CA2729519C - Gas separation devices - Google Patents
Gas separation devices Download PDFInfo
- Publication number
- CA2729519C CA2729519C CA2729519A CA2729519A CA2729519C CA 2729519 C CA2729519 C CA 2729519C CA 2729519 A CA2729519 A CA 2729519A CA 2729519 A CA2729519 A CA 2729519A CA 2729519 C CA2729519 C CA 2729519C
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- Prior art keywords
- fluid
- containing body
- chamber
- aperture
- inlet aperture
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Classifications
-
- B—PERFORMING OPERATIONS; TRANSPORTING
- B01—PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
- B01D—SEPARATION
- B01D19/00—Degasification of liquids
-
- B—PERFORMING OPERATIONS; TRANSPORTING
- B01—PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
- B01D—SEPARATION
- B01D19/00—Degasification of liquids
- B01D19/0042—Degasification of liquids modifying the liquid flow
- B01D19/0052—Degasification of liquids modifying the liquid flow in rotating vessels, vessels containing movable parts or in which centrifugal movement is caused
- B01D19/0057—Degasification of liquids modifying the liquid flow in rotating vessels, vessels containing movable parts or in which centrifugal movement is caused the centrifugal movement being caused by a vortex, e.g. using a cyclone, or by a tangential inlet
-
- 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
- A61M1/34—Filtering material out of the blood by passing it through a membrane, i.e. hemofiltration or diafiltration
- A61M1/342—Adding solutions to the blood, e.g. substitution solutions
- A61M1/3424—Substitution fluid path
- A61M1/3437—Substitution fluid path downstream of the filter, e.g. post-dilution with filtrate
-
- 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
- A61M1/3639—Blood pressure control, pressure transducers specially adapted therefor
- A61M1/3641—Pressure isolators
-
- 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
- A61M1/3672—Means preventing coagulation
- A61M1/3676—Means preventing coagulation by interposing a liquid layer between blood and air
-
- B—PERFORMING OPERATIONS; TRANSPORTING
- B01—PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
- B01F—MIXING, e.g. DISSOLVING, EMULSIFYING OR DISPERSING
- B01F25/00—Flow mixers; Mixers for falling materials, e.g. solid particles
- B01F25/10—Mixing by creating a vortex flow, e.g. by tangential introduction of flow components
-
- B—PERFORMING OPERATIONS; TRANSPORTING
- B04—CENTRIFUGAL APPARATUS OR MACHINES FOR CARRYING-OUT PHYSICAL OR CHEMICAL PROCESSES
- B04C—APPARATUS USING FREE VORTEX FLOW, e.g. CYCLONES
- B04C5/00—Apparatus in which the axial direction of the vortex is reversed
- B04C5/08—Vortex chamber constructions
- B04C5/103—Bodies or members, e.g. bulkheads, guides, in the vortex chamber
-
- 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
- A61M1/3639—Blood pressure control, pressure transducers specially adapted therefor
-
- 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
- A61M2205/00—General characteristics of the apparatus
- A61M2205/33—Controlling, regulating or measuring
- A61M2205/3379—Masses, volumes, levels of fluids in reservoirs, flow rates
- A61M2205/3382—Upper level detectors
-
- 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
- A61M2206/00—Characteristics of a physical parameter; associated device therefor
- A61M2206/10—Flow characteristics
- A61M2206/16—Rotating swirling helical flow, e.g. by tangential inflows
Abstract
Disclosed is a fluid mixing device with gas separation, comprising a containing body having an internal active surface and having at least one first inlet aperture for a physiological fluid, and at least one fluid outlet aperture, spaced apart from the first inlet aperture. In this device, the containing body has at least one second inlet aperture located above the first inlet aperture and designed to convey a second fluid into the containing body to form a layer of the second fluid above the physiological fluid.
Description
GAS SEPARATION DEVICES
The present application is a division of Canadian application No. 2,490,174 corresponding to international patent application No. PCT/IB 2003/002281 filed on May 26, 2003.
Background of the Invention.
The present invention relates to a gas separation device for physiological fluids, particularly for cellular fluids such as blood. The present invention relates also to a fluid mixing device with gas separation.
It is known that any gas particles present in a physiological fluid, such as blood circulating in an extracorporeal circuit, must be effectively removed when the fluid is to be administered to a patient. It should be pointed out that this is because excessively large gas particles can be dangerous if they are transferred to a patient's cardiovascular system.
It is also known that some treatments require the simultaneous administration to a patient of both a physiological fluid, for example blood circulating in an extracorporeal circuit, and an additional fluid, for example an infusion or replacement liquid. However, before the two fluids, for example blood and infusion liquid, are transferred to the patient, it is necessary to remove any gas particles that may be present.
This document makes reference, without restrictive intent, to the field of machines for extracorporeal blood treatment, such as dialysis machines, in which field there is a known method of using at least one gas separation device operating in a line for the return of blood to the patient.
la A gas separation device suitable for the application described above comprises, .typically, a containing body providing within itself a chamber designed to be partially occupied by the blood which is to undergo the degassing operation. Suitable shaping of the chamber allows the blood ak 02729519 2011-01-19 7.0 accumulate in a lower part of the chamber, thus promoting the separation of the gas bubbles. These bubbles can be removed through a service line or discharged directly to the exterior.
Normally, the pressure within the separation device is kept below atmospheric pressure, in order to promote the separation of the air bubbles.
The blood leaving the device described above then passes through an air bubble sensor which, in turn, can ooerate a safety clamp. The clamp is typically positioned on the line returning the blood to the patient, in order to prevent any event considered to be dangerous from being propagated into the patient's cardiovascular system.
Another gas separation device of a known type is illustrated in US Patent No. 5707431. This device comprises a cylindrical chamber divided radially into two parts by a filter, also cylindrical, located centrally in the chamber.
The blood inlet is located in a top part of the chamber and is directed tangentially towards the outer part of the chamber to create a vortex flow. The vortex flow of blood in the outer part of the chamber is converted to an essentially vertical flow as a result of the passage of the fluid through the cylindrical filter. The blood proceeds downwards and passes out through an aperture in the lower Dart of the separation chamber.
The air bubbles, which because of the vortex motion of the blood tend to move towards a perimetric area of the chamber, move upwards towards a hydrophobic membrane which is located at the top of the chamber and which allows the gas to be discharged to the external atmosphere.
Finally, a one-way valve located next to the membrane Prevents the air from returning into the chamber.
The following publications:
- FR 2,508,319;
- EP 0 661 063;
- US 5,421,215;
- JP 90-182404;
- "Interaction of blood and air in venous line air trap chamber", extract from Artificial Organs (vol. 14, suppl. 4), K. Ota and T. Agishi, ICAOT Press, Cleveland 1991, pp. 230-232; and - ASAIO Journal (1993), "Suppression of thrombin formation during hemodialysis with triglyceride"
disclose the use of a layer of fluid interposed between the free surface of the blood and the air, in order to reduce the appearance of coagulation phenomena.
