CA1144835A - Cardiotomy reservoir - Google Patents
Cardiotomy reservoirInfo
- Publication number
- CA1144835A CA1144835A CA000327200A CA327200A CA1144835A CA 1144835 A CA1144835 A CA 1144835A CA 000327200 A CA000327200 A CA 000327200A CA 327200 A CA327200 A CA 327200A CA 1144835 A CA1144835 A CA 1144835A
- Authority
- CA
- Canada
- Prior art keywords
- blood
- tubular member
- tubular
- reservoir
- defoaming
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Expired
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
- A61M1/14—Dialysis systems; Artificial kidneys; Blood oxygenators ; Reciprocating systems for treatment of body fluids, e.g. single needle systems for hemofiltration or pheresis
- A61M1/32—Oxygenators without membranes
- A61M1/322—Antifoam; Defoaming
- A61M1/325—Surfactant coating; Improving wettability
Abstract
ABSTRACT OF THE DISCLOSURE
A cardiotomy reservoir is disclosed and includes a rigid casing having inlet and outlet means for blood and blood filter and defoaming means therein. Improved inlet means is provided and comprises a plurality of tubular-apertures positioned adjacent the upper end of the reservoir and having open ends which are out-wardly directed normally of the longitudinal axis of the reservoir.
The apertures inwardly terminate in open-bottom, downwardly curved end wall means, to direct fluid flow inwardly through the apertures and then downwardly by means of a gently, curved flow in the reservoir.
A cardiotomy reservoir is disclosed and includes a rigid casing having inlet and outlet means for blood and blood filter and defoaming means therein. Improved inlet means is provided and comprises a plurality of tubular-apertures positioned adjacent the upper end of the reservoir and having open ends which are out-wardly directed normally of the longitudinal axis of the reservoir.
The apertures inwardly terminate in open-bottom, downwardly curved end wall means, to direct fluid flow inwardly through the apertures and then downwardly by means of a gently, curved flow in the reservoir.
Description
s IMPROVED CARDIOTOMY RESERVOIR
Inventors: Thomas W. Crockett Patrick N. Huehls sarry G. Slotnick John M. Munsch Ludwig Wolf, Jr.
Cardiotomy reservoirs are currently used in major surgical procedures, such as open heart surgery, for receiving blood from a cardiotomy sucker and other sources, for defoaming the blood, filtering out debris ~ and returning it to the patient.
Numerous designs of cardlotomy reservoirs are commercially offered, for example, a cardiotomy reservoir similar to that disclosed in U.S. Patent No. 3,993,461, and its predecessor in design being as disclosed in U.S. Patent ~; No. 3,891,416. In both of these cardiotomy reservoirs, a hollow casing is provided in which a tubular member is . positioned within the casing and extends between the ends thereof. Blood enters the boktom of the tubular member, rising upwardly until it passes out of an aperture to the exterior of the tubular member.
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;3~ii The Shiley cardiotomy reservoir which is currently commercially available also comprises a casing having a tu-bular member extending through the interior from end to end, with filter and defoaming material carried outside of the tubular member. Blood enters the top of the reservoir ~- through inlet ports at a side thereof, then normally falling downwardly and then passing through the defoaming material within the casing from where it is returned to the patient.
The space within the tubular member is not used.
The lower end of the tubular member of the Shiley reservoir is retained by a bottom hump, in the lower end of the casing. The periphery of the lower end is sloped slightly to allow blood to flow to the lowest point, where the outlet is positioned.
One problem with this reservoir and its side entry blood inlet ports is that some blood coming in one port can swing around the circumference of the tubular casing and flow out one of the other ports, rather than falling downwardly into the defoaming material.
In introducing blood to a cardiotomy reservoir, it is also highly desirable to avoid the harsh impingement of blood upon a wall surface or the like, since that can result in an increase in the hemolysis level of the blood.
On the other hand~ blood which is introduced into one of the entry ports of a cardiotomy reservoir should not have the tendency to squirt out of the other entry ports.
Furthermore/ the reservoir should have a configuration that prevents -the trapping of air pockets during use.
I,ikewise, it is desirable to be able to provide calibration of the amount of blood in the reservoir, down to volumes .~
as low as 25 or 50 cc The above and other advantages are provided in the cardiotomy reservoir of this invention, for improved pro~
cessing of blood with reduced hemolysis.
Further, in accordance with this invention, the above described type of cardiotomy reservoir m~y be improved by the use of a double stage defoaming structure.
The defoaming sponge within the tubular member may be surrounded by a fine weave filter netting, which confines large gas bubbles to the region containing the first defoaming sponge material. Small bubbles, however, may pass through the filter screen.
In the structure of this invention, those small bubbles which do pass through the filter screen to the area which is outside of the tubular member encounter a second defoaming sponge, where they also are broken down. Unlike the situation in the ~irst defoaming means, the second stage can dissipate the fine bubbles without interference from the large bubbles, which can tend to create small bubbles and inhibit their dissipation.
Also, the structure of this invention may be adapted so that small bubbles which are formed or otherwise reside within the reservoir outside of the tubular member and fine weave filter netting may easily enter into contact with the second defoaming means for further bubble removal.
