EP1191959A2 - Ensemble de gestion de la circulation extracorporelle et procede d'utilisation associe - Google Patents

Ensemble de gestion de la circulation extracorporelle et procede d'utilisation associe

Info

Publication number
EP1191959A2
EP1191959A2 EP01924876A EP01924876A EP1191959A2 EP 1191959 A2 EP1191959 A2 EP 1191959A2 EP 01924876 A EP01924876 A EP 01924876A EP 01924876 A EP01924876 A EP 01924876A EP 1191959 A2 EP1191959 A2 EP 1191959A2
Authority
EP
European Patent Office
Prior art keywords
blood
reservoir
fluid
rigid housing
interior space
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.)
Withdrawn
Application number
EP01924876A
Other languages
German (de)
English (en)
Inventor
Kirk Weimer
Bruce Ellingboe
James Little
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.)
Cobe Cardiovascular Inc
Original Assignee
Cobe Cardiovascular Inc
Priority date (The priority date 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 date listed.)
Filing date
Publication date
Application filed by Cobe Cardiovascular Inc filed Critical Cobe Cardiovascular Inc
Publication of EP1191959A2 publication Critical patent/EP1191959A2/fr
Withdrawn legal-status Critical Current

Links

Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M1/00—Suction or pumping devices for medical purposes; Devices for carrying-off, for treatment of, or for carrying-over, body-liquids; Drainage systems
    • A61M1/36—Other treatment of blood in a by-pass of the natural circulatory system, e.g. temperature adaptation, irradiation ; Extra-corporeal blood circuits
    • A61M1/3621—Extra-corporeal blood circuits
    • A61M1/3627—Degassing devices; Buffer reservoirs; Drip chambers; Blood filters
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M1/00—Suction or pumping devices for medical purposes; Devices for carrying-off, for treatment of, or for carrying-over, body-liquids; Drainage systems
    • A61M1/36—Other treatment of blood in a by-pass of the natural circulatory system, e.g. temperature adaptation, irradiation ; Extra-corporeal blood circuits
    • A61M1/3621—Extra-corporeal blood circuits
    • A61M1/3666—Cardiac or cardiopulmonary bypass, e.g. heart-lung machines
    • A61M1/3667—Cardiac or cardiopulmonary bypass, e.g. heart-lung machines with assisted venous return
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M1/00—Suction or pumping devices for medical purposes; Devices for carrying-off, for treatment of, or for carrying-over, body-liquids; Drainage systems
    • A61M1/60—Containers for suction drainage, adapted to be used with an external suction source
    • A61M1/604—Bag or liner in a rigid container, with suction applied to both

