JP2017225534A - Blood storage tank - Google Patents

Abstract

PROBLEM TO BE SOLVED: To easily and speedily complete priming with a small flow rate.SOLUTION: A blood storage tank 1 comprises: a venous blood inflow port 50; and a blood storage part 12 capable of temporarily reserving blood having flowed therein from the venous blood inflow port 50. The venous blood inflow port 50 comprises a bent part 53 obtained by bending the channel of the blood. The bending angle θ of the channel at the bent part 53 is 90 degree or less.SELECTED DRAWING: Figure 3

Description

  The present invention relates to a blood reservoir for temporarily storing blood during extracorporeal circulation in an extracorporeal blood circulation circuit used when performing cardiac surgery or the like. In particular, the present invention relates to a blood reservoir equipped with a venous blood flow inlet port through which venous blood flows.

  When performing cardiac surgery or the like, an extracorporeal blood circulation circuit including a blood pump or an artificial lung for substituting the functions of a patient's heart and lungs is used. The extracorporeal blood circulation circuit temporarily stores venous blood removed from the patient's veins to adjust the blood volume of the circulation circuit (sometimes called a “venous blood reservoir”), A blood reservoir (sometimes called "intracardiac blood reservoir") is provided for aspirating, collecting, and temporarily storing blood that overflows the operative field (sometimes called "intracardiac blood") . Since intracardiac blood contains more foreign bodies and bubbles such as meat pieces, fat, and blood clots than venous blood, the intracardiac blood reservoir is defoamed with a filter and bubbles for removing foreign bodies. The cardiotomy part which consists of a defoaming material for carrying out is provided. It is also widely performed to store venous blood and intracardiac blood in a common blood reservoir (sometimes referred to as “intracardiac blood reservoir integrated venous blood reservoir”; see Patent Document 1).

  Prior to circulating blood through the extracorporeal blood circulation circuit, a liquid (for example, physiological saline, hereinafter referred to as “priming solution”) is introduced into the blood flow path constituting the circuit, and the air existing in the flow path A work called “priming” is performed to discharge the water to the outside world. This is because if blood circulation is started in the presence of air in the extracorporeal blood circulation circuit, air flows into the blood vessels of the patient, and serious health damage may occur.

  In priming for a blood reservoir, a priming liquid is used to flow through a venous blood flow inlet port (sometimes called a “blood removal port”) provided on the upper surface of the blood reservoir to allow venous blood to flow into the blood reservoir. It is necessary to satisfy.

JP 2014-183947 A

  A venous blood flow inlet port provided in a conventional blood reservoir includes a first portion to which a tube of a blood removal line is connected, and a second portion extending upward from the upper surface of the blood reservoir. The first part and the second part are connected by a bent part so that the flow path bends at 105 to 120 degrees. When the priming liquid flows from the tube of the blood removal line to the flow path of the venous blood flow port, there is a problem that it is difficult to discharge the bent portion where the flow direction of the priming liquid changes or the air in the vicinity thereof with the priming liquid. is there.

  Conventionally, in order to discharge the air in the venous blood inflow port, (1) the flow rate of the priming solution is increased, or (2) the tube connected to the venous blood inflow port is intermittently crushed with a finger. Therefore, an operation such as intermittently flowing the priming solution into the venous blood flow inlet port is required.

  An object of the present invention is to provide a blood reservoir equipped with a venous blood flow inlet port that can easily complete priming with a small flow rate in a short time.

  The blood reservoir layer of the present invention includes a venous blood flow inlet port and a blood reservoir that can temporarily store blood flowing from the venous blood inlet port. The venous blood flow port includes a bent portion in which a flow path through which blood flows is bent. The bending angle of the flow path at the bent portion is 90 degrees or less.

  According to the present invention, since the bend angle of the flow path at the bent portion is 90 degrees or less, the flow direction of the priming liquid flowing through the venous blood flow inlet port changes suddenly at the bent portion during priming. For this reason, vortices and turbulent flow are generated in the priming liquid at the bent portion and in the vicinity thereof, so that the priming liquid is unlikely to stay, and the bubbles flow together with the priming liquid. As a result, the flow path in the venous blood flow inlet port can be filled with the priming liquid easily and in a short time with a small flow rate of the priming liquid.

