U.S. patent number 3,885,251 [Application Number 05/338,093] was granted by the patent office on 1975-05-27 for artificial heart pump or assist.
This patent grant is currently assigned to North American Philips Corporation. Invention is credited to Raul Ismael Pedroso.
United States Patent |
3,885,251 |
Pedroso |
May 27, 1975 |
Artificial heart pump or assist
Abstract
An implantable artificial heart pump or heart assist for
providing or enhancing a controlled cyclic blood flow through an
artery, the pump including a tubular section secured between
adjacent ends of a severed artery forming a continuous blood flow
passage, and having a plurality of axially spaced but adjacent
sleeves encircling this section. The sleeves are sequentially
constricted about the tubular section to provide alternately
pumping and suction upon the blood flowing through the section, the
sleeves being energized by high and low pressure working fluid from
an external or implantable power source. Where the power source is
an implantable Stirling engine, pressure variations are available
from the gas working space, or from an oil pump in the crankcase,
or from a compressor driven by the engine.
Inventors: |
Pedroso; Raul Ismael (Ossining,
NY) |
Assignee: |
North American Philips
Corporation (New York, NY)
|
Family
ID: |
23323382 |
Appl.
No.: |
05/338,093 |
Filed: |
March 5, 1973 |
Current U.S.
Class: |
623/3.17;
128/899; 417/394; 417/479 |
Current CPC
Class: |
F02G
1/043 (20130101); F04B 43/113 (20130101); A61M
60/40 (20210101); F02G 2280/005 (20130101); A61M
60/284 (20210101); A61M 60/122 (20210101) |
Current International
Class: |
A61M
1/10 (20060101); F04B 43/00 (20060101); F04B
43/113 (20060101); F02G 1/00 (20060101); F02G
1/043 (20060101); A61M 1/12 (20060101); A61f
001/24 () |
Field of
Search: |
;3/1,DIG.2
;128/1D,DIG.3,214R,346 ;417/383,394,479 |
References Cited
[Referenced By]
U.S. Patent Documents
Primary Examiner: Frinks; Ronald L.
Attorney, Agent or Firm: Trifari; Frank R.
Claims
What is claimed is:
1. An implantable heart pump for pumping and controlling the flow
of blood through an artery which is severable to expose two
adjacent ends to accommodate the pump therebetween, this pump being
operable with first and second sources of high and low pressure
fluid respectively, the pump comprising a tube securable between
said severed ends of said artery to form a continuous blood flow
passage, at least two sleeves each having a generally cylindrical
bore at least partially surrounding and contacting said tube, the
sleeves being axially spaced apart but adjacent to each other, a
core element formed as a rod fixedly positioned generally centrally
within the bore of said tube and adjacent the inner surface
thereof, the tube having a bore diameter that is variable between
large and small, each sleeve being responsive to a pressure change
whereby its diameter is variable between large and small
corresponding to said tube bore diameters, and valve means for
communicating selectively said high and low pressure sources to
said sleeves, whereby each sleeve periodically has
a. a small diameter for constricting the tube to have a small bore
diameter at the area of the tube adjacent said sleeve, and
b. a large diameter permitting a corresponding large bore diameter
of said tube with the tubes inner surface at that area being urged
closely against said core to prevent blood flow in that area, the
valve providing a predetermined sequence of constrictions and
expansions of the sleeves and therefor of the tube to produce a
pumping action in one direction on the blood flow therein, said
apparatus further comprising an implantable Stirling engine
including a heat source for operating the engine, the engine having
a working space wherein working gas experiences a cyclic pressure
variation between high and low, the apparatus further comprising
duct means communicating said high and low pressure gas to said
valve means.
