U.S. patent number 3,689,204 [Application Number 05/038,353] was granted by the patent office on 1972-09-05 for laminated liquid pump and method of making same.
This patent grant is currently assigned to General Motors Corporation, Detroit, MI. Invention is credited to Bert C. Prisk.
United States Patent |
3,689,204 |
|
September 5, 1972 |
LAMINATED LIQUID PUMP AND METHOD OF MAKING SAME
Abstract
A liquid pump is formed by superposing several sheets of thin
flexible material which may be fused together, for example,
polyvinyl chloride. The flexible sheets form a displacement
chamber, an air pressure operated pumping chamber inlet and outlet
passages and check valve flaps in the passages. The valve flaps are
formed from the flexible sheets by slitting in appropriate places
or are provided by separate flexible sheets. The several sheets are
laminated by applying heat and pressure in a predetermined pattern
to provide the essential pump elements. The pumping air chamber may
be omitted.
Inventors: |
Bert C. Prisk (Grosse Pointe
Woods, MI) |
Assignee: |
General Motors Corporation,
Detroit, MI (N/A)
|
Family
ID: |
21899453 |
Appl.
No.: |
05/038,353 |
Filed: |
May 18, 1970 |
Current U.S.
Class: |
417/394;
417/479 |
Current CPC
Class: |
F04B
43/025 (20130101); F04B 43/06 (20130101); F04B
53/1092 (20130101); F04B 43/0054 (20130101); F04B
43/10 (20130101); A61M 60/148 (20210101); A61M
60/892 (20210101); A61M 60/896 (20210101); A61M
60/268 (20210101); A61M 60/40 (20210101); A61M
60/894 (20210101) |
Current International
Class: |
A61M
1/10 (20060101); F04B 43/06 (20060101); F04B
43/02 (20060101); F04B 53/10 (20060101); F04B
43/10 (20060101); F04B 43/00 (20060101); F04b
043/10 (); F04b 045/00 (); F04b 043/00 () |
Field of
Search: |
;417/394,478,479,480 |
References Cited
[Referenced By]
U.S. Patent Documents
Primary Examiner: Robert M. Walker
Attorney, Agent or Firm: Jean L. Carpenter Paul Fitzpatrick
Warren D. Hill
Claims
The embodiment of the invention described herein is for purposes of
illustration and the scope of the invention is intended to be
limited only by the following claims:
1. A liquid pump operable by pulsed air pressure having a
displacement chamber with walls formed of two flat sheets of
flexible material joined at their sides, inlet and outlet passages
communicating with the displacement chamber and having walls formed
of the same sheets, an inflatable pumping chamber within the
displacement chamber and formed of two flat sheets of flexible
material joined at their periphery, inlet means for supplying air
to the pumping chamber for varying the volume of the displacement
chamber, and inlet and outlet valves in the inlet and outlet
passages respectively, the valves comprising pairs of flexible
flaps each secured to one of the sheets and cooperating to provide
unidirectional fluid flow.
2. A liquid pump operably by pulsed air pressure having a
displacement chamber with walls formed of flat sheets of flexible
material joined at their sides, inlet and outlet passages
communicating with the displacement chamber and having walls formed
of the same sheets, at least a portion of each displacement chamber
wall being double layered to define an air chamber between the two
wall layers, an inlet means for supplying pulsed air pressure to
the air chambers for varying the volume of the displacement
chamber, and inlet and outlet valves in the inlet and outlet
passages respectively, each valve comprising a pair of flexible
flaps each secured to one of the sheets and cooperating to provide
unidirectional fluid flow.
Description
This invention relates to a liquid pump and a method of making the
same. More specifically, the invention relates to a blood pump
suitable for use during open heart surgery or for use in
implantable hearts in animals or humans and a method of making such
a pump from sheet material.
It has previously been proposed to provide extracorporeal blood
pumps for use during heart surgery to bypass the heart and give the
surgeons a dry field free of blood so that they can see what they
are doing. The presently available pumps of this type are
expensive, require an inordinate amount of service before, during
and after the operation and tend to cause serious damage to the
blood. In addition, intrathoracic blood pumps have been proposed to
be used as artificial hearts. However, these designs have been
extremely complex and also have a record of damaging blood. It is
now recognized that the design of a blood pump should include the
following features: (1 ) the pumping action should simulate the
natural heart's action and be hemodynamically accurate, (2 ) the
valve action should allow for free flow and low turbulence in the
open position and should be hydraulically active to match the
pumping action of the chambers, (3 ) the construction materials
should be sterile and non-thrombogenic, (4 ) the fabrication should
be simple and of reasonable cost.
