US3784323A - Peristaltic pump - Google Patents

Peristaltic pump Download PDF

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Publication number
US3784323A
US3784323A US00304975A US3784323DA US3784323A US 3784323 A US3784323 A US 3784323A US 00304975 A US00304975 A US 00304975A US 3784323D A US3784323D A US 3784323DA US 3784323 A US3784323 A US 3784323A
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US
United States
Prior art keywords
tube
pump
pressure
pumping
pumping portion
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Expired - Lifetime
Application number
US00304975A
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English (en)
Inventor
A Sausse
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Gambro Industries SAS
Original Assignee
Rhone Poulenc SA
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Filing date
Publication date
Priority claimed from FR6936805A external-priority patent/FR2063677A5/fr
Priority claimed from FR7032932A external-priority patent/FR2105536A6/fr
Application filed by Rhone Poulenc SA filed Critical Rhone Poulenc SA
Application granted granted Critical
Publication of US3784323A publication Critical patent/US3784323A/en
Assigned to SOCIETE DES INDUSTRIES PLASTIQUES-SODIP reassignment SOCIETE DES INDUSTRIES PLASTIQUES-SODIP ASSIGNMENT OF ASSIGNORS INTEREST. Assignors: RHONE-POULENC S.A.
Assigned to HOSPAL SODIP S.A., A SOCIETE ANONYME, MEYZIEU 69330 7 AVENUE LIONEL TERRAY, LYONS reassignment HOSPAL SODIP S.A., A SOCIETE ANONYME, MEYZIEU 69330 7 AVENUE LIONEL TERRAY, LYONS CHANGE OF NAME (SEE DOCUMENT FOR DETAILS). 2-18-81 Assignors: SOCIETE DES INDUSTRIES PLASTIQUES SODIP
Assigned to HOSPAL INDUSTRIE reassignment HOSPAL INDUSTRIE CHANGE OF NAME (SEE DOCUMENT FOR DETAILS). EFFECTIVE OCT. 4, 1983 Assignors: HOSPAL SODIP S.A.
Anticipated expiration legal-status Critical
Expired - Lifetime legal-status Critical Current

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Classifications

    • F—MECHANICAL ENGINEERING; LIGHTING; HEATING; WEAPONS; BLASTING
    • F04—POSITIVE - DISPLACEMENT MACHINES FOR LIQUIDS; PUMPS FOR LIQUIDS OR ELASTIC FLUIDS
    • F04B—POSITIVE-DISPLACEMENT MACHINES FOR LIQUIDS; PUMPS
    • F04B43/00—Machines, pumps, or pumping installations having flexible working members
    • F04B43/12—Machines, pumps, or pumping installations having flexible working members having peristaltic action
    • F—MECHANICAL ENGINEERING; LIGHTING; HEATING; WEAPONS; BLASTING
    • F04—POSITIVE - DISPLACEMENT MACHINES FOR LIQUIDS; PUMPS FOR LIQUIDS OR ELASTIC FLUIDS
    • F04B—POSITIVE-DISPLACEMENT MACHINES FOR LIQUIDS; PUMPS
    • F04B43/00—Machines, pumps, or pumping installations having flexible working members
    • F04B43/12—Machines, pumps, or pumping installations having flexible working members having peristaltic action
    • F04B43/1215—Machines, pumps, or pumping installations having flexible working members having peristaltic action having no backing plate (deforming of the tube only by rollers)