In accordance with this invention a blood reservoir is provided which comprises a rigid casing and a perforated tubular member positioned within the casing and extending be-tween the ends thereof. Inlet aperture means are positioned at the upper end of the reservoir in communication with the bore of the -tubular member, to provide fluid communication from the exterior to the bore~
, Flow aperture means positioned at the lower end - of -the tubular member provide fluid communication between the bore and the casing interior. The bore preferably con-tains a first blood defoaming means such as conventional, silicone-coated sponge or metal turnings as has been previously used in bubble-type oxygenators. Also, the tubular member carries blood clot filter means, typically on its exterior, to filter flow through the perforations of the tubular member and the ~low aperture means.
The inlet aperture means defines a plurality of tubular apertures having open ends which are outwardly directed normally of the longitudinal axis of the tubular member. These apertures terminate inwardly in open-bottom, - downwardly curved end wall means, to direct fluid flow inwardly through the apertures and then downwardly by means of a gentle, curved flow into the defoaming means.
Outlet aperture means are positioned adjacent the bottom oE the casing.
Preferably, side wa:Lls project downwardly from the downwardly curved end wall means, to prevent the interconnect-ing flow of blood or other fluid from one of the tubular aper-tures to another, to prevent the spurting of blood out of an open inlet aperture.
Also, it is preferred for the tubular apertures to be each positioned radially about the axis of the tubular member.
Typically, the tubular apertures are all positioned in no more than an arc of 120.
At the bottom of the casing, it is preferred for the reservoir to define an upstanding central hump surrounded by an annular trough. The plane of the bottom of the annular trough preferably defines an acute angle to the axis of the tubular member, preferably 45 to 70 with the outlet aperture commu-nicating through the lowest portion of the trough This causes - ' .
the liquid level a-t low volumes to change substantially with small changes in liquid volume. Thus, small amounts of blood in the reservoir can be accurately measured down to 25 or 50 cc A perforated plate member may be carried on the hump, with the plate member carrying the lower end of the tubular member.
Second blood defoaming means may be positioned about the exterior of the tubular member to dissipate fine bubbles without interference from larger bubbles previously removed by the first blood defoaming means.
Preferably the second blood defoaming means are enclosed in a tubular, coarse-weave cover, capable of allowing small bubbles outside of the cover to pass therethrough into contact with the second blood defoaming means. Thus bubbles which are generated or otherwise reside exterior to the tubular rnember and fine weave filter netting can be dissipated with the assistance of the second blood defoaming means.
The first and second blood defoaming means may be separated by the blood filter means, with the filter member being of tubular shape and fine-weave construction. This permits the filter, which is made of generally hydrophilic material, to retain larger bubbles to prevent their passage from the inside to the outside of the filter means. Typically, the tubular, fine-weave filter member may have a pore size of, for example, 1~0 to 130 microns, and may be made of a nylon material.
Because of the second stage blood defoaming means present in accordance with this invention, a significant im-provement in the performance of the cardiotomy reservoir of this invention is provided over those of the prior art~
The cardiotomy reservoir of this invention operates without spilling blood out of the various upper apertures, as has been a possibility in certain prior embodiments, and also has improved foam-removing capacity because of the position of the defoaming material within ~he bore of the tubular member with respect to the inlet. The de-foaming material also deflects the downward flow of the blood so that the cells do not impact with great velocity on any surface after a substantial fall, but instead they fall gently in a circuitous path through the bulk of the defoaming sponge and then out of the bottom or sides of the tubular member, through the filter means.
Referring to the drawings, Figure 1 is a top plan view of a cardiotomy reservoir of this invention.
Figure 2 is an elevational view of the same reservoir.
Fiyure 3 is a sectional view taken along the line 4-4 of Figure 1.
lS Figure 4 is a plan view of the isolated perforated plate member which carries the lower end of the tubular member.
Figure 5 is a vertical sectional view of a different embodiment of a cardiotomy reservoir of this invention, utilizing a pair of blood defoaming members.
Referring to the drawings, cardiotomy reservoir 1~ comprises a rigid housing 12, which may be made from a pair of shells 14, 16, sealed together about flanges 18 by radio frequency sealing, solvent sealing, or the like.
Casing 12 may be made of transparent acrylic plastic or similar material.
As shown by Figure 3, casing 12 encloses a per-forated tubular member 20, which may be made out of poly-ethylene, and typically carries numerous perforations 22 so that the walls of the tubular member can pass fluids. The .
upper end of tubular member 20 is positioned within an annular gasket 24 which may be made out of silicone rubher, and which fits about flange 26 positioned at the end of shell 14 about aperture 15 in a sealing manner.
The lower end of tubular member 20 rests in an annular ledge 28 of a plate 30, which defines perforations or slots 32 to permit the flow of blood out of the bottom of tubular member 20. Also, this eliminates the possibility of forming an air pocket at the bottom of tube 20 when the blood level rises in reservoir 10. Plate 30 is retained by a sili-cone rubber end plug 34, defining an aperture which surrounds protrusion 36. Protrusion 36 is part o~ inwardl~ upstanding hump 38, which is defined at the bottom end of shell 16.
Tu~ular member 20 carries, preferably about its exterior, a tubular nylon filter screen 35, which may have a mesh size of about 120 microns for filtration of the blood and the retention of debris. Optional outer tubular sock filter 37 may be a knitted nylon cover layer.
Filter screen 35 and filter 37 are folded at their upper ends about the upper end of tubular member 20, inside of slot 39 of the silicone rubber gasket 24, for Erictional retention of the ends of the tubular filters 35, 37. At the lower end, filters 35, 37 pass under slots 32, and then fit through the central aperture of plate 30, between the plate and plug 34, for frictional retention.