2. An implantable heart pump for pumping and controlling the flow
of blood through an artery which is severable to expose two
adjacent ends to accomodate the pump therebetween, this pump being
operable with first and second sources of high and low pressure
fluid respectively, the pump comprising a tube securable between
said severed ends of said artery to form a continuous blood flow
passage, at least two sleeves each at least partially surrounding
said tube, the sleeves being axially spaced apart but adjacent to
each other, the tube having a bore diameter that is variable
between large and small, each sleeve being responsive to a pressure
change whereby its diameter is variable between large and small
corresponding to said tube bore diameters, valve means for
communicating selectively said high and low pressure sources to
said sleeves, whereby each sleeve periodically has a small diameter
for constricting the tube to have a small bore diameter adjacent
said sleeve, and a large diameter permitting a corresponding large
bore diameter of said tube, the valve providing a predetermined
sequence of constrictions and expansions of the sleeves and
therefore of the tube to produce a pumping action in one direction
on the blood flow therein, the pump further comprising an
implantable Stirling engine including a heat source for operating
the engine and a lubricating oil pump in the crankcase of the
engine for providing oil under pressure, with crankcase interior
being at a pressure lower than said oil pump pressure, the
apparatus further comprising means communicating a portion of said
oil under pressure to said valve means as said source of high
pressure fluid, and means communicating the crankcase interior to
said valve means as said source of low pressure fluid.
3. An implantable heart pump for pumping and controlling the flow
of blood through an artery which is severable to expose two
adjacent ends to accommodate the pump therebetween, this pump being
operable with first and second sources of high and low pressure
fluid respectively, the pump comprising an implantable Stirling
engine including a heat source for operating the engine and a
mechanical power output of the engine a compressor driven by said
power output, the compressor having a high pressure output port and
a low pressure inlet port which constitute said high and low
pressure sources of fluid, duct means communicating said ports to a
valve means, and corresponding high and low pressure buffer
chambers respectively intermediate said valve and said ports, a
tube securable between said severed ends of said artery to form a
continuous blood flow passage, at least two sleeves each at least
partially surrounding said tube, the sleeves being axially spaced
apart but adjacent to each other, the tube having a bore diameter
that is variable between large and small, each sleeve being
responsive to a pressure change whereby its diameter is variable
between large and small corresponding to said tube bore diameters,
said valve means for communicating selectively said high and low
pressure sources to said sleeves, whereby each sleeve periodically
has
a. a small diameter for constricting the tube to have a small bore
diameter adjacent said sleeve, and
b. a large diameter permitting a corresponding large bore diameter
of said tube, the valve providing a predetermined sequence of
constrictions and expansions of the sleeves and therefor of the
tube to produce a pumping action in one direction on the blood flow
therein.
4. An implantable heart pump for pumping and controlling the flow
of blood through an artery which is severable to expose two
adjacent ends to accommodate the pump therebetween, this pump being
operable with first and second sources of high and low pressure
fluid respectively, the pump comprising a tube securable between
said severed ends of said artery to form a continuous blood flow
passage, at least two sleeves each at least partially surrounding
said tube, the sleeves being axially spaced apart but adjacent to
each other, the tube having a bore diameter that is variable
between large and small, each sleeve being responsive to a pressure
change whereby its diameter is variable between large and small
corresponding to said tube bore diameters, valve means for
communicating selectively said high and low pressure sources to
said sleeves, and wherein each sleeve comprises a tubular element
defining a ringshaped hollow chamber with only one inlet-outlet
port, each ring having a normal small diameter that is expandable
to a large diameter when high pressure fluid is communicated to
said inlet-outlet port, each ring having resilience to return to
its normal small diameter when in communication with low pressure
fluid whereby each sleeve periodically has a small diameter for
constricting the tube to have a small bore diameter adjacent said
sleeve, and a large diameter permitting a corresponding large bore
diameter of said tube, the valve providing a predetermined sequence
of constrictions and expansions of the sleeves and therefor of the
tube to produce a pumping action in one direction on the blood flow
therein.
5. An implantable heart pump for pumping and controlling the flow
of blood through an artery which is severable to expose two
adjacent ends to accommodate the pump therebetween, this pump being
operable with first and second sources of high and low pressure
fluid respectively, the pump comprising a tube securable between
said severed ends of said artery to form a continuous blood flow
passage, a core element formed as a rod fixedly positioned
generally centrally within the bore of said tube and adjacent the
inner surface thereof, at least two sleeves each at least partially
surrounding said tube, the sleeves being axially spaced apart but
adjacent to each other, the tube having a bore diameter that is
variable between large and small, each sleeve being responsive to a
pressure change whereby its diameter is variable between large and
small corresponding to said tube bore diameter, valve means for
communicating selectively said high and low pressure sources to
said sleeves, the pump further comprising an implantable Stirling
engine including a heat source for operating the engine, the engine
having a working space wherein working gas experiences a cyclic
pressure variation between high and low, the apparatus further
comprising duct means communicating said high and low pressure gas
to said valve means whereby each sleeve periodically has a small
diameter for constricting the tube to have a small bore diameter
adjacent said sleeve, and a large diameter permitting a
corresponding large bore diameter of said tube, and constriction of
each sleeve constricts the adjacent part of said tube, with the
inner surface of said part urged closely against said core to
prevent blood flow past said part, the valve providing a
predetermined sequence of constrictions and expansions of the
sleeves and therefor of the tube to produce a pumping action in one
direction on the blood flow therein.