Definitions

  • the present invention relates to a peristaltic pump, which maybe used, for example, for transferring blood from a patient to an extra-corporal circulation device.
  • peristaltic pumps are suitable for extra-corporal circulation devices because of their simplicity of operation and because they avoid any contact of the blood with frictional surfaces responsible for various hazards.
  • they suffer from a serious disadvantage inherent in all volumetric pumps; their flow rate is a function of their speed.
  • a pump If such a pump is connected to a vein and driven by a constant speed motor, it sucks the blood at a practically constant rate whilst the vein is supplied at an unknown rate, which depends particularly on the position of the body, on the arterial pressure and on the average venous pressure. If the supply of the vein drops below the flow rate of the pump, the vein is gradually emptied of its blood and collapses. In the extreme case the puncture needle can cause lesion of the wall of the vessel.
  • Regulating devices have been proposed which either control the speed of the pump by the pressure reduction created upstream or by the level of the blood in a tank interposed between the patient and the pump. These devices are delicate and bulky and have not found general application.
  • a peristaltic pump comprising at least one flexible compressible tube, means for successively compressing the pumping portion of said tube at two points spaced apart and moving the points of compression longitudinally along said portion.
  • the tube, at least along said pumping portion has such a wall thickness and is made of such a material that collapse of the walls of the pumping portion will occur when a predetermined pressure differential exists between the interior and exterior of the pumping portion to restrict the volume aspired therein.
  • the predetermined pressure differential between the interior and the exterior of the pumping portion is less than 250 cms of water.
  • a suitable material for the collapsible portion of the tube is a silicone elastromer.
  • the wall thickness of the collapsible portion may be any suitable value, for example less than 2 millimetres.
  • the tube With the pump according to the invention should the pressure in the tube fall below the predetermined value, the tube will begin to collapse or flatten and thus restrict the volume of liquid aspired therein.
  • FIG. 1 shows one embodiment of pump according to the invention, interposed between a patient and a haemodialyser
  • FIG. 2 is a graph showing how the cross-section of the tube changes as a function of the differences in pressure
  • FIG. 3 is a graph schematically showing the relationship between the shape and the surface of the crosssection of the tube
  • FIGS. 4 and 5 are graphs showing the operating curves of a pump according to the invention as a function of various parameters
  • FIGS. 6a, 6b, and show sectional elevation of embodiments of a roller of the pump flattening the tube.
  • the pump 10 illustrated in FIG. 1 as shown is used for pumping blood from the arm 11 of a patient to a dialyser 12 and back to the arm.
  • An upstream portion 13 of flexible tubing is connected to a pumping portion 14, which, in turn, is connected to a downstream portion 15 leading to the dialyser.
  • the pumping peristaltic action is produced by three rollers 16 having larger diameter portions at their longitudinal centers than at their ends.
  • the three rollers 16 are rotatable as a set about a central axis 17 and the rollers are also rotatable about their own axes.
  • Secured to a support 18 are two clamps 19 and 20 which are arranged to tension the pumping portion 14 over the array of rollers 16.
  • the pumping portion is lightly stretched and the downstream portion 13 and the upstream portion 15 of the tube are below the pumping portion 14.
  • the pump mayfunction in open air, and the differences in pressure arise solely from the variations in the internal pressure of the tube.
  • the possibility of placing the pump inside a controllable pressure chamber is not excluded, and in this case the differences in pressure arise either from the variations in the pressure of the chamber alone or, simultaneously, from the variations in the chamber pressure and the internal pressure of the tube.
  • FIG. 3 shows how the surface S of an ellipse of constant circumference varies as a function of the length of itssmall axis A.
  • Thelimit S lOO and A 1 corresponds to the circle.
  • the tube can also be manufactured to have an elliptical or fusiform cross-section when relaxed. In thiscase,
  • the free cross-section can vary both under the effect of an internal reductionin pressure and of an internal excess pressure.
  • the free cross-section can also vary through elastic stretching of the wall, with the tube increasing in diameter under the action of the internal pressure.
  • Such an expansion however demands much higher differences in pressure and does not occur in the case of flexible but inextensible tubes.