Annular trough 40 is defined about hump 38 in shell 16, and is angularly positioned to define an acute angle 42 (Figure 2) to -the axis 44 of tubular member 20.
; Outlet aperture 46 communicates through the lowest portion of trough ~0, so that all blood will easil~ drain 33~
from the reservoir.
As an added advantage of the above described arrangement of the lower end of reservoir 10, -the reduced volume of the extreme low end 48 of the reservoir provides improved calibration of low blood volumes in the reservoir.
Accordingly, calibration strip 50, having volume indication markings, may be provided along a face of the reservoir so that, at a minimum blood level, blood volumes as small as 25 or 50 cc. can be measured.
At the upper end oE reservoir 10 several inlet members are defined. Aperture 52 defines a sleeve member 54 passing through casing 12 in which is fitted luer-lock connector 56 for the addition of supplemental medication when desired. The connector 56 may be of conventional ; 15 design.
Vent tube 58 is provided with a closable rubber vent cap 60. If desired, a porous hydrophobic material may be placed in vent tube 58, to filter out any contamination while permitting the flow of gas into and out of the reservoir.
Port tube 59 may be used as a connection to a vacuum pump, if desired, being adapted with conventional yripping rinys to receive and hold a flexible vacuum line.
Also, port tube 59 may be used to prime the reservoir.
Positioned within sleeve 26 is a molded inlet assembly 62. Apertures are defined in inlet assembly 62 in which are positioned a pair of luer-lock connectors 64 similar in desiyn, if desired, to connector 56. The connec-~- tors are heat or solvent sealed as desired to the inlet assembly 62. These may be used for adding blood, medica-.~ tiOllS, or the like.
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' Also, inlet assembly 62 defines the three inlet aperture tubes 66 which extend horizontally, i.e., normally to the longitudinal axis of perforated tubular member 20.
Tubular apertures 66 terminate inwardly in downwardly curved end walls 68, having open bottoms, so that the blood or other fluid which is directed inwardly through apertures 66 is gently directed downwardly by the curvature of walls 68, passiny through sleeve 26 into the defoaming means 23.
Side walls 70 project downwardly from -the curved end walls 68 to channel the blood Elow, so that interconnec-ting flow from one tubular aperture 66 to another is substan-tially prevented. Also, the gentle, curved downward direc-tion of blood greatly reduces spattering through luer aper-tures 64 when they are open.
Tubular apertures 66 can be seen from Figure 1 to be positioned radially about the axis 44 of tubular member 20. This provides adequate space for manual access to the tube 66, while at the same time directing all of the flow through them centrally into the reservoir. It can be seen that the e~tent of the tubes 66 defines an arc of essentially 900 .
The cardiotomy reservoir of this invention thus provides smooth, non-hemolytic inlet of blood without spat-tering or f low out of other upper apertures. The blood flows downwardly through a relatively large amount of de-; foaming sponge 23 for gentle and thorough removal o~ foam and then passes outwardly through slots 32 or apertures 22, depending upon the amount of blood in the reservoir, the flow rate and the llke. Complete emptying of the reservoir is provided by the configuration of the bottom of the structure.
_ g _ Also, tubular member 20 provides internal rein-forcement of the casing 12 in the case where a reduced pres-sure is used inside of the reservoir.
Referring to Figure 5, the cardiotomy reservoir which is shown herein is similar in its design to the previous embodiment, except as otherwise indicated herein.
Cardiotomy reservoir 110 comprises a rigid housing 112 which may be made from a pair of shells 114, 116, sealed together about flanges 118 by radio-frequency sealing, 1~ solvent sealing, or the like~ Casing 112 may be made of a transparent acrylic plastic or similar material.
Casing 112 encloses a perforated tubular member 120, which may be made out of polyethylene, or other similar plas-tic, and typically carries numerous perforations 122 so that the walls of the tubular member can pass fluid. The upper end of tubular member 120 is positioned within an annular gasket 124 which may be made out of silicone rubber, and which fits about flange 126 positioned at the end of shell - 114 about aperture 115 in a sealing manner.
The lower end of tubular member 120 rests in an annular ledge 128 of a plate 130. Plate 130 is retained by a silicone rubber end plug 134, defining an aperture which surrounds protrusion 136. Protrusion 136 is part of inwardly upstanding hump 138, which is defined at the bottom end of shell 116.
Tubular member 120 carries, preferably about its exterior, a tubu]ar nylon filter screen 138, which may ; have a mesh size of about 135 microns for filtration of the blood and the retention of debris.
A fine weave filter 135 is folded at its upper end :
about the upper end of tubular member 120, inside of slot 139 " ' ,, -- 1 0 ,~
:
of silicone rubber gasket 124, for frictional retention of the ends of tubular filter 135. ~t the lower end, filter 135 passes under plate 130, and then fits through the central aperture of plate 130, between the plate and plug 134, for frictional retention. Filter 135 may have a pore size on the order of 120 to 130 microns, specifically 125 microns.
Annular trough 140 is defined about hump 138 in shell 116, and is angularly positioned to define an acute angle to the longitudinal axis of tubular member 120.
Outlet aperture 146 communicates through the lowest portion of trough 140, so that all blood will easily drain from the reservoir.
If desired, a calibration strip having volume indi-cation markings may be provided on an outer wall of the - 15 reservoir so that, at a minimum blood level, blood volumes as small as 25 or 50 cc. can be measured.
A mass of conventional blood defoaming sponge 123 is positioned within tube 120.