FIG. 1 is a perspective view of a blood reservoir according to Embodiment 1 of the present invention as viewed from above. FIG. 2 is a cross-sectional view of the blood reservoir according to Embodiment 1 of the present invention. FIG. 3 is an enlarged cross-sectional view of a venous blood flow inlet port and its vicinity in the blood reservoir according to Embodiment 1 of the present invention. FIG. 4 is an enlarged cross-sectional view of a venous blood flow inlet port and its vicinity in a conventional blood reservoir. FIG. 5 is an enlarged cross-sectional view of a venous blood flow inlet port and its vicinity in another blood reservoir according to Embodiment 1 of the present invention. FIG. 6A is an enlarged cross-sectional view of a venous blood flow inlet port and the vicinity thereof in a blood reservoir according to Embodiment 2 of the present invention. FIG. 6B is an enlarged perspective view of the venous blood flow entry port of the blood reservoir according to Embodiment 2 of the present invention and the vicinity thereof, cut along a horizontal plane parallel to the central axis of the first part.

  In one configuration of the blood reservoir layer of the present invention, the bending angle is 60 degrees or more. According to such a configuration, it is possible to suppress a decrease in the manageability of the blood removal line tube connected to the venous blood flow inlet port, and an increase in hemolysis and flow path resistance.

  The venous blood flow inlet port may include a first portion upstream of the bent portion and a second portion downstream of the bent portion. In this case, the second part may extend in the vertical direction, and the first part may be configured to be connected to a blood removal line tube. According to this configuration, the inclination of the first part approaches the inclination in the vicinity of the first part of the tube connected to the first part. This is advantageous in preventing an increase in the flow resistance of the extracorporeal blood circulation circuit due to the kink, since it is possible to suppress the occurrence of kinks due to local bending of the tube in the vicinity of the first part.

  Protrusions projecting into the flow path downstream of the bent portion (that is, the flow path of the second part) are provided on the inner surface of the inner surface defining the flow path or in the vicinity thereof. It may be done. As a result, the bubbles collide with the protrusions and become finer. Therefore, the above configuration is more advantageous for filling the flow path in the venous blood flow inlet port easily and in a short time with a small priming liquid flow rate.

  Below, this invention is demonstrated in detail, showing suitable embodiment. However, it goes without saying that the present invention is not limited to the following embodiments. Each drawing referred to in the following description shows simplified main members constituting an embodiment of the present invention for convenience of description. Therefore, the present invention can include any member not shown in the following drawings. Further, within the scope of the present invention, each member shown in the following drawings can be changed or omitted. In the drawings cited in the respective embodiments, members corresponding to the members shown in the drawings cited in the preceding embodiments are denoted by the same reference numerals as in the drawings of the preceding embodiments. About such a member, the overlapping description is abbreviate | omitted and you should consider the description of previous embodiment suitably.

(Embodiment 1)
FIG. 1 is a perspective view showing a schematic configuration of a blood reservoir 1 according to Embodiment 1 of the present invention, and FIG. 2 is a side sectional view thereof. The blood reservoir 1 is an intracardiac blood reservoir integrated venous blood reservoir that stores venous blood and intracardiac blood. The blood reservoir 1 is used in the orientation shown in FIG. The “upper”, “lower”, and “horizontal direction” used in the following description are defined based on the actual usage state of the blood reservoir 1 shown in FIG.

  As shown in FIG. 1, the blood reservoir 1 includes a housing 10 including a housing main body 11 and a lid body 16 placed on top of the housing main body 11.

  The housing body 11 includes a blood reservoir 12 in which a part off the center protrudes in a wedge shape downward, and a blood outflow port 13 provided at the lower end of the blood reservoir 12 through which blood flows out.

  The lid body 16 is provided with a plurality of blood inflow ports for allowing blood to flow into the blood reservoir 1. The blood inflow ports include a plurality of intracardiac blood inflow ports 21 through which intracardiac blood flows in and venous blood inflow ports (sometimes referred to as “blood removal ports”) 50 through which venous blood flows. Further, the lid 16 has a plurality of chemical solution injection ports 23 and 24 for mixing a chemical solution or the like into the blood, an urgent mixture of a large amount of chemical solution into the blood, or an intracardiac portion of the cardiotomy section 30 (see FIG. 2). Service port 25 for allowing blood that has passed through an alternative cardiotomy section to flow in when blood filter 37 cannot be used due to clogging, and suction assist blood removal port for adjusting the pressure in blood reservoir 1 26, a pressure regulating valve 27 for preventing the pressure in the blood reservoir 1 from becoming an abnormal positive pressure or negative pressure is provided. The venous blood inlet port 50 is inserted with a temperature probe 28 for measuring the temperature of venous blood.

