U.S. patent number 3,896,794 [Application Number 05/424,813] was granted by the patent office on 1975-07-29 for venous flow stimulator.
This patent grant is currently assigned to The British Oxygen Company Limited. Invention is credited to John Alan McGrath.
United States Patent |
3,896,794 |
McGrath |
July 29, 1975 |
Venous flow stimulator
Abstract
Apparatus for automatically inflating and deflating, in a
predetermined pressure cycle, at least one double-walled pneumatic
boot fitted to the lower limb of a patient undergoing surgery.
Inventors: |
McGrath; John Alan (Harlow,
EN) |
Assignee: |
The British Oxygen Company
Limited (London, EN)
|
Family
ID: |
23683979 |
Appl.
No.: |
05/424,813 |
Filed: |
December 14, 1973 |
Current U.S.
Class: |
601/152 |
Current CPC
Class: |
A61H
9/0078 (20130101) |
Current International
Class: |
A61H
23/04 (20060101); A61h 001/00 () |
Field of
Search: |
;128/24R,64,DIG.10,DIG.20,325-327 |
References Cited
[Referenced By]
U.S. Patent Documents
Primary Examiner: Trapp; Lawrence W.
Attorney, Agent or Firm: Dennison, Dennison, Townshend &
Meserole
Claims
What we claim is:
1. An apparatus useable in conjunction with a source or pressurized
gas for stimulating venous blood flow in the legs of patients
undergoing surgery, said apparatus including at least one
double-walled pneumatic boot positioned on and completely enclosing
a patient's leg and foot; said boot having an operating space
defined between the walls thereof; a supply valve operative to
control the supply of gas at a suitable pressure from a pressurized
source to the operating space; means responsive to the gas pressure
in the operating space for closing the supply valve when the
pressure reaches a chosen maximum valve; a timer means adapted to
produce a series of successive set and reset pulses, and an inlet
valve means, controlled by the timer, for supplying gas to the
supply valve upon receipt of a set pulse, and for discontinuing the
supply of gas upon receipt of a reset pulse.
2. A venous flow stimulator as claimed in claim 1, including
injector means positioned downstream of the supply valve between
the supply valve and boot for receiving high-pressure gas from the
open supply valve and for diluting it with atmospheric air thereby
producing a larger volume of gas at lower pressure for feeding to
the pneumatic boot as long as the supply valve is open.
3. A venous flow stimulator as claimed in claim 1, including means
for energizing the timer only when the pressure of the supply of
gas to the said inlet valve is above a chosen minimum.
4. A venous flow stimulator as claimed in claim 3, in which the
timer is electronic and is composed of units of integrated
circuitry.
5. A venous flow stimulator as claimed in claim 1, in which the
said supply valve includes a magnetic rocker valve and two
permanent magnets mounted for relative movement, said rocker valve
being operated by relative movement of said magnets.
6. A venous flow stimulator as claimed in claim 5, in which the
said supply valve includes a bellows having a portion thereof
movable relative to said rocker valve, said movable portion
carrying one of the said two permanent magnets for movement thereof
toward and away from actuating relationship with the rocker
valve.
7. A venous flow stimulator as claimed in claim 6, including an
adjustable bleed valve in the bellows, said bleed valve venting the
bellows to atmosphere at a desired rate.
8. A venous flow stimulator as claimed in claim 1, including an
exhaust valve biased to the open position, said exhaust valve being
operatively controlled by the outlet pressure of the gas from the
supply valve in a manner whereby when the outlet pressure exceeds a
chosen valve the exhaust will close, the inlet of the exhaust valve
being in communication with the operating space of the boot for a
selective venting thereof.
9. A venous flow stimulator as claimed in claim 4, in which the
timer produces set and reset pulses of opposite polarity.
10. A venous flow stimulator as claimed in claim 9, in which the
intervals between successive set and reset pulses is approximately
10 seconds, and between successive reset and set pulses is
approximately 100 - 120 seconds.
11. A venous flow stimulator as claimed in claim 10, in which
shunted across input terminals of the timer is a capacitor adapted
to be discharged through the timer to contribute energy to the
pulses, and to be charged in the intervals between the pulses.
12. The method of stimulating venous blood flow in the leg of a
patient undergoing surgery comprising intermittently forcing blood
from the veins of the leg by an intermittent pressurization of a
leg and foot encasing pneumatic boot at an increasing rate of 8 mm
of mercury per second to a maximum on the order of 50 mm of
mercury, and subsequently releasing the pressure.