At the upper end of reservoir 10, inlet members are defined, being oE a conEiguration similar to that of the pre-viously described in the previous embodiment.
An aperture is defined by a sleeve member 154 which passes through casing 112 and in which is fitted luer lock connector 156 for the addition of supplemental medication when desired. The connector 56 may be of conventional design.
Vent tube 158 may be provided with a closable rubber vent cap 160. If desired, a porous, hydrophobic material may be placed in vent tube 158, to filter out any contamina-tion, while permitting the flow of gas into and out of the ; reservoir.
3~
A port tube ~not shown) may also be present to be used as a connection to a vacuum pump, if desired.
Positioned within sleeve 126 is a molded inlet assembly 162, which is also of a design similar to that disclosed at page 9 with reference to Figure 3 of the drawings, including three inlet aperture tubes 166.
In accordance with this inventionl the conventional blood defoaming sponge 123 positioned in the interior of tube 120 may be supplemented with a second blood defoaming means, which constitutes a generally tubular mass of conventional blood defoaming sponge material 168 such as silicone coated metal turnings, positioned about the exterior of tube 120.
Second blood defoaming means 168 is retained in its position by means of a tubular coarse-weave fabric cover 170, which is retained at its ends in a manner similar to the retention of tubular filter 135. The weave of tubular cover 170 may be coarse enough te.g., an aperture size on the order of l/L6 or 1/32 inch) to allow any small bubbles outside of the cover 170 to pass back into the area occupied by second defoaming means 168 to be dissipated. Cover 170 may, for example, be a knit material. This provides an advantage to the device of this invention, since the presence of fine weave filter member 135 ;~ has hitherto generally prevented the passage of such bubbles back into the interior of tube 120 for dissipation.
Accordingly, blood enters the device through an in-let port 166, spilling through the first defoaming means 123 and then passing out of tube 120 through fine weave filter member 135. Any large bubbles are prevented from passage by the presence of fine weave filter 135. Any small bubbles which remain pass through the second ~.!
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4~3~
defoaming means 168 in the absence of larger bubbles.
Blood and bubbles external to the outer coarse-weave retainer member 170 are free to pass relatively unhin-dered back to the second defoaming sponge 168, which tends to increase the removal rate of such fine bubbles.
Blood is then withdrawn through outlet 46, with the sloping trough 140 serving to facilitate the complete drainage thereof.
The above has been offered for illustrative purposes only, and is not to be viewed as limiting the invention of this application, which is as defined in the claims below.
Inventors: Thomas W. Crockett Patrick N. Huehls sarry G. Slotnick John M. Munsch Ludwig Wolf, Jr.
Cardiotomy reservoirs are currently used in major surgical procedures, such as open heart surgery, for receiving blood from a cardiotomy sucker and other sources, for defoaming the blood, filtering out debris ~ and returning it to the patient.
Numerous designs of cardlotomy reservoirs are commercially offered, for example, a cardiotomy reservoir similar to that disclosed in U.S. Patent No. 3,993,461, and its predecessor in design being as disclosed in U.S. Patent ~; No. 3,891,416. In both of these cardiotomy reservoirs, a hollow casing is provided in which a tubular member is . positioned within the casing and extends between the ends thereof. Blood enters the boktom of the tubular member, rising upwardly until it passes out of an aperture to the exterior of the tubular member.
:; :
:' ''. ~';
.; , .
.. . .
;3~ii The Shiley cardiotomy reservoir which is currently commercially available also comprises a casing having a tu-bular member extending through the interior from end to end, with filter and defoaming material carried outside of the tubular member. Blood enters the top of the reservoir ~- through inlet ports at a side thereof, then normally falling downwardly and then passing through the defoaming material within the casing from where it is returned to the patient.
The space within the tubular member is not used.
The lower end of the tubular member of the Shiley reservoir is retained by a bottom hump, in the lower end of the casing. The periphery of the lower end is sloped slightly to allow blood to flow to the lowest point, where the outlet is positioned.
One problem with this reservoir and its side entry blood inlet ports is that some blood coming in one port can swing around the circumference of the tubular casing and flow out one of the other ports, rather than falling downwardly into the defoaming material.
In introducing blood to a cardiotomy reservoir, it is also highly desirable to avoid the harsh impingement of blood upon a wall surface or the like, since that can result in an increase in the hemolysis level of the blood.
On the other hand~ blood which is introduced into one of the entry ports of a cardiotomy reservoir should not have the tendency to squirt out of the other entry ports.
Furthermore/ the reservoir should have a configuration that prevents -the trapping of air pockets during use.
I,ikewise, it is desirable to be able to provide calibration of the amount of blood in the reservoir, down to volumes .~
as low as 25 or 50 cc The above and other advantages are provided in the cardiotomy reservoir of this invention, for improved pro~
cessing of blood with reduced hemolysis.
Further, in accordance with this invention, the above described type of cardiotomy reservoir m~y be improved by the use of a double stage defoaming structure.
The defoaming sponge within the tubular member may be surrounded by a fine weave filter netting, which confines large gas bubbles to the region containing the first defoaming sponge material. Small bubbles, however, may pass through the filter screen.
In the structure of this invention, those small bubbles which do pass through the filter screen to the area which is outside of the tubular member encounter a second defoaming sponge, where they also are broken down. Unlike the situation in the ~irst defoaming means, the second stage can dissipate the fine bubbles without interference from the large bubbles, which can tend to create small bubbles and inhibit their dissipation.
