TITLE: PSEUDO STATIC PERISTALTIC PUMP
FIELD OF THE INVENTION
The present invention relates generally to pumps, and more particularly to peristaltic
type pumps.
5 The invention has been developed primarily for use in medical applications, and will
therefore be described primarily with reference to this application. It will be appreciated,
however, that the invention is not limited to this particular field of use, but may also be
used in numerous other applications, a notable example being mineral slurry transportation.
I o BACKGROUND OF THE INVENTION
In the past, various attempts have been made to transport slurries over relatively long
distances as a means, for example, of efficiently transporting coal, sand, cement and
minerals. In most cases, however, conventional pumping technology has been found to be
inadequate, particularly where longer distances are involved, because of the unusual fluid
15 flow characteristics and other properties which many slurries typically exhibit.
For example, positive displacement type pumps incoφorating various arrangements
of pistons are often used to pump liquids. However, the vibrational pulses imparted by
pumps of this type can cause blockages in hydraulic transport lines. Also, the valve
characteristics inherent in piston type pumps typically render them inadequate for handling
0 larger particles. This is due primarily to the susceptibility of the valves and valve seats to
mechanical damage and rapid abrasive wear, as well as to the inability of the valves to pass
larger particles.
Centrifugal pumps are also known and these tend to produce less vibration and accommodate a larger range of particle size. However, because of the rotary nature of such
pumps, rapid wear remains a common problem, particularly in shafts, bearings, seals and
the like which translate into high capital and maintenance costs.
Peristaltic pumps are also known. These typically comprise compression elements
such as pressure rollers which are passed in succession along the length of a flexible tube
to induce fluid flow through the tube. In the past, however, such pumps have typically
been unable to generate sufficient pressure or flow rate to be effective in large scale commercial operations. One problem is that if the tube is formed from a material
sufficiently strong to withstand high internal pressures, it is then resistant to the required
external compression from the pressure rollers, without relatively high energy inputs and
consequential inefficiency and rapid mechanical wear. On the other hand, when more
flexible tubes are used, these have a lower pressure capacity and a tendency to collapse,
particularly on the suction side, thereby substantially diminishing the performance and
efficiency of the pump. For these reasons, peristaltic pumps have hitherto been generally
confined to low pressure or flow rate applications, such as in the medical field.
For example, numerous attempts have been made to produce a pump suitable for use
in artificial hearts. In most cases, however, conventional pump technology has been found
to be inadequate. Typical problems encountered with positive displacement pumps include
mechanical failures due to the small size and intricate nature of the componentry,
inadequate reliability due to excessive complexity or rapid wear, blockages caused by
inadequate valve clearances, damage to blood cells due to the interaction of valve
mechanisms, excessive power consumption due to electrical or mechanical inefficiency, and excessive bulk due to the basic limitations inherent in conventional pump technology.
Peristaltic pumps have been found to overcome several of these problems and are
therefore used in some medical applications. In the past, however, these too have typically
been unable to provide the required combination of characteristics in terms of performance, efficiency, reliability and longevity for use in artificial hearts and other specialised
applications. A particular problem again relates to the tendency of the primary tube to
collapse over time, progressively diminishing the performance and efficiency of the pump,
as well as requiring frequent replacement.
It is an object of the present invention to provide an improved pump which
overcomes or substantially ameliorates at least some of these disadvantages of the prior art.
DISCLOSURE OF THE INVENTION
Accordingly, the invention as presently contemplated provides a peristaltic type
pump comprising a primary flexible fluid conduit, a fluid inlet and a fluid outlet disposed
at opposite ends of the conduit, compression means disposed along a length of the conduit,
and actuation means adapted progressively to actuate the compression means in
predetermined sequence so as to induce peristaltic compression along the length of the
conduit and thereby move fluid from the inlet to the outlet of the pump.
Preferably, the compression means comprise a plurality of compression elements
arranged as a series of discrete mutually opposed pairs. The compression elements of each
pair are preferably movable alternately and in unison between an expanded configuration
and a contracted configuration. The pairs are preferably actuated sequentially to induce
peristaltic compression along the length of the primary conduit.
Each compression element preferably comprises a flexible cell containing a
compression medium adapted to move between an expanded configuration corresponding
to an activated state and a contracted configuration corresponding to a deactivated state in
response to control stimuli from the actuation means. The compression medium is
preferably a polymer based piezoelectric gel and the control stimuli are preferably applied
electric currents or voltages.
In the preferred embodiment, the pump further includes expansion means adapted to
effect radial expansion of the primary conduit behind or upstream of each peristaltic
compression wave. The expansion means preferably include a flexible jacket surrounding
the primary conduit. The jacket preferably contains an expansion medium adapted
selectively for localised pressurisation or expansion so as to increase hoop stresses and thereby to induce a circular cross-sectional profile in the primary conduit, immediately
upstream of each compression wave.
