U.S. patent number 3,639,084 [Application Number 05/025,782] was granted by the patent office on 1972-02-01 for mechanism for control pulsatile fluid flow.
This patent grant is currently assigned to Baxter Laboratories, Inc.. Invention is credited to Richard Paul Goldhaber.
United States Patent |
3,639,084 |
Goldhaber |
February 1, 1972 |
MECHANISM FOR CONTROL PULSATILE FLUID FLOW
Abstract
This application relates to an apparatus for imparting a
pulsatile flow to fluid in a conduit, which has pumping means for
providing the pulsatile flow of fluid therein. The apparatus
includes an elastic tubular section defining a portion of the
conduit and located downstream of the pulsatile flow providing
means. The tubular section is surrounded by a sealed sleeve to
define a pressurizable space about the tubular section. The space
is pressurizable so that the pulsatile flow pattern of fluid
passing through the tubular section is controlled in a manner
responsive to the pressure within said space. If desired, a portion
of the flow conduit upstream of the pumping means is of enlarged
transverse dimension and sealed within a second sleeve to define a
second pressurizable space to provide a means for increasing the
flow of fluid into the pulsatile pumping means.
Inventors: |
Goldhaber; Richard Paul
(Chicago, IL) |
Assignee: |
Baxter Laboratories, Inc.
(Morton Groove, IL)
|
Family
ID: |
21828030 |
Appl.
No.: |
05/025,782 |
Filed: |
April 6, 1970 |
Current U.S.
Class: |
417/394; 128/897;
422/44; 623/3.1; 128/DIG.3; 435/284.1 |
Current CPC
Class: |
A01N
1/02 (20130101); A01N 1/0247 (20130101); Y10S
128/03 (20130101) |
Current International
Class: |
A01N
1/02 (20060101); F04b 043/10 (); F04b 045/00 ();
A61b 019/00 (); A61m () |
Field of
Search: |
;128/1,DIG.3 ;23/258.5
;195/1.7 ;417/395,394,540,53,542 |
References Cited
[Referenced By]
U.S. Patent Documents
Other References
The Lancet-Jan. 25, 1958, page 197 By Rotellar.
|
Primary Examiner: Walker; Robert M.
Claims
That which is claimed is:
1. In an organ perfusion apparatus for passing fluid in a conduit
through an organ in a container including pump means for providing
a pulsatile pressure to cause flow of fluid in said conduit, in
which said pump means comprises a cylinder containing an elastic
tube positioned axially therein, means for sealing the interior of
said tube from the exterior thereof to define a sealed flow path
for fluid to be pumped, and inlet and outlet means to allow said
fluid to pass through the tube, said inlet and outlet means each
containing a one-way valve to prevent backflow of fluid, said
cylinder defining an entrance port to receive fluid within the
cylinder and outside said tube from first oscillatory pressure
providing means, to actuate said pulsatile pressure providing means
by repeatedly collapsing said tube and permitting it to expand
again by application of oscillatory pressure, in which a portion of
said conduit defines an atrium space of enlarged transverse
dimension, said atrium space being located directly upstream of and
extending to said inlet means of the pump means, in which said
atrium space is surrounded by a second sealed sleeve to define a
second pressurizable space about said portion of conduit, and in
which said second sleeve has second means for pressurizing said
second space with oscillatory pressure which is out of phase from
the oscillatory pressure provided by said first oscillatory
pressure providing means, so that when the elastic tube of the pump
means is in its filling phase, the portion of conduit defining said
atrium space is in its collapsing phase to provide pressurized
fluid to said inlet means, for greater pumping efficiency.
2. The organ perfusion apparatus of claim 1 in which an elastic
tubular section defines a portion of said conduit and is located
between said pump means and said organ container, the elastic
tubular section being surrounded by a sealed sleeve to define a
pressurizable space about said tubular section, and means for
controlling the pressure in said space, whereby the pulsatile flow
pattern of fluid passing through said tubular section is controlled
in a manner responsive to the pressure within said space.
3. The apparatus of claim 2 in which said elastic tubular section
is positioned downstream of and adjacent to said pulsatile pressure
providing means.
4. The apparatus of claim 2 in which said conduit for pulsatile
fluid flow defines a closed loop circuit.
5. The apparatus of claim 2 in which said sealed sleeve and said
cylinder define a single, integral member.
6. An organ perfusion device incorporating the apparatus defined in
claim 2.