6. Apparatus according to claim 5 wherein said sleeves define an
axial length between them and said core has length approximately
equal to said axial length, the apparatus further comprising web
means for fixedly positioning each end of said core relative to
said tube.
7. A heart pump for attachment between the severed ends of a
severed artery, comprising an implantable Stirling engine including
a fluid therein that is cyclically under high and low pressure, a
tube securable between said severed ends to form a continuous blood
flow path, three sleeves axially spaced and having generally
cylindrical bores positioned about and in contact with said tube, a
core element formed as a rod fixedly positioned generally centrally
within the bore of said tube and adjacent the inner surface
thereof, valve means for cyclically and sequentially communicating
said high and low pressure fluid to said sleeves, a buffer tank
between said valve and each of said high and low pressure sources,
means interconnecting said engine and said valve for cyclically
controlling said valve according to the operation cycle of the
engine, said sleeves designated first, second and third moving
downstream of the flow, each having its diameter reduced when said
high pressure is communicated thereto and expanded when said low
pressure is communicated thereto and the tube in the areas
surrounded by the sleeves having corresponding diameter
constrictions and expansions with the tubes inner surface at each
of said areas being urged closely against said core to prevent
blood flow in said areas respectively, whereby the tube diameter
adjacent the sleeves is as follows:
8. An implantable heart pump for pumping and controlling the flow
of blood through an artery which is severable to expose two
adjacent ends to accommodate the pump therebetween, this pump being
operable with first and second sources of high and low pressure
fluid respectively, the pump comprising a tube securable between
said severed ends of said artery to form a continuous blood flow
passage, at least two sleeves each having a generally cylindrical
bore at least partially surrounding and contacting said tube, the
sleeves being axially spaced apart but adjacent to each other, a
core element formed as a rod fixedly positioned generally centrally
within the bore of said tube and adjacent the inner surface
thereof, the tube having a bore diameter that is variable between
large and small, each sleeve being responsive to a pressure change
whereby its diameter is variable between large and small
corresponding to said tube bore diameters, and valve means for
communicating selectively said high and low pressure sources to
said sleeves, whereby each sleeve periodically has
a. a small diameter for constricting the tube to have a small bore
diameter at the area of the tube adjacent said sleeve with the
tubes's inner surface at the area being urged closely against said
core to prevent blood flow in that area, and
b. a large diameter permitting a corresponding large bore diameter
of said tube, and thereby permitting blood flow, the valve
providing a predetermined sequence of constrictions and expansions
of the sleeves and therefor of the tube to produce a pumping action
in one direction on the blood flow therein.
Description
BACKGROUND OF THE INVENTION
Existing artifical heart pumps generally comprise substitute or
assist mechanisms which include one or more valves which are
cyclically opened and closed, in response to either the pressure
build-up of blood on the valve or to a timing device separate from
the valve. In all of the heart pumps having valves there are
necessarily stagnation points in the blood flow path; namely a part
of the flow channel where a portion of the blood flow is halted
from flowing for a prolonged period of time, and in its worst case
where a portion of the blood flow is permanently halted. Blood in
the vicinity of stagnation points has a tendency to coagulate,
deposit, or build up on the adjacent valve surfaces, which impedes
subsequent flow of blood past said surfaces. Such blood clots may
eventually break loose and cause fatal injury to the patient.
A further problem area in typical heart assist devices utilizing
valves is that some constituents of the blood may be damaged due to
excessive pressure, velocity and shear forces occurring when a
valve is being closed and the pressure drop through the
reduced-size flow passage is substantially increased over normal
values.