  • pumps in which the tubes change in cross-section through flexing of the wall are preferred; this allows a considerable variation in flow rate for a small variation in pressure, contrary to what would be the case with a change in cross-section by stretching.
  • FIG. 2 shows the standardisation of three silicone elastomer tubes of internal/external diameters 9/l2, lO/l2.6 and 12/14 mm.
  • the ordinate of the graph indicates the thickness of the tube (small external axis) and the abscissa shows the internal pressure reduction, expressed as the height of water raised, all in mm.
  • the forking of the curve corresponds to the appearance of an 8-shaped cross-section with the opposite walls of the tube touching in the middle part (this is not a case of the characteristic displacement of a hysteresis).
  • FIG. 4 shows how the maximum flow rate of a pump varies for a given speed of rotation as a function of the pressure reduction in the suction tube and the lifting pressure, expressed in centimetres of water. For a given speed and a given delivery pressure, it is thus possible to vary the average flow rate by simply changing the height of the pump, so that the peristaltic tube falls in the central portion of the sensitive range.
  • the internal pressure of the peristaltic tube at the pump inlet is equal to the sum of three pressures:
  • any variation in pressure of the liquid to be pumped manifests itself through a variation in pressure in the peristaltic tube, causing a variation in its crosssection and its flow rate.
  • the flow rate necessary and sufficient to maintain a quasi-constant pressure upstream from the pump is self-regulating.
  • the pumps according to the invention are particularly suitable for use as level regulators, because a rise or lowering of the level of the liquid to be pumped respectively causes an increase or reduction in the flow rate of the pump. They are equally suitable for the extra-corporal circulation of blood (for example for haemodialysis), and very particularly when the circulation is from a vein supplied by an arterio-venous fistula; it is, in effect, known that the average pressure in the vein, at the point of entry of the withdrawal needle, can vary. When this pressure drops, the flow rate of a pump according to the invention decreases spontaneously. Thus emptying the vein to the point of complete flattening, which would cause the hazards indicated above, is avoided.
  • the end of the intravenous needle or catheter can come close to the wall of the vessel and change the pressure drop of the whole device. Under these conditions, if the flow rate does not drop very rapidly, the end of the needle or catheter can adhere by suction to the wall of the vessel, entirely stop the flow and cause lesion of the wall.
  • the mechanical part of the pump can theoretically be of any type (with fingers, with rollers and a fixed idling stator or without stator), a rotating pump without stator is preferred in practice.
  • a pump with 3 rollers such as is shown in FIG. 1, is preferred. This pump in effect has particularly valuable advantages in cases where the life of a patient is at stake because if the delivery tube should be partially or completely clocked it acts as a pressure restrictor.
  • the liguid can flow back through the elastic tube which is blocked only through its tension around at least one roller, instead of being flattened between two incompressible elements, and the pump feeds more or less nothing and thus does not present the risk of causing the tube to burst.
  • the pump functions correctly in any position, it is advantageous to locate the pumping tube in a non-horizontal (preferably vertical) plane, with its pumping portion, as illustrated in FIG. 1, at a higher level than its outlet section; this arrangement allows a bubble of air accidentally introduced into the circuit to be retained if the speed of the. liquid pumped is less than the speed of rise of the bubble. This is the case particularly for haemodialysis, where the blood flow rate is low (6.5 to 7 cm/sec in a tube of about one centimetre diameter).
  • the pumping tube is not entirely blocked at the point of the pressure elements, fingers or rollers (at least for the position of the rotor which corresponds to the minimum elongation of the tube in normal operation in the case of a pump without stator): the tube remains open along a crosssection of between 0.01 and 2 mm and preferably about 1 mm. Under these conditions the back-flow of blood upstream is negligible but the backflow of air is complete; the pump cannot feed air towards the patient. When the pump has built up sufficient air it stops and requires the removal of air from the pump to restart.
  • the rollers are not cylindrical but have a smaller diameter at the point of the lateral folds of the tube than in their middle portion. They can, in particular, be a double cone or a doubly conically tapered cylinder. This shape facilitates adjusting the tension of the tube (as defined above) and improves the risistance of the tube to repeated flexing. This shape is also suitable for pumps with a stator, in particular to avoid complete blockage of the tube.