Description
BACKGROUND OF THE INVENTION
Equipment for providing a pulsatile flow of fluid through a conduit
is currently used in experimental and clinical work relating to
organ perfusion and the like. It has been found that the life span
of surgically removed living organs, such as livers, hearts, or
kidneys, can be prolonged by perfusing the organs with an
oxygenated solution. In particular, it has been found that the
viability of such separated organs is prolonged by perfusing them
with oxygenated solution in a pulsatile flow pattern simulating the
beating of the heart.
While several systems for providing a pulsatile flow of oxygenated
fluid to living organs have been constructed, deficiencies have
been noted in that the prior art devices are unable to provide a
wide variation of pulsatile flow patterns, so that the user can
select the precise amplitude and shape of the pulsatile flow
pressure waves desired. Also, the pumps which provide pulsatile
flow do not operate with an optimum volume of flow.
DESCRIPTION OF THE INVENTION
The invention of this application provides a simple means for
controlling the pattern of pulsatile flow of fluid through a
conduit, permitting the alteration of both the amplitude and shape
of the pulse or pressure wave as measured against time.
Furthermore, this application provides a means for providing
increased volumes of fluid through a narrow conduit to the
pulsatile flow pump for greater pumping efficiencies.
In accordance with this invention, an apparatus for imparting flow
to fluid in a conduit is provided, having pump means for providing
a pulsatile pressure to cause flow of fluid in said conduit. The
apparatus contains aorta means comprising an elastic tubular
section defining a portion of the conduit. The tubular section is
located downstream of the pulsatile flow providing means, and is
surrounded by a sealed sleeve to define a pressurizable space about
the section. The space within the sleeve is pressurizable as
desired to alter the compliance of the tubular section by
controllable pressure to any degree and in any pattern desired.
Hence, the pulsatile flow pattern of fluid passing through the
sleeve having pulsations provided by the pulsatile pump means is
modulated in a manner responsive to the pressure within the space
about the sleeve. For example, a constant pressure can be used, or
an in-phase oscillatory pressure to augment the amplitude and alter
the shape of the pulsations, or an out-of-phase oscillatory
pressure to reduce, modify, or even eliminate, the pulsations. As a
result of this, the ultimate flow pattern is controllable by the
selective controlling of the pressure within the space about the
tubular section as described further below.
The tubular sections used herein can be of any cross section
defining a closed figure, e.g., round, oval, or the like.
Furthermore, a portion of the fluid flow conduit located directly
upstream of and communicating with the inlet of the pulsatile pump
means can define an atrium space of enlarged transverse dimension
to provide a greater pulsatile flow efficiency, in accordance with
the teachings of Anderson, et al., American Heart Journal, Jan.,
1967, pages 92-105.
In accordance with this invention, the portion of the conduit
defining the atrium space is surrounded by a second sealed sleeve
to define a second pressurizable space about the portion of
conduit. The second space is pressurized with oscillatory pressure
which causes the atrium space to collapse during the filling phase
of the pulsatile pumping means and to expand during the pumping
phase of the pulsatile pumping means. Thus, abundant fluid is
provided to the pulsatile pumping means, resulting in greater
pumping efficiency.
Referring to the drawings:
FIG. 1 is a schematic view of an organ preservation system in
accordance with this invention.
FIG. 2 is a view, taken in vertical section, of the pulsatile
pumping means and related portions used in this invention.
FIG. 3 is a partial vertical sectional view of another embodiment
of the atrium space and the pulsatile pumping means.
Referring to the drawings, an organ perfusion system is shown in
which perfusate fluid, for example blood or plasma, is pumped
through a typically transparent organ preservation chamber 10 to
permit viewing of the organ. The fluid is driven by a pulsatile
pump 12 through conduit 14 into chamber 10, through a cannulated
organ contained therein, and then out conduit 16. Access port 17 is
provided in organ chamber 10 for use as needed. Port 17 can be
connected to the organ to conduct organ secretions out of the
chamber 10 to an accumulating container (not shown), if desired.
The perfusate flow path of the organ preservation system is
disposed in a hyperbaric chamber, if desired, for hyperbaric
perfusion. The device can include a compact container for easy
transportability.
The liquid perfusate is conducted uniformly from the organ in
chamber 10 through conduit 16 to a conventional heat exchanger 18,
in which the temperature of the perfusate is brought to a desired
temperature, generally between 4.degree. and about 37.degree. C. to
control the temperature within the system. A separate circuit for
heat exchanger fluid 20 passes into close heat exchanging relation
with the perfusate passing into the heat exchanger from conduit 16,
but the two fluids are separated by a thin metal heat transfer
partition. Heat exchange fluid such as saline is circulated in
conduits 22 between heat exchanger 18 and a conventional
temperature control source and pump 24.