In particular, EP 0 661 063 and US 5,421,815 illustrate a blood/air separation chamber comprising a tubular containing body provided with a to cover to which a blood inlet tube is connected. In the described chamber, the blood accumulates in a lower part of the tubular body; in order to separate the blood from direct contact with the air, a static layer of anticoagulant material is used, comprising triglyceride acids and an antioxidant interposed between the free surface of the blood and the air. Since this static layer is carried on the surface and is only miscible with difficulty with the blood, it prevents direct contact between the blood and the air.
Finally, document WO 00/32104 discloses a pressure sensing system in which a service tube, partially filled with a cell-free solution, is interposed between a pressure sensor and a blood circuit. The cell-free solution creates a separating column between the blood and air which, because of the small section of the service tube, prevents or reduces to a minimum the propagation of one or more oik 02729519 2011-01-19 components of the blood towards the end of the service tube which is occupied by the air.
The technical solutions described above have been found to have certain aspects that could be improved.
In the first place, many of the devices mentioned have large blood-air interfaces which, as is known, promote the formation of clots and encrustations, or, alternatively, in solutions using a static layer to separate the air from the blood, require the use of chemical substances immiscible with blood which float on the surface of the blood to prevent its direct contact with the air.
In the second place, the devices mentioned are not capable of both efficiently mixing the blood with any infusion or replacement fluid that may be present and simultaneously and effectively degassing both fluids.
It should also be noted that the conventional solutions require the presence of a relatively high volume within the gas separation device; in the case of dialysis treatment, for example, the quantity of blood constantly occupying the 90 interior of the separation device increases to a considerable and undesired extent the total amount of blood kept outside the patient.
It should also be noted that, if a tangential blood inlet is to be used to create a vortex to promote the separation of air bubbles from the blood according to the known method, it is necessary to have a central filter to prevent the transfer of the air bubbles to the exit of the separator. The presence of the filter not only increases the overall cost of the device, but also constitutes an additional element which may lead to encrustation and undesired deposits of particles, particularly when part of the filter is located in an air-blood interface area.
Moreover, the known devices which have been described are relatively unsuitable for permitting high blood flows (of the order of 500 ml/min.), low pressure drops and absence of stagnation points, with simultaneous and effective mixing of any infusion liquid.
Summary of the Invention.
An object of the present invention is to provide a gas separation device for a physiological fluid, for example blood, which is capable of operating effectively even at high flow rates, while minimizing the total volume of blood that is to be held within the said device.
A further object of the invention is to provide an optimal quality of the flow through the gas separation device, by essentially eliminating the presence of stagnation points and reducing pressure drops to a minimum.
Another object of the invention is a gas separation device made in such a way that the flow leaving the said device is not capable of generating undesired phenomena of return of gas bubbles towards the outlet of the device.
Another object of the invention is to provide a gas separation device capable of offering an optimal area for access by at least one infusion line, thus permitting an efficient mixing of the blood with the infusion fluid while carrying out effective and simultaneous separation of any gas from the infusion fluid and from the blood, and while minimizing the air-blood interface.
A further object of the present invention which is actually the one specifically claimed hereinafter, is to provide a fluid mixing device with gas separation, capable of operating effectively even at high flow rates, while minimizing the air-blood interface.
The invention also has the object of reducing to the smallest possible level the total volume of blood occupying the said device.
. .
, Another object of the invention is to provide a device for actively adjusting the thickness of a layer of infusion liquid lying above the blood or other cellular fluid.
So, more specifically, the present invention as claimed is directed to a fluid mixing device with gas separation, comprising a containing body having an internal active surface and having at least one first inlet aperture for a physiological fluid, and at least one fluid outlet aperture, spaced apart from the first inlet aperture, characterized in that the containing body has at least one second inlet aperture located above the first inlet aperture and designed to convey a second fluid into the containing body to form a layer of the second fluid above the physiological fluid, wherein the second inlet aperture is directed centrally towards and substantially perpendicular to a longitudinal central axis of the containing body.
Further characteristics and advantages of the invention will be demonstrated by the detailed description of a preferred, but not exclusive, embodiment of a device according to the invention.
The description given below with reference to the attached drawing, is provided purely for guidance and therefore without restrictive intent.
Brief Description of the Drawings - Figure 1 is a view in longitudinal section, showing the device according to the invention in a vertical position similar to that in which it is used;
- Figure 2 shows a longitudinal section through an upper half of the containing body of the device according to the invention;
- Figure 3 shows a longitudinal section through a lower half of the containing body of the device according to the invention;
- Figure 4 is a view through the line IV-IV in Figure 2;
6a - Figure 5 is a view through the line V-V in Figure 3;
- Figure 6 shows a blood treatment line using the device according to the invention;
- Figure 7 shows a plan view of a detail of Figure 1.
Detailed Description.
ak 02729519 2011-01-19 With reference 7.o Figure 1, the number 1 indicates a fluid mixing device with gas separation.
As shown in Figure 6, the device 1 can operate in a disposable line 2 for extracorporeal blood treatment, comprising a branch 3 for withdrawing the blood from the patient, a blood treatment unit 4 and a branch 5 for returning the blood to the patient.
In greater detail, the unit 4, a dialysis filter for example, is interposed between the two branches 3 and 5, while the device 1 operates on the return branch 5, up-line from the point of access to the patient's vascular system.
The device 1 comprises a containing body 6, having a longitudinal axis of symmetry 6a; the body 6 forms an internal volume 16 which is designed to receive a specified quantity of fluid and which has a radial dimension significantly larger than that of the branches 3 and 5, so that the velocity of the said fluid is decreased and the gas is efficiently separated, as described below.
In operating conditions, both the device 1 and the treatment 4 are positioned with their longitudinal axes orientated vertically, although the device can in fact operate with its longitudinal axis inclined.
The fluid, for example blood, flowing through the line 3 passes through the unit 4 with a vertical upward motion and /5 then enters the device 1 and is returned to the patient, as a result of which an optimal degassing of the liquid is achieved.
The containing body 6 has four apertures: a first inlet aperture 7 for the physiological fluid from which the gas is to be separated, a second inlet aperture 3 designed to convey an infusion fluid into the containing body, an cutlet or discharge aperture 9 from which the physiological fluid and any infusion fluid can pass out, and a faurth aperture 10 designed to be connected to a service 14r1 11 for acquirina pressure information, or to be connected directly to the external atmosphere.
In greater detail, the first inlet aperture 7 is formed by a tubular element 7a which communicates with the interior of the containing body and to which a tube 12 for conveying the physiological fluid can be fixed; the first inlet aperture 7 and the corresponding tubular portion 7a are positioned tangentially to the containing body.
The second inlet aperture 8 is spaced apart from and located above the first inlet aperture 7. It should be noted that the second inlet aperture is directed centrally towards the axis 6a of the containing body 6.
The discharge aperture 9, formed by a tubular channel 9a located at the lower end of the containing body, permits the progressive discharge of the blood, or of the blood mixed with the infusion liquid if required.
The containing body 6, whose structure is formed from two halves 13, 14 assembled together, has an active surface 15 which delimits its internal volume 16 where a guide element 17 operates.