  As shown in FIG. 2, the cardiotomy section 30 is provided at substantially the center of the lower surface of the lid body 16. The intracardiac blood that has passed through the intracardiac blood inflow port 21 flows into the cardiotomy section 30.

  The cardiotomy section 30 includes a casing 31 having a substantially cylindrical shape with a bottom. A hole 32 for allowing blood to flow out is provided on the outer peripheral edge of the circular bottom plate of the housing 31. An antifoam material 35, a frame 36, and an intracardiac blood filter 37 are provided in the housing 31.

  The defoaming material 35 has a defoaming function for breaking bubbles coming into contact with the defoaming material 35, and is not limited. For example, the surface of polyurethane as a base layer is coated with silicone as a defoaming agent. Can be composed of materials. The form of the base layer may be a foam having a continuous cell, woven fabric, knitted fabric, non-woven fabric, or the like. Preferably, a material obtained by coating a soft polyurethane foam with silicone as the defoaming material 35 can be used. In the present embodiment, the defoaming material 35 has a cylindrical shape.

  The intracardiac blood filter 37 has a function of capturing foreign substances and air bubbles in blood when blood (intracardial blood) passes through the intracardiac blood filter 37, and is not limited to, for example, polyester, nylon, A known filter material such as a mesh filter made of a resin material such as polypropylene can be used. An antifoaming agent (for example, silicone) may be coated on the intracardiac blood filter 37 to give a bubble defoaming function. In the present embodiment, the intracardiac blood filter 37 is formed by bending a long sheet-like filter material into a pleated shape in a direction opposite to each other at a constant pitch, and then the longitudinal direction of the filter material so that the overall shape has a substantially cylindrical shape. It is configured by connecting both ends in the direction. The intracardiac blood filter 37 is disposed outside the antifoam material 35.

  The frame 36 is disposed between the antifoam material 35 and the intracardiac blood filter 37 so as to be separated from each other. The frame 36 has a substantially cylindrical shape, and a plurality of openings are provided in the wall.

  A defoaming frame 40 is accommodated in the housing 10. The defoaming frame 40 has a shape that substantially conforms to the inner surface of the housing body 11 at a substantially constant interval. The defoaming frame 40 includes a frame-like portion 41 extending downward so as to be inserted into the blood reservoir 12 of the housing body 11. A plurality of openings are provided in the wall of the defoaming frame 40 (particularly, the frame-like portion 41). The filter screen 45 is fixedly held on the defoaming frame 40 so as to close the plurality of openings. The area | region which attached | subjected many dots in FIG. 2 shows the filtration net | network 45 which plugs up opening. The filtration network 45 has a function as a filter that removes foreign matters and bubbles in the blood when the blood passes through the filtration network 45. For example, a screen filter having a large number of fine openings can be used as the filter network 45. The filter network 45 may be coated with an antifoaming agent (for example, silicone) to give a bubble defoaming function. The cardiotomy section 30 is accommodated in the defoaming frame 40.

  The venous blood flow port 50 is communicated with the first conduit 29a and the second conduit 29b in order. The 1st conduit | pipe 29a is arrange | positioned so that the center of the cardiotomy part 30 may be penetrated to an up-down direction. The second conduit 29 b is inserted into the frame-like portion 41 of the defoaming frame 40, and the opening at the lower end thereof is located below the lowest blood level L of the blood reservoir 1.

  A fixing hole 14 for holding the blood reservoir 1 by inserting the upper end of a support column erected in the operating room is provided on the lower surface of the housing body 11.

  The blood reservoir 1 is used by being incorporated into an extracorporeal blood circulation circuit. A tube of an intracardiac blood suction line is connected to the intracardiac blood flow inlet port 21, and a blood removal line tube of an extracorporeal blood circulation circuit is connected to the venous blood flow inlet port 50. The blood outflow port 13 is connected to a tube of a blood supply line of the extracorporeal blood circulation circuit. The chemical solution injection ports 23 and 24 are connected to a chemical solution injection line tube connected to a predetermined chemical solution container. The drug solution flowing in from the drug solution injection port 23 flows into the blood storage unit 12 without passing through the cardiotomy unit 30, and the drug solution flowing in from the drug solution injection port 24 flows into the blood storage unit 12 after passing through the cardiotomy unit 30. Various lines of tubes are connected to the service port 25. The temperature probe 28 is connected to electrical wiring connected to the temperature measuring device.