It is therefore an object of this invention to provide a simple
inexpensive hemodynamically accurate blood pump.
Another object of this invention is to provide a liquid pump formed
of laminated flat flexible sheets.
A further object is to provide a method of making a liquid pump by
laminating several flexible sheets.
Yet another object of the invention is to provide a method of
making a liquid pump by slitting the walls of an existing passage
formed of flexible sheets and laminating thereto additional
flexible sheets.
The invention is carried out by securing together thin sheets of a
fusible flexible material to form a displacement chamber, inlet and
outlet passages and check valves in the passages. The invention
further contemplates forming an air pumping chamber within or
adjacent the displacement chamber.
More specifically, the invention is carried out by laminating
several layers of thin flexible sheet material to define a
displacement chamber and air pumping chamber and inlet and outlet
passages and providing slits in certain of the flexible sheets to
provide cooperating flaps to form a check valve in each
passage.
The invention is also carried out by providing a liquid pump having
walls and valves formed of thin flexible sheet-like material
defining displacement, inlet and outlet passages and check valves
in each passage. The invention further contemplates one or more air
pumping chambers adjacent or within the displacement chamber also
formed of thin flexible sheet material.
The above and other advantages will be made more apparent from the
following specification taken in conjunction with the accompanying
drawings wherein like reference numerals refer to like parts and
wherein:
FIG. 1 is a plan view of a liquid pump according to the
invention;
FIG. 2 is an elevational cross-section view of the pump of FIG. 1
taken along lines 2--2 thereof and illustrating an intermediate
step in the formation of the blood pump;
FIG. 3 is a cross-sectional view of the pump of FIG. 1 taken along
lines 2--2 illustrating the pump in its filling mode;
FIG. 4 is a cross-sectional view of the pump of FIG. 1 taken along
lines 2--2 illustrating the pump in its pumping mode;
FIG. 5 is an elevational view of a second embodiment of a liquid
pump;
FIG. 6 is a cross-sectional elevational view of the pump of FIG. 5
taken along lines 6--6;
FIG. 7 is a cross-sectional view of the pump of FIG. 6 taken along
the lines 7--7;
FIG. 8 is a plan view of a third embodiment of a liquid pump
according to the invention;
FIG. 9 is an exploded cross-sectional side view of the pump of FIG.
8 taken along lines 9--9 thereof illustrating an intermediate step
in the process of making it; and,
FIG. 10 is a schematic view of the blood pump of FIG. 8 and an
apparatus for operating the pump.
The fabrication of the preferred embodiment is best explained with
reference to FIGS. 1 and 2. The pump is formed entirely of thin
sheets of non-thrombogenic flexible material such as a medical
grade of polyvinyl chloride. Two sheets 10 of this material,
preferable 0.008 inch thick are laid together and spaced slits 12
and 14 at the desired position of the valves are cut transversely
of the desired pumping channel to the width of the channel. Then
sheets of stop-off material 16 are laid outside the sheets 10
between the slits 12 and 14 and extending at either end through the
slits and finally between the sheets 10 outboard of the slits 12
and 14. The width of the stop-off material 16 conforms to the width
of the desired channel. The stop-off material may be any dielectric
sheet material having a melting point substantially higher than the
material to be laminated. Where polyvinyl chloride is used to form
the pump, Teflon (tetrafluoroethylene) is a suitable stop-off
material. An outer pair of flexible sheets 18 are placed on either
side of the assembly, these sheets being preferably of 0.016 inches
thickness. Another small sheet of stop-off material 20 is placed
somewhere between the slits 12 and 14 and between the sheets 10 and
extends beyond the side of the channel. Then the sheets are
simultaneously laminated according to a predetermined pattern under
heat and pressure sufficient to fuse together the four sheets of
flexible material in the area of that pattern except in those
regions where the sheets are separated by stop-off material.
