic motion of the actuator produces the rhythmic
piston pumping action which is adjusted to have a pressure gradient
corresponding to the natural heart's diastolic-systolic blood
pressure range.
The pump-chamber is located within the patient's chest cavity while
the external actuator is located on the outside directly over the
imbedded pump chamber. At the distal end of the pump is located a
plurality of flow check valves which are adapted to be attached to
the left atrium and the aorta in order to control blood flow during
the pumping stages.
The invention accordingly comprises the features of construction,
combination of elements, and arrangement of parts which will be
exemplified in the construction hereinafter set forth, and the
scope of the invention will be indicated in the claims.
For a fuller understanding of the nature and objects of the
invention, reference should be had to the following detailed
description taken in connection with the accompanying drawings in
which:
FIG. 1 is a cross-section view of the magnetically driven pump of
the present invention.
FIG. 2 is a front view of the heart pump showing the external
actuator, cam throw arm and cam torque unit.
FIG. 3 is a cross-section view of a flow check valve.
FIG. 4 is a front view of the valve plate chamber guide struts for
the flow check valve.
Similar reference characters refer to similar parts throughout the
several views of the drawing.
Referring now to FIG. 1, heart pump 10 of the present invention is
generally shown to consist of two separate units, the internal pump
chamber 12 and the external actuator 14. The internal pump chamber
12 is adapted to be placed within the thoracic cavity and secured
to the rib cage while external actuator 14 is located on the
outside of the body directly over and proximate with internal pump
chamber 12 and is adapted to be strapped to the patient. External
actuator 14 has a circular disc magnet 16 made of a high
permeability substance such as Alnico I, Alconax II, Genoflux II or
any other like substance. Magnet 16 is adapted to reciprocate in
the direction indicated in the arrows of FIG. 1, between the
positions shown by magnet 16 and 16a, in response to the movement
of cam operated throw arm 18. A schematic of this mechanical
movement is illustrated in FIG. 1 wherein cam shaft 20, cam riser
arm 22 and throw arm 18 are shown operatively connected to disc
magnet 16 by pivot axis 24 and pivot pin 26. The opposite extreme
of the mechanical movement is illustrated by the phantoms, cam
shaft 20a, cam riser arm 22a, throw arm 18a, cam 20a, and disc
magnet 16a.
Referring now to FIG. 2, a front view of heart pump 10 is shown.
Here, external actuator 14 is shown supported upon mounting plate
28. Plate 28 is shaped to fit the chest of the wearer and can be
made of a light plastic such as nylon, lexan or some other suitable
material. The surface of mounting plate 28 in contact with the skin
29 may also be lined with a foam strip or other material to reduce
contact discomfort. Mounting plate 28 is attached to the body by
any conventional means such as body harness straps (not shown)
which are attached to mounting plate 28 through slots 30.
Circular disc magnet 16 has a centrally located aperture 32 which
is adapted to receive disc guide rod 34 attached to mounting plate
28. Guide rod 34 keeps disc magnet 16 aligned during its
reciprocating movement to and from internal pump chamber 12. Pivot
pins 26 radially extend from disc magnet 16 and are received by
yokes 36 of throw arm 18. Throw arm 18 is here shown to be
generally Y-shaped and made of a rigid, lightweight material and
pivotally attached at 38 to pivot axis 24 which is in turn fixedly
attached to mounting plate 28 by suitable fastening means such as
screws, clamps and the like. Cam riser arm 22 is attached to the
end of throw arm 18 so as to contact with and follow cam 20 as it
is rotated by a conventional power source 40, such as a cam torque
unit. Power source 40 shown here is a small DC gear head motor,
either linear or rotary conversion, which is powered by a portable
power pack 41. However, the specific power source is not critical
and any motive means of this generalized type may be used. In
addition, in the event of a power failure, a cam riser arm
extension 42 is provided so that the user can maintain the pumping
action by manually depressing the cam riser arm at a normal pumping
rate until the unit can be repaired. The entire external actuator
assembly 14 is designed to be covered by a snap-on high impact
molded, plastic cover (not shown) or similar covering in order that
the unit be protected from damage by impact.