  The flow of blood in the blood reservoir 1 will be described.

  In FIG. 2, intracardiac blood sucked from the patient's operative field passes through the intracardiac blood inflow port 21 and flows into the cardiotomy section 30. The air bubbles mixed in the intracardiac blood float on the blood surface, but break the bubbles when they come into contact with the defoaming material 35. The intracardiac blood sequentially passes through the defoaming material 35, the frame 36, and the intracardiac blood filter 37, and further flows through the hole 32 provided in the bottom plate of the housing 31 into the defoaming frame 40. Foreign matters and bubbles such as meat pieces, fat, and blood clots contained in the intracardiac blood are captured by the intracardiac blood filter 37.

  On the other hand, the venous blood removed from the patient's vein passes through the venous blood inlet port 50, the first conduit 29a, and the second conduit 29b in this order, and enters the antifoaming frame 40 from the opening at the lower end of the second conduit 29b. Flow into.

  The intracardiac blood and venous blood are mixed in the defoaming frame 40, pass through the filtration network 45, and flow out of the blood reservoir 1 through the blood outflow port 13.

  In this process, the blood is temporarily stored in the blood reservoir 12 so that the blood level is above the minimum blood level L.

  Prior to blood circulation using the blood reservoir 1, priming is performed on the extracorporeal blood circulation circuit. In the priming for the blood reservoir 1, first, a priming solution is injected into the blood reservoir 1 through the chemical solution injection port 23, and the blood storage unit 12, the blood outflow port 13, and the blood supply line tube are filled with the priming solution. Then, it is necessary to sequentially flow the priming solution with the blood pump to the blood removal line tube, the venous blood flow inlet port 50, the first conduit 29a, and the second conduit 29b, and to fill them with the priming solution.

  FIG. 3 is an enlarged cross-sectional view of the venous blood flow inlet port 50 and the vicinity thereof. The venous blood flow port 50 includes a first portion 51 to which a blood removal line tube (not shown) is connected and a second portion 52 extending upward from the lid body 16. The first part 51 and the second part 52 each include a flow path through which blood flows. The flow path of the first part 51 and the flow path of the second part 52 are communicated to form a flow path of the venous blood flow inlet port 50. The one-dot chain line 51a and the one-dot chain line 52a are the central axes of the flow paths of the first part 51 and the second part 52, respectively. Each flow path of the first part 51 and the second part 52 extends straightly. The channel cross section of the first part 51 and the channel cross section of the second part 52 have a circular shape having substantially the same diameter (the diameter is not limited, but is 10 to 13 mm). In the present embodiment, the first portion 51 extends substantially along the horizontal direction, while the second portion 52 extends substantially along the vertical direction. Accordingly, the flow path in the venous blood flow inlet port 50 is bent at the bent portion 53 between the first portion 51 and the second portion 52. In the present invention, the “bent part 53” refers to the boundary between the first part 51 and the second part 52 and the vicinity thereof. The bending angle (angle formed by the central axis 51a and the central axis 52a) θ of the flow path at the bending portion 53 is 90 degrees.

  In the present embodiment, by reducing the bending angle θ at the bent portion 53 of the venous blood flow inlet port 50, the air in the venous blood flow inlet port 50 can be easily and quickly discharged with the priming liquid during priming. Can do. The present inventors generally consider this reason as follows.