As shown in FIG. 1 the lamination pattern 22 as defined by a
dielectric embossing die 23 extends fully along either side of the
stop-off material 16 to define the pumping channel. The pattern
further extends transversely of the channel to the left of the
slits 12 and again to the right of the slits 12 to define
semi-elliptical valve flaps 24 adjacent the slits 12. The area
around the slits 14 is laminated in the same pattern to define a
valve flap 26 in each sheet 10 opening in the same direction as the
flaps 24. As best seen in FIGS. 2, 3 and 4, the flaps 24 are fused
together at their upstream end as at 28 whereas the flaps 26 are
each fused at their upstream ends as at 30 to an adjacent sheet 18.
The sheets 10 are fused together along the side of the pumping
channel as well as transversely as at 28 and 32 to form a
completely enclosed air pumping chamber 34 except in the area
defined by the stop-off material 20 which provides an inlet to the
pumping chamber 34. An additional fused area extends from the edge
of the pumping channel adjacent the inlet and forms a finger 36
extending parallel to the pumping chamber to define an air supply
channel 37.
The lamination of the several sheets is preferably carried out by
the well-known method of dielectric embossing using a die 23 or
dies having the shape of the desired pattern 22 as described. By
reason of the stop-off material 16 and 20 selective lamination of
the several sheets is accomplished. After the lamination step the
sheets 16 and 20 of stop-off material are pulled out of the pump.
The completed pump then includes an inlet passage 38, and an outlet
passage 40 containing valve flaps 26 and 24, respectively. The
volume between the valve flaps 24 and 26 and between the sheets 18
exclusive of the pumping chamber 34 comprises a displacement
chamber 42.
In operation, the air supply channel 37 is connected by a tube 44
to a pulsating air source 46 thereby causing the air pumping
chamber 34 to alternately expand and contract. The inlet and outlet
passages 38 and 40 are connected by any suitable means to a blood
circulation system and the pump is primed by filling it with blood.
As the air pumping chamber 34 is deflated, blood is drawn in
through the inlet 38 and through the valve flaps 26 to fill the
displacement chamber 42. Blood flow in the opposite direction from
the outlet passage 40 is prevented by the valve flaps 24 which seat
against the walls of the outlet passage 40. Then when the pumping
chamber 34 is inflated, the valve flaps 26 close together and the
flaps 24 fold together to permit blood flow through the outlet
passage 40. Thus the valve flaps 24 and 26 serve as check valves on
either side of the displacement chamber 42 to permit blood flow in
only one direction as the pumping chamber 34 pulsates.
There are several advantages of the pump as described when used as
an extracorporeal pump during surgery: (1 ) The pumping action is
pulsatile (that is, similar to the normal heart), (2 )
physiologically accurate pressure pulses are applied to the blood,
(3 ) pumping volume and pulse rate can be adjusted to meet the
needs of the body, (4 ) pumping can be synchronized with the bodies
own electrical pulse, (5 ) the priming volume of the pump is small,
(6 ) the pump is completely disposable and sterile so that
extensive servicing before, during and after the operation is not
required as with conventional blood pumps, (7 ) the valve action
allows free flow and low turbulence in the open position and is
hydraulically active to match the pumping action of the chambers,
and (8 ) blood damage is minimal.
Another embodiment of a blood pump having these same advantages is
fabricated as shown in FIGS. 5, 6 and 7. The first step of
fabricating this pump is to laminate two sheets 50 of thin flexible
material which may be thermally fused such as polyvinyl chloride
along straight spaced lines 52 to form a channel 54. Alternatively,
this pump may be formed in a previously formed channel of thin
flexible material such as is found in a commercial blood
oxygenator. The sheets 50 are then slit as at 56 and 58
transversely of the channel 54 to form the free ends of valve flaps
60 and 62. Stop-off material, not shown, is inserted in the channel
between the sheets 50. Then a pair of sheets 64 are laid against
the outer surfaces of the sheets 50 and the assembly is laminated
according to a pattern defined by an embossing die 66 which is very
much like that described for the previous embodiment except that an
outer opening is allowed to form inlets to the pumping chambers as
will appear. In this manner, each sheet 50 is fused to its adjacent
sheet 64 according to the pattern 66 to provide the attachments as
shown at 68 in FIG. 6. Finally, the stop-off material is
removed.