Definitions

  • This invention generally relates to extracorporeal assemblies used to handle body fluids during surgical procedures and, more particularly, to extracorporeal assemblies involving closed, flexible reservoirs used in the drawing and temporary storage of blood from a patient during cardiopulmonary surgical procedures.
  • blood is removed from a patient and passed through an extracorporeal blood handling circuit.
  • blood may be drawn directly from a patient's blood vessels and directed to an extracorporeal circuit for oxygenation, filtration and ultimately return to the patient.
  • the extracorporeal oxygenation step may be omitted.
  • the drawn blood typically is stored temporarily in a reservoir, often referred to as a venous reservoir.
  • the extracorporeal circuit acts as part of the patient's circulatory system, thereby handling up to 2-6 liters of blood or more per minute.
  • a patient's blood may be suctioned off the area surrounding the surgical site.
  • This suctioned blood typically contains significantly more air and other contaminants than blood drawn directly from the blood vessels, and therefore requires greater or additional processing. Nonetheless, it is generally desirable to direct the suctioned blood to an extracorporeal circuit for temporary storage, processing and possible return to the patient.
  • blood is drawn from a patient for extracorporeal processing by gravity alone or by gravity plus mechanical assistance.
  • the most common mechanical assistance procedures are referred to as kinetic assistance and vacuum assistance.
  • Blood drawn from the veins of a patient also known as venous blood, is under a lower pressure than arterial blood and thus gravity and/or mechanical assistance is desirable for venous drainage.
  • the venous blood may be drawn into either an open or a closed reservoir.
  • An open reservoir typically is a rigid or hard shell into which blood flows.
  • the open reservoir may include a calibrated scale to allow an operator, or perfusionist, to readily determine the volume of blood in the reservoir.
  • Open reservoirs have an interface between the ambient air and the top surface of the blood in the reservoir. As such, gas bubbles within the blood can migrate upward in the reservoir and escape. However, the exposure of the blood near the surface to the air may damage components of the blood.
  • a closed reservoir typically is a flexible shell or bag that may be deformed under pressure and may be suspended from a stand near the patient. Blood typically flows into the closed, flexible reservoir from the bottom up.
  • closed, flexible reservoir usually deforms irregularly under pressure, it is not easily calibrated to show the volume of blood contained therein.
  • closed flexible reservoirs largely avoid blood damage caused by exposure to air.
  • closed, flexible reservoirs are generally preferred to open reservoirs for use with blood in applications where the clinician is attempting to minimize blood damage.
  • a system known as kinetic assistance was developed to address the problems of relying on gravity alone to draw venous blood from the patient.
  • a kinetic assistance system uses a mechanical pump connected directly to the patient's venous drainage tube, and consequently, directly to the patient's circulatory system.
  • the pump outflow is connected to a rigid, open venous reservoir and a second pump circulates the blood back to the patient, often after passing through an oxygenator.
  • Kinetic assistance can place significant negative pressure directly on the patient's circulatory system and requires the operation and monitoring of two dynamic, hydraulic circuits.
  • higher negative pressures are required to move adequate volumes of blood. This is a significant problem, as inadvertent application of highly negative pressures associated with some conventional systems may cause the patient's blood vessels to be damaged or even to collapse.
  • vacuum assistance With the increased use of smaller cannulas, a more preferable system to augment gravity drainage is referred to as vacuum assistance.
  • a system in conventional use draws blood into a closed, rigid reservoir by applying a vacuum force directly on the blood in the rigid reservoir. A pump then pumps the blood out of the reservoir, through an oxygenator, if appropriate, and back to the patient. Since the vacuum is applied within the rigid reservoir itself, a flexible, bag-type closed reservoir is impractical. That is, when a vacuum is created within a closed, flexible reservoir, it collapses.
  • vacuum assistance assemblies There are no known vacuum assistance assemblies that have used closed, flexible reservoirs for drawing venous blood in these applications.
  • the vacuum draws not only venous blood directly from the patient's circulatory system, but also blood suctioned from the surgical site.
  • the suctioned blood is typically foamy, as it is drawn into the reservoir with large amounts of air and is often contaminated with other matter.
  • the reservoir includes a defoamer that breaks down the air bubbles in the blood and filters out other contaminants before sending the blood on to an oxygenator. Since the blood in the reservoir is under a vacuum in this system, the air in the bubbles expands even further, making the task of defoaming more difficult.
  • the perfusionist In both the kinetic and vacuum assistance systems, the perfusionist must manage two independent, dynamic blood circuits, one from the patient to the venous reservoir and another from the venous reservoir, through the oxygenator, and back to the patient. This dual circuit approach inevitably presents greater cost and operating complexity to what is typically an expensive and critically complex life sustaining procedure.