Also, the structure of this invention may be adapted so that small bubbles which are formed or otherwise reside within the reservoir outside of the tubular member and fine weave filter netting may easily enter into contact with the second defoaming means for further bubble removal.
In accordance with this invention a blood reservoir is provided which comprises a rigid casing and a perforated tubular member positioned within the casing and extending be-tween the ends thereof. Inlet aperture means are positioned at the upper end of the reservoir in communication with the bore of the -tubular member, to provide fluid communication from the exterior to the bore~
, Flow aperture means positioned at the lower end - of -the tubular member provide fluid communication between the bore and the casing interior. The bore preferably con-tains a first blood defoaming means such as conventional, silicone-coated sponge or metal turnings as has been previously used in bubble-type oxygenators. Also, the tubular member carries blood clot filter means, typically on its exterior, to filter flow through the perforations of the tubular member and the ~low aperture means.
The inlet aperture means defines a plurality of tubular apertures having open ends which are outwardly directed normally of the longitudinal axis of the tubular member. These apertures terminate inwardly in open-bottom, - downwardly curved end wall means, to direct fluid flow inwardly through the apertures and then downwardly by means of a gentle, curved flow into the defoaming means.
Outlet aperture means are positioned adjacent the bottom oE the casing.
Preferably, side wa:Lls project downwardly from the downwardly curved end wall means, to prevent the interconnect-ing flow of blood or other fluid from one of the tubular aper-tures to another, to prevent the spurting of blood out of an open inlet aperture.
Also, it is preferred for the tubular apertures to be each positioned radially about the axis of the tubular member.
Typically, the tubular apertures are all positioned in no more than an arc of 120.
At the bottom of the casing, it is preferred for the reservoir to define an upstanding central hump surrounded by an annular trough. The plane of the bottom of the annular trough preferably defines an acute angle to the axis of the tubular member, preferably 45 to 70 with the outlet aperture commu-nicating through the lowest portion of the trough This causes - ' .
the liquid level a-t low volumes to change substantially with small changes in liquid volume. Thus, small amounts of blood in the reservoir can be accurately measured down to 25 or 50 cc A perforated plate member may be carried on the hump, with the plate member carrying the lower end of the tubular member.
Second blood defoaming means may be positioned about the exterior of the tubular member to dissipate fine bubbles without interference from larger bubbles previously removed by the first blood defoaming means.
Preferably the second blood defoaming means are enclosed in a tubular, coarse-weave cover, capable of allowing small bubbles outside of the cover to pass therethrough into contact with the second blood defoaming means. Thus bubbles which are generated or otherwise reside exterior to the tubular rnember and fine weave filter netting can be dissipated with the assistance of the second blood defoaming means.
The first and second blood defoaming means may be separated by the blood filter means, with the filter member being of tubular shape and fine-weave construction. This permits the filter, which is made of generally hydrophilic material, to retain larger bubbles to prevent their passage from the inside to the outside of the filter means. Typically, the tubular, fine-weave filter member may have a pore size of, for example, 1~0 to 130 microns, and may be made of a nylon material.
Because of the second stage blood defoaming means present in accordance with this invention, a significant im-provement in the performance of the cardiotomy reservoir of this invention is provided over those of the prior art~
The cardiotomy reservoir of this invention operates without spilling blood out of the various upper apertures, as has been a possibility in certain prior embodiments, and also has improved foam-removing capacity because of the position of the defoaming material within ~he bore of the tubular member with respect to the inlet. The de-foaming material also deflects the downward flow of the blood so that the cells do not impact with great velocity on any surface after a substantial fall, but instead they fall gently in a circuitous path through the bulk of the defoaming sponge and then out of the bottom or sides of the tubular member, through the filter means.
Referring to the drawings, Figure 1 is a top plan view of a cardiotomy reservoir of this invention.
Figure 2 is an elevational view of the same reservoir.
Fiyure 3 is a sectional view taken along the line 4-4 of Figure 1.
lS Figure 4 is a plan view of the isolated perforated plate member which carries the lower end of the tubular member.
Figure 5 is a vertical sectional view of a different embodiment of a cardiotomy reservoir of this invention, utilizing a pair of blood defoaming members.
Referring to the drawings, cardiotomy reservoir 1~ comprises a rigid housing 12, which may be made from a pair of shells 14, 16, sealed together about flanges 18 by radio frequency sealing, solvent sealing, or the like.
Casing 12 may be made of transparent acrylic plastic or similar material.
As shown by Figure 3, casing 12 encloses a per-forated tubular member 20, which may be made out of poly-ethylene, and typically carries numerous perforations 22 so that the walls of the tubular member can pass fluids. The .
upper end of tubular member 20 is positioned within an annular gasket 24 which may be made out of silicone rubher, and which fits about flange 26 positioned at the end of shell 14 about aperture 15 in a sealing manner.
The lower end of tubular member 20 rests in an annular ledge 28 of a plate 30, which defines perforations or slots 32 to permit the flow of blood out of the bottom of tubular member 20. Also, this eliminates the possibility of forming an air pocket at the bottom of tube 20 when the blood level rises in reservoir 10. Plate 30 is retained by a sili-cone rubber end plug 34, defining an aperture which surrounds protrusion 36. Protrusion 36 is part o~ inwardl~ upstanding hump 38, which is defined at the bottom end of shell 16.
Tu~ular member 20 carries, preferably about its exterior, a tubular nylon filter screen 35, which may have a mesh size of about 120 microns for filtration of the blood and the retention of debris. Optional outer tubular sock filter 37 may be a knitted nylon cover layer.