Description
This application relates to a venous flow stimulator, by which is
meant a device used in some surgical operations to apply pulsating
pneumatic pressure to the legs of a patient while undergoing
surgery, in order to prevent the occurrence of post-operative deep
venous thrombosis.
A known venous flow stimulator includes an electrically driven pump
connected to one or a pair of inflatable pressure applicators (or
pneumatic boots) adapted to be positioned around the patient's legs
and feet. Pressure is applied (and released periodically) to the
calf muscles of the legs of the patient by means of the boots so as
to prevent stasis of blood flow in the deep veins of the legs. This
reduces the risk of deep venous thrombosis occurring.
It is necessary to use the known form of venous flow stimulator to
treat a patient throughout the preoperative, operative and
postoperative period, treatment ceasing when the patient is ready
to get out of bed. Each patient requires a machine for a relatively
long period, and post-operatively the treatment may cause him
discomfort and apprehension. Because the treatment is prolonged a
considerable number of machines have to be employed and surgeons
are reluctant to bring them into general use.
It is the aim of the present invention to provide an improved
venous flow stimulator giving more effective treatment to enable
the period of treatment to be reduced to that taken up by the
surgical operation itself, so that the venous flow stimulator can
therefore be essentially an apparatus for use only in the operating
theatre.
According to the present invention there is provided a venous flow
stimulator which is as claimed in the appended claims.
The venous flow stimulator of the present invention will now be
described by way of example with reference to the accompanying
drawings, in which:
FIG. 1 is a schema of one form of flow stimulator of the present
invention;
FIG. 2 is a diagrammatic view of the stimulator in position during
a surgical operation;
FIG. 3 is a graph of voltage v. time for the electrical pulses
controlling operation of the stimulator, and
FIG. 4 is a graph of pressure v. time for the pneumatic pulses
supplied by the stimulator to the boots encasing the patient's
legs.
The venous flow stimulator shown in FIG. 1 includes a source 2 of
pressurised gas usually in the form of the portable cylinder 4
shown in FIG. 2 leading through a solenoid-operated valve 6 to a
flow regulator 8 (for example, of the type described in our UK
patent specification No. 1,039,528). The flow regulator 8 leads
through conduit 10, to a device 12 adapted to generate pulses of
pressurised gas.
The device 12 has a gas supply chamber 14 of which an outlet 16 is
controlled by a rocker valve 18. One wall of chamber 14 is formed
by a diaphragm 20 carrying a permanent magnet 22. The device 12
also has a control chamber 24 formed by bellows 26, of which the
end wall carries a second permanent magnet 28 and a conduit 30
leading to an adjustable bleed valve 32. Extending from the device
12 is a conduit 34 in which is positioned an injector 36. The
injector is adapted to receive gas under high pressure from conduit
34 and dilute it substantially with air from the atmosphere in
order to produce larger volumes of gas at lower pressure suitable
for pressurising both boots 38 fitted to the feet and legs of the
patient.
Downstream of the injector 36 the conduit 34 leads to two further
conduits 40 and 42. The conduit 40 leads to the inlet of a
pneumatically operated exhaust valve 44, while the conduit 42 leads
to a pressure-relief valve 46 and to the interior of chamber 24
through a non-return valve 48.
Operation of the device 12 is governed by the pivotal position of
rocker 18, which is in turn controlled by the relative positions of
magents 22 and 28. The rocker 18 is of a soft magnetic material,
such as Swedish iron, so that the rocker is able to be pivoted
about its fulcrum when one or other of the magnets becomes
dominant. As magnet 22 is positioned on the stationary diaphragm
20, the force it applies on rocket 18 in the valve-closing
direction is substantially constant. Because the magnet 28 is
positioned on the movable end wall of bellows 26, the magnet 28 is
movable between two limit positions, in one of which its magnetic
field overcomes that exerted on rocker 18 by magnet 22 and forces
the rocker to pivot in the valve-opening direction. In the other
limit position the magnetic field produced by magnet 28 falls below
that exerted on rocket 18 by magnet 22 thus causing the rocker to
be moved in the valve-closing direction.
A conduit 50 is pressurised from source 2 and leads to a pressure
switch 52 which, when closed, causes a battery 54 to be connected
across a capacitor C and across the input terminals of an
electronic timer 56 having three outlets (labelled X, Y and Z)
which are connected to respective terminals on a solenoid 58
controlling operation of valve 6.