  • the kinetic and vacuum assistance systems must maintain a balance between applying sufficient negative pressure to keep the blood flowing and not applying too great a vacuum on the patient's circulatory system. To help maintain this balance, these systems continue to employ gravity as a force to draw blood from the patient.
  • the perfusionist must carefully and continuously monitor the patient and the volume of blood circulating through the extracorporeal blood handling circuit.
  • the perfusionist typically has a short period of time, usually a matter of seconds, to correct a stoppage of blood flow during such a surgical procedure.
  • An extracorporeal blood handling assembly of the present invention comprises a flexible reservoir having an inlet, an outlet and a vent.
  • the flexible reservoir is encompassed within a rigid housing, which is connected to a pump to adjust the pressure within the rigid housing.
  • a pump is connected to the flexible reservoir to withdraw blood from the flexible reservoir.
  • a further embodiment of the invention is directed to an extracorporeal blood handling assembly comprising a flexible reservoir encompassed by a rigid housing having at least two pieces releasably connected together, means to mount a flexible reservoir on the interior of the rigid housing and openings for an inflow conduit, an outflow conduit and a vent conduit.
  • a pump is connected to the rigid housing to adjust the pressure within the rigid housing.
  • Another pump is connected to the flexible reservoir to withdraw blood from the flexible reservoir.
  • the inflow conduit, outflow conduit and vent conduit of the flexible reservoir pass through the corresponding openings in the rigid housing in a releasable, sealed relationship.
  • Yet another embodiment of the invention is directed to an extracorporeal blood handling assembly comprising a flexible reservoir within a fluid filled, rigid housing.
  • the rigid housing is fluidly connected to a reservoir which is partially filled with fluid. Negative pressure applied to the air above the fluid in the reservoir draws fluid from the rigid housing, allowing the flexible reservoir to expand and drawing blood from the patient.
  • a pump is connected to the flexible reservoir to withdraw blood from the flexible reservoir.
  • the invention is also directed to an extracorporeal blood handling assembly comprising a flexible reservoir within a fluid filled, rigid housing.
  • the rigid housing is fluidly connected to a reservoir, which is at least partially filled with fluid and physically located below the rigid housing. Adjusting the volume of fluid in the fluid reservoir creates, maintains and adjusts the negative pressure on the flexible reservoir, drawing the desired blood flow from the patient.
  • the volume of fluid in the fluid reservoir is controlled by, for example, drawing a vacuum on the air above the fluid in the reservoir or, for example, by the force of gravity upon adjusting the height of the fluid reservoir relative to the flexible reservoir.
  • a pump is connected to the flexible reservoir to withdraw blood from the flexible reservoir.
  • a still further embodiment of the invention is to provide a method for extracorporeal blood handling comprising removing blood from a patient through a conduit to a flexible reservoir in a rigid housing by reducing the pressure within the rigid housing. Blood is removed from the flexible reservoir through an outlet conduit by applying negative pressure to the outlet conduit and then returned to the patient.
  • volume control of the flexible reservoir can be achieved through the use of mechanical plates to limit the distension of the flexible reservoir.
  • a flexible bladder can be used, which is connected with a tube to an exterior pump and a reservoir capable of adding or removing fluid to the bladder and blocking the flow of fluid into or out of the bladder. Use of either the plates or the bladder limit distention of the flexible reservoir and thus provide control from the outside, while under vacuum.
  • FIG. 1 is an isometric view of one embodiment of the disclosed invention showing a flexible reservoir and a rigid housing.
  • FIG. 2 is a front elevational view of the embodiment of the invention shown in FIG. 1.
  • FIG. 3 is a side interior sectional view of the embodiment of the invention shown in FIG. 1.
  • FIG. 4 is a schematic view of present invention showing a flexible reservoir and a rigid housing as part of an extracorporeal blood handling system and showing blood flow during normal bypass.
  • FIG. 5 is a schematic view of the embodiment shown in FIG. 4, showing an alternative blood flow through the extracorporeal blood handling system, as during return of blood to the patient.
  • FIG. 6 is a schematic view of the embodiment shown in FIG. 4, showing another alternative blood flow through the extracorporeal blood handling system, as during removal of blood from the patient.
  • FIG. 7 is a schematic view of one embodiment of the invention showing a flexible reservoir within a fluid filled, rigid housing and a vacuum/fluid reservoir.
  • FIG. 8 is a schematic view of another embodiment of the invention showing a flexible reservoir within a fluid filled, rigid housing located above a vacuum/fluid reservoir.
  • FIG. 9 is a cross-sectional side view of an embodiment of the invention having a flexible bladder.
  • FIGS. 1 and 2 generally show an assembly 10 for extracorporeal blood handling comprising a closed, flexible reservoir 12, having blood inlet port 16, a blood outlet port 18 and a vent outlet port 20.
  • the blood inlet port 16 provides a connection for blood from the patient to the flexible reservoir 12.
  • the blood outlet port 18 provides a connection for blood from the flexible reservoir 12 back to the patient.
  • the vent outlet port 20 provides a connection for air and at least some foamy blood, if present, to be evacuated from the flexible reservoir 12.