In the preferred embodiment, the jacket includes a flexible secondary conduit or tube
extending spirally around the outer periphery of the primary conduit to form a composite
tube. The secondary conduit is preferably divided into discrete longitudinal expansion
segments, each of which is filled with a polymer based piezoelectric gel. The expansion
segments are preferably activated in predetermined phase relationship behind the
compression elements, by electrical control stimuli from the actuation means.
In one particularly preferred embodiment, the spiral secondary conduit is formed
within the side wall of the primary conduit, in which case the primary conduit, the
secondary conduit and the outer jacket are effectively integral.
According to a second aspect, the invention provides a flexible primary tube for use
with a peristaltic type pump as defined above, said tube being initially formed with an
elliptical profile in a relaxed condition, as manufactured.
Preferably, the elliptical profile of the primary tube is defined by a minor axis X and
a major axis Y, determined by the relationships: o s
X = D_ ; and Y = X x 7
where D is the nominal internal diameter of the primary tube when fully expanded to a
circular cross-sectional profile.
In this way, the inner circumference of the primary tube does not substantially
change, despite variations in the cross-sectional profile during the compression cycles. Advantageously also, the elliptical profile reduces the extent of maximum deformation
during each compression phase by effectively dividing the operational flexure into two
opposite phases of bending, about a median position corresponding to the relaxed
configuration of the tube, rather than a single bending phase of twice the magnitude.
BRIEF DESCRIPTION OF THE DRAWINGS
A preferred embodiment of the invention will now be described, by way of example
only, with reference to the accompanying drawings in which:-
Figure 1 is a longitudinal cross-section showing a peristaltic pump according to a
first embodiment of the invention;
Figure 2 is a transverse cross-sectional view taken along line 2-2 of Figure 1 ; Figure 3 is a transverse cross-sectional view taken along line 3-3 of Figure 1 ;
Figure 4 is a longitudinal cross section showing a peristaltic pump according to a
second embodiment of the invention;
Figure 5 is a transverse cross-sectional view taken along line 5-5 of Figure 4;
Figure 6 is a longitudinal cross section showing the electrical control inputs to the secondary spiral tube;
Figure 7 is a transverse cross-sectional view taken along line 7-7 of Figure 6;
Figure 8 is a longitudinal cross section showing a peristaltic pump according to a
third embodiment of the invention;
Figure 9 is a transverse cross-sectional view taken along line 9-9 of Figure 8;
Figure 10 is a transverse cross-sectional view taken along line 10-10 of Figure 8;
Figure 1 1 is a transverse cross-section showing the elliptical profile of the composite
tube, in a relaxed configuration as manufactured;
Figure 12 is a transverse section showing the composite tube of Figure 11 in a compressed configuration; and
Figure 13 is a transverse section showing the composite tube of Figure 1 1 in an
expanded configuration.
PREFERRED EMBODIMENTS OF THE INVENTION
Referring to Figures 1 to 3, wherein corresponding features are denoted by
corresponding reference numerals, the invention, according to a first embodiment, provides
a peristaltic type pump 1 comprising a flexible primary fluid conduit 2 having a fluid inlet
3 and a fluid outlet 4. The primary conduit 2 is surrounded by radial expansion means in
the form of a flexible jacket 5. The jacket 5 contains a secondary flexible tube 6 extending
spirally around the outside of the primary tube. Alternatively, a composite tube may be
provided with an internal spiral passage, in which case the primary conduit is defined by
the inner surface of the composite tube, the surrounding jacket is defined by the outer
surface of the composite tube and the secondary spiral conduit is defined within the
sidewall of the tube, and all three are thus effectively integral. In another embodiment, the
jacket 5 may simply be formed by a separate spiral tube, wound around and secured to the
outer surface of the primary conduit, again to form a composite tube.
The pump further includes compression means in the form of a series of compression
elements 10 arranged in corresponding mutually opposed pairs along the length of the
primary tube, external to the secondary spiral tube 6. The compression elements are
housed within a surrounding tubular casing 1 1 and annular end caps 12 which enable the
assembly within the casing to be sealed and pressurised if required. The casing may also
be flexible such that a degree of flexibility is afforded to the entire pump assembly.
The compression elements 10 take the form of flexible cells containing a
compression medium adapted to move alternately between an expanded or active state and
a contracted or inactive state in response to control stimuli from an actuation mechanism
(not shown) which may include a microprocessor based controller. The compression
medium is preferably a polymer based gel having piezoelectric characteristics, and as such
expands in response to stimuli in the form of applied electric currents or voltages. It will
be appreciated, however, that the compression elements may be solid, liquid or gaseous,
and as such may take a variety of other forms. Also, it will be appreciated that any suitable
number of compression elements may be used in a variety of configurations to provide the required flow characteristics.
The secondary spiral tube 6 also contains an expansion medium, preferably the same
piezoelectric polymer gel as in the compression elements, adapted for controlled expansion
so as selectively to increase the hoop stresses in, and thereby to effect radial expansion of,
the primary conduit. The spiral tube is divided longitudinally into discrete segments, to
provide optimum localised expansion characteristics. Each segment is approximately 4
turns in length, in a spiral defining a helix angle of between 1° and 20°, ideally around 5°.