The new invention is a mechanism for use in a human or animal body
to improve blood flow, the mechanism having structure and geometry
which avoids or at least reduces significantly the above-mentioned
problems.
SUMMARY OF THE NEW INVENTION
The invention is a heart pump that may substitute for or assist an
existing human heart in its operation of pumping blood through
arteries. The new device is an implantable pump in communication
with the high and low pressure variations occurring, in its
preferred embodiment, in a pressure source such as an implantable
Stirling or Rankin engine, using the gas working space, or oil
pump, or the high and low pressure variations of a compressor
driven by the engine. The new device includes a tubular section
that is joined to and between the severed ends of an artery, such
that the blood will have a continuous and substantially
uninterrupted flow path through the artery and the tube-section. At
least two and preferably three sleeves axially spaced apart but
adjacent, encircle this section. Each sleeve has its diameter
cyclically contracted and enlarged about the tube, such that the
bore or flow passage through the tube is cyclically (a) constricted
to reduce or stop blood flow and then (b) enlarged to permit normal
flow therethrough. When all three sleeves are subjected to the high
pressure, all would be expanded, and the tube and artery continuous
therewith would fill with blood. In operation the first sleeve
(which would be designated as in the upstream position) is
constricted; this is followed by the second sleeve being
constricted while the first remains constricted, and then the third
is constricted while the first and second remain constricted. This
tends to force the blood from the first into the second, then into
the third, and finally out of all of the sleeve areas and
downstream. Still later, the two sleeves at the downstream end are
kept closed to prevent backflow while the first sleeve is opened
such that a new charge of blood can begin to enter the pump
mechanism. Then the second is also opened, followed by the third,
such that all are open again, this sequence functioning at least in
part as a suction stage.
One possible sleeve configuration comprises a tubular member formed
into a ring that has one end sealed and the other end connected to
a source of fluid that is supplied either at a low or a high
relative pressure. The ring has a normal diameter, and application
of the high pressure causes the ring to uncoil and enlarge its
diameter; the ring's resilience will return it to its normal
diameter when pressure is reduced or discontinued. Alternatively,
the sleeves (rings) could be designed to contract or reduce in
diametral dimension upon the application of high fluid pressure,
with their resilience returning them to a normal enlarged
diameter.
A valve or timing mechanism situated between the source of fluid
and the sleeves, will control the selection of sleeves to be
pressurized to alter the diameter of each relative to the others.
Since these sleeves contact and operate on the outer surface of the
tube, they are entirely external of the actual blood flow, which
overcomes numerous disadvantages in prior art devices, as discussed
below. Another variation of the above invention would be to leave
the artery unsevered, to omit the tube section, and position the
sleeves directly upon the outer surface of the artery.
The pump mechanism of this invention has a variety of significant
advantages over prior art pumps and heart assists. First, there are
no stagnation points for the blood flow throughout the entire
mechanism; the mechanism is in fact totally external of the artery,
such that the blood flows through a substantially clear and
unobstructed tubular portion of the artery that is free of valves
or other obstacles found in other pumps. As mentioned above, this
stagnation problem has been significant, and to avoid it is a
considerable benefit and achievement. Second, the pump mechanism is
extremely uncomplicated and inexpensive, in comprising simple
sleeves which change dimension but otherwise do not move and do not
have to mate with other parts, and do not have close tolerances,
and do not have seals, bearings, and other parts which can wear
out. The sleeves will merely expand and constrict, and there are
numerous materials available including metals, plastics and rubber
which have proven ability to flex thousands or millions of cycles
without deteriorating excessively or losing their necessary
characteristics. Also, the sleeves would be secured together in
some manner to maintain their axial spacing, such that the
constriction of one sleeve effecting the blood flow therein would
not be remote and unrelated to the application of pressure upon
blood in the adjacent sections of the artery. The number of sleeves
can be increased to provide a smoother flow of the blood, however a
minimum number of two sleeves is required, and presumably three
would function reasonably well.
In order to operate a pump of this type, it is necessary to have a
source of both high and low pressure gas or liquid working fluid.
An implantable Stirling engine has a gas working space and also a
lubricating oil pump that experience such appropriate high and low
pressure differentials; this gas space or the oil pump can be
connected directly to the sleeves through a valve which
automatically selects the suitable pressure level for each sleeve.