The guide element 17 has its own active surface 18, with a continuous profile designed to contact and guide the fluid, as described in detail below. In practice, the guide element is a solid or internally hollow solid of rotation, designed to reduce the internal volume of the containing body that can be actually occupied by the fluid entering through the aforesaid apertures; the guide element 17 is fixed to the said body 6 by means of a support structure comprising radial supports 19 (see Figure 7), spaced apart at equal angular intervals, interposed between the guide element and the containing body. The guide element extends coaxially with the body 5 and is placed above and spaced axially apart from the discharge aperture 9.
A first chamber 20, which has an essentially annular profile and into which the first inlet aperture opens directly, is thus formed between the active surface 18 of the guide element and the active surface 15 of the containing body.
The active surfaces 15 and 18 of the said containing body and the said guide element face each other and are shaped in the form of surfaces of revolution about a common axis of symmetry which is transverse with respect to the tangential direction of access of the said flow. The geometrical configuration and the relative positions of the active surfaces 15 and 18, combined with the tangential direction of the first access aperture, produce a rotary motion of the blood entering from the first aperture 7 around the guide element. This rotary motion promotes the centrifugal radial movement of the gas bubbles having a relatively low mass (c 10 microlitres), while the larger bubbles tend to accumulate in the proximity of the surface of the guide element, whose profile tends to make them move upwards towards the aperture 10.
It should be noted that the guide element 17 comprises, in detail, a central portion 21, a first terminal portion 22 facing the said discharge aperture, and a second terminal portion 23 axially opposed to the first terminal portion.
The first terminal portion 22 has a cross section whose radial dimension is reduced progressively towards the said discharge aperture: in the illustrated example, the first portion is conical with its vertex facing the discharge aperture; and the second terminal portion 23 has a cross section whose radial dimension is reduced progressively away from the said discharge aperture.
In the illustrated example, the second terminal portion is also conically shaped with its vertex facing away from the discharge aperture; the central portion 21 has a cross section whose radial dimension is reduced progressively away from the said terminal portions, to form an intermediate area having a minimum radial dimension. More precisely, the central portion has a curved profile in longitudinal section. It is this special configuration of the central portion that makes the gas bubbles accumulating 5 on the element 17 tend to rise along a path that essentially follows the profile of the said guide element.
in other words, the guide element has a cross section with a constant profile (preferably circular) whose radial dimension first increases and then decreases from the 10 centre of the element towards the two axially opposed ends, thus forming the aforesaid conical terminal portions 22, 23.
The geometry of the containing body 6 will now be described.
In Figure 1 it will be noted that the active surface 15 of the body 6 is divided axially into a plurality of consecutive areas. A first area 24, having the maximum radial dimension and a constant radius, extends around the central portion 21 of the guide element. A second area 25, whose radial dimension is reduced progressively towards the discharge aperture, extends consecutively to the first area 24 and essentially around the first terminal portion of the guide element. A third area 26 whose radial dimension is reduced progressively away from the discharge aperture 75 extends consecutively to the first area and essentially around the second terminal portion of the guide element, at the opposite end from the second area.
As is clearly shown in the attached figures, the first inlet aperture opens into the said first chamber 20, in the said first area 24; thus the entering fluid follows a circular path and is effectively decelerated.
Because cf the guide element 17, the flow in the first chamber rotates about the axis of the containing body, without being allowed to enter the central area of the said first chamber 20, and without giving rise to areas in which the flow velocity is zero. The absence of stagnation points and zero-velocity areas advantageously prevents the development of a siphon effect towards the discharge outlet, thus preventing a harmful return of bubbles and a practically uncontrolled motion of the fluid.
As mentioned above, the containing body also comprises a second inlet aperture 8 located above the first inlet aperture 7 and connected to a line 27 designed to carry a second fluid into the containing body. Normally, an infusion fluid can be sent through the aforesaid line 27 and introduced into the containing body to mix the fluid with the blood or other physiological fluid.
In particular, the containing body has at least a second chamber 28 located above the guide element, in an axially consecutive position and in fluid communication with the said first chamber 20 via an annular passage 29.
The second inlet aperture 8 opens directly into the said second chamber, and creates a layer of infusion liquid which extends above and in contact with the physiological fluid.
It should be noted that the second aperture is positioned with a direction of access 7b which is parallel to the direction of access 8b of the first aperture 8. In greater , detail, as shown in Figures 4 and 5, the directions 7b and 8b are parallel but staggered, or in other words are located in vertical planes which are spaced apart from each other.
A mixing interface is thus formed between the physiological fluid, such as blood, present in the first chamber and the infusion liquid entering the second chamber.
The uniform and rapid mixing, and the simultaneous deaassing, of the two fluids are clearly promoted by the rotary motion imparted to the physiological fluid, by the ak 02729519 2011-01-19 1, relative positioning of the corresponding anertures 7 and 8, and by the interaction between the containing body and the guide element.
Moreover, direct contact between the air and the physiological fluid occupying the first chamber is prevented by the provision of a layer of infusion licuid in the second chamber.
In the illustrated case, if the blood or other physiological fluid flows at a rate of approximately 450 ml/min through the first aperture and a saline fluid flows at a rate of 1 ml/min through the second aperture, it is possible to produce a constant saline-blood layer with a thickness of 5-10 mm in the second chamber.
The thickness of the said layer is greater than 2 mm and smaller than the maximum diameter of the internal surface of the containing body, in order to combine effective de-airing with optimal mixing of the fluids; in the case considered here, the maximum thickness is 20 mm.
The supply of fluid along the line 27 is regulated by means of a pump 27a controlled by a control unit 36. The unit 36 is programmed to control the pump 27a and to provide a specified rate of flow for each specified time interval, in either continuous or intermittent mode. In other words, the control unit can be programmed to follow a specified constant flow rate, or a flow rate variable with time according to a specified profile, or, finally, to supply specified volumes of fluid in intermittent mode at specified time intervals.
A device for measuring the actual flow through the line 27 interacts with the control unit 36. This measuring device comprises, for example, a weighing machine 27b designed to weigh a container of liquid 27c and to send to the unit 36 information relating to the actual weight of the container ak 02729519 2011-01-19 during the treatment. Alternatively, a flowmeter interacting with the said control unit can be provided.
The control unit is capable of controlling the flow rate of the blood pump 3a and the infusion pump 27a in order to ensure that a layer of infusion liquid whose thickness falls within a specified range is constantly present and is located above the blood.
Finally, the containing body includes a third chamber 30, axially consecutive to the said second chamber, and . designed to hold and recover the gas separated from the said fluids; the third chamber extends in the top of the containing body, above the theoretical liquid level BL.
In the illustrated example, the third chamber 30 is bell-shaped and its theoretical volume is delimited below by the level BL and above by the fourth aperture, which connects the internal volume of the containing body, and Particularly that of the third chamber 30, to a service line or directly to the external environment.
In the illustrated example, a service line 11 is provided, with a first end ha placed in fluid communication with the said third chamber 30, and a second end llb connected for operation to a pressure sensor element 31.
As an alternative to what is described above, the pressure sensor element 34 can be made to operate down-line from the /5 device 1.