Filter screen 35 and filter 37 are folded at their upper ends about the upper end of tubular member 20, inside of slot 39 of the silicone rubber gasket 24, for Erictional retention of the ends of the tubular filters 35, 37. At the lower end, filters 35, 37 pass under slots 32, and then fit through the central aperture of plate 30, between the plate and plug 34, for frictional retention.
Annular trough 40 is defined about hump 38 in shell 16, and is angularly positioned to define an acute angle 42 (Figure 2) to -the axis 44 of tubular member 20.
; Outlet aperture 46 communicates through the lowest portion of trough ~0, so that all blood will easil~ drain 33~
from the reservoir.
As an added advantage of the above described arrangement of the lower end of reservoir 10, -the reduced volume of the extreme low end 48 of the reservoir provides improved calibration of low blood volumes in the reservoir.
Accordingly, calibration strip 50, having volume indication markings, may be provided along a face of the reservoir so that, at a minimum blood level, blood volumes as small as 25 or 50 cc. can be measured.
At the upper end oE reservoir 10 several inlet members are defined. Aperture 52 defines a sleeve member 54 passing through casing 12 in which is fitted luer-lock connector 56 for the addition of supplemental medication when desired. The connector 56 may be of conventional ; 15 design.
Vent tube 58 is provided with a closable rubber vent cap 60. If desired, a porous hydrophobic material may be placed in vent tube 58, to filter out any contamination while permitting the flow of gas into and out of the reservoir.
Port tube 59 may be used as a connection to a vacuum pump, if desired, being adapted with conventional yripping rinys to receive and hold a flexible vacuum line.
Also, port tube 59 may be used to prime the reservoir.
Positioned within sleeve 26 is a molded inlet assembly 62. Apertures are defined in inlet assembly 62 in which are positioned a pair of luer-lock connectors 64 similar in desiyn, if desired, to connector 56. The connec-~- tors are heat or solvent sealed as desired to the inlet assembly 62. These may be used for adding blood, medica-.~ tiOllS, or the like.
.' .
' Also, inlet assembly 62 defines the three inlet aperture tubes 66 which extend horizontally, i.e., normally to the longitudinal axis of perforated tubular member 20.
Tubular apertures 66 terminate inwardly in downwardly curved end walls 68, having open bottoms, so that the blood or other fluid which is directed inwardly through apertures 66 is gently directed downwardly by the curvature of walls 68, passiny through sleeve 26 into the defoaming means 23.
Side walls 70 project downwardly from -the curved end walls 68 to channel the blood Elow, so that interconnec-ting flow from one tubular aperture 66 to another is substan-tially prevented. Also, the gentle, curved downward direc-tion of blood greatly reduces spattering through luer aper-tures 64 when they are open.
Tubular apertures 66 can be seen from Figure 1 to be positioned radially about the axis 44 of tubular member 20. This provides adequate space for manual access to the tube 66, while at the same time directing all of the flow through them centrally into the reservoir. It can be seen that the e~tent of the tubes 66 defines an arc of essentially 900 .
The cardiotomy reservoir of this invention thus provides smooth, non-hemolytic inlet of blood without spat-tering or f low out of other upper apertures. The blood flows downwardly through a relatively large amount of de-; foaming sponge 23 for gentle and thorough removal o~ foam and then passes outwardly through slots 32 or apertures 22, depending upon the amount of blood in the reservoir, the flow rate and the llke. Complete emptying of the reservoir is provided by the configuration of the bottom of the structure.
_ g _ Also, tubular member 20 provides internal rein-forcement of the casing 12 in the case where a reduced pres-sure is used inside of the reservoir.
Referring to Figure 5, the cardiotomy reservoir which is shown herein is similar in its design to the previous embodiment, except as otherwise indicated herein.
Cardiotomy reservoir 110 comprises a rigid housing 112 which may be made from a pair of shells 114, 116, sealed together about flanges 118 by radio-frequency sealing, 1~ solvent sealing, or the like~ Casing 112 may be made of a transparent acrylic plastic or similar material.
Casing 112 encloses a perforated tubular member 120, which may be made out of polyethylene, or other similar plas-tic, and typically carries numerous perforations 122 so that the walls of the tubular member can pass fluid. The upper end of tubular member 120 is positioned within an annular gasket 124 which may be made out of silicone rubber, and which fits about flange 126 positioned at the end of shell - 114 about aperture 115 in a sealing manner.
The lower end of tubular member 120 rests in an annular ledge 128 of a plate 130. Plate 130 is retained by a silicone rubber end plug 134, defining an aperture which surrounds protrusion 136. Protrusion 136 is part of inwardly upstanding hump 138, which is defined at the bottom end of shell 116.
Tubular member 120 carries, preferably about its exterior, a tubu]ar nylon filter screen 138, which may ; have a mesh size of about 135 microns for filtration of the blood and the retention of debris.
A fine weave filter 135 is folded at its upper end :
about the upper end of tubular member 120, inside of slot 139 " ' ,, -- 1 0 ,~
:
of silicone rubber gasket 124, for frictional retention of the ends of tubular filter 135. ~t the lower end, filter 135 passes under plate 130, and then fits through the central aperture of plate 130, between the plate and plug 134, for frictional retention. Filter 135 may have a pore size on the order of 120 to 130 microns, specifically 125 microns.
Annular trough 140 is defined about hump 138 in shell 116, and is angularly positioned to define an acute angle to the longitudinal axis of tubular member 120.