Perfusate at a desired temperature passes from heat exchanger 18
via conduit 26 to a conventional oxygenator 28 (such as described
in Belgian Pat. No. 726,886) for transferring oxygen to and
expelling carbon dioxide from the perfusate. Oxygenator 28 also
contains an oxygen flow path comprising line 30 and exhaust line
32. From the oxygenator the perfusate is passed through conduit 34
and sealed connection 36 into an enlarged portion of the conduit
which defines atrium space 38, typically made of flexible, limp,
thin-walled rubber tubing. Atrium space 38 provides a flexible
storage chamber for perfusate to accumulate between filling phases
of the pulsatile pump 12, and is surrounded by tubular guard
37.
The amount of perfusate flowing in the system is regulated by
adding perfusate as needed from reservoir 41, controlled by valve
43, to compensate for liquid lost as secretions through port 17 and
the like.
As shown in FIG. 2, pulsatile pump 12 comprises a cylinder 42
containing an elastic tube 44 positioned axially within cylinder
42. The space 45 between tube 44 and cylinder 42 is sealed by
annular seals 47, 49 to define a sealed annular chamber. Inlet
means 46 and outlet means 48 from the pump each include a one-way
leaf-type flap valve 50, each of which opens to permit flow into
tube 44 through inlet 46 and out outlet 48 while preventing
backflow of fluid.
Cylinder 42 defines an entrance port 52 to receive fluid from an
oscillatory pressure providing system, which includes tube 54
containing a head of hydraulic fluid 56 and which is connected
through line 58 to a conventional oscillatory pressure generating
control source 60 (FIG. 1), operated by gas supply 61, typically
oxygen. Control source 60 is shown to provide oscillatory oxygen
pressure to line 58, and also to provide an oxygen flow to
oxygenator 28, typically using oxygen passing through a flowmeter
in control source 60. The oscillatory pressure causes fluid to pass
back and forth through port 52 to a space 45 within cylinder 42 and
outside of tube 44 to actuate pump 12 by alternately collapsing
tube 44 and permitting it to expand again in accordance with the
pressure and relaxation cycles of the oscillatory pressure. As tube
44 collapses, fluid is forced out of outlet means 48 in each
pumping phase, and as tube 44 expands, fluid passes in through
inlet means 46 in each filling phase. Typically, pump 12 is
positioned at a vertically lower position than organ chamber 10 to
provide a hydrostatic pressure head of fluid to assist in filling
of tube 44 during the filling phase. Oxygenator 28 is also
positioned vertically lower than chamber 10 for pressurization
there.
A suitable pneumatic control source 60 for providing oscillatory
pressure to line 58 and entrance port 52 is disclosed in the
article by Demers et al., entitled "A Perfusion Circuit for Organ
Preservation in Portable Chambers," J. Surgical Research, vol. 9,
No. 2, pp. 95-99 (1969). This article also refers to a suitable
combined heat exchanger-oxygenator which can be used in
substitution for the separate members 18 and 28 in this invention.
This or other pneumatic systems can be adjusted to provide the
desired period between pulses.
In accordance with this invention, an elastic tubular section 62
defines a portion of the conduit for pulsatile flow of fluid, and
is located downstream of pulsatile pump 12. Tubular section 62 is
surrounded by a sealed sleeve 64, integral with cylinder 42, to
define a pressurizable space 66 between sleeve 64 and tubular
section 62. Line 68 leads between space 66 and a pressure control
70 (FIG. 1) which connects to pressurized oxygen source 61 via line
72.
Pressure control 70 can be a simple constant pressure regulator,
or, if desired, can be a source of variable pressure, coordinated,
if desired, with the oscillatory pressure provided by source 60. As
fluid is forced out of pump 12 in a pulse of pressure, the
amplitude and shape of the pressure wave can be varied by varying
the resilience or compliance of tubular section 62. This
resilience, or compliance, is controlled as desired by controlling
the pressure provided through line 68, thus varying the capacity of
tubular section 62 to receive perfusate. If high pressure is
provided, the compliance characteristics of tube 62, when exposed
to the pressure wave passing out of pump 12, are quite different
from the compliance characteristics of tube 62 when there is a low
pressure or a reduced pressure within conduit 68 and space 66. A
constant pressure can be provided within space 66, as well as an
oscillatory pressure of any type desired, either in phase or out of
phase with the oscillatory pressure used to drive pump 12. Thus
great flexibility is available in the control of the shape of the
pressure pulse of the oscillatory fluid flow passing through
conduit 14 to organ chamber 10.