Referring again to FIG. 1, internal pump chamber 12 of heart pump
10 consists of pump chamber 44 within which is located a second
circular disc magnet 46 and a return spring 48, together with check
valves 50 and 52 to control in flow and out flow from pump chamber
44. Pump chamber 44 is adapted to be fixedly attached within the
thoracic cavity by suitable fastening means such as plastic coated
wire (not shown) to the ribs of the wearer. Internal pump chamber
12 could be made of materials such as tantalum, molded lexan,
nylon, dacron, vitailium, stainless steel (teflon lined) or other
durable, non-reactive substance. This magnet 46 is generally of the
same design as magnet 16 and is similarly made of a material such
as Alnico V, Alconax II, Genoflux II or any similar material which
has a high permeability. Magnet 46 also has a centrally located
aperture which receives a second disc guide rod 56. This guide rod
56 is molded integrally with or fixedly attached to walls 58 and 60
of pump chamber 44 and serves to guide disc 46 during its
reciprocating motion. Located between disc magnet 46 and front wall
58 is a return spring 48 which is designed to urge disc magnet 46
against rear wall 60 of pumping chamber 44, as illustrated by the
solid lines in FIG. 1. Return spring 48 can be made of any suitable
substance such as tantalum or a tempered teflon coated, stainless
steel. The spring is designed for telescopic compression such that
on full compression, the spring length equals the thickness of the
spring wire.
Located in front wall 58 of pumping chamber 44 are apertures 62
into which check valves 50 and 52 are threadably engaged. These
check valves serve to control blood flow to and from chamber 44.
Referring now to FIG. 3, it is noted that check valve 50 is
constructed from two sections, 64 and 66, which may be made of a
molded plastic such as lexan, nylon, or dacron. The periphery of
section 66 is circular and adapted to be placed within section 64
and sealed by a molecular solvent so as to form a cohesive, leak
proof bond between the outer wall 68 of section 66 and the interior
wall 70 of section 64. Section 64 is provided with threads 72 which
are adapted to engage and provide a leak proof seal between check
valve 50 and aperture 62 of front wall 58. The distal end of check
valve 50 is provided with a radially extending annular suture ring
74 to aid in graft attachment of the valve to living tissue. Within
valve 50 is floating valve plate 76 which consists of a molded
plastic disc 78 having three radially extending guide struts 80
which are integrally molded at a 120.degree. radial spacing about
the periphery of disc 78. Floating valve plate 76 is free to move
transversely within valve chamber 70 in response to a pressure
differential within valve 50. As indicated by the arrows of FIG. 3,
the leftward movement of floating valve plate 76 is checked by an
inwardly extending annular ring 82 molded to the interior wall 70
of section 64 and the rightward movement of floating valve plate 76
is checked by internally extending annular ring 84 molded to
section 66.
The face 86 of plastic disc 78 may be provided with a resilient,
contour forming substance so as to provide a uniform seal on the
valve seat portion of the valve port opening 88 formed by annular
ring 84, despite wearing of the valve seat.
Check valve 52 is of similar construction as check valve 50 except
that the relative positions of the elements are reversed so as to
check the flow of blood in the opposite direction.
The natural heart pumps blood by means of rhythmic contractions,
this type of pump action is generally called pulsatile since the
pumping pressure varies from diastolic to systolic. Diastolic
pressure is the pressure in the arterial system during the relaxed
heart condition, that is, during which period the left ventricle
chamber is filling with blood from the left atrium chamber. The
systolic pressure is the pressure generated in the arterial system
during the contracted heart conditions, that is, during the period
when the heart's left ventricle chamber pumps blood into the
arterial system via the aorta. This rhythmic variation of pumping
pressure, from diastolic to systolic and vice versa, produces the
pulsatile blood flow characteristic of the heart's pumping action.
The description of operation of heart pump 10, infra, shall begin
at the end of the diastolic pumping cycle. At this period of the
pumping cycle, pump chamber 44 is full of oxygenated blood received
from the natural heart's left atrium chamber via check valve 50.
Check valve 52, which is fully closed due to the diastolic pressure
of the blood in the aorta, controls the flow of blood from pump
chamber 44 to the aorta of the body's arterial system. At this
time, circular disc magnets 16 and 46 are in the solid line
positions as shown in FIG. 1, as are throw arm 18, cam riser arm 22
and cam 20.
