US3769982A - Physiological drainage system with closure means responsive to downstream suction - Google Patents

Physiological drainage system with closure means responsive to downstream suction Download PDF

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US3769982A
US3769982A US00183463A US3769982DA US3769982A US 3769982 A US3769982 A US 3769982A US 00183463 A US00183463 A US 00183463A US 3769982D A US3769982D A US 3769982DA US 3769982 A US3769982 A US 3769982A
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flow
diaphragm
cavity
suction
sealing surface
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R Schulte
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Baxter International Inc
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Assigned to AMERICAN HOSPITAL SUPPLY CORPORATION; A CORP OF IL. reassignment AMERICAN HOSPITAL SUPPLY CORPORATION; A CORP OF IL. ASSIGNMENT OF ASSIGNORS INTEREST. Assignors: AMERICAN HEYER- SCHULTE CORPORATION
Assigned to AMERICAN HEYER-SCHULTE CORPORATION reassignment AMERICAN HEYER-SCHULTE CORPORATION ASSIGNMENT OF ASSIGNORS INTEREST. Assignors: HEYER-SCHULTE CORPORATION
Assigned to BAXTER TRAVENOL LABORATORIES, INC. A CORP. OF DE reassignment BAXTER TRAVENOL LABORATORIES, INC. A CORP. OF DE MERGER (SEE DOCUMENT FOR DETAILS). EFFECTIVE ON 11/25/1985 ILLINOIS Assignors: AMERICAN HOSPITAL SUPPLY CORPORATION INTO
Assigned to BAXTER INTERNATIONAL INC. reassignment BAXTER INTERNATIONAL INC. CHANGE OF NAME (SEE DOCUMENT FOR DETAILS). EFFECTIVE ON 10/17/1988 Assignors: BAXTER TRAVENOL LABORATORIES, INC., A CORP. OF DE
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    • 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
    • A61M27/00—Drainage appliance for wounds or the like, i.e. wound drains, implanted drains
    • A61M27/002—Implant devices for drainage of body fluids from one part of the body to another
    • A61M27/006—Cerebrospinal drainage; Accessories therefor, e.g. valves

Definitions

  • ABSTRACT A physiological drainage system for draining liquids from a source of the human body to a region where it is disposed of. The latter region is at a different elevation'from the source region.
  • the system is provided with a control which is responsive to downstream suction. When the suction is excessive, the control closes the system to flow so as to prevent over-drainage of the source region.
  • the control comprises a valve which remains open to flow at normal rates and downstream suction levels, and which closes when the downstream suction level is above some predetermined level.
  • I N VEN TOR. 1Q (/DULF Q. SCHULTZ? PHYSIOLOGICAL DRAINAGE SYSTEM WITH CLOSURE MEANS'RIESPONSIVE TO DOWNSTREAM SUCTION
  • This invention relates to physiological drainage systems of the type used for draining excess liquid from a source region of the human body to a drainage region.
  • An example is found in the alleviation of the symptoms of hydrocephalus, in which ailment the natural drainage systems from the cranium fail to provide sufficient drainage. It is necessary to drain excess fluid from the cranium in order to prevent brain damage and death.
  • Drainage systems for alleviation of the symptoms of hydrocephalus and of other ailments of the body in which unwanted quantities of fluid remain in some source region of the human body are well known.
  • a classical example of one such system is shown in U.S. Pat. No. 3,111,125, issued to Rudolf R. Schulte on Nov. 19, 1963.
  • a drainage catheter is inserted in a source region to be drained, the ventricles of the brain, for example.
  • the catheter isconnected to a shunt tube which extends along a selected route to another region of the human body, such as to the heart, where the excess fluid is disposed of.
  • a pump in the system to assist the systems functioning.
  • the pump means ordinarily remains open to forward flow, may act as a reverse flow check valve, and can also impel fluid in one or both directions depending on how the valve is manipulated.
  • This device is, in one sense a siphon breaker," but is not to be confused with ordinary siphon breakers which are widely known.
  • the classical type of siphon breaker which seeks to avoid siphoning from a region as the consequence of an upstream break in a line, ordinarily functions to admit gas into a fluid stream so as to break the suction.