  • a preferred reservoir 12 for use with the present invention is shown and described in U.S. Patent Nos. 5,352,218; 5,693,039 and 5,720,741.
  • a rigid housing 14 encompasses the flexible reservoir 12 in a substantially sealed relationship to allow a vacuum to be drawn on the interior of the rigid housing 14 in the space between the rigid housing 14 and the exterior surface of the flexible reservoir 12.
  • the rigid housing 14 comprises sealed openings 17, 19, 21 for each of the ports 16, 18, 20 of the flexible reservoir 12. That is, the rigid housing 14 comprises an opening 17 to allow a conduit 25 to connect the patient or other source of blood to the blood inlet port 16, an opening 19 to allow a conduit 27 to connect the blood outlet port 18 back to the patient and an opening 21 to allow a conduit 29 to connect the vent outlet port 20 to a second reservoir for further processing, as will be further described below.
  • the rigid housing 14 also comprises a vacuum conduit opening 23 to connect a vacuum conduit 22 to the interior of the rigid housing 14, so that a vacuum may be drawn on the interior of the rigid housing 14.
  • a valve/gauge 24 may be connected to the vacuum conduit 23 or the vacuum conduit port 22 to measure and/or regulate the vacuum conditions within the rigid housing 14.
  • the openings 17, 19, 21, 23 form a seal around the respective port or conduit passing through the respective walls of the rigid housing 14, thereby allowing a vacuum to be drawn on the space between the rigid housing 14 and the exterior surface of the flexible reservoir 12.
  • the assembly 10 may be manufactured as a disposable unit, with the flexible reservoir 12 assembled within the rigid housing 14, which may not be intended to be opened.
  • the rigid housing 14 comprises at least two pieces 15A and 15B that are releasably connected together, e.g., by one or more hinges and/or locking mechanisms such as mechanism 31, by a snap fit, sealed configuration or by other suitable mechanism.
  • Each piece 15A and 15B forms a sealed relationship with its corresponding connecting piece, preferably with at least one elastomer strip.
  • the rigid housing is shaped to contain and facilitate the repeated insertion and removal of a disposable flexible reservoir 12 for each use and the rigid housing 14 may be fabricated of plastic, such as clear polycarbonate.
  • the flexible reservoir 12 is mounted on the interior of the rigid housing 14.
  • a variety of mechanisms may be employed to mount the flexible reservoir 12 on the interior of the rigid housing 14, including hooks corresponding to openings defined in the outside edges of the flexible reservoir 12, a swing arm to hold the flexible reservoir 12 against one side of the rigid housing 14, or hook and loop fasteners on the flexible reservoir 12 and the interior of the rigid housing 14.
  • the rigid housing may also comprise mechanisms to limit the distension of the flexible bag 12, and thereby adjust and limit its volume.
  • a mechanism could take any of several different forms, including a swinging plate or arm, threaded plunger or a lever. In all cases the mechanism will be capable of changing the maximum volume of the flexible reservoir, and would also be capable of changing the volume of the reservoir during use as desired by the clinician. These volume changes would preferably be made without removing vacuum from the rigid shell.
  • the volume adjustment method employed in the embodiment depicted in FIGS. 1, 2 and 3 consists of two flat plates, the rear plate 90 rectangular and the front plate 91 approximately the same size and shape of the flexible reservoir 12 mounted within the rigid housing.
  • the rear plate 90 is fixed to the rear housing 15B and slanted such that the flexible reservoir inlet 16 and outlet 18 align with the inlet port 17 and outlet port 19 of the rigid enclosure 15.
  • the front plate 91 is attached to the rear plate by a hinge 92 at its bottom, below the flexible reservoir 12 and is shaped similarly to the flexible reservoir 12 with cutaway areas for the inlet 16 and outlet 40 ports of the flexible reservoir 12.
  • the front plate 90 may be swung forward and backward to vary the maximum volume of the flexible reservoir 12 by an arm 93 equipped with a linkage 94 which engages a bar 95 attached to the top edge of the front plate 91.
  • the arm 93 is fixed on a shaft 96 which extends through either side of the rear of the rigid housing 15B via o-ring sealed holes 97, 98.
  • the shaft 96 passes through bearing plates 99, 100 mounted to the exterior of the rear housing 15B at either end.
  • Bearing plated 99 and 100 are preferably made from a material commercially available under the trade designation DELRIN.
  • It is rotated by a second arm 101 mounted on the outer end of the shaft 96 and having two forks which accommodate a trunion block 102 running on a threaded rod 104 mounted in a bushing block 103.
  • the bushing block is preferably made from a material commercially available under the trade designation DELRIN.
  • the threaded rod 104 is actuated by a small handwheel 105.
  • the threaded trunion block 102 travels forward and backward, causing the forked arm 101 to rotate the shaft 96 causing the arm 93 and linkage 94 to swing the front plate 91 forward and backward within the closed rigid housing 15. This change in the position of the front plate 91 allows the operator to vary the maximum volume of the flexible reservoir 12.
  • Provisions will also preferably be made in the present invention to allow for the monitoring of the volume of blood in the reservoir.
  • This monitoring method could include the use of optical sensors, magnetic sensors, weight sensors, mechanical indicators, ultrasonic sensors, or displacement of fluid surrounding the flexible reservoir 12.
  • the assembly 10 is shown as part of a larger extracorporeal blood handling system 30.
