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US3896794A - Venous flow stimulator - Google Patents

Venous flow stimulator Download PDF

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US3896794A
US3896794A US42481373A US3896794A US 3896794 A US3896794 A US 3896794A US 42481373 A US42481373 A US 42481373A US 3896794 A US3896794 A US 3896794A
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valve
pressure
flow
stimulator
venous
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John Alan Mcgrath
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BOC Group Ltd
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BOC Group Ltd
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    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61HPHYSICAL THERAPY APPARATUS, e.g. DEVICES FOR LOCATING OR STIMULATING REFLEX POINTS IN THE BODY; ARTIFICIAL RESPIRATION; MASSAGE; BATHING DEVICES FOR SPECIAL THERAPEUTIC OR HYGIENIC PURPOSES OR SPECIFIC PARTS OF THE BODY
    • A61H9/00Pneumatic or hydraulic massage, e.g. sprays
    • A61H9/005Pneumatic massage
    • A61H9/0078With intermittent or alternately inflated bladders or cuffs

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.

Description

United States Patent McGrath July 29, 1975 541 VENOUS FLOW STIMULATOR 2,140,898 12/1938 Collens et al. 128/24 R r 3,179,106 4/1965 Meredith 128/64 X 1 lnvemo" McGrafl" Harm, 3,303,841 2/1967 Dennis 128/24 R England 3,390,674 7/1968 Jones l28/DIG. 10 Assignee: The British yg p y 3,527,207 9/l970 Gottfried l28/24 R Limited, London, England Primary Examiner-Lawrence W. Trapp [2,2] Flled 1973 Attorney, Agent, or FirmDennison, Dennison, [21'] Appl. No.2 424,813 Townshend & Meserole 52 us. c1. 128/24 R 57 ABSTRACT [51] Int. Cl A6lh l/00 1 Field 05 Search 28/ Apparatus for automatically inflating and deflating, in

l28/D lG. 20, 325- a predetermined pressure cycle, at least one doublewalled pneumatic boot fitted to the lower limb of a pa- [56] References Cited tient undergoing surgery.

UNITED STATES PATENTS 12 Cl 4 D 2,071,215 2/1937 Petersen 128/24 R guns .1 Z ,5? 72 if 24 28 L 7 Nt 45 PATENTEI] JUL 2 91975 l VENOUS FLOW STIMULATOR This application relates to a venous flow Stimulator, by which is meant a device used in some surgical opera tions 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 ora pair of inflatable pressure applicators (or pneumaticboots) adapted to be positioned around the patients 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. r

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 patients 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'FlG. 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 adaptedto generate pulses of pressurisedgas. I

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 34in 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 atmospherefin 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 nonretu rn valve 48. I

Operation of the device [2 is governed by the pivotal position of rocker 18, which is in turn controlled bythe relative positions of magents 22 and 28. The rocker I8 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 valveclosing 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 --120s after the occurrence of the negative-going :and some 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 gasjis supplied to regulator 8, the conduit upstream thereof being vented to atmosphere.

The function of capacitor C is to act as an energystoring 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 takeup the contours of the patients 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 patients limb. This pressure is transmitted to the patients 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 bodys 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. I

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 ata 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. lt 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 bloodpumping 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.

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 patients 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 I, 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 I, 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, in-

cluding 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 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.

Claims (12)

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.
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Cited By (35)

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US4086920A (en) * 1976-09-13 1978-05-02 Miniere Jack K Intermittent inflatable apparatus
US4396010A (en) * 1980-06-30 1983-08-02 The Kendall Company Sequential compression device
US4763893A (en) * 1985-02-01 1988-08-16 Barthlome Donald E Pumping unit for therapeutic hand exerciser
US5007411A (en) * 1989-04-12 1991-04-16 The Kendall Company Device for applying compressive pressures against a patient's limb
US5080089A (en) * 1990-09-05 1992-01-14 Breg, Inc. Therapeutic apparatus applying compression and a nonambient temperature fluid
US5179941A (en) * 1988-06-07 1993-01-19 Siems Otto Siemssen Contractile sleeve element and compression sleeve made therefrom for the peristaltic treatment of extremities
US5330519A (en) * 1990-09-05 1994-07-19 Breg, Inc. Therapeutic nonambient temperature fluid circulation system
US5588955A (en) * 1993-07-08 1996-12-31 Aircast, Inc. Method and apparatus for providing therapeutic compression for reducing risk of DVT
US5662695A (en) * 1990-09-05 1997-09-02 Breg, Inc. Occlusion-resistant fluid pad conformable to a body for therapeutic treatment thereof
US5676639A (en) * 1993-03-12 1997-10-14 Huntleigh Technology Plc. Adjustable pressure relief valve for compression garment
DE19636278A1 (en) * 1996-09-06 1998-03-12 Globalmind Consumer Electronic Device for compression treatment of body parts
US5769797A (en) * 1996-06-11 1998-06-23 American Biosystems, Inc. Oscillatory chest compression device
US6030353A (en) * 1998-04-28 2000-02-29 American Biosystems, Inc. Pneumatic chest compression apparatus
US6117164A (en) * 1997-06-06 2000-09-12 Dj Orthopedics, Llc Flexible multijoint therapeutic pads
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US6231532B1 (en) 1998-10-05 2001-05-15 Tyco International (Us) Inc. Method to augment blood circulation in a limb
US6379316B1 (en) 1999-08-31 2002-04-30 Advanced Respiratory, Inc. Method and apparatus for inducing sputum samples for diagnostic evaluation
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US6547749B2 (en) 2000-07-13 2003-04-15 Electromed, Inc. Body pulsating method and apparatus
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US9737454B2 (en) 2012-03-02 2017-08-22 Hill-Rom Services, Inc. Sequential compression therapy compliance monitoring systems and methods
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Cited By (77)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4086920A (en) * 1976-09-13 1978-05-02 Miniere Jack K Intermittent inflatable apparatus
US4396010A (en) * 1980-06-30 1983-08-02 The Kendall Company Sequential compression device
US4763893A (en) * 1985-02-01 1988-08-16 Barthlome Donald E Pumping unit for therapeutic hand exerciser
US5179941A (en) * 1988-06-07 1993-01-19 Siems Otto Siemssen Contractile sleeve element and compression sleeve made therefrom for the peristaltic treatment of extremities
US5007411A (en) * 1989-04-12 1991-04-16 The Kendall Company Device for applying compressive pressures against a patient's limb
US5080089A (en) * 1990-09-05 1992-01-14 Breg, Inc. Therapeutic apparatus applying compression and a nonambient temperature fluid
US5330519A (en) * 1990-09-05 1994-07-19 Breg, Inc. Therapeutic nonambient temperature fluid circulation system
US5662695A (en) * 1990-09-05 1997-09-02 Breg, Inc. Occlusion-resistant fluid pad conformable to a body for therapeutic treatment thereof
US5676639A (en) * 1993-03-12 1997-10-14 Huntleigh Technology Plc. Adjustable pressure relief valve for compression garment
US5588955A (en) * 1993-07-08 1996-12-31 Aircast, Inc. Method and apparatus for providing therapeutic compression for reducing risk of DVT
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