The systolic pumping cycle proceeds then as follows: Cam shaft 20
rotates from the initial solid line position toward its dotted line
position, 20a. The downward urging of cam riser arm 22 pivots throw
arm 18 about pivot axis 24 in a clockwise direction, hence urging
actuator magnet 16 toward its dotted line position 16a. As magnet
16 moves to the right along guide rod 34, the magnetic polarity
configuration shown causes magnet 46, located within pumping
chamber 44, to be urged to the right also. The field strength of
magnet 16 is sufficiently high to overcome return spring 48 and
magnet 46 proceeds to its dotted line position 46a. As the pressure
within pump chamber 44 becomes greater than the diastolic pressure
within the aorta, check valve 52 opens and blood flows into the
arterial system. Simultaneously, floating valve plate 76 of check
valve 50 is seated against annular ring valve seat 84. As the
volume of blood within chamber 44 decreases, the velocity of magnet
46 increases, then decreases. This is due to a lessening of
pressure in the aorta together with the inertia of magnet 46, blood
flow, and the increasing spring force. This naturally occurring
velocity gradient in the motion of magnet 46 produces a pumping
pressure gradient corresponding to the blood pressure gradient
defined by the natural diastolic-systolic range. When cam 20 and
throw arm 18 has advanced their respective dotted line positions,
20a and 18a, the systolic pumping cycle is completed and the
configuration of the moving elements will all be in their dotted
line position as shown in FIG. 1. At this time, the diastolic
pumping cycle begins and all elements begin the movement back to
the solid line position. This return motion of magnet 16 permits
magnet 46 to return to its initial starting position by virtue of
the restoring force provided by return spring 48. As magnet 46
begins to return toward rear wall 60 of pumping chamber 44, check
valve 50 opens and check valve 52 closes since relative internal
pressure is now that of the diastolic cycle and oxygenated blood
from the left atrium is beginning to fill pump chamber 44. Also,
the velocity gradient decreases as magnet 46 approaches its initial
start position due to the continuous decrease in restoration force
resulting from the continued relaxation of return spring 48. This
continued reduction in velocity gradient results in a pumping
pressure gradient corresponding to the systolic-diastolic blood
pressure transition of the natural heart. Therefore, when cam 20
and throw arm 18 have returned to the solid line position, the
diastolic pumping cycle is complete and the system is ready to
commence another systolic pumping cycle as is described above.
While check valves 50 and 52 have been described herein as used in
combination with the magnetic heart pump 10, it is within the
contemplation of this invention that these check valves also be
used separately as replacements for defective natural heart valve
such as the aortic, mitral, tricuspid and pulmonary valves
independent of and separately from the above described heart pump
10. Valve 50 may be adapted for use in any system wherein a
pulsating pressure gradient exists across floating valve plate 76.
The flow associated with the pressure gradient will move valve
plate 76 in the direction of decreasing pressure and the maximum
displacement of the valve plate 76 will be determined by the
location of annular ring 82 relative to the annular ring 84. As
illustrated by the solid and dotted line position, shown in FIG. 3,
the valve plate guide strut 80 serves to maintain constant axial
alignment with valve port opening 88 regardless of any axial
rotation that may occur. Also, struts 80 and disc 78 permit
symmetrical blood flow through the valve chamber thereby reducing
the probability of blood clot formation tendency due to uneven flow
rates as may occur in ball valve structures. In addition, resilient
seat 86 is provided in order that a uniform seal is present despite
possible surface variations which may occur in the valve seat
during use.
It is also within the contemplation of this invention that
electro-magnets be used in place of magnet 16 and 46 or that a
combination of permanent magnets and electro-magnets be used.
It is further within the contemplation of this invention that the
above described pumping unit be used outside the body of the
patient thereby utilizing only connecting tubes to transmit the
pumped blood.
It will thus be seen that the objects set forth above, among those
made apparent from the preceding description, are efficiently
attained and, since certain changes may be made in the above
construction without departing from the scope of the invention, it
is intended that all matter contained in the above description or
shown in the accompanying drawings shall be interpreted as
illustrative and not in a limiting sense.
It is also to be understood that the following claims are intended
to cover all of the generic and specific features of the invention
herein described, and all statements of the scope of the invention,
which, as a matter of language, might be said to fall
therebetween.
Now that the invention has been described:
* * * * *