  • this device acts to break a suction force, it is not to be confused with classical suction or siphon breakers, because it does not relieve the suction force. Instead, it blocks it.
  • Another classical device utilized in controlling unwanted movement of fluids is a common check valve which operates on a differential pressure concept, usually being spring-loaded to a closed position, and opened in the direction of forward flow by a differential force which overcomes the spring bias.
  • the device of this invention needs carefully to be distinguished from the classical check valve.
  • In the check valve there is an impediment to flow in one direction and free flow in the opposite direction under a suitable or sufficient differential pressure.
  • it may physically resemble a check valve, it closes to stop the flow of fluid in the intended direction of forward flow when excessive downstream suction is exerted. Such suction would open the classical check valve because it would contribute all the more to the differential pressure needed to open the same. Accordingly, the usual considerations of stopping flow with check valves and with siphon breakers are not pertinent to this invention.
  • This invention provides a control which permits the free flow of fluid from a source region to be drained to a receiving region to receive the same which will close to the forward direction of flow when an excessive downstream suction exists.
  • the control will remain closed regardless of the upstream pressure, and will not open again until the downstream suction is relieved, such as by the persons assuming a position in which a lesser suction exists.
  • this closure means might tend to keep the system closed for an unwarranted length of time.
  • the ordinary motions of turning over in bed, of sitting up, standing up, sitting down, and leaning over will of themselves cause changes of suction level which are likely to permit the control to open and again permit drainage.
  • itis another object of this invention to provide a control responsive to downstream suction which will permit drainage to occur under predetermined suction and differential pressure conditions, stop the drainage when an excessive downstream suction is exerted on the system which might over-drain the region to be drained, and still be open in a number of normal positions of the human body such that proper drainage will in fact occur with sufficient frequency to meet the needs of the user.
  • a device includes a body having a pair of flow ports entering a cavity, and between them flexible means which is adapted to move to close the outlet which is downstream as to direction of flow when excessive suction exists downstream.
  • the flexible means is so disposed and arranged that, when once it closes the control, the control remains closed until the suction is sufficiently relieved, regardless of the upstream pressure, assuming it to be greater than the suction level, of course.
  • FIG. 1 shows a reclining person with a system according to the invention implanted in him;
  • FIG. 2 shows the same person in an erect position
  • FIG. 3 is a schematic view of a system according to the invention.
  • FIG. 4 is an enlarged fragmentary view of a portion of the system of FIG. 3;
  • FIG. 5 is a cross-section taken at line 55 in FIG. 2;
  • FIGS. 6 and 7 are cross-sections taken at lines 6-6 and 7-7, respectively, in FIG. 4;
  • FIG. 8 is an axial section of an embodiment ofa control according to the invention in one operating position
  • FIGS. 9 and 10 are views similar to FIG. 8 showing the device of FIG. 8 in other operating conditions
  • FIG. 11 shows an optional feature which may be embodied in the device of FIG. 8;
  • FIG. 12 is a cross-section taken at line l212 in FIG. 8;
  • FIG. 13 is a fragmentary cross-section taken at line 13-13 in FIG. 8;
  • FIG. 14 is a fragmentary cross-section taken at line 14--14 in FIG. 11;
  • FIGS. 15 and 16 are axial cross-sections of another embodiment of the invention, shown in two operating positions;
  • FIGS. 17 and 18 are axial cross-sections of another embodiment of the invention in two different operating positions
  • FIGS. 19 and 20 are axial cross-sections of still another embodiment of the invention in two different operating conditions
  • FIGS. 21 and 22 are cross-sections taken at lines 21-21 and 2222 in FIGS. 19 and 20, respectively;
  • FIG. 23 shows an optional type of diaphragm useful in this invention.
  • FIGS. 24 and 25 are axial cross-sections of the presently preferred embodiment of the invention in two operating positions
  • FIG. 26 is a perspective view of the device of FIG. 24;
  • FIG. 27 is a top plan view of the device of FIG. 24.
  • FIG. 28 is a cross-section taken at line 2828 of FIG. 24.
  • FIG. 1 illustrates a person 30 afflicted with hydrocephalus having a cranium 31 enclosing a brain 32, the
  • ventricles of which are surfeited with fluid because the normal drainage passages of the body are not draining the same.