At least one hydrophobic membrane 32 is associated for operation with an intermediate area llc of the service line to prevent the access of liquid to the pressure sensor (if present) and to ensure sterile separation between the machine side and the side in which the physiological fluid is present and circulates.
The third chamber has a volume such that any increase in pressure in a range from a minimum value to a maximum value ak 02729519 2011-01-19 of Pressure (from 100 to 350 mmHg, for example) does not cause any penetration of liquid into the service line 11, but instead leaves a constant gas space in the third chamber.
it should be noted that different operating modes can be Provided to control the level of the gas that is progressively separated from the fluids or that reaches the device 1 in any way.
1 - Fully manual mode.
At least one access site 33 can be provided in the service line 11, to enable a user to draw off gas in a fully manual way (by means of a syringe).
The present application is a division of Canadian application No. 2,490,174 corresponding to international patent application No. PCT/IB 2003/002281 filed on May 26, 2003.
Background of the Invention.
The present invention relates to a gas separation device for physiological fluids, particularly for cellular fluids such as blood. The present invention relates also to a fluid mixing device with gas separation.
It is known that any gas particles present in a physiological fluid, such as blood circulating in an extracorporeal circuit, must be effectively removed when the fluid is to be administered to a patient. It should be pointed out that this is because excessively large gas particles can be dangerous if they are transferred to a patient's cardiovascular system.
It is also known that some treatments require the simultaneous administration to a patient of both a physiological fluid, for example blood circulating in an extracorporeal circuit, and an additional fluid, for example an infusion or replacement liquid. However, before the two fluids, for example blood and infusion liquid, are transferred to the patient, it is necessary to remove any gas particles that may be present.
This document makes reference, without restrictive intent, to the field of machines for extracorporeal blood treatment, such as dialysis machines, in which field there is a known method of using at least one gas separation device operating in a line for the return of blood to the patient.
la A gas separation device suitable for the application described above comprises, .typically, a containing body providing within itself a chamber designed to be partially occupied by the blood which is to undergo the degassing operation. Suitable shaping of the chamber allows the blood ak 02729519 2011-01-19 7.0 accumulate in a lower part of the chamber, thus promoting the separation of the gas bubbles. These bubbles can be removed through a service line or discharged directly to the exterior.
Normally, the pressure within the separation device is kept below atmospheric pressure, in order to promote the separation of the air bubbles.
The blood leaving the device described above then passes through an air bubble sensor which, in turn, can ooerate a safety clamp. The clamp is typically positioned on the line returning the blood to the patient, in order to prevent any event considered to be dangerous from being propagated into the patient's cardiovascular system.
Another gas separation device of a known type is illustrated in US Patent No. 5707431. This device comprises a cylindrical chamber divided radially into two parts by a filter, also cylindrical, located centrally in the chamber.
The blood inlet is located in a top part of the chamber and is directed tangentially towards the outer part of the chamber to create a vortex flow. The vortex flow of blood in the outer part of the chamber is converted to an essentially vertical flow as a result of the passage of the fluid through the cylindrical filter. The blood proceeds downwards and passes out through an aperture in the lower Dart of the separation chamber.
The air bubbles, which because of the vortex motion of the blood tend to move towards a perimetric area of the chamber, move upwards towards a hydrophobic membrane which is located at the top of the chamber and which allows the gas to be discharged to the external atmosphere.
Finally, a one-way valve located next to the membrane Prevents the air from returning into the chamber.
The following publications:
- FR 2,508,319;
- EP 0 661 063;
- US 5,421,215;
- JP 90-182404;
- "Interaction of blood and air in venous line air trap chamber", extract from Artificial Organs (vol. 14, suppl. 4), K. Ota and T. Agishi, ICAOT Press, Cleveland 1991, pp. 230-232; and - ASAIO Journal (1993), "Suppression of thrombin formation during hemodialysis with triglyceride"
disclose the use of a layer of fluid interposed between the free surface of the blood and the air, in order to reduce the appearance of coagulation phenomena.
In particular, EP 0 661 063 and US 5,421,815 illustrate a blood/air separation chamber comprising a tubular containing body provided with a to cover to which a blood inlet tube is connected. In the described chamber, the blood accumulates in a lower part of the tubular body; in order to separate the blood from direct contact with the air, a static layer of anticoagulant material is used, comprising triglyceride acids and an antioxidant interposed between the free surface of the blood and the air. Since this static layer is carried on the surface and is only miscible with difficulty with the blood, it prevents direct contact between the blood and the air.
Finally, document WO 00/32104 discloses a pressure sensing system in which a service tube, partially filled with a cell-free solution, is interposed between a pressure sensor and a blood circuit. The cell-free solution creates a separating column between the blood and air which, because of the small section of the service tube, prevents or reduces to a minimum the propagation of one or more oik 02729519 2011-01-19 components of the blood towards the end of the service tube which is occupied by the air.
The technical solutions described above have been found to have certain aspects that could be improved.
In the first place, many of the devices mentioned have large blood-air interfaces which, as is known, promote the formation of clots and encrustations, or, alternatively, in solutions using a static layer to separate the air from the blood, require the use of chemical substances immiscible with blood which float on the surface of the blood to prevent its direct contact with the air.
In the second place, the devices mentioned are not capable of both efficiently mixing the blood with any infusion or replacement fluid that may be present and simultaneously and effectively degassing both fluids.
It should also be noted that the conventional solutions require the presence of a relatively high volume within the gas separation device; in the case of dialysis treatment, for example, the quantity of blood constantly occupying the 90 interior of the separation device increases to a considerable and undesired extent the total amount of blood kept outside the patient.
It should also be noted that, if a tangential blood inlet is to be used to create a vortex to promote the separation of air bubbles from the blood according to the known method, it is necessary to have a central filter to prevent the transfer of the air bubbles to the exit of the separator. The presence of the filter not only increases the overall cost of the device, but also constitutes an additional element which may lead to encrustation and undesired deposits of particles, particularly when part of the filter is located in an air-blood interface area.
Moreover, the known devices which have been described are relatively unsuitable for permitting high blood flows (of the order of 500 ml/min.), low pressure drops and absence of stagnation points, with simultaneous and effective mixing of any infusion liquid.
Summary of the Invention.
An object of the present invention is to provide a gas separation device for a physiological fluid, for example blood, which is capable of operating effectively even at high flow rates, while minimizing the total volume of blood that is to be held within the said device.
A further object of the invention is to provide an optimal quality of the flow through the gas separation device, by essentially eliminating the presence of stagnation points and reducing pressure drops to a minimum.
Another object of the invention is a gas separation device made in such a way that the flow leaving the said device is not capable of generating undesired phenomena of return of gas bubbles towards the outlet of the device.
Another object of the invention is to provide a gas separation device capable of offering an optimal area for access by at least one infusion line, thus permitting an efficient mixing of the blood with the infusion fluid while carrying out effective and simultaneous separation of any gas from the infusion fluid and from the blood, and while minimizing the air-blood interface.
A further object of the present invention which is actually the one specifically claimed hereinafter, is to provide a fluid mixing device with gas separation, capable of operating effectively even at high flow rates, while minimizing the air-blood interface.