  • a pump without a stator equipped with a stretched tube has an additional advantage; its maximum delivery pressure can be defined with a small margin of variation over a large part ofits range of flow rates (see FIG. 4 and Example 2)..
  • the tube with which a pump according to the invention is equipped can be made of any elastic material sufficiently resistant to repeated flexing, and expecially of elastomers which are suitable for customary peristaltic pumps. Silicone elastomers generally prove satisfactory for biological liquids and furthermore their elastic memory is excellent. Additionally, a tube according to the invention has a thinner wall than in the customary pumps because it must flex as a function of the variations in internal pressure. This reduction in thickness improves the working life of the tube, which is an additional advantage, especially in the case of extracorporal circulation.
  • the peristaltic pump according to the invention possesses the advantages of centrifugal pumps (variable flow rate at constant speed) without suffering from their disadvantages (settling-out and destruction of shaped elements), nor from those of volumetric pumps. It thus simultaneously provides optimum guarantees of safety in suction, in delivery and with regard to the accidental indroduction of air into its suction.
  • EXAMPLE 1 For circulating the blood of patients fitted with arterio-venous fistulas and treated by chronic haemodialysis, the pump represented in FIG. [has the following characteristics: I
  • Doubly conical rollers diameter 6 mm at the centre, apex angle 430, spaced at 120 from one another on a circle of 60 mm radius,
  • silicone elastomer tube of diameter 9 X 12 mm, hardness 55 Shore, stretching by percent under the tension of a weight of 1.2 kg, I
  • Telaxedleiigth s5s''mm length in operation 3 93 to 404 mm (depending on the angular position of the rollers).
  • the pump sucks the blood through a puncture needle (internal diameter 1.6 mm) and lifts it into a haemodialyser connected by appropriate tubes.
  • a speed of about 25 rpm is chosen, corresponding to 75 pulsations; for an approximate height of 70 cm below the patient, and with average flattening of the tube, the blood flow rate is about 300 em /minute.
  • EXAMPLE 2 The following modifications are introduced intgthe pump of Example 1: rollers comprising a cylindrical middle part (12 mm length, 5 mm diameter) ending in truncated cones (length 5 mm, apex angle 430). These rollers, made of stainless steel, run with spindles carried in self-lubricated rings.
  • FIG. 4 represents the maximum flow rate curves of the pump as a function of the lift height (downstream pressure) for two suction heights (upstream presure reduction): 0 to 50 mm of mercury at 25 rpm. It is seen that for a suction of 50 mm Hg., the maximum flow rate only changes from 350 to 300 em /minute for a lift pressure of 0 to 220 mm Hg, whilst it drops from 300 to 0 between about 220 and 260 mm Hg. Safety against excessive delivery pressure is hence very rapidly ensured.
  • the drop in flow rate between 0 and 220 mm Hg is due to the intentional lack of leakproofnes's of the pump; its effect is hence small in the range of pressures used.
  • the flow rates are 340 cm/minute for an upstream pressure reduction of 50 mm Hg and 410 cm /minute for zero pressure reduction.
  • FIG. 5 respectively shows:
  • a method of peristaltic pumping comprising providing a flexible compressible tube said tube being constructed from a silicone elastomer and a pumping portion thereof and reducing the inlet pressure to said tube until the pressure difference between the inside and outside of the pumping portion of the tube becomes so high that said pumping portion partially collapses along the entire length thereof, and successively compressing said partially collapsed pumping portion at spaced apart points of compression and moving the points of compression longitudinally of said portion thereby to reduce the available pumping volume whereby the output from the pump is controlled as a function of the inlet pressure.
  • a method of operating a peristaltic pump to pump liquid from a source said pump being of the type comprising a flexible compressible tube, a pumping portion to said tube and means for successively compressing said pumping portion at spaced apart points of compression and moving the points of compression longitudinally of said portion, including the step of progressively increasing the height of the pump above the source of liquid to be pumped until said pumping portion at least partially collapses clue to reduction of the pressure of fluid within the tube thereby toreduce the available pumping volume whereby the output from the pump is controlled as a function of the inlet pressure.