  • the patient 32, or other source of blood is connected by conduit 25 to the inlet port 16 of the flexible reservoir 12.
  • the blood is returned to the patient 32, or the other source of blood, through the outlet port 18, the conduit 27, the pump 36, and the oxygenator 38.
  • a safety outlet closure valve 40 may be placed between the flexible reservoir 12 and the pump 36.
  • the safety venous outlet valve 40 which is an integral component of the COBE VRB closed reservoir (see U.S. Patent Nos. 5,352,218; 5,693,039 and 5,720,741) as part of outlet port 18 may be used to prevent the pump 36 from applying excessive negative pressure on the flexible reservoir 12 when there is insufficient or no blood in the flexible reservoir 12.
  • Air, other gases and relatively small amounts of blood may be vented from the flexible reservoir 12 through the vent outlet port 20 and the vent conduit 29 to waste or to a second reservoir 46, typically referred to as a cardiotomy reservoir.
  • a pump 44 or other means of negative pressure, may be connected to the vent conduit 29 to draw this material through the vent outlet port 20.
  • a vent outlet check valve 42 may be connected to restrict air from flowing back into the flexible reservoir 12.
  • a hydrophobic filter also may be provided to the vent outlet port 20 to facilitate the separation of air from blood in the venting process.
  • a source of blood from the patient is blood suctioned from the surgical site or otherwise.
  • the volume of suctioned blood and blood vented from the flexible reservoir 12 is significantly less than the volume of blood circulating through the extracorporeal system, typically in the range of about 0.1 to 0.5 liters per minute. Nonetheless, it is often desirable to temporarily store, process, and possibly return to the patient this suctioned blood and vented blood.
  • a vacuum source 52 draws suctioned blood from the surgical site of the patient 32 through a conduit 48 to the second reservoir 46.
  • the suctioned blood is typically more contaminated, more foamy and generally more difficult to process for return to the patient 32.
  • the second reservoir 46 preferably is a rigid, open reservoir to allow easier monitoring of blood volume and easier treatment of unwanted air, other gas and other contaminants.
  • the blood from the second reservoir 46 may require additional processing steps, such as defoaming, filtration and oxygenation before being returned to the patient 32.
  • the vacuum conduit 22 is connected to a suitable source of vacuum 34, which is typically available in the operating room environment.
  • the vacuum source 34 is regulated to the desired negative pressure through the use of an appropriate vacuum regulator 24.
  • the level of negative pressure is adjusted to maintain the flexible reservoir 12 at a predetermined, fixed volume. That is, the flexible reservoir is preferably fully expanded to the mechanical or hydraulic limits imposed in fixing its desired volume. As set forth below, this negative pressure level represents the maximum level of negative pressure that would be applied to the patient's circulatory system in the event of a venous occlusion.
  • the mechanical limit is the volume limit imposed by the adjustable plates in the embodiment depicted in FIGS. 1, 2 and 3 or a swinging arm, threaded plunger or lever, depending on the mechanism employed.
  • the hydraulic limit is the fixed volume limit maintained by the hydraulic systems as described in FIGS. 7-9. In the case of the systems in FIG. 7, the hydraulic limit is maintained by a level sensor 76 in the vacuum/fluid reservoir 64 feeding back to the electronic vacuum regulator 72.
  • the blood inlet conduit 25 makes a fluid connection from the circulatory system of the patient 32 to the flexible reservoir 12 and the blood outlet conduit 27 makes another fluid connection from the flexible reservoir 12 through pump 36 and back to the patient 32. This completes an entirely hydraulic circuit from the patient and back.
  • the vent outlet port 20 is connected to a pump 44, or other suitable means capable of removing air or other gas trapped in the bag, either continuously or as desired, to the second reservoir 46. If not previously installed, the flexible reservoir 12, with little or no distention, is mounted within the inside of the rigid housing 14.
  • the rigid housing 14 is substantially sealed around the flexible reservoir 12 and the conduits 25, 27, 29 connected thereto.
  • the vacuum source 34 begins to draw a vacuum in the space between the exterior surface of the flexible reservoir 12 and the interior surface of the rigid housing 14. This vacuum will apply a vacuum force on the walls of reservoir 12 , and consequently, also to the inside of the flexible reservoir 12.
  • This vacuum force inside the flexible reservoir 12 draws blood directly from the vasculature of the patient 32 through the blood inlet conduit 25 through the inlet port 16 and into the flexible reservoir 12.
  • the pump 36 may be started, drawing blood from the flexible reservoir 12 through the outlet conduit 27 for eventual return to the patient 32.
  • the pump 36 is a roller or centrifugal pump having a capacity of about 0 to about 8 liters per minute, and operates at about 2 to about 6 liters per minute.
  • the flexible reservoir 12 is being pulled open by the vacuum force.
  • the negative pressure within the rigid housing 14 is from about 0 mmHg to about negative 120 mmHg, and more preferably is from about negative 20 mmHg to about negative 60 mmHg.
  • a vacuum/fluid reservoir 64 is fluidly connected by conduit 61 to the rigid housing 14.
  • the vacuum/fluid reservoir 64 is connected by conduit 69 to a vacuum regulator 72 and to a vacuum source 74.
  • a sensor 76 measures the level of liquid 66 in the vacuum/fluid reservoir 64.