The invention also has the object of reducing to the smallest possible level the total volume of blood occupying the said device.
. .
, Another object of the invention is to provide a device for actively adjusting the thickness of a layer of infusion liquid lying above the blood or other cellular fluid.
So, more specifically, the present invention as claimed is directed to a fluid mixing device with gas separation, comprising a containing body having an internal active surface and having at least one first inlet aperture for a physiological fluid, and at least one fluid outlet aperture, spaced apart from the first inlet aperture, characterized in that the containing body has at least one second inlet aperture located above the first inlet aperture and designed to convey a second fluid into the containing body to form a layer of the second fluid above the physiological fluid, wherein the second inlet aperture is directed centrally towards and substantially perpendicular to a longitudinal central axis of the containing body.
Further characteristics and advantages of the invention will be demonstrated by the detailed description of a preferred, but not exclusive, embodiment of a device according to the invention.
The description given below with reference to the attached drawing, is provided purely for guidance and therefore without restrictive intent.
Brief Description of the Drawings - Figure 1 is a view in longitudinal section, showing the device according to the invention in a vertical position similar to that in which it is used;
- Figure 2 shows a longitudinal section through an upper half of the containing body of the device according to the invention;
- Figure 3 shows a longitudinal section through a lower half of the containing body of the device according to the invention;
- Figure 4 is a view through the line IV-IV in Figure 2;
6a - Figure 5 is a view through the line V-V in Figure 3;
- Figure 6 shows a blood treatment line using the device according to the invention;
- Figure 7 shows a plan view of a detail of Figure 1.
Detailed Description.
ak 02729519 2011-01-19 With reference 7.o Figure 1, the number 1 indicates a fluid mixing device with gas separation.
As shown in Figure 6, the device 1 can operate in a disposable line 2 for extracorporeal blood treatment, comprising a branch 3 for withdrawing the blood from the patient, a blood treatment unit 4 and a branch 5 for returning the blood to the patient.
In greater detail, the unit 4, a dialysis filter for example, is interposed between the two branches 3 and 5, while the device 1 operates on the return branch 5, up-line from the point of access to the patient's vascular system.
The device 1 comprises a containing body 6, having a longitudinal axis of symmetry 6a; the body 6 forms an internal volume 16 which is designed to receive a specified quantity of fluid and which has a radial dimension significantly larger than that of the branches 3 and 5, so that the velocity of the said fluid is decreased and the gas is efficiently separated, as described below.
In operating conditions, both the device 1 and the treatment 4 are positioned with their longitudinal axes orientated vertically, although the device can in fact operate with its longitudinal axis inclined.
The fluid, for example blood, flowing through the line 3 passes through the unit 4 with a vertical upward motion and /5 then enters the device 1 and is returned to the patient, as a result of which an optimal degassing of the liquid is achieved.
The containing body 6 has four apertures: a first inlet aperture 7 for the physiological fluid from which the gas is to be separated, a second inlet aperture 3 designed to convey an infusion fluid into the containing body, an cutlet or discharge aperture 9 from which the physiological fluid and any infusion fluid can pass out, and a faurth aperture 10 designed to be connected to a service 14r1 11 for acquirina pressure information, or to be connected directly to the external atmosphere.
In greater detail, the first inlet aperture 7 is formed by a tubular element 7a which communicates with the interior of the containing body and to which a tube 12 for conveying the physiological fluid can be fixed; the first inlet aperture 7 and the corresponding tubular portion 7a are positioned tangentially to the containing body.
The second inlet aperture 8 is spaced apart from and located above the first inlet aperture 7. It should be noted that the second inlet aperture is directed centrally towards the axis 6a of the containing body 6.
The discharge aperture 9, formed by a tubular channel 9a located at the lower end of the containing body, permits the progressive discharge of the blood, or of the blood mixed with the infusion liquid if required.
The containing body 6, whose structure is formed from two halves 13, 14 assembled together, has an active surface 15 which delimits its internal volume 16 where a guide element 17 operates.
The guide element 17 has its own active surface 18, with a continuous profile designed to contact and guide the fluid, as described in detail below. In practice, the guide element is a solid or internally hollow solid of rotation, designed to reduce the internal volume of the containing body that can be actually occupied by the fluid entering through the aforesaid apertures; the guide element 17 is fixed to the said body 6 by means of a support structure comprising radial supports 19 (see Figure 7), spaced apart at equal angular intervals, interposed between the guide element and the containing body. The guide element extends coaxially with the body 5 and is placed above and spaced axially apart from the discharge aperture 9.
A first chamber 20, which has an essentially annular profile and into which the first inlet aperture opens directly, is thus formed between the active surface 18 of the guide element and the active surface 15 of the containing body.
The active surfaces 15 and 18 of the said containing body and the said guide element face each other and are shaped in the form of surfaces of revolution about a common axis of symmetry which is transverse with respect to the tangential direction of access of the said flow. The geometrical configuration and the relative positions of the active surfaces 15 and 18, combined with the tangential direction of the first access aperture, produce a rotary motion of the blood entering from the first aperture 7 around the guide element. This rotary motion promotes the centrifugal radial movement of the gas bubbles having a relatively low mass (c 10 microlitres), while the larger bubbles tend to accumulate in the proximity of the surface of the guide element, whose profile tends to make them move upwards towards the aperture 10.
It should be noted that the guide element 17 comprises, in detail, a central portion 21, a first terminal portion 22 facing the said discharge aperture, and a second terminal portion 23 axially opposed to the first terminal portion.
The first terminal portion 22 has a cross section whose radial dimension is reduced progressively towards the said discharge aperture: in the illustrated example, the first portion is conical with its vertex facing the discharge aperture; and the second terminal portion 23 has a cross section whose radial dimension is reduced progressively away from the said discharge aperture.
In the illustrated example, the second terminal portion is also conically shaped with its vertex facing away from the discharge aperture; the central portion 21 has a cross section whose radial dimension is reduced progressively away from the said terminal portions, to form an intermediate area having a minimum radial dimension. More precisely, the central portion has a curved profile in longitudinal section. It is this special configuration of the central portion that makes the gas bubbles accumulating 5 on the element 17 tend to rise along a path that essentially follows the profile of the said guide element.
in other words, the guide element has a cross section with a constant profile (preferably circular) whose radial dimension first increases and then decreases from the 10 centre of the element towards the two axially opposed ends, thus forming the aforesaid conical terminal portions 22, 23.
The geometry of the containing body 6 will now be described.
In Figure 1 it will be noted that the active surface 15 of the body 6 is divided axially into a plurality of consecutive areas. A first area 24, having the maximum radial dimension and a constant radius, extends around the central portion 21 of the guide element. A second area 25, whose radial dimension is reduced progressively towards the discharge aperture, extends consecutively to the first area 24 and essentially around the first terminal portion of the guide element. A third area 26 whose radial dimension is reduced progressively away from the discharge aperture 75 extends consecutively to the first area and essentially around the second terminal portion of the guide element, at the opposite end from the second area.