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  • Engineering & Computer Science (AREA)
  • Mechanical Engineering (AREA)
  • General Engineering & Computer Science (AREA)
  • External Artificial Organs (AREA)
  • Reciprocating Pumps (AREA)
US00304975A 1969-10-27 1972-11-09 Peristaltic pump Expired - Lifetime US3784323A (en)

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
FR6936805A FR2063677A5 (en, 2012) 1969-10-27 1969-10-27
FR7032932A FR2105536A6 (en, 2012) 1970-09-10 1970-09-10

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US3784323A true US3784323A (en) 1974-01-08

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US00304975A Expired - Lifetime US3784323A (en) 1969-10-27 1972-11-09 Peristaltic pump

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US (1) US3784323A (en, 2012)
JP (1) JPS493403B1 (en, 2012)
BE (1) BE758029A (en, 2012)
CA (1) CA939193A (en, 2012)
CH (1) CH516742A (en, 2012)
CS (1) CS163228B2 (en, 2012)
GB (1) GB1287836A (en, 2012)
LU (1) LU61939A1 (en, 2012)
NL (1) NL7015294A (en, 2012)
NO (1) NO128846B (en, 2012)

Cited By (33)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US3949744A (en) * 1973-09-04 1976-04-13 Ellis Whiteside Clarke Apparatus for the administration of liquids
FR2317526A1 (fr) * 1975-07-08 1977-02-04 Rhone Poulenc Ind Pompe peristaltique
FR2363333A1 (fr) * 1976-09-07 1978-03-31 Union Carbide Corp Appareil d'hemodialyse
US4083777A (en) * 1976-09-07 1978-04-11 Union Carbide Corporation Portable hemodialysis system
EP0004600A3 (de) * 1978-03-22 1980-04-16 Hoechst Aktiengesellschaft Peristaltische Dialysatlösungspumpe
US4492531A (en) * 1982-04-30 1985-01-08 Kuraray Co., Ltd. Apparatus for producing a controlled pulsed liquid flow
US4515589A (en) * 1981-03-23 1985-05-07 Austin Jon W Peristaltic pumping method and apparatus
DE3420861A1 (de) * 1984-06-05 1985-12-05 Biotest Pharma GmbH, 6000 Frankfurt Schlauchpumpe fuer medizinische zwecke
US4586882A (en) * 1984-12-06 1986-05-06 Baxter Travenol Laboratories, Inc. Tubing occluder pump
GB2190145A (en) * 1986-05-07 1987-11-11 Cobe Lab Peristaltic pumps
US5222880A (en) * 1991-10-11 1993-06-29 The Regents Of The University Of Michigan Self-regulating blood pump
US5281112A (en) * 1992-02-25 1994-01-25 The Regents Of The University Of Michigan Self regulating blood pump with controlled suction
US5336051A (en) * 1989-09-22 1994-08-09 Yehuda Tamari Inline non-invasive pressure monitoring system for pumps
US5533878A (en) * 1994-05-11 1996-07-09 Daiichi Techno Co., Ltd. Squeeze type pump
WO1996024425A1 (en) * 1995-02-09 1996-08-15 First Medical, Inc. Peristaltic system and method for plasma separation
US5927956A (en) * 1998-09-01 1999-07-27 Linvatec Corporation Peristaltic pump tubing system with latching cassette
US6406267B1 (en) 2000-06-16 2002-06-18 Claude F. Mondiere Extracorporeal circulation pump
US20050074732A1 (en) * 2003-10-02 2005-04-07 Morris Gary Jay Blood pressure simulation apparatus with tactile interface
US20090259089A1 (en) * 2008-04-10 2009-10-15 Daniel Gelbart Expandable catheter for delivery of fluids
US20090280016A1 (en) * 2008-05-07 2009-11-12 Manning Environmental, Inc. Peristaltic pump
JP2012180845A (ja) * 2012-06-26 2012-09-20 Toyo Tire & Rubber Co Ltd スクイーズ式ポンプ用ゴムローラ
US20140271273A1 (en) * 2013-03-15 2014-09-18 Novartis Ag Handheld ocular aspiration tool
US20150104330A1 (en) * 2013-10-14 2015-04-16 Elwha, Llc Peristaltic pump systems and methods
US9126219B2 (en) 2013-03-15 2015-09-08 Alcon Research, Ltd. Acoustic streaming fluid ejector
US9545337B2 (en) 2013-03-15 2017-01-17 Novartis Ag Acoustic streaming glaucoma drainage device
US9624920B2 (en) 2013-10-14 2017-04-18 Elwha Llc Peristaltic pump systems and methods
US9693896B2 (en) 2013-03-15 2017-07-04 Novartis Ag Systems and methods for ocular surgery
US9750638B2 (en) 2013-03-15 2017-09-05 Novartis Ag Systems and methods for ocular surgery
US9861522B2 (en) 2009-12-08 2018-01-09 Alcon Research, Ltd. Phacoemulsification hand piece with integrated aspiration pump
US9915274B2 (en) 2013-03-15 2018-03-13 Novartis Ag Acoustic pumps and systems
US9962288B2 (en) 2013-03-07 2018-05-08 Novartis Ag Active acoustic streaming in hand piece for occlusion surge mitigation
US10182940B2 (en) 2012-12-11 2019-01-22 Novartis Ag Phacoemulsification hand piece with integrated aspiration and irrigation pump
US20240093683A1 (en) * 2021-01-22 2024-03-21 Enplas Corporation Fluid handling system