The detailed circuitry of timer 56 is not described in this
specification, but it is based on the use of digital integrated
circuitry of the COS/MOS type. In particular, although this is not
shown in the drawings or described herein in any greater detail,
the timer includes a square-wave oscillator adapted to be energised
by battery 54. The output of the oscillator is fed through a
pulse-shaping circuit to a solid state switching circuit. Both the
oscillator and pulse-shaper consist of two input, quadded NOR
gates, which are available commercially, one form thereof being
sold by RCA as an item in their COS/MOS CD4000A series of
integrated circuits. The various components of these integrated
circuits are interconnected through suitably rated electrical
components to derive an output having the characteristics shown in
FIG. 3 of the accompanying drawings. In a typical output, there is
a positive-going pulse of 9 V amplitude and lasting 50 ms, followed
after an interval of about 10 s by a negative-going pulse of the
same amplitude and duration. At a period of between 100-120s after
the occurrence of the negative-going pulse, a further pair of
successive positive-going and negative-going pulses is generated.
The positive-going pulses are labelled `set` pulses while the
negative-going pulses are labelled ` reset` pulses.
The reason for choosing set and reset pulses of opposite polarity
is to avoid ambiguity in question of solenoid 58 when the circuit
is first energised. If the circuit were previously deenergized
while in the resting state, and if the first pulse received when
next energized is a negative-going pulse, the solenoid 58 is not
operated, and so the circuit is kept static until arrival of the
next positive pulse. Thus the risk is avoided of having the boots
inflated during the long resting phase, and kept deflated during
the intended inflation phase, as could happen were both the set and
reset pulses were of the same polarity.
As already mentioned, these pulses are applied to the respective
terminals of solenoid 58, the setting pulses serving to switch the
valve 6 into the position in which the source 2 applies a
continuous stream of gas under pressure to device 12 through
pressure regulator 8. When a reset pulse is received, the valve is
returned to the illustrated position in which no further
pressurised gas is supplied to regulator 8, the conduit upstream
thereof being vented to atmosphere.
The function of capacitor C is to act as an energy-storing device
to ensure that the current drain on battery 54 is reduced to the
minimum constant with reliable operation, while at the same time
lengthening the life of battery 54 so that it needs to be replaced
only at infrequent intervals. The timing circuit 56 is such that
when a set or reset pulse is applied by it to solenoid 58, most of
the energy for the pulse is derived from capacitor C. Thus ensures
that the capacitor C is charged by battery 54 when no pulses are
being produced by the timer, thus converting a substantially
constant current drain on battery 54 into intermittent current
pulses of relatively high amplitude. The function of pressure
switch 52 is to disconnect the battery 54, and disable the timer
circuit, when there is insufficient gas pressure in the inlet to
the pneumatic circuit to operate the pneumatic boots 38.
The boots 38 themselves are already known, and so will not be
described in great detail in this specification. The boots are
double-walled, and at least the inner wall is made of a flexible
plastics material which is able to take up the contours of the
patient's lower leg and foot. Air under pressure is introduced into
the space between the two walls. When the air of other gas is first
introduced, it causes the outer wall to distend until it reaches
its final shape, after which the further increase in pressure
forces the inner wall more and more firmly against the patient's
limb. This pressure is transmitted to the patient's veins and other
blood vessels, causing them to dilate.
This contraction expels blood from the vessels in the direction
dictated by the usual valving arrangements forming part of the
body's vascular system. When a desired maximum pressure has been
reached the pneumatic pressure in the boot is released, as by
venting to atmosphere the space between the two walls of the boot.
This reduction in pressure allows fresh blood to be pumped by the
heart into the limbs and blood vessels. The cyclic compression and
expansion applied by the boots simulates the `massaging` of the
legs' blood vessels which is normally applied by the calf muscles
when the patient is standing or walking, but which action is
inhibited or stopped when the patient is anaesthetized and is in a
lying position.
The present invention therefore increases both the peak femoral
vein flow and pulsatility, leading to the same mean mass transfer
of blood as when the body is working normally.
In accordance with the present invention, it has been found that
the effectiveness of the pneumatic boots is related closely to the
pattern of the pressure cycle to which they are subjected. In
particular, it has been found that amongst the critical factors
are: the rate at which pressurizing gas is applied to the pneumatic
boots; the maximum which this pressure reaches; the speed with
which the pressure is reduced, and the timing between successive
pressurization cycles. These characteristics are indicated
diagrammatically in FIG. 4. Before these are discussed in any
further detail, the operation of the venous flow stimulator will be
described in further detail.
In the initial, unenergized, state of the stimulator, the bellows
26 is in its deflated condition, being biased to that position by a
compression spring (not shown). The detailed construction and
operation of the bellows is as described in our UK patent
specification No. 866 758, and so will not be described in greater
detail herein. In this position the magnet 28 is more effective
than is magnet 22, thus biasing the rocker 18 open so that the
inlet 16 of conduit 34 is in communication with chamber 14. The
exhaust valve 44 is open, allowing the interior of both boots 38 to
vent to atmosphere.