  FIG. 4 is an enlarged cross-sectional view showing the venous blood flow inlet port 950 of the conventional blood reservoir and the vicinity thereof as in FIG. 4, members corresponding to those shown in FIG. 3 are denoted by the same reference numerals. In the conventional venous blood flow inlet port 950, the first portion 51 is inclined with respect to the horizontal direction so that the tip thereof is obliquely upward, and the bending angle θ at the bending portion 53 is about 105 to 120 degrees. It is. A tube (not shown) of a blood removal line is connected to the first part 51. Before priming, the tube and the flow path in the port 950 are filled with air. In priming, a priming solution is caused to flow into the port 950 through the tube. The priming liquid flows in the first portion 51 along its central axis 51a. Next, the priming liquid collides with the bent portion outer region 54 on the inner surface defining the flow path of the port 950 (hereinafter referred to as “flow path inner surface”), and the flow direction thereof is changed. Here, the bent portion outer region 54 is a neighboring region including a position where the extension line of the central axis 51a of the first portion 51 intersects in the inner surface of the flow path, and in the bent portion 53 or in the vicinity of the bent portion 53. Is located in the second part 52. In the vicinity of the bent portion outer region 54, the pressure of the priming liquid is relatively high. On the other hand, in the vicinity of the bent portion inner region 55 on the inner surface of the flow path, the pressure of the priming liquid tends to be relatively low. Here, the bent portion inner region 55 is a region substantially opposite to the bent portion outer region 54 and is located in the bent portion 53 or in the second portion 52 in the vicinity of the bent portion 53. In the above description, “outside” and “inside” mean the far side and the near side when viewed from the center of the arc when the flow direction of the priming solution changes along the arc at the bent portion 53. To do.

  In the conventional venous blood flow inlet port 950, the bending angle θ of the bent portion 53 is an obtuse angle, so the change in the flow direction of the priming liquid at the bent portion 53 is relatively gradual. For this reason, in the vicinity of the bent portion inner region 55, the priming liquid tends to stay because the flow rate of the priming liquid is slow or a steady vortex is generated in the priming liquid. Therefore, the air existing in the vicinity of the bent portion inner region 55 before the start of priming continues to remain in the vicinity of the bent portion inner region 55 together with the priming liquid as a so-called “bubble pool” after the start of priming. For this reason, as described above, in the conventional blood reservoir, it is difficult to discharge the air in the bent portion 53 or the vicinity thereof to the outside of the port 950 with the priming liquid.

  On the other hand, in the first embodiment, as shown in FIG. 3, the bending angle θ of the bending portion 53 is 90 degrees. In the present embodiment, the flow direction of the priming liquid changes abruptly at the bent portion 53 during priming. For this reason, the flow of the priming liquid is greatly disturbed by the bent portion 53, and unsteady vortices and turbulent flows are easily generated in the priming liquid. The disturbance of the flow of the priming liquid occurs not only in the vicinity of the bent portion outer region 54 but also in the vicinity of the bent portion inner region 55. For this reason, the priming liquid does not easily stay in the vicinity of the bent portion inner region 55, and the air existing in the vicinity of the bent portion inner region 55 before the start of priming is easily discharged out of the port 50 together with the priming liquid. . For this reason, in the first embodiment, the flow path in the port 50 can be filled with the priming liquid easily and in a short time even if the flow rate of the priming liquid is small.

  The material of the venous inflow port 50 is not limited, but is a hard material such as polycarbonate, polyethylene, polyester, polymethylpentene, methacryl, ABS resin (acrylonitrile / butadiene / styrene copolymer), PET resin (polyethylene). Resin materials such as terephthalate) and PVC (polyvinyl chloride) can be used, and among these, polycarbonate is preferable. The port 50 can be manufactured by such an injection molding method using such a resin material. In the present embodiment, the entire port 50 is integrally molded as one component, but the present invention is not limited to this, and the port 50 may be configured by combining a plurality of separately molded components.

  FIG. 5 is an enlarged cross-sectional view of the venous blood flow inlet port 50 ′ of another blood reservoir according to the first embodiment and the vicinity thereof. In this example, the bending angle θ of the flow path at the bending portion 53 is 75 degrees. Compared with the port 50 shown in FIG. 3, the change in the flow direction of the priming liquid at the bent portion 53 is larger at the port 50 ′ in FIG. 5. Accordingly, also in this case, the air in the vicinity of the bent portion inner region 55 is easily discharged out of the port 50 ′ together with the priming liquid, and the flow path in the port 50 ′ can be primed easily and in a short time even if the flow rate of the priming liquid is small Can be filled with liquid.

  The present inventors have found that the bending angle θ at the bending portion 53 is 90 degrees (see FIG. 3) and 75 degrees (see FIG. 5) compared with the case where it is about 105 to 120 degrees (see FIG. 4). Thus, it has been confirmed by experiments that the priming property for the venous blood flow inlet port is improved.