Families Citing this family (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
CA1110137A (en) * 1976-05-24 1981-10-06 Ingemar H. Lundquist Intravenous liquid pumping system and method

Citations (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US2572658A (en) * 1948-02-16 1951-10-23 Albert G Perkins Automatic teat cup release device for milking machines
US3180272A (en) * 1963-07-09 1965-04-27 Roger L Culbertson Deformable-hose fluid pump

Patent Citations (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US2572658A (en) * 1948-02-16 1951-10-23 Albert G Perkins Automatic teat cup release device for milking machines
US3180272A (en) * 1963-07-09 1965-04-27 Roger L Culbertson Deformable-hose fluid pump

Cited By (42)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US3949744A (en) * 1973-09-04 1976-04-13 Ellis Whiteside Clarke Apparatus for the administration of liquids
FR2317526A1 (fr) * 1975-07-08 1977-02-04 Rhone Poulenc Ind Pompe peristaltique
US4131399A (en) * 1975-07-08 1978-12-26 Rhone-Poulenc Industries Peristaltic tube pump with means preventing complete occlusion of tube
FR2363333A1 (fr) * 1976-09-07 1978-03-31 Union Carbide Corp Appareil d'hemodialyse
US4083777A (en) * 1976-09-07 1978-04-11 Union Carbide Corporation Portable hemodialysis system
EP0004600A3 (de) * 1978-03-22 1980-04-16 Hoechst Aktiengesellschaft Peristaltische Dialysatlösungspumpe
US4515589A (en) * 1981-03-23 1985-05-07 Austin Jon W Peristaltic pumping method and apparatus
US4492531A (en) * 1982-04-30 1985-01-08 Kuraray Co., Ltd. Apparatus for producing a controlled pulsed liquid flow
DE3420861A1 (de) * 1984-06-05 1985-12-05 Biotest Pharma GmbH, 6000 Frankfurt Schlauchpumpe fuer medizinische zwecke
WO1986003561A1 (en) * 1984-12-06 1986-06-19 Baxter Travenol Laboratories, Inc. Tubing occluder pump
US4586882A (en) * 1984-12-06 1986-05-06 Baxter Travenol Laboratories, Inc. Tubing occluder pump
GB2190145A (en) * 1986-05-07 1987-11-11 Cobe Lab Peristaltic pumps
GB2190145B (en) * 1986-05-07 1990-05-16 Cobe Lab Peristaltic pumps
US5336051A (en) * 1989-09-22 1994-08-09 Yehuda Tamari Inline non-invasive pressure monitoring system for pumps
US5222880A (en) * 1991-10-11 1993-06-29 The Regents Of The University Of Michigan Self-regulating blood pump
US5281112A (en) * 1992-02-25 1994-01-25 The Regents Of The University Of Michigan Self regulating blood pump with controlled suction
US5533878A (en) * 1994-05-11 1996-07-09 Daiichi Techno Co., Ltd. Squeeze type pump
WO1996024425A1 (en) * 1995-02-09 1996-08-15 First Medical, Inc. Peristaltic system and method for plasma separation
US6039868A (en) * 1995-02-09 2000-03-21 First Medical, Inc. Blood separator system