Outlet aperture 146 communicates through the lowest portion of trough 140, so that all blood will easily drain from the reservoir.
If desired, a calibration strip having volume indi-cation markings may be provided on an outer wall of the - 15 reservoir so that, at a minimum blood level, blood volumes as small as 25 or 50 cc. can be measured.
A mass of conventional blood defoaming sponge 123 is positioned within tube 120.
At the upper end of reservoir 10, inlet members are defined, being oE a conEiguration similar to that of the pre-viously described in the previous embodiment.
An aperture is defined by a sleeve member 154 which passes through casing 112 and in which is fitted luer lock connector 156 for the addition of supplemental medication when desired. The connector 56 may be of conventional design.
Vent tube 158 may be provided with a closable rubber vent cap 160. If desired, a porous, hydrophobic material may be placed in vent tube 158, to filter out any contamina-tion, while permitting the flow of gas into and out of the ; reservoir.
3~
A port tube ~not shown) may also be present to be used as a connection to a vacuum pump, if desired.
Positioned within sleeve 126 is a molded inlet assembly 162, which is also of a design similar to that disclosed at page 9 with reference to Figure 3 of the drawings, including three inlet aperture tubes 166.
In accordance with this inventionl the conventional blood defoaming sponge 123 positioned in the interior of tube 120 may be supplemented with a second blood defoaming means, which constitutes a generally tubular mass of conventional blood defoaming sponge material 168 such as silicone coated metal turnings, positioned about the exterior of tube 120.
Second blood defoaming means 168 is retained in its position by means of a tubular coarse-weave fabric cover 170, which is retained at its ends in a manner similar to the retention of tubular filter 135. The weave of tubular cover 170 may be coarse enough te.g., an aperture size on the order of l/L6 or 1/32 inch) to allow any small bubbles outside of the cover 170 to pass back into the area occupied by second defoaming means 168 to be dissipated. Cover 170 may, for example, be a knit material. This provides an advantage to the device of this invention, since the presence of fine weave filter member 135 ;~ has hitherto generally prevented the passage of such bubbles back into the interior of tube 120 for dissipation.
Accordingly, blood enters the device through an in-let port 166, spilling through the first defoaming means 123 and then passing out of tube 120 through fine weave filter member 135. Any large bubbles are prevented from passage by the presence of fine weave filter 135. Any small bubbles which remain pass through the second ~.!
' ' ''--I
~ .
4~3~
defoaming means 168 in the absence of larger bubbles.
Blood and bubbles external to the outer coarse-weave retainer member 170 are free to pass relatively unhin-dered back to the second defoaming sponge 168, which tends to increase the removal rate of such fine bubbles.
Blood is then withdrawn through outlet 46, with the sloping trough 140 serving to facilitate the complete drainage thereof.
The above has been offered for illustrative purposes only, and is not to be viewed as limiting the invention of this application, which is as defined in the claims below.
Claims (10)
PROPERTY OR PRIVILEGE IS CLAIMED ARE DEFINED AS FOLLOWS:
1. A blood reservoir which comprises: a rigid casing, a perforated tubular member positioned within said casing and extending between the ends thereof; inlet aperture means posi-tioned at the upper end of said reservoir in communication with the bore of said tubular member to provide fluid communication from the exterior to said bore; flow aperture means positioned at the lower end of said tubular member to provide fluid com-munication between said bore and the casing interior, said bore containing blood defoaming means, and said tubular member carrying blood filter means to filter flow through the perfor-ations of the tubular member and the flow aperture means, said inlet aperture means defining a plurality of tubular apertures having open ends which are outwardly directed normally of the longitudinal axis of the tubular member, said apertures inwardly terminating in open-bottom, downwardly curved end wall means to direct fluid flow inwardly through said apertures and then downwardly by means of a gentle, curved flow into said defoaming means, and outlet aperture means positioned adjacent the bottom of said casing in exterior relation to said tubular member.
2. The blood reservoir of claim 1 in which side walls project downwardly from said downwardly curved end wall means to prevent interconnecting flow from one tubular aperture to another.
3. The blood reservoir of claim 1 or 2 in which said tubular apertures are each positioned radially of the axis of said tubular member.
4. The blood reservoir of claim 1 or 2 in which the bottom of said casing defines an upstanding central hump sur-rounded by an annular trough, the plane of the bottom of said annular trough defining an acute angle to the axis of said tubular member, said outlet aperture communicating through the lowest portion of said trough, and a perforated plate member carried on said hump, said plate member carrying the lower end of said tubular member.
5. The blood reservoir of claim 1 or 2 in which said radially positioned tubular apertures are all positioned in no more than an arc of 120°.
6. The blood reservoir of claim 1 in which second blood defoaming means are carried by said tubular member, one of said first and second blood defoaming means positioned inside of said tubular member and the other of said blood defoaming means positioned about the exterior of said tubular member to dis-sipate fine bubles without interference from larger bubbles previously removed by the blood defoaming means within said tubular member.
7. The blood reservoir of claim 6 in which said second blood defoaming means is positioned on the exterior of said tubular member and is enclosed in a tubular, coarse-weave cover capable of allowing small bubbles outside of said cover to pass therethrough into contact with the second blood defoaming means.
8. The blood reservoir of claim 6 in which said first and second defoaming means are separated by said blood filter means, said blood filter means being tubular shaped and fine-weave construction.