There is thus formed a completely enclosed channel having an inlet
portion 70, an outlet portion 72 and containing the valve flaps 60
and 62 each of which is secured at its upstream end to an outer
sheet 64. A displacement chamber 74 lies between the two pairs of
valve flaps and a pair of separate air pumping chambers 76 are
formed on either side of the displacement chamber 74 and confined
between sheets 50 and 64. Each air pumping chamber 76 is connected
with an air inlet channel 78 adapted to be connected to a pulsating
air source. The cross-sectional view of FIG. 7 illustrates the
pumping chamber 74 bounded on either side by an air pumping chamber
76 which is connected to the inlet channels 78, all formed from the
initially flat sheets 50 and 64. In operation, as the pumping
chambers 76 are inflated and deflated, the displacement chamber 74
is compressed and expanded respectively. Since the valve flaps 60
and 62 and cooperate to form check valves operable to permit flow
in the same direction, pumping is effected much as in the
embodiment of FIGS. 1 -4.
FIGS. 8, 9 and 10 illustrate a further embodiment of the invention
which is formed without an attached air pumping chamber but which
is particularly well-suited for use as an intrathoracic blood pump
80 or artificial heart ventricle. This pump 80 is preferably formed
of a medical grade of silicone rubber since its non-thromobogenic
qualities are superior to those of polyvinyl chloride and therefore
better suited to long term use. The silicon rubber sheets used for
fabrication are initially non-vulcanized and thus may be fused
together upon application of heat. The pump 80 comprises a pair of
outer sheets 82 of silicone rubber 0.030 inches thick reinforced
with dacron. A sheet of stop-off material 84, preferably aluminum
foil 0.001 inches thick, is inserted between the rubber sheets 82.
This stop-off material 84 is generally circular in shape with a
pair of upwardly extending neck portions 86 which extend at least
to the upper edge of the rubber sheets 82. Adjacent each neck
portion 86 are small rectangular flaps 88 of silicone rubber 0.01
inches thick which are placed on either side of the stop-off
material 84 and are of sufficient width to extend beyond the sides
of the neck portion 86. Additional sheets of aluminum stop-off
material 90 are placed partially between the flaps 88 and the
sheets 82. The stop-off material 90 is elliptically shaped along
its lower edge which is spaced above the lower edge of the flaps 88
in the case of the outlet valve which is depicted in FIG. 9. The
inlet valve is the same as the outlet valve but is inserted so that
the flap 88 and the stop-off material 90 for the outlet valve are
somewhat differently placed than for the inlet valve. To laminate
the pump the sandwich of material is heated under sufficient
pressure to hold the sheets together until the rubber sheets, to
the extent they are not separated by the stop-off material, are
fused or vulcanized together. Then the aluminum foil stop-off
material is dissolved by hydrochloric acid.
Thus there is formed a generally circular displacement chamber 92
between the sheets 82, and inlet and outlet passages 94 each
containing a pair of flaps 88 defining a check valve. As indicated
schematically in FIG. 9 at 96 at least the lower portion of the
flaps 88 of the outlet valve will be secured to its adjacent wall
82 while the upper ends of the flaps will be free to open or close
according to the hydraulic action of the displacement chamber 84.
In the case of the inlet valve in the left passage 94 of FIG. 8,
the free end of the flaps 88 will be the lower ends.
In operation, external pulsing must be applied to alternately
compress and relieve the displacement chamber 92 to effect pumping.
FIG. 10 diagrammatically illustrates a device for actuating the
pump 80. This device includes a bracket 100 having a reaction plate
102 on one side of the pump 80 and a pressure plate 104 on the
other side of the portion 80, the pressure plate being reciprocally
driven by an electromagnetic motor or solenoid 106. The solenoid
106 is electrically connected to a pulsating electrical power
supply 108. This arrangement is intended to be merely suggestive of
one means for actuating the pump 80. Where it is desired to
simulate a natural heart, two pumps 80 may be used to represent the
two heart ventricles. The two pumps 80 would be juxtaposed for
simultaneous operation by a pressure actuator and if desired, may
share a common wall so that only three sheets 82 and four pairs of
valve flaps 88 would be required.
* * * * *