Referring to FIG. 3, there is shown a modification of a device
which is otherwise similar to the device of FIGS. 1 and 2 except as
stated. The portion of conduit defining atrium space 38 and
disposed within guard or sleeve 37 is sealed by cap 70 to define
another pressurizable space 72. The conduit defining atrium chamber
38 is typically glued to cap 70 at 74 to make the space fluidtight.
Line 76 leads between space 72 and a source of oscillatory pressure
such as source 60. The pressure oscillations in spaces 45 and 72
are arranged to be out of phase with each other, generally with the
pulses in space 72 shortly preceding the pulses in space 45. Hence,
as elastic tube 44 of pump 12 is in the filling phase of its
pumping cycle for receiving fluid through inlet 46, line 76 is
providing a pulse of pressure to space 72 to collapse the conduit
defining atrium space 38 to force fluid into pump 12. No check
valve is needed to prevent excessive backflow of fluid from atrium
space 38. The majority of fluid in atrium space 38 passes into pump
12 without such a valve because inlet 46 is wider than conduit 34
and because the pressure in conduit 34 caused by the elevated organ
chamber 10 is greater than the pressure within tube 44 during the
filling cycle, because of the inherent resiliency of the tube and
its tendency to spring back to its uncollapsed position. For
greater efficiency, a check valve can be provided, if desired.
Out of phase oscillatory pressure is provided to space 45 through
line 78 and port 79 by a conventional time delay device connected
to line 76 to operate a pilot valve in line 78 which opens the line
in one position and closes, but permits backward venting, in
another position, to provide oscillatory pressure in tube 80 and
space 45. Line 78 is then connected to a pressure source such as
oxygen supply 61, to provide a constant pressure to line 78
upstream of the pilot valve.
A typical time delay device can constitute a conduit connected to
line 76, running through a chamber of predetermined volume, and
then past an adjustable needle valve to a pressure responsive
switching control of the pilot valve. The size of the chamber and
the needle valve are adjusted to give the desired time delay. A
suitable pilot valve is available from the Fluidonics Division of
Imperial Eastman Corporation of Chicago, Illinois under the part
number 300135.
During the pumping phase of pump 12 in FIG. 3, flap valve 50 of
inlet 46 is closed, and the oscillatory pressure in space 72 and
line 76 is at a reduced level to permit the conduit which defines
atrium chamber 38 to fill once again with perfusate.
The pressure pattern in space 72 can be arranged so that the
duration of each pressure pulse with collapses the portion of
conduit defining atrium space 38 lasts for only a portion of the
filling phase of tube 44.
In a specific embodiment, the oscillatory pressure in line 76 has a
maximum pressure of about 20 mm. Hg, while the oscillatory pressure
provided to lines 58 or 78 and from thence to pump 12 has a maximum
pressure of about 100 mm. Hg. The frequency of oscillation for both
oscillatory pressures is, for example, 60 cycles per minute. The
pressure provided in line 68 can be constant at 20 mm. Hg. A
constant pressure of this level in line 68 assures that a minimum
bias diastolic pressure is constantly present in the system between
pulsations of flow, and particularly that such minimum bias
pressure is imposed upon the organ within chamber 10 through line
14. It is believed that this prolongs organ viability.
The parts which contact the perfusate are typically made of
silicone rubber to be atraumatic to blood.
The apparatus of this invention can use any fluid in conduit 68 and
the space between tubular section 62 and sleeve 64, and in the
other pressurizable areas, depending upon the compliance
characteristics desired. Liquids of varying viscosity such as oil,
silicone fluid, or water, provide differing compliance
characteristics, which in turn differ from the compliance
characteristics of gases. An incompressible liquid such as saline
can be used, while closing off conduit 68, to provide very little
compliance to tubular section 62, in which there is very little
damping or modulation of the pressure pulses passing
therethrough.
The above specific disclosure is for illustrative purposes only and
is not for purposes of limiting the scope of the invention of this
application. Broadly, the invention of this application can be
utilized in many different devices, including organ perfusion
apparatus comprising (a) container means for receiving an organ;
(b) means for delivering perfusate to the organ within the
container; (c) means for developing pulsatile pressure in the
perfusate delivered to the organ; (d) means for imposing a minimum
pressure bias on perfusate circulated through the organ between
pressure pulses; (e) means for oxygenating perfusate conducted from
the organ; and (f) control means for determining the pump output,
the control means comprising means for setting the period of each
high pressure pulse.
Manual control means can be provided to vary the temperature and
pressure of perfusate provided to the organ, as well as for
regulating the pulse rate and systole period of each pulse
developed by the pump means.
* * * * *