US5927956A (en) * 1998-09-01 1999-07-27 Linvatec Corporation Peristaltic pump tubing system with latching cassette
US6406267B1 (en) 2000-06-16 2002-06-18 Claude F. Mondiere Extracorporeal circulation pump
US20050074732A1 (en) * 2003-10-02 2005-04-07 Morris Gary Jay Blood pressure simulation apparatus with tactile interface
US7320599B2 (en) * 2003-10-02 2008-01-22 Gary Jay Morris Blood pressure simulation apparatus with tactile interface
US20080118901A1 (en) * 2003-10-02 2008-05-22 Morris Gary J Blood pressure simulation apparatus with tactile feedback
US7972141B2 (en) 2003-10-02 2011-07-05 Gary Jay Morris Blood pressure simulation apparatus with tactile feedback
US20090259089A1 (en) * 2008-04-10 2009-10-15 Daniel Gelbart Expandable catheter for delivery of fluids
US20090280016A1 (en) * 2008-05-07 2009-11-12 Manning Environmental, Inc. Peristaltic pump
US9861522B2 (en) 2009-12-08 2018-01-09 Alcon Research, Ltd. Phacoemulsification hand piece with integrated aspiration pump
JP2012180845A (ja) * 2012-06-26 2012-09-20 Toyo Tire & Rubber Co Ltd スクイーズ式ポンプ用ゴムローラ
US10182940B2 (en) 2012-12-11 2019-01-22 Novartis Ag Phacoemulsification hand piece with integrated aspiration and irrigation pump
US9962288B2 (en) 2013-03-07 2018-05-08 Novartis Ag Active acoustic streaming in hand piece for occlusion surge mitigation
US9126219B2 (en) 2013-03-15 2015-09-08 Alcon Research, Ltd. Acoustic streaming fluid ejector
US9545337B2 (en) 2013-03-15 2017-01-17 Novartis Ag Acoustic streaming glaucoma drainage device
US9693896B2 (en) 2013-03-15 2017-07-04 Novartis Ag Systems and methods for ocular surgery
US9750638B2 (en) 2013-03-15 2017-09-05 Novartis Ag Systems and methods for ocular surgery
US9915274B2 (en) 2013-03-15 2018-03-13 Novartis Ag Acoustic pumps and systems
WO2014152343A1 (en) * 2013-03-15 2014-09-25 Novartis Ag Handheld ocular aspiration tool
US20140271273A1 (en) * 2013-03-15 2014-09-18 Novartis Ag Handheld ocular aspiration tool
US9541081B2 (en) * 2013-10-14 2017-01-10 Elwha Llc Peristaltic pump systems and methods
US9624920B2 (en) 2013-10-14 2017-04-18 Elwha Llc Peristaltic pump systems and methods
US20150104330A1 (en) * 2013-10-14 2015-04-16 Elwha, Llc Peristaltic pump systems and methods
US20240093683A1 (en) * 2021-01-22 2024-03-21 Enplas Corporation Fluid handling system

Also Published As

Publication number Publication date
GB1287836A (en, 2012) 1972-09-06
DE2052660B2 (de) 1977-06-30
JPS493403B1 (en, 2012) 1974-01-26
BE758029A (fr) 1971-04-26
LU61939A1 (en, 2012) 1971-08-10
NO128846B (en, 2012) 1974-01-21
NL7015294A (en, 2012) 1971-04-29
CA939193A (en) 1974-01-01
DE2052660A1 (de) 1971-05-06
CS163228B2 (en, 2012) 1975-08-29
CH516742A (fr) 1971-12-15

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