Alternatively a Stirling or other implantable power source can
drive a compressor whose high and low pressure ducts are fed to the
sleeves via a valve. Stirling engines can operate over a long,
extended period of time, by using an isotope heat source, and can
run maintenance-and-adjustment-free. The sleeves could be timed to
operate at the same rate as the compressor and/or the engine, or
could cycle at a multiple or fraction of the valve speed.
A preferred embodiment of this invention is disclosed with
reference to the drawings described below.
BRIEF DESCRIPTION OF THE FIGURES
FIG. 1 is a schematic diagram of heart assist system including an
artery pump and a Stirling engine providing high and low working
gas pressure.
FIG. 2 is schematic diagram of another embodiment of a system
similar to FIG. 1, wherein a Stirling engine drives a compressor
which provides the high and low pressures.
FIG. 3 is a schematic diagram of another embodiment similar to
FIGS. 1 and 2, with the oil pump in the crankcase providing high
and low pressures.
FIG. 4 is a partial elevation view of the pump of the new
invention.
FIG. 5 is a sectional view taken along line 5--5 of FIG. 4.
FIG. 6 is a sectional view taken along line 6--6 of FIG. 4.
FIG. 7 is a schematic view showing the pumping and suction cycles
of the device of FIG. 4.
FIG. 8 is a pressure vs time diagram showing six periods for a
complete (FIG. 7) cycle of the FIG. 4 embodiment.
FIG. 9 is a partial elevation view in section of a second
embodiment of the invention with a center core.
FIG. 10 is a sectional view of another embodiment similar to FIG.
9.
FIG. 11 is an end view taken along line 11--11 in FIG. 10.
FIG. 12 is a sectional view taken along line 12--12 in FIG. 10.
FIG. 13 is a diagrammatic view of a rotary control valve to
selectively provide high and low pressure to the three sleeves in
selective sequence of the device in FIGS. 4, 9 and 10.
DESCRIPTION OF THE PREFERRED EMBODIMENT
The invention as a whole implantable system is shown in FIG. 1
where a Stirling engine 1 has a working or compression space that
experiences high and low pressures available at ports 2 and 3
respectively, which are connected via ducts and corresponding high
and low pressure buffer tanks h.sub.1 and h.sub.2 to a valve 4; one
embodiment of this valve is shown in detail in FIG. 13. The valve
selectively feeds high and low pressure to sleeves 5, 6, and 7
which encircle tube 8 connected between the severed ends 9 and 9'
of an artery as a continuous blood flow duct, the valve being
controlled by a connection 4' with engine. The sleeves and tube 8
together form the pump component 10 which pumps blood in the
direction of the arrows. the operation of the pump and valve
components will be described in detail below, while the operation
of a Stirling engine is known and described in numerous
publications such as U.S. Pat. Nos. 3,443,079, 2,885,855, 3,318,089
and 3,318,100.
FIG. 2 shows schematically a variation from FIG. 1 with similar
components given the same reference numerals but modified, for
example, from 1 to 1a. Accordingly a Stirling engine 1a has a
mechanical or hydraulic power output 1b that drives compressor 1c
which has a low pressure connection 3a feeding a buffer tank 3b to
valve 4a, and a high pressure connection 2a which also feeds valve
4a via a buffer tank 1d for storing high pressure working fluid.
The valve 4a automatically feeds the appropriate high and low
pressure fluid to sleeves 5a, 6a and 7a about tube 8a of pump
10a.
FIG. 3 shows a third variation wherein the heart assist system
comprises the lubricating oil pump 1e in the crankcase 1f of
Stirling engine 1g. High pressure oil is fed to a high pressure
buffer tank 3c and then to the control valve 4b for sleeves 5b, 6b,
and 7b. A spring bellows expander may be situated inside of the
buffer tank (see FIG. 3a) will help maintain a generally constant
tank pressure when valve 4a opens and draws fluid from the tank.
The spring-loaded or gas-pressure biased bellows in the tank would
maintain an oil supply pressure substantially constant. Where a
Stirling engine is utilized to provide directly, or indirectly the
high and low pressure fluid, a radioactive isotope capsule is
suggested to supply heat for long-term operation of the engine.