  As in the first embodiment, reducing the bending angle θ at the bending portion 53 is unlikely to cause a problem that the flow resistance increases due to the bending of the blood removal line tube connected to the first portion 51. There is an accompanying effect of becoming. This is due to the following reason. The tube of the blood removal line connects, for example, the blood pump and the first part 51. Since the tube has flexibility, it hangs down between the blood pump and the first part 51 due to gravity. When the first portion 51 is inclined so that the tip thereof is obliquely upward like the port 950 in FIG. 4, the tube connected to the first portion 51 is locally near the tip of the first portion 51. A phenomenon called “kink” tends to occur because the tube is bent and the flow path in the tube is blocked. On the other hand, when the bending angle θ decreases, the tip of the first portion 51 faces in the horizontal direction (see FIG. 3) or obliquely downward (see FIG. 5), so that the inclination of the first portion 51 is less than that of the hung tube. The inclination near the first part 51 is approached. For this reason, the possibility that the tube is locally bent in the vicinity of the first portion 51 is reduced, and the occurrence of kinks can be suppressed. As a result, it is possible to prevent an increase in channel resistance of the extracorporeal blood circulation circuit due to the occurrence of kinks.

  If the bending angle θ at the bent portion 53 of the venous blood flow inlet port is generally 90 degrees or less, the priming of the venous blood flow inlet port can be completed easily and in a short time with a small priming fluid flow rate. However, if the bending angle θ is too small, the following problems may occur. First, the handling property of the tube, such as the tube connected to the first part 51 colliding with the lid 16 of the blood reservoir 1, may be deteriorated. This problem may be solved by lengthening the second part 52 and enlarging the vertical distance between the first part 51 and the lid body 16, but this is a problem in the flow path in the venous blood flow inlet port. Increase blood filling volume. Second, since the blood flow is greatly disturbed in the vicinity of the bent portion 53, there is a high possibility that red blood cells are destroyed (hemolysis). Third, since the flow path direction in the venous blood flow inlet port changes abruptly at the bent portion 53, the flow path resistance when blood flows through the venous blood flow inlet port after priming increases. From these viewpoints, the lower limit of the bending angle θ is not limited, but is preferably 60 degrees or more, and more preferably 75 degrees or more. The present inventors have confirmed through experiments that the hemolysis and the channel resistance do not increase to such a degree that they can become a practical problem when the bending angle θ is 60 degrees or more.

(Embodiment 2)
6A is an enlarged cross-sectional view of the venous blood flow inlet port 50 ″ and its vicinity of the blood reservoir according to Embodiment 2 of the present invention. FIG. 6B is a cross section taken along a horizontal plane parallel to the central axis 51a of the first portion 51. FIG. 5 is an enlarged perspective view of the venous blood flow inlet port 50 ″ and the vicinity thereof.

  As shown in FIG. 6B, in the second embodiment, a protrusion 57 is provided on the inner side of the bent portion of the flow path inner surface of the venous blood flow inlet port 50 ″. The protrusion 57 is the second portion 52. The protrusion 57 connects the first surface 57a obtained by extending the inner surface of the first portion 51 into the second portion 52, and the tip of the first surface 57a and the inner surface of the second portion 52. 6A, from a direction (hereinafter referred to as “lateral direction”) perpendicular to a plane including the central axis 51a and the central axis 52a (hereinafter referred to as “vertical plane”). The shape of the protrusion 57 seen is a triangle. The first surface 57a is parallel to the central axis 51a of the first part 51, and the second surface 57b is relative to the central axis 52a so that the distance from the central axis 52a of the second part 52 increases on the lower side. Is inclined. The width of the protrusion 57 along the horizontal direction is relatively thin, and the protrusion 57 has a rib shape along the vertical plane as a whole.

  As described in the first embodiment, when the bending angle θ is reduced to 90 degrees or less, vortices and turbulence are likely to occur in the priming liquid in the vicinity of the bent portion inner region 55 during priming. Bubbles in the priming liquid move violently with vortices and turbulent flow in the vicinity of the bent portion inner region 55. In the second embodiment, a projection 57 is provided in such a bent portion inner region 55. For this reason, the bubbles collide with the protrusions 57 and are broken into smaller bubbles. The micronized bubbles are easily discharged from the port 50 ″ together with the priming liquid along the flow of the priming liquid. For this reason, the second embodiment has a smaller priming liquid flow rate than the first embodiment. The flow path inside can be more easily and quickly filled with the priming liquid.

  The protrusion 57 is provided on the inner surface of the inner surface of the flow path at the bent portion 53 or in the vicinity thereof so as to protrude into the flow path of the second portion 52. Thereby, a bubble can be refined | miniaturized efficiently.