When it is desired to start operation of the apparatus, the gas
under pressure is applied to pressure switch 52 and to valve 6 from
a suitable source, such as a cylinder of compressed air, nitrogen
or oxygen. The use of oxygen might seem surprising, in view of its
higher cost but it has been found that oxygen is usually more
readily available in hospitals than the other gases and so is more
convenient to use despite its higher cost. The possible or
preferred use of oxygen means that none of the valves in the
apparatus, at least on the high-pressure side thereof, can be
lubricated, because oxygen can react explosively with some
lubricants under certain conditions. The valves are therefore
designed with the use of oxygen in mind.
Closure of pressure switch 52 causes the timer 56 to send out a set
pulse to solenoid 58. This switches over valve 6 to the position in
which gas under pressure flows through the pressure regulator 8 and
into the interior of chamber 14. From there, the rocker 18 being
open, it passes into injector 36, is diluted with atmospheric air
and passes into the operating volume of the pneumatic boots 38. As
soon as a superatmospheric pressure is generated in conduit 34 this
causes the exhaust valve 44 to be switched over so that the conduit
is isolated from the atmosphere. By virtue of conduits 34 and 42,
the pressure in the interior of the boots 38 is transmitted to the
pressure-relief valve 46 and to the interior of control chamber 24
of device 12. As this pressure is greater than that needed to
overcome the force of the biasing spring, the chamber 24 starts to
increase in volume, although gas is bled away from chamber 24 at a
rate determined by the setting of needle valve 32. Under normal
conditions of operation, the valve 32 bleeds gas away from chamber
24 at a rate much lower than that at which gas enters the chamber
from conduit 42, so that the bellows 26 are distended at a chosen
rate. As the magnet 28 is moved away from rocker 18 by this
distention of the bellows, there comes a point when the field of
magnet 28 is less effective than that of magnet 22, and the rocker
valve closes. This is arranged to take place when the pressure in
the interior of boots 38 has reached a desired maximum. According
to the teaching of the present invention, a desired rate of
pressurization of the boots is such that the operating pressure
therein should increase at the rate of 8 mm of mercury (Hg) per
second, and the desired maximum value should be of the order of 50
mm Hg, all the pressures being measured above atmospheric. Thus the
boots would take about 6-7 seconds to inflate.
When the rocker 18 has switched over, this causes the pressure in
chamber 14 to increase until the arrival of the next reset pulse at
solenoid 58, but this pressure is not passed on the pneumatic
boots, because of the closure of the rocker valve 18. When the
reset pulse does arrive, it switches over valve 6 and enables
chamber 14 to be vented to atmosphere
With closure of rocker valve 18, the reduction of pressure in
conduit 34 allows valve 44 to open, thus venting to atmosphere the
interior of both boots 38. It is envisaged that this venting would
take place under the natural compliance of the system but it could
be assisted by a partial-vacuum device (not shown) adapted to apply
a measure of vacuum to the interior of the boot to increase the
rate at which they are deflated. This reduction in pressure closes
the non-return valve 48, but the chamber 24 continues to be vented
through valve 32, thus allowing magnet 28 to move towards the
position in which it is effective to open rocker 28. However, the
rate-of-return of magnet 28 is governed so that by the time it is
effective to open the rocker valve, the inlet valve 6 has received
the reset pulse and closed.
The stimulator then stays in its rest position awaiting the arrival
of the next set pulse, which occurs some 100 to 120 seconds after
the preceding reset pulse. This interval is usually set by the
manufacture of the stimulator, or it may be under the control of
the anaesthetist or other person in the operating theatre.
It has been found that the stimulation of the blood-pumping
movement of the calf muscles is so effective that the venous flow
stimulator of the present invention need be used only during the
surgical operation.
It is within the purview of the present invention to apply the
pressure pulses to the two boots alternately. This would require a
modification in the outlet circuit of the stimulator, involving
principally the addition of a pneumatic flip-flop valve, and to
altering the timing circuit of the stimulator so that it generates
pulses of the same shape but at twice the frequency described
above. This would ensure that alternate pulses would be applied to
each of the boots, so that each of the boots would receive exactly
the same cycle of pulses as described above, but with the two
cycles being out of phase with each other. However, so far it has
been found by experiments that there is no significant advantage to
the patient in having alternate pressurization of the boots, and so
the additional cost and complication of providing this option are
not usually justified.
* * * * *