As is clearly shown in the attached figures, the first inlet aperture opens into the said first chamber 20, in the said first area 24; thus the entering fluid follows a circular path and is effectively decelerated.
Because cf the guide element 17, the flow in the first chamber rotates about the axis of the containing body, without being allowed to enter the central area of the said first chamber 20, and without giving rise to areas in which the flow velocity is zero. The absence of stagnation points and zero-velocity areas advantageously prevents the development of a siphon effect towards the discharge outlet, thus preventing a harmful return of bubbles and a practically uncontrolled motion of the fluid.
As mentioned above, the containing body also comprises a second inlet aperture 8 located above the first inlet aperture 7 and connected to a line 27 designed to carry a second fluid into the containing body. Normally, an infusion fluid can be sent through the aforesaid line 27 and introduced into the containing body to mix the fluid with the blood or other physiological fluid.
In particular, the containing body has at least a second chamber 28 located above the guide element, in an axially consecutive position and in fluid communication with the said first chamber 20 via an annular passage 29.
The second inlet aperture 8 opens directly into the said second chamber, and creates a layer of infusion liquid which extends above and in contact with the physiological fluid.
It should be noted that the second aperture is positioned with a direction of access 7b which is parallel to the direction of access 8b of the first aperture 8. In greater , detail, as shown in Figures 4 and 5, the directions 7b and 8b are parallel but staggered, or in other words are located in vertical planes which are spaced apart from each other.
A mixing interface is thus formed between the physiological fluid, such as blood, present in the first chamber and the infusion liquid entering the second chamber.
The uniform and rapid mixing, and the simultaneous deaassing, of the two fluids are clearly promoted by the rotary motion imparted to the physiological fluid, by the ak 02729519 2011-01-19 1, relative positioning of the corresponding anertures 7 and 8, and by the interaction between the containing body and the guide element.
Moreover, direct contact between the air and the physiological fluid occupying the first chamber is prevented by the provision of a layer of infusion licuid in the second chamber.
In the illustrated case, if the blood or other physiological fluid flows at a rate of approximately 450 ml/min through the first aperture and a saline fluid flows at a rate of 1 ml/min through the second aperture, it is possible to produce a constant saline-blood layer with a thickness of 5-10 mm in the second chamber.
The thickness of the said layer is greater than 2 mm and smaller than the maximum diameter of the internal surface of the containing body, in order to combine effective de-airing with optimal mixing of the fluids; in the case considered here, the maximum thickness is 20 mm.
The supply of fluid along the line 27 is regulated by means of a pump 27a controlled by a control unit 36. The unit 36 is programmed to control the pump 27a and to provide a specified rate of flow for each specified time interval, in either continuous or intermittent mode. In other words, the control unit can be programmed to follow a specified constant flow rate, or a flow rate variable with time according to a specified profile, or, finally, to supply specified volumes of fluid in intermittent mode at specified time intervals.
A device for measuring the actual flow through the line 27 interacts with the control unit 36. This measuring device comprises, for example, a weighing machine 27b designed to weigh a container of liquid 27c and to send to the unit 36 information relating to the actual weight of the container ak 02729519 2011-01-19 during the treatment. Alternatively, a flowmeter interacting with the said control unit can be provided.
The control unit is capable of controlling the flow rate of the blood pump 3a and the infusion pump 27a in order to ensure that a layer of infusion liquid whose thickness falls within a specified range is constantly present and is located above the blood.
Finally, the containing body includes a third chamber 30, axially consecutive to the said second chamber, and . designed to hold and recover the gas separated from the said fluids; the third chamber extends in the top of the containing body, above the theoretical liquid level BL.
In the illustrated example, the third chamber 30 is bell-shaped and its theoretical volume is delimited below by the level BL and above by the fourth aperture, which connects the internal volume of the containing body, and Particularly that of the third chamber 30, to a service line or directly to the external environment.
In the illustrated example, a service line 11 is provided, with a first end ha placed in fluid communication with the said third chamber 30, and a second end llb connected for operation to a pressure sensor element 31.
As an alternative to what is described above, the pressure sensor element 34 can be made to operate down-line from the /5 device 1.
At least one hydrophobic membrane 32 is associated for operation with an intermediate area llc of the service line to prevent the access of liquid to the pressure sensor (if present) and to ensure sterile separation between the machine side and the side in which the physiological fluid is present and circulates.
The third chamber has a volume such that any increase in pressure in a range from a minimum value to a maximum value ak 02729519 2011-01-19 of Pressure (from 100 to 350 mmHg, for example) does not cause any penetration of liquid into the service line 11, but instead leaves a constant gas space in the third chamber.
it should be noted that different operating modes can be Provided to control the level of the gas that is progressively separated from the fluids or that reaches the device 1 in any way.
1 - Fully manual mode.
At least one access site 33 can be provided in the service line 11, to enable a user to draw off gas in a fully manual way (by means of a syringe).
2 - Semiautomatic mode.
The service line 11 is connected to the pressure sensor 31, which is connected down-line to a solenoid valve 34 and to an air pump 35. The valve and the pump can be used to send gas to, or to draw gas from, the service line. If the operating level of the liquid to be maintained in the containing body is indicated by EL, the user can control the pneumatic pump and valve circuit, using a keypad for example, to move the level in one or other direction until EL is reached.
The service line 11 is connected to the pressure sensor 31, which is connected down-line to a solenoid valve 34 and to an air pump 35. The valve and the pump can be used to send gas to, or to draw gas from, the service line. If the operating level of the liquid to be maintained in the containing body is indicated by EL, the user can control the pneumatic pump and valve circuit, using a keypad for example, to move the level in one or other direction until EL is reached.
3 - Automatic mode.
For operation in fully automatic mode, use is made of a liquid level sensor LLS, of the optical, ultrasonic or other type for example. The sensor LLS is located above the level BL. The level sensor LLS can operate at or near the tcp of the containing body; alternatively, the level sensor LLS can be made to operate in a section of the tubing 11a, for example in a terminal area of the tubing, essentially next to the fourth aperture 10 as shown in Figure 1. A
control unit 36 is connected to the sensor LLS and operates the pump 35 and the solenoid valve 34, in order to maintain the liauid level in the vicinity of 3L. In greater detail, the control unit can order the execution of the following steps:
if LLS signals the presence of liquid:
5 a) activation of the pump 35 to drive towards the third chamber a volume V1, equal to the volume between LLS and the fourth aperture;
b) activation of the pump 35 to draw gas from the third chamber while LLS continues to signal the 10 presence of liquid;
c) activation of the pump 35 to drive towards the third chamber a volume of liquid V21 equal to V1 +
V,, where V, is the volume of the third chamber.
if LLS does not signal the presence of liquid, then the 15 aforementioned three steps a), b) and c) are repeated automatically in succession at specified time intervals.
It should be noted that the automatic procedure described above has the significant advantage of not allowing liquid /0 to remain stationary in the section in which the sensor LLS
operates. This is rather important because the upper layer of liquid, even in the presence of a saline infusion injected through the second aperture, always contains a certain percentage of cellular material which, in the long /5 term, can generate encrustations which adversely affect the correct operation of the sensor LLS and consequently the efficient monitoring of the liquid level.