  • the flexible reservoir 12 is essentially emptied of fluid, including gas, and installed within the rigid housing 14, which is then closed and filled with liquid 66.
  • the vacuum/fluid reservoir 64 is partially filled with liquid 66, thereby leaving a volume of air 68 in the vacuum/fluid reservoir 64.
  • sensor 76 is then calibrated to display the volume of the flexible reservoir 12 as zero.
  • Vacuum source 74 through the vacuum regulator 72, applies a desired negative pressure on the air 68 in the vacuum/fluid reservoir 64.
  • liquid 66 is drawn from the rigid housing 14 into the vacuum/fluid reservoir 64, which causes the flexible reservoir 12 to expand and draw blood from the patient.
  • the flexible reservoir 12 is maintained at a constant volume by using a feedback loop between the electronic vacuum regulator 72 and the continuous level sensor 76.
  • the vacuum regulator 72 may be used to maintain a constant negative pressure, while the volume of the flexible reservoir 12 is monitored to make sure the fluid volume in reservoir 12 is maintained within safe operating limits.
  • the vacuum pressure on the surface of the flexible reservoir 12 will vary with the height of the vacuum/fluid reservoir 64 with respect to the flexible reservoir 12.
  • the vacuum pressure is preferably measured in the rigid housing 14, instead of at the vacuum regulator 72, or alternatively the level of fluid 66 in the rigid housing 14 is compensated for in the regulator setting.
  • a preferred arrangement would place the vacuum/fluid reservoir 64 no higher than necessary to allow adequate flow from it into the rigid enclosure 15 when filling the rigid enclosure and high enough so that the level of the fluid in the vacuum/fluid reservoir 64 would always be above the top of the interior of the rigid enclosure 15.
  • the vacuum/fluid reservoir's aspect ratio (height to width) is preferably minimized to minimize the variation in pressure at the surface of the flexible reservoir 12 as the volume of the flexible reservoir is varied.
  • Volume of the vacuum/fluid reservoir 64 should be greater than the volume of the rigid enclosure 15 to ensure that the rigid enclosure 15 would remain full of fluid during operation.
  • FIG. 8 An alternative vacuum/fluid reservoir system of the present invention is shown in FIG. 8. In this embodiment, the rigid housing 14 is physically located above a vacuum/fluid reservoir 64, which is fluidly connected by conduit 61 to the rigid housing 14.
  • a sensor 76 measures the level of liquid 66 in the vacuum/fluid reservoir 64.
  • the flexible reservoir 12 is emptied of fluid, including gas, and installed within the rigid housing 14, which is then closed and filled with liquid 66.
  • the conduit 61 is filled with liquid 66, while the vacuum/fluid reservoir 64 is at least partially filled with liquid 66, leaving a volume of air 68 in the vacuum/fluid reservoir 64.
  • sensor 76 is then calibrated to display the volume of the flexible reservoir 12 as zero.
  • a vacuum on the flexible reservoir 12 is generated by the presence and weight of the liquid 66 and is adjusted by adjusting the height of the vacuum/fluid reservoir with respect to the flexible reservoir 12.
  • the vacuum on the flexible reservoir 12 may be generated and adjusted by changing the volume of liquid 66 in the vacuum/fluid reservoir 64. This may be accomplished by a number of ways.
  • liquid 66 may simply be added or withdrawn from the vacuum/fluid reservoir 64.
  • the vacuum/fluid reservoir 64 may be constructed to have an adjustable volume, such as by connecting two rigid plates with a bellows or convoluted gasket. The vacuum/fluid reservoir 64 may then be held rigidly at a desired volume, with a separate vacuum regulator attached. Alternatively, the vacuum/fluid reservoir 64 may be spring loaded to maintain a constant vacuum by varying its volume. In any event, such a system does not require a pump or other vacuum source operating on the flexible reservoir 12, the rigid housing 14 or the vacuum/fluid reservoir 64 to draw blood from the patient.
  • Another alternative method for limiting the volume of the flexible reservoir 12 as illustrated in FIG. 9 is to include within the rigid housing a second flexible reservoir or bladder 110 in close proximity to the flexible reservoir 12 and attached to one or both of the interior walls of the rigid housing.
  • This second flexible reservoir or bladder 110 is connected via a port 111 in the rigid housing to a fluid or gas source with a reservoir of adequate volume 112 and a pump 113 capable of moving fluid or gas into or out of this second flexible reservoir or bladder 110 to limit the maximum volume of the flexible reservoir 12.
  • the above described mechanism serves to allow the adjustment of the volume of the flexible reservoir 12 within the closed rigid housing in a way similar to the swinging arm or plate or threaded plunger referred to elsewhere but with fewer and less costly components.
  • Air in the blood is capable of migrating to the top of the flexible reservoir 12.
  • vent outlet port 20 By providing a vent outlet port 20, vent conduit 29 and pump 44, the air or other gas in the flexible reservoir 12 may be removed from the blood.
  • the venting of the flexible reservoir 12 is desirable in a dynamic extracorporeal blood handling assembly, particularly with continuous, or nearly continuous blood flow through reservoir 12.
  • the extracorporeal blood handling assembly acts as part of the patient's circulatory system, often handling about 2 to about 6 liters or more of blood per minute. Absent an effective vent of the flexible reservoir 12, small amounts of air or other gases could accumulate in the flexible reservoir 12 and eventually reduce the volume of the reservoir available for blood and could potentially be returned to the patient's circulatory system and cause patient injury.