  The protrusion 57 provided in the bent portion inner region 55 so as to protrude into the flow path of the second portion 52 hardly increases the flow path resistance of the blood flowing through the port 50 ″ after priming. There is almost no pressure increase in the vicinity of the inlet of the port 50 ″ due to the provision of. Further, there is almost no destruction of red blood cells (hemolysis) due to the provision of the protrusions 57.

  Preferably, the protrusion 57 does not protrude into the flow path of the first portion 51. In the first part 51, almost no vortex or turbulent flow is generated in the priming liquid, and therefore no bubble accumulation occurs. Therefore, even if the protrusion 57 protrudes into the flow path of the first portion 51, such an effect that the protrusion 57 makes the bubbles fine can hardly be expected. Rather, if the protrusion 57 protrudes into the first portion 51, there is a high possibility that the flow path resistance of the blood flowing through the port 50 ″ will increase, or the destruction of red blood cells (hemolysis) will occur.

  The protrusion 57 having a thin rib shape along the vertical plane is advantageous for further reducing the possibility of increasing the flow resistance of blood flowing through the port 50 "and destroying red blood cells.

  6A and 6B are merely examples, and the present invention is not limited thereto. For example, the shape of the protrusion 57 can be changed as appropriate. The first surface 57a does not need to extend in parallel with the central axis 51a, and may be inclined so as to be separated from the central axis 51a as the distance from the first portion 51 increases, for example. The shape of the protrusion 57 viewed from the lateral direction does not have to be a triangle having the first surface 57a and the second surface 57b, and may be, for example, a trapezoid or an arc. The positions of the protrusions do not need to be adjacent to the boundary between the first part 51 and the second part 52 as shown in FIGS. 6A and 6B, and may be slightly separated from the boundary downstream. Two or more protrusions may be arranged at different positions in the lateral direction or the direction of the central axis 52a.

  The second embodiment is the same as the first embodiment except for the above. 6A and 6B, the protrusion 57 is provided on the venous blood flow inlet port 50 ″ having the bending angle θ of 90 degrees. However, the protrusion 57 described in the second embodiment is not limited to the arbitrary venous blood flow inlet port of the present invention. Can be provided.

  The above-described first and second embodiments are merely examples. The present invention is not limited to Embodiments 1 and 2, and can be modified as appropriate.

  For example, the cardiotomy section 30 can have any configuration other than the above. For example, the defoaming material 35 and the filter 36 do not need to have a cylindrical shape, and may have a substantially bag shape opened only upward. The frame 36 between the defoamer 35 and the intracardiac blood filter 37 may be omitted. The shape of the housing 31 and the position of the hole 32 can be arbitrarily changed.

  The blood reservoir of the present invention need not be an intracardiac blood reservoir integrated venous blood reservoir as shown in the first and second embodiments, but a vein into which venous blood does not flow but does not flow into the heart. It may be a blood reservoir. In this case, members related to intracardiac blood, such as the intracardiac blood inflow port 21 and the cardiotomy section 30, are omitted.

  The present invention can be widely used as a blood reservoir provided in an extracorporeal blood circulation circuit used when performing cardiopulmonary surgery or the like. In particular, it can be used as a blood reservoir equipped with a venous blood flow inlet port into which venous blood flows.

DESCRIPTION OF SYMBOLS 1 Blood reservoir 12 Blood storage part 50, 50 ', 50 "Venous blood inflow port 51 1st part 52 2nd part 53 Bending part 57 Projection (theta) Bending angle

Claims (4)

A blood reservoir comprising a venous blood flow port, and a blood reservoir that can temporarily store blood flowing from the venous blood flow port,
The venous blood flow port includes a bent portion where a flow path through which blood flows is bent,
The blood reservoir, wherein the bending angle of the flow path at the bent portion is 90 degrees or less.   The blood reservoir according to claim 1, wherein the bending angle is 60 degrees or more. The venous blood flow port includes a first portion upstream of the bent portion and a second portion downstream of the bent portion,
The second part extends along the vertical direction,
The blood reservoir according to claim 1 or 2, wherein the first part is configured to be connected to a tube of a blood removal line.   The protrusion which protruded toward the inside of the flow path of the downstream with respect to the said bending part is provided in the inner side of the said bending part or its vicinity of the inner surface which defines the said flow path. The blood reservoir according to one item.

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