It should also be noted that the described level monitoring procedure prevents the flow of liquid towards the service 30 line 11, thus providing a further means of ensuring safety and guaranteeing the absolute sterility of the fluid present in the device 1.
For operation in fully automatic mode, use is made of a liquid level sensor LLS, of the optical, ultrasonic or other type for example. The sensor LLS is located above the level BL. The level sensor LLS can operate at or near the tcp of the containing body; alternatively, the level sensor LLS can be made to operate in a section of the tubing 11a, for example in a terminal area of the tubing, essentially next to the fourth aperture 10 as shown in Figure 1. A
control unit 36 is connected to the sensor LLS and operates the pump 35 and the solenoid valve 34, in order to maintain the liauid level in the vicinity of 3L. In greater detail, the control unit can order the execution of the following steps:
if LLS signals the presence of liquid:
5 a) activation of the pump 35 to drive towards the third chamber a volume V1, equal to the volume between LLS and the fourth aperture;
b) activation of the pump 35 to draw gas from the third chamber while LLS continues to signal the 10 presence of liquid;
c) activation of the pump 35 to drive towards the third chamber a volume of liquid V21 equal to V1 +
V,, where V, is the volume of the third chamber.
if LLS does not signal the presence of liquid, then the 15 aforementioned three steps a), b) and c) are repeated automatically in succession at specified time intervals.
It should be noted that the automatic procedure described above has the significant advantage of not allowing liquid /0 to remain stationary in the section in which the sensor LLS
operates. This is rather important because the upper layer of liquid, even in the presence of a saline infusion injected through the second aperture, always contains a certain percentage of cellular material which, in the long /5 term, can generate encrustations which adversely affect the correct operation of the sensor LLS and consequently the efficient monitoring of the liquid level.
It should also be noted that the described level monitoring procedure prevents the flow of liquid towards the service 30 line 11, thus providing a further means of ensuring safety and guaranteeing the absolute sterility of the fluid present in the device 1.
Claims (38)
1. A fluid mixing device with gas separation, comprising a containing body having an internal active surface and having at least one first inlet aperture for a physiological fluid, and at least one fluid outlet aperture, spaced apart from the first inlet aperture, characterized in that the containing body has at least one second inlet aperture located above the first inlet aperture and designed to convey a second fluid into the containing body to form a layer of the second fluid above the physiological fluid, wherein the second inlet aperture is directed centrally towards and substantially perpendicular to a longitudinal central axis of the containing body.
2. The device according to claim 1, characterized in that the second inlet aperture is located closer to the central axis of the containing body than the first inlet aperture.
3. The device according to claim 1, characterized in that the said containing body includes:
- at least a first chamber extending in a lower area of the containing body and in fluid communication with the outlet aperture;
- at least a second chamber, extending in an axially consecutive upper area and in fluid communication with the first chamber.
- at least a first chamber extending in a lower area of the containing body and in fluid communication with the outlet aperture;
- at least a second chamber, extending in an axially consecutive upper area and in fluid communication with the first chamber.
4. The device according to claim 3, characterized in that the first chamber and the second chamber are configured to allow formation of a mixing interface between the physiological fluid present in the first chamber and the second liquid entering the second chamber.
5. The device according to claim 3, characterized in that the containing body includes a third chamber, which is axially consecutive to the second chamber and which is designed to contain the gas separated from the said fluids, the third chamber extending in the top of the containing body and having a fourth aperture.
6. The device according to claim 5, characterized in that it comprises at least one service line having a first end which is brought into fluid communication with the third chamber by means of the fourth aperture formed in the containing body.
7. The device according to claim 6, characterized in that it also comprises at least one pressure sensor element associated for operation with the service line.
8. The device according to claim 7, characterized in that it also comprises at least one hydrophobic membrane associated for operation with an intermediate area of the service line, between the fourth aperture and the pressure sensor element.
9. The device according to Claim 5, characterized in that the third chamber has a nominal volume Vc delimited below by a theoretical maximum level line BL and above by the fourth aperture.
10. The device according to claim 6, characterized in that it also comprises a pneumatic circuit for selectively sending gas to the service line and drawing gas from the line.
11. The device according to claim 6, characterized in that it also comprises at least one access site located in the service line for manually drawing fluid from the line or sending fluid to it.
12. The device according to claim 1, characterized in that it comprises:
- a first line for sending the physiological fluid into the said containing body through the first inlet aperture, - a second line for sending the second fluid into the containing body through the second inlet aperture, - a pump operating to create a flow along the first line, - a pump operating to create a flow along the second line, - a programmable control unit for controlling the pumps operating in the first and second lines and for ensuring the constant presence in the containing body of a layer whose thickness lies within a specified range, this layer being located above the physiological fluid.
- a first line for sending the physiological fluid into the said containing body through the first inlet aperture, - a second line for sending the second fluid into the containing body through the second inlet aperture, - a pump operating to create a flow along the first line, - a pump operating to create a flow along the second line, - a programmable control unit for controlling the pumps operating in the first and second lines and for ensuring the constant presence in the containing body of a layer whose thickness lies within a specified range, this layer being located above the physiological fluid.
13. The device according to claim 12, characterized in that the control unit activates the pump operating in the second line in a continuous or intermittent mode, to provide a specified flow rate at every specified time interval.
14. The device according to claim 12, characterized in that it also comprises a means for sensing the actual flow in the second line, this sensor means sending corresponding signals to the said control unit.
15. The device according to claim 12, characterized in that the thickness of the layer is smaller than the maximum diameter of the internal surface of the containing body.
16. The device according to claim 3, characterized in that the first inlet aperture opens directly into the first chamber in a tangential direction of access, and the second inlet aperture opens directly towards the second chamber in a direction of access parallel to that of the first aperture.
17. The device according to claim 16, characterized in that it also comprises a guide element housed at least partially within the body and having a continuous active surface designed to contact and guide the fluid, the first chamber having an annular configuration and being formed between the active surface of the element and the active surface of the containing body.
18. The device according to claim 17, characterized in that the guide element is wholly housed within the containing body, extends coaxially with the latter and is spaced axially apart from the outlet aperture.
19. The device according to claim 17, characterized in that the active surfaces of the containing body and of the guide element face each other and are shaped in the form of surfaces of revolution about a common axis of symmetry which is transverse with respect to the tangential direction of access of the flow.
20. The device according to claim 17, characterized in that the outlet aperture is positioned in a lower end of the containing body, the guide element and the first chamber extending above the outlet aperture.
21. The device according to claim 19, characterized in that the guide element is a solid or internally hollow solid of rotation, designed to reduce the volume of at least the first chamber.
22. The device according to claim 17, characterized in that the guide element comprises:
- a central portion;
- a first terminal portion, facing towards the outlet aperture; and - a second terminal portion, axially opposed to the first terminal portion and facing towards the second chamber.
- a central portion;
- a first terminal portion, facing towards the outlet aperture; and - a second terminal portion, axially opposed to the first terminal portion and facing towards the second chamber.