The pump 10 of FIG. 1 is shown in FIG. 4 where a section of tubing
10c is surrounded by three sleeves 11, 12 and 13. The direction of
flow is from left to right as indicated by arrow 14, and the tube
has a nominal undisturbed diameter d.sub. 1, as compared to a
constricted diameter d.sub. 2 resulting from reducing the diameter
of the sleeves. FIG. 5 shows the tube 10c and sleeve 11 in an
expanded state, and FIG. 6 shows the tube and sleeve 13 or 12 in a
contracted state. Each sleeve is normally constricted as in FIG. 6
and is expanded when a fluid pressure is applied to the internal
chamber of the hollow sleeve causing it to expand as indicated in
FIG. 5.
The operation of the above pumping device is shown in six stages
symbolically in FIG. 7 and diagrammatically in FIG. 8. In stage 1
of FIG. 7 the first sleeve is expanded while the second and third
sleeves are constricted; this corresponds to the chart of FIG. 8
which shows sleeve 1 at high pressure, namely that it is expanded
and blood can fill the space it encloses, in contrast to sleeves 2
and 3 which are indicated to be energized with low fluid pressure
or that they are constricted resulting in greater resistance to the
blood flow. Stage 2 of FIG. 7 shows that the first two sleeves are
expanded while the third remains constricted; FIG. 8 in stage 2,
corresponds by showing sleeves 1 and 2 energized with high fluid
pressure while sleeve 3 is still at low pressure. Stage 3 in FIG. 6
shows all three sections to be expanded such that all three sleeves
are being energized with high pressure fluid, and this corresponds
to FIG. 8 stage 3 where all three sleeves are indicated to be at
high pressure. Stage 4 in FIG. 7 shows the first section to be
constricted by corresponding action of sleeve 1; FIG. 8 shows the
corresponding diagram whereby only sleeve 1 is constricted, whereas
sleeves 2 and 3 remain expanded, that is, subjected to high
energizing fluid pressure. Stage 5 shows that the first sleeve has
remained constricted and the second is constricted thus forcing net
flow in the direction of the arrow to the right out through section
3. And, stage 6 shows all sleeves to be constricted thus forcing
the net flow from section 3 further outward, while the first two
closed sections prevent to some extent the fluid from moving
backward. As the cycle beings again, we return to stage 1 where
section 1 is opened while sections 2 and 3 remain closed. This
permits fluid to enter section 1 while it substantially prevents
fluid from flowing backwards into sections 2 and 3. Next, section 2
is opened which allows more net fluid flow to move to the right
into the pump and in fact draws the fluid in because resilience of
the section causes it to open creating a partial vacuum therein.
And, finally, all three sections are opened in stage 3. Again in
stage 4 the first section is closed which forces net fluid flow
toward the right in the direction of the arrows in FIG. 7.
FIGS. 7 and 8 demonstrate a pumping action comprising a suction or
priming cycle in stages 1, 2 and 3, and a pumping forcing cycle in
stages 4, 5, and 6. It would be possible to use only two sleeves
but the efficiency of the pump would be considerably reduced.
FIG. 9 shows another embodiment of the invention which is similar
to but modified from that in FIG. 4. The pumping device 15 is in a
housing 16 with a section of tubing 17 axially disposed in a
housing. The entire pumping device is to be attached to the severed
ends 18, 19 of an artery along junction lines 18' and 19'. The
three sleeves for producing the pumping action are shown as 20, 21
and 22 with each being connected to a fluid port 20', 21' and 22'
which feeds energizing fluid under pressure to the sleeves for
expanding same according to the method earlier described.
Significantly different in the FIG. 9 embodiment from FIG. 4, is
center core 23 which is fixedly positioned in the center or
thereabouts of the tube section 17; FIG. 11 shows streamlined webs
29 at the entrance and exit of the tube for supporting the core
element. Sleeve 20 as shown constricts the flexible tube 17, until
it closes substantially or completely about core 23; subsequent
closing of sleeve 21 would force fluid flow in the direction to the
right, past sleeve 22. It should be obvious that the presence of
the core allows the constricted tube to nearly completely close off
flow in contrast to the prior embodiment where there is no core and
the constriction of the first sleeve would only tend to restrict
flow, but obviously there would be considerable leakage backward
because the passage within the tube remains open. It is
contemplated that this pump device of FIG. 9 would be embedded as a
unit within the body while the two ends thereof are attached to the
severed artery at 19 and 18, and the fluid ports 20', 21' and 22'
would be attached to pressurized fluid means to be discussed
later.