  • the volume of the flexible reservoir 12 remains constant, regardless of blood flow volume or pressure, within normal operating parameters. This fixed volume may be changed or adjusted to allow expansion of the flexible reservoir 12 to any one of various preselected volumes. However, once the volume of the flexible reservoir 12 is fixed, it remains constant, under normal operating parameters. This further reduces the workload of the perfusionist, who is generally responsible for managing the circulating blood volume of the patient 32.
  • the controlled negative pressure at the blood inlet port 16 may also be used as the driving force to manage patient blood volume located between the patient 32, the closed, flexible reservoir 12, and an open, second reservoir 46.
  • the inlet conduit 25 comprises a single conduit from the patient 32 to the flexible reservoir 12.
  • a first control conduit 25A may branch from the inlet conduit 25 to the second reservoir 46 and a second control conduit 25B may connect the second reservoir 46 back to the inlet conduit 25.
  • first control conduit 25 A may directly connect the patient 32 to the second reservoir 46 and/or the second control conduit 25B may directly connect the second reservoir 46 to the flexible reservoir 12.
  • a flow control mechanism such as a clamp, a valve, or other suitable means, may be used to allow full, partial or no flow in each of the first control conduit 25 A, the second control conduit 25B and the inlet conduit 25.
  • such a flow control mechanism on the inlet conduit 25 may be placed between the connection with the first control conduit 25A and the connection with the second control conduit 25B.
  • the motive force moving the blood through the blood outlet conduit 27 is the pump 36, not the vacuum force or gravity, as in prior systems. That is, blood movement out of the blood outlet conduit 27 generally stops when the pump 36 stops. If a preferable peristalic pump is used for pump 36, this occludes the outlet tubing repeatedly during operation and then provides a constant occlusion when pump 36 is stopped thereby even stopping gravity outflow from reservoir 12.
  • the vacuum force is required to hold the outflow conduit 27 open to its desired volume and to provide negative pressure regulation to the blood inlet port 16, and subsequently, the circulatory system of the patient 32. The vacuum force is thus the maximum negative force to which the patient's circulatory system is exposed. But the vacuum force does not move blood out of the flexible reservoir 12.
  • An outlet valve 40 may be provided to automatically close off the blood outlet conduit if the volume of blood in the flexible reservoir 12 drops to an insufficient level, or to zero. If valve 40 closes, pump 36 will no longer draw blood, or anything else, from the flexible reservoir 12. Pump 36 presents a negative pressure to the interior of the flexible reservoir 12, which may collapse the flexible reservoir if there is no blood therein, and thus will not draw blood into the flexible reservoir 12. This will consequently not apply a negative pressure through inlet 16 or conduit 25 on the circulatory system of the patient 32. The flexible reservoir 12 thereby acts as a pressure buffer between the pump 36 and the circulatory system of the patient 32. This limits the maximum amount of negative pressure applied to the patient 32, which is important as excessive negative pressure can seriously damage the patient's circulatory system.
  • the disclosed invention also allows the use of roller pumps in venous blood drainage assistance, in a single pump, single circuit system.
  • kinetic assistance was performed using centrifugal pumps because of the low negative stall pressure generated by the centrifugal pump.
  • Low stall pressure is critical when a mechanical pump is acting directly on the patient's circulatory system, as high negative stall pressure may cause vascular damage and injury to the patient.
  • Roller pumps are typically simpler and less costly to operate, in part due to the expensive disposable components required in centrifugal pumps.
  • the flexible reservoir 12 may hold up to about 2 liters of blood, or even more. If a cannula is occluded, the flexible reservoir 12 can supply the pump 36 with the entire volume of blood in the flexible reservoir 12. When it is full with about 2 liters of blood, the perfusionist has up to about 30 seconds to recognize and attempt to resolve the problem before there is no additional blood to process and/or return to the patient 32.
  • Blood removed from the flexible reservoir 12 through the blood outlet conduit 27 may then be processed for return to the patient.
  • this blood is passed through an oxygenator 38, and perhaps a filter, before being returned directly to the blood vessels of the patient 32.
  • the oxygenator should be of sufficient capacity so as process the desired blood flow from both the venous reservoir 12 and the second reservoir 46, including maximum blood flows of up to about 2 to about 6 liters or more of blood per minute, as well as possible periods of time with little or no blood flow.
  • the oxygenator mechanism and/or step may be omitted.
  • the present invention is not a two circuit system, requiring the perfusionist to manage and monitor two independent and dynamic hydraulic circuits.
  • the circulating volume of the blood may be managed with a single blood pump and a single blood pump control, simplifying and reducing the workload of the perfusionist and reducing the cost and complexity of the equipment.
  • the disclosed invention may also be used in a number of other applications, such as where it is desirable to safely connect a single inexpensive pump circuit directly to a patient's circulatory system.
  • These applications could include kidney dialysis pump systems and "at the table” cardio-pulmonary bypass systems, among others.