9. The blood reservoir of claim 8 in which said tubular-fine-weave filter means has a pore size of 120 to 130 microns.
10. The blood reservoir of claims 8 and 9 in which said tubular filter means is made of nylon.
Applications Claiming Priority (4)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| US910,323 | 1978-05-30 | ||
| US05/910,323 US4243531A (en) | 1978-05-30 | 1978-05-30 | Cardiotomy reservoir |
| US959,113 | 1978-11-09 | ||
| US05/959,113 US4208193A (en) | 1978-11-09 | 1978-11-09 | Cardiotomy reservoir having two-stage defoaming means |
Publications (1)
| Publication Number | Publication Date |
|---|---|
| CA1144835A true CA1144835A (en) | 1983-04-19 |
Family
ID=27129550
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CA000327200A Expired CA1144835A (en) | 1978-05-30 | 1979-05-08 | Cardiotomy reservoir |
Country Status (10)
| Country | Link |
|---|---|
| AU (1) | AU4704579A (en) |
| BR (1) | BR7903328A (en) |
| CA (1) | CA1144835A (en) |
| CH (1) | CH637545A5 (en) |
| DE (1) | DE2920283A1 (en) |
| ES (1) | ES480947A1 (en) |
| FR (1) | FR2427102B1 (en) |
| GB (1) | GB2022434B (en) |
| NL (1) | NL7904111A (en) |
| SE (1) | SE442087B (en) |
Families Citing this family (8)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US4743371A (en) * | 1983-04-08 | 1988-05-10 | Shiley, Inc. | Blood filter |
| DE3468170D1 (en) * | 1983-04-08 | 1988-02-04 | Shiley Inc | Blood filter |
| GB2247415A (en) * | 1990-08-29 | 1992-03-04 | Shell Int Research | Discharge device for reducing foam |
| GB2263874B (en) * | 1992-02-05 | 1995-05-17 | M G Electric | Filter for printing equipment dampening system |
| DE29718473U1 (en) * | 1997-10-16 | 1997-12-11 | Schneider Lothar | Filter for a device for collecting and roughly cleaning blood from operations |
| US8414515B2 (en) * | 2007-08-27 | 2013-04-09 | Jms Co., Ltd. | Blood reservoir |
| US9545472B2 (en) * | 2012-03-02 | 2017-01-17 | Medtronic, Inc. | Extracorporeal blood circuit reservoir with angled venous inlet luer port |
| DE202013000654U1 (en) | 2013-01-23 | 2013-12-06 | Heimbach Gmbh & Co. Kg | defoamer |
Family Cites Families (8)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| GB1407982A (en) * | 1971-10-15 | 1975-10-01 | Nat Heart Chest Hospitals Boar | Blood filter and defoamer |
| US4054523A (en) * | 1973-07-10 | 1977-10-18 | General Electric Company | Cardiotomy reservoir with integral filter |
| US3891416A (en) * | 1973-07-20 | 1975-06-24 | Baxter Laboratories Inc | Cardiotomy reservoir |
| US3993461A (en) * | 1973-07-20 | 1976-11-23 | Baxter Laboratories, Inc. | Cardiotomy reservoir |
| IT1005695B (en) * | 1974-03-25 | 1976-09-30 | Bellco Spa | BLOOD OXYGENATOR DEVICE WITH HEAT EXCHANGER |
| SE406039B (en) * | 1974-08-29 | 1979-01-22 | Transcodan | IN THE LIQUID CROOM FROM INFUSION AND TRANSFUSION DEVICES CONNECTED FILTER UNIT |
| US4038191A (en) * | 1975-10-14 | 1977-07-26 | Davis Harold R | Manifold for ultra filtration machine |
| US4067696A (en) * | 1976-02-03 | 1978-01-10 | Swiley Laboratories, Inc. | Blood oxygenator |
-
1979
- 1979-05-08 CA CA000327200A patent/CA1144835A/en not_active Expired
- 1979-05-15 FR FR7912331A patent/FR2427102B1/en not_active Expired
- 1979-05-16 AU AU47045/79A patent/AU4704579A/en not_active Abandoned
- 1979-05-18 DE DE19792920283 patent/DE2920283A1/en not_active Ceased
- 1979-05-23 CH CH485979A patent/CH637545A5/en not_active IP Right Cessation
- 1979-05-24 GB GB7918242A patent/GB2022434B/en not_active Expired
- 1979-05-25 ES ES480947A patent/ES480947A1/en not_active Expired
- 1979-05-25 NL NL7904111A patent/NL7904111A/en not_active Application Discontinuation
- 1979-05-28 BR BR7903328A patent/BR7903328A/en unknown
- 1979-05-29 SE SE7904683A patent/SE442087B/en not_active IP Right Cessation
Also Published As
| Publication number | Publication date |
|---|---|
| CH637545A5 (en) | 1983-08-15 |
| SE7904683L (en) | 1979-12-01 |
| GB2022434B (en) | 1982-09-02 |
| ES480947A1 (en) | 1980-02-01 |
| AU4704579A (en) | 1979-12-06 |
| FR2427102B1 (en) | 1986-03-14 |
| BR7903328A (en) | 1979-12-11 |
| NL7904111A (en) | 1979-12-04 |
| DE2920283A1 (en) | 1979-12-06 |
| GB2022434A (en) | 1979-12-19 |
| FR2427102A1 (en) | 1979-12-28 |
| SE442087B (en) | 1985-12-02 |
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Legal Events
| Date | Code | Title | Description |
|---|---|---|---|
| MKEX | Expiry |