FIG. 10 shows a more detailed view of an embodiment similar to that
of FIG. 9. The sleeves 24, 25 and 26 are indicated as coil sections
of hollow tubing each connected to a port through which pressurized
fluid is directed. It is necessary to support the center core 27
centrally of tubing 28, and this is done by webs 29 shown in FIG.
11 which is a right end view of FIG. 10. The webs are thin and
streamlined and represent minimum obstruction to the flow of blood
in the annular space 29' about the center core and within tube
section 28. FIG. 12 includes a sectional view of the port 30 for
energizing a sleeve 24.
With any of the above-described pump components it is necessary to
provide both high and low pressure fluid to the different sleeves
in a proper sequence. This may be accomplished with a compressor or
other means to develop high and low pressure in a liquid or a gas,
and a valve such as rotary valve means according to FIG. 13 which
directs fluid flow to appropriate sleeves. This valve has outlets
P.sub.1, P.sub.2, P.sub.3, connected respectively to sleeves 24,
25, and 26 of FIG. 10, or to three sleeves of any other embodiment;
it also has a low pressure inlet P.sub.L, and a high pressure inlet
P.sub.H. During stage 1 for example, with FIG. 10, we will need a
high pressure at sleeve 24 and low pressure at sleeves 25 and 26.
The inner rotor permits communication of high pressure inlet
P.sub.H with outlet P.sub.1, and low pressure inlet P.sub.L with
outlets P.sub.2 and P.sub.3.
The exit ports are positioned around the housing of the valve such
that rotation of the rotor exposes appropriate exit ports at the
correct timing to provide a cyclic pressure variation for the three
sleeves, or any number that is chosen, according to FIGS. 7 and
8.
It should be noted that the section of tubing i.e. 17 in FIG. 9,
used in any of the pumps, preferably should have resiliency, such
that it tends to hold its open shape; this eliminates direct
outward radial pulling contact between the sleeve and section of
the tube. Furthermore, each sleeve is resilient member which tends
to hold its constricted shape at low energizing pressure. Thus,
when a sleeve is energized by having a pressure applied to its
hollow inner chamber, and said sleeve expands, the portion of the
tube adjacent to the sleeve will expand on its own due to its own
resiliency. Obviously, it would be possible to reverse these
features such that the sleeve would have a normal expanded
condition and that the application of fluid pressure would cause it
to contract; then the tubular section within the sleeves would also
have a normal open position with its resilience tending to maintain
it that way; when pressure to the sleeve was reduced or relaxed,
the sleeve and tube therein would automatically open to full
diameter.
The opening of the first and second sections of the tube while the
third section remains closed, acts as a suction or priming phase of
the device, as the sleeve creates a greater volume and a partial
vacuum such that blood will flow into these open sections mainly in
the pumping direction; and during later phases of the cycle the
blood will be pumped out mainly in the same direction.
If a gas rather than a liquid, is used to pressurize the sleeves,
then dry friction seals (made from a plastic sold under the
trademark Rulon) might be necessary in the valve mechanism.
However, if a liquid such as oil is used as the energizing fluid,
then the sealing requirements are greatly reduced, and metal
surfaces moving in close proximity could fulfill the sealing
function satisfactorily. The valve shown in FIG. 13 can be designed
to control the flow to as many sleeves as desired, except that the
diameter of the valve would increase as the number of flow
connections increased. In general, if the pump has "N" number of
sleeves, then it would have to have "N" number of flow outlets, and
the angle ".THETA." in the valve according to FIG. 13 would be
.pi./N radians. When one or more sleeves constrict the central
tube, wrinkles in the constricted portion can be avoided by axially
fixing the opposite ends of the tube; then the constricted part of
the tube is also stretched lengthwise, and will not experience
compression on bending.
The structures shown in these drawings are merely preferred
embodiments for practising the invention, these structures being
merely representative of the invention with no intention that the
scope of the invention be limited to their configurations.
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