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  • Health & Medical Sciences (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Vascular Medicine (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Engineering & Computer Science (AREA)
  • Anesthesiology (AREA)
  • Biomedical Technology (AREA)
  • Hematology (AREA)
  • Cardiology (AREA)
  • Animal Behavior & Ethology (AREA)
  • General Health & Medical Sciences (AREA)
  • Public Health (AREA)
  • Veterinary Medicine (AREA)
  • Pulmonology (AREA)
  • External Artificial Organs (AREA)

Abstract

La présente invention concerne un appareil et un procédé de gestion de la circulation extracorporelle dans lesquels on utilise un réservoir souple enfermé dans un contenant rigide pour soutirer et conserver momentanément le sang veineux pendant des interventions chirurgicales. On crée du vide dans l'espace situé entre le réservoir souple et le contenant rigide pour faciliter l'aspiration par gravité du sang veineux dans le réservoir souple. Un évent peut être prévu pour évacuer l'air, d'autres gaz et du sang spumeux du réservoir souple et une pompe peut être utilisée pour soutirer le sang du réservoir souple. Les forces primaires s'exerçant sur le sang veineux du patient pour le faire circuler à l'intérieur du contenant rigide sont la force de gravité et la force du vide, aucune autre pompe n'intervenant dans le système. .
EP01924876A 2000-04-06 2001-04-06 Ensemble de gestion de la circulation extracorporelle et procede d'utilisation associe Withdrawn EP1191959A2 (fr)

Applications Claiming Priority (3)

Application Number Priority Date Filing Date Title
US54398400A 2000-04-06 2000-04-06
US543984 2000-04-06
PCT/US2001/011584 WO2001076656A2 (fr) 2000-04-06 2001-04-06 Ensemble de gestion de la circulation extracorporelle et procede d'utilisation associe

Publications (1)

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EP1191959A2 true EP1191959A2 (fr) 2002-04-03

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EP01924876A Withdrawn EP1191959A2 (fr) 2000-04-06 2001-04-06 Ensemble de gestion de la circulation extracorporelle et procede d'utilisation associe

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EP (1) EP1191959A2 (fr)
JP (1) JP2003530160A (fr)
AU (1) AU2001251489A1 (fr)
WO (1) WO2001076656A2 (fr)

Families Citing this family (10)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
EP1557186B1 (fr) * 2004-01-20 2010-11-17 Sorin Group Deutschland GmbH Système automatique d'élimination d'air
EP2246080B1 (fr) 2007-10-12 2016-02-10 DEKA Products Limited Partnership Système de circulation sanguine extracorporel
DE102009026592B4 (de) * 2009-05-29 2014-08-28 Sorin Group Deutschland Gmbh Vorrichtung zur Festlegung des venösen Zuflusses zu einem Blutreservoir eines extrakorporalen Blutkreislaufs
DE102009027195A1 (de) 2009-06-25 2010-12-30 Sorin Group Deutschland Gmbh Vorrichtung zur Förderung von Blut in einem extrakorporalen Kreislauf
US8506513B2 (en) 2010-04-20 2013-08-13 Sorin Group Italia S.R.L. Blood reservoir with ultrasonic volume sensor
US8500673B2 (en) 2010-04-20 2013-08-06 Sorin Group Italia S.R.L. Blood reservoir with level sensor
EP2545948B1 (fr) 2011-07-12 2014-04-16 Sorin Group Italia S.r.l. Réservoir de sang à double chambre
EP3142719B1 (fr) 2014-05-16 2019-11-06 Sorin Group Italia S.r.l. Réservoir de sang à mesure de volume de fluide basée sur un capteur de pression
JP6510645B2 (ja) * 2014-11-26 2019-05-08 ソリン・グループ・イタリア・ソシエタ・ア・レスポンサビリタ・リミタータＳｏｒｉｎ Ｇｒｏｕｐ Ｉｔａｌｉａ Ｓ．ｒ．ｌ． 静脈バッグのクランピング機構
US10338029B2 (en) 2014-12-10 2019-07-02 General Electric Company Systems and methods for improved physiological monitoring

Family Cites Families (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
DE2922957A1 (de) * 1979-06-06 1980-12-18 Mottaghy Khosrow Verfahren und vorrichtung zum umwaelzen bzw. pumpen organisch-biologischer fluessigkeiten, insbesondere von blut
DE3172813D1 (en) * 1980-05-20 1985-12-12 Haemonetics Corp Suction liquid collection assembly and flexible liquid collection bag suitable for use therein
US5201703A (en) * 1987-09-29 1993-04-13 Conmed Corporation Apparatus for collecting blood from a chest drainage unit and reinfusion of the blood
US6039078A (en) * 1989-09-22 2000-03-21 Tamari; Yehuda Inline extracorporeal reservoir and pressure isolator
CA2044666C (fr) * 1990-06-15 1999-01-05 John Thomas Buckley Poche-reservoir pour le sang veineux
US6017493A (en) * 1997-09-26 2000-01-25 Baxter International Inc. Vacuum-assisted venous drainage reservoir for CPB systems

Non-Patent Citations (1)

* Cited by examiner, † Cited by third party
Title
See references of WO0176656A2 *

Also Published As

Publication number Publication date
WO2001076656A3 (fr) 2002-02-07
JP2003530160A (ja) 2003-10-14
WO2001076656A2 (fr) 2001-10-18
AU2001251489A1 (en) 2001-10-23

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