In the second embodiment of the invention, as shown in Figures 4 to 7, the spiral segments are activated sequentially by control voltages applied where indicated to provide
localised control over the radial expansion mechanism, as described more fully below. In
alternative arrangements a pump may be used to alternately pressurise and depressurise the segments to effect the desired radial expansion.
In a third embodiment of the invention, as shown in Figures 8 to 10, the spiral
5 segments are only approximately two turns in length, and the compression elements are
correspondingly sized to provide more precise shape control over the peristaltic
compression waves during each pumping cycle.
Turning now to describe the operation of the pump in more detail, the actuator or
controller (not shown) progressively activates the opposing piezoelectric compression
l o elements 10 of each pair simultaneously, and the pairs in linear sequence, so as to induce a peristaltic compression wave 13 along the length of the primary conduit, thereby displacing
fluid from the inlet 3 to the outlet 4 of the pump. At the same time, the controller activates
the piezoelectric gel (or alternatively pressurises a fluid ) contained in the surrounding
spiral conduit 6. In the case of a longitudinally segmented spiral tube, the segments A, B,
15 C, etc are progressively activated in linear succession immediately behind or upstream of
the activated compression cells. This increases the hoop stresses in the primary conduit,
and thereby tends to induce a circular cross-sectional profile in the primary conduit, following each compression wave. In other words, the control voltages applied to the
compression cells are coordinated with the control voltages applied to the corresponding
20 segments of the outer spiral tube, such that the peristaltic compression and subsequent
positive expansion of the composite tube are appropriately synchronised. Advantageously,
this enhances the negative pressure on the suction side of the pump and thereby improves
the overall pumping efficiency. It also prevents the primary tube from permanently de¬
forming or collapsing into a flattened configuration over time in response to prolonged
compression cycles, as typically occurs in prior art pumps. This arrangement also obviates
the need for moving parts and thereby offers significant benefits in terms of maintenance,
reliability, size and cost. As such, it is particularly advantageous in medical applications.
It will be appreciated that by appropriate simultaneous or sequential activation of the
compression elements, the pump may be configured to move fluid in either direction, as
well as to act as a valve by blocking fluid flow altogether. In addition, it will be
appreciated that surplus or redundant compression elements may be included as a safety
feature. These would not normally be activated, but would remain in a standby mode, to be triggered by the actuator in the event of failure of active elements in the system.
Figures 1 1 to 13 show the shape and configuration of composite tube in more detail.
Referring firstly to Figure 11, the tube is initially formed with an elliptical profile in the
relaxed condition as manufactured, so as to reduce the extent of maximum deformation during each compression phase. In terms of the pumping cycle, the elliptical profile of the
conduit in the relaxed condition as shown in Figure 1 1 corresponds to the configuration of
the conduit mid-way through a compression phase. In this way, it will be appreciated that
the elliptical shape effectively divides the operational flexure into two opposite phases of bending, as shown in Figures 12 and 13 respectively, rather than a single phase of twice the
magnitude. This in effect halves the maximum extent of deformation from the relaxed or
equilibrium condition.
Most preferably, the composite tube is formed on an elliptical mandrel having a
minor axis X and a major axis Y, as shown. If the internal diameter of the primary conduit
in the fully expanded circular condition is D, then the following relationships are applied:-
X = D ; and Y = X x 7° 5
2
The significance of these mathematical relationships is that the inner circumference
of the primary inner tube does not substantially change, despite variations in the cross-
sectional profile during the compression cycles, which minimises internal stress and
fatigue. However, the mean diameter of the spiral defined by the secondary tube is
necessarily larger than the inner diameter of the primary tube and hence the mathematical
identity no longer applies. Consequently, pressurisation of the secondary tube still induces the desired change from elliptical to circular profile on the suction side of each
compression element, as described above. This arrangement thus optimises the service life
of the composite tube, and enables the use of higher pressure capacity materials and
designs which might otherwise lack the required degree of flexibility.
The present invention thus provides a peristaltic pump which is compact in size,
flexible in configuration and operation, extremely reliable due to the absence of moving
parts, gentle to blood cells due to the absence of harsh mechanical valve interactions, and
efficient in terms of power consumption. This makes the invention, optionally in a twin
lobe configuration, ideal for use in medical applications and in particular for use in
artificial hearts.
The present invention is also applicable to a wide variety of fluids and slurries with
abrasive, corrosive or generally contaminate characteristics. It further has the capacity to
be set up to generate a reasonable flow with only minimal compression in a dynamic
pseudo wave action simply by reducing the control voltage to the compression elements. It
may therefore accommodate relatively large particle size and may even be used to transfer
live specimens, such as fish, between storage tanks. The invention is also particularly well
adapted to pump relatively high viscosity liquids which in prior art pumps would cause the
peristaltic tube on the suction side to collapse under atmospheric pressure. In all these
respects, the invention represents a commercially significant improvement over the prior
art.
Although the invention has been described with reference to specific examples, it
will be appreciated by those skilled in the art that the invention may be embodied in many
other forms.