23. The device according to claim 22, characterized in that the first terminal portion has a cross section whose radial dimension is reduced progressively towards the outlet aperture.
24. The device according to claim 23, characterized in that the first terminal portion has a conical shape with its vertex facing towards the outlet aperture.
25. The device according to claim 22, characterized in that the second terminal portion has a cross section whose radial dimension is reduced progressively away from the outlet aperture.
26. The device according to claim 25, characterized in that the second terminal portion has a conical shape with its vertex opposed to the outlet aperture.
27. The device according to claim 22, characterized in that the central portion has a cross section with a radial dimension which is reduced progressively away from the terminal portions, to form an intermediate area having a minimum radial dimension
28. The device according to claim 27, characterized in that the central portion has a curved profile in longitudinal section.
29. The device according to claim 22, characterized in that the said active surface of the containing body has:
- a first area, of maximum radial dimension, extending around the central portion of the guide element;
- a second area, whose radial dimension is reduced progressively towards the outlet aperture, the second area extending consecutively to the first area and essentially around the first terminal portion of the guide element;
- a third area, whose radial dimension is reduced progressively away from the outlet aperture, the third area extending consecutively to the first area and essentially around the second terminal portion of the guide element.
- a first area, of maximum radial dimension, extending around the central portion of the guide element;
- a second area, whose radial dimension is reduced progressively towards the outlet aperture, the second area extending consecutively to the first area and essentially around the first terminal portion of the guide element;
- a third area, whose radial dimension is reduced progressively away from the outlet aperture, the third area extending consecutively to the first area and essentially around the second terminal portion of the guide element.
30. The device according to claim 29, characterized in that the first inlet aperture opens into the said first chamber, in the intermediate first area.
31. The device according to claim 29, characterized in that the first area of the active surface has a constant radius.
32. A fluid mixing device with gas separation, comprising a containing body having an internal active surface and having at least one first inlet aperture for a physiological fluid, and at least one fluid outlet aperture, spaced apart from the first inlet aperture, characterized in that the containing body has at least one second inlet aperture located above the first inlet aperture and designed to convey a second fluid into the containing body to form a layer of the second fluid above the physiological fluid, wherein the second inlet aperture is located closer to a longitudinal central axis of the containing body than the first inlet aperture.
33. The device according to claim 32, characterized in that the second inlet aperture is directed centrally towards and substantially perpendicular to the central axis of the containing body.
34. A fluid mixing device with gas separation, comprising a containing body having an internal active surface and having at least one first inlet aperture for a physiological fluid, and at least one fluid outlet aperture, spaced apart from the first inlet aperture, characterized in that the containing body has at least one second inlet aperture located above and parallel to the first inlet aperture and designed to convey a second fluid into the containing body to form a layer of the second fluid above the physiological fluid, the second inlet aperture being directed centrally towards and substantially perpendicular to a longitudinal central axis of the containing body, characterized in that the said containing body includes:
- at least a first chamber extending in a lower area of the containing body and in fluid communication with the outlet aperture; and - at least a second chamber, extending in an axially consecutive upper area and in fluid communication with the first chamber; wherein the first chamber and the second chamber are configured to allow formation of a mixing interface between the physiological fluid present in the first chamber and the second liquid entering the second chamber.
- at least a first chamber extending in a lower area of the containing body and in fluid communication with the outlet aperture; and - at least a second chamber, extending in an axially consecutive upper area and in fluid communication with the first chamber; wherein the first chamber and the second chamber are configured to allow formation of a mixing interface between the physiological fluid present in the first chamber and the second liquid entering the second chamber.
35. A fluid mixing method with gas separation, comprising the following steps:
- providing a containing body having an internal active surface and having a first inlet aperture, at least one fluid outlet aperture spaced apart from the first inlet aperture, and a second inlet aperture located above the first inlet aperture;
- sending a first physiological fluid into the containing body through the first aperture;
- conveying a second fluid into the containing body through the second aperture to form a layer of the second fluid above the physiological fluid, the second aperture being directed centrally towards the central axis of the containing body;
- conveying a separated gas from the first and second fluids above the layer.
- providing a containing body having an internal active surface and having a first inlet aperture, at least one fluid outlet aperture spaced apart from the first inlet aperture, and a second inlet aperture located above the first inlet aperture;
- sending a first physiological fluid into the containing body through the first aperture;
- conveying a second fluid into the containing body through the second aperture to form a layer of the second fluid above the physiological fluid, the second aperture being directed centrally towards the central axis of the containing body;
- conveying a separated gas from the first and second fluids above the layer.
36. The method according to claim 35, characterized in that it comprises the steps of:
- measuring the flow rate of the first fluid;
- measuring the flow rate of the second fluid;
- regulating the flow rate of the first and the second fluid to provide a layer of the second fluid with a thickness lying within a specified range.
- measuring the flow rate of the first fluid;
- measuring the flow rate of the second fluid;
- regulating the flow rate of the first and the second fluid to provide a layer of the second fluid with a thickness lying within a specified range.
37. The method according to claim 36, characterized in that the second fluid is sent, in continuous or intermittent mode, in a direction of access to the containing body parallel to that of the first fluid.
38. The method according to claim 36, characterized in that the thickness of the layer is kept below the maximum diameter of the internal surface of the containing body.
Applications Claiming Priority (5)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| IT2002MI001389A ITMI20021389A1 (en) | 2002-06-24 | 2002-06-24 | MIXING DEVICE FOR FLUIDS WITH GAS SEPARATION |
| ITMI2002A001389 | 2002-06-24 | ||
| IT2002MI001390A ITMI20021390A1 (en) | 2002-06-24 | 2002-06-24 | GAS SEPARATION DEVICE FOR PHYSIOLOGICAL FLUIDS |
| ITMI2002A001390 | 2002-06-24 | ||
| CA2490174A CA2490174C (en) | 2002-06-24 | 2003-05-26 | Gas separation devices |
Related Parent Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CA2490174A Division CA2490174C (en) | 2002-06-24 | 2003-05-26 | Gas separation devices |
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| CA2729519A Expired - Lifetime CA2729519C (en) | 2002-06-24 | 2003-05-26 | Gas separation devices |
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| EP (2) | EP2055331B1 (en) |
| JP (1) | JP4358736B2 (en) |
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| DE (1) | DE60326847D1 (en) |
| ES (2) | ES2324707T3 (en) |
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| JP4358736B2 (en) | 2009-11-04 |
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| CA2729519A1 (en) | 2003-12-31 |
| ES2473627T3 (en) | 2014-07-07 |
| EP2055331B1 (en) | 2014-05-14 |
| ATE426420T1 (en) | 2009-04-15 |
| KR100947006B1 (en) | 2010-03-11 |
| AU2003233023B2 (en) | 2008-05-15 |
| US20050247203A1 (en) | 2005-11-10 |
| CA2490174C (en) | 2011-04-19 |
| DE60326847D1 (en) | 2009-05-07 |
| CA2490174A1 (en) | 2003-12-31 |
| JP2005530543A (en) | 2005-10-13 |
| US7517387B2 (en) | 2009-04-14 |
| WO2004000391A1 (en) | 2003-12-31 |
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