  • development of this brain would be retarded unless the resulting fluid pressure were relieved.
  • the persons skull would be distended, and in general, he would be subjected to intense pain, mental retardation, and possibly death.
  • the system 35 drains fluid from the ventricles of the brain to the heart 36, from which it is carried in the bloodstream to be disposed of by normal physiological functions of the purification of the blood.
  • This system includes a drainage catheter 37 which has, as best shown in FIGS. 2 and 5, a tubular cylindrical wall 38 with a plurality of drainage ports 39 therethrough near one end. The catheter is inserted so that these ports are placed in the source region. The other end passes through the burr hole in the skull through which the drainage end of the catheter was inserted.
  • a pump 40 according to the aforesaid Schulte US Pat. No. 3,111,125 is connected to the drainage catheter.
  • This pump is optional. It exists to flush either the upstream or the downstream portions of the system, and to create pumping surges should such be desired. This is a very useful additional feature for use with this invention, but it is not essential to the practice of this invention.
  • the pump has an inlet 41 connected to the drainage catheter and an outlet 42 connected to the control 45 according to this invention. Both the pump and the control may be formed with flat bottoms and low profiles so they can be laid against the skull and fit beneath the scalp.
  • the control has a first and second flow port 46, 47, respectively, the first upstream flow port (46) being connected to the outlet of the pump and the second downstream flow port (47) being connected to a shunt 50 of the type shown in the aforesaid Schulte patent and also shown in FIG. 4. If the pump is not used, the control is connected directly to the catheter.
  • upstream is used to mean the direction from which flow originates. In some embodiments of this system, both ends are regarded as potentially upstream. However, speaking generally, upstream" means toward the source region from the control, and down stream means toward the disposal region.
  • the shunt may be a simple open-ended tube, but it is usually best for it to include check valve means at its free end so that reverse flow of fluids will not occur into the shunt from the disposal region.
  • the shunt is tubular and has a cylindrical wall 51 extending to a closed end 52 adjacent to which there is a check valve 53 in the form of a slit 54.
  • Slit 54 is cut through the wall of the tube without removal of material so that a differential pressure derived from a greater pressure on the outside than on the inside will tend to press the edges of the slit together and close the valve, while a reverse differential pressure will tend to bow the wall outward, opening the slit and permitting drainage.
  • the system taps a region 57 to be drained by the drainage catheter 37.
  • Pump 40 passes fluid from the catheter to control 45 and shunt 50, and then into a disposal region where the fluid is disposed of.
  • FIG. 1 wherein the person is shown reclining. It will be seen that the maximum pressure in the system is derived from a column of fluid whose height is shown by dimension A. This is the height of a vertical column measured from the inlet end of the drainage catheter to the discharge end of the shunt. It will be noted that there is substantially no suction exerted below the pump or the control.
  • FIG. 2 An extreme but common situation, and one which it is the function of this invention to control, is shown in FIG. 2 with the person in the erect position.
  • a dimension B represents the column between the two tips.
  • the hanging column of fluid in shunt 50 is very long, perhaps 12-18 inches in length, and its effect would be to siphon liquid out of the brain, perhaps excessively.
  • the means whereby this has been resisted in the past has been to make the slit valve 53 open at a relatively high pressure, thereby lessening the effective sun'ction column above level 56 as heretofore discussed.
  • this makes the system less sensitive, and is something ofa brute force means of approaching the problem.
  • close selection of the level 56 is quite difficult, and adjustment is impossible in the implanted tube.
  • a better technique would be to enable the region to be drained at any desired outlet pressure, but to prevent it from being drained excessively because of excessive suction forces.'That is the purpose of the control of the instant invention.
  • the pulsing variations of suction derived from frequent changes of position cause strong pumping pulses, which could overcome a slit valve, but which are stopped by the control.
  • FIG. 8 shows one embodiment of a control 60 according to the invention which may be utilized at the location shown schematically by control 45in the system, as may the other embodiments hereafter disclosed.
  • Control 60 hasa body 61 with a flat base 62 and a dome 63 forming a cavity 64 therein which is divided into two chambers 65, 66 by a flexible diaphragm 67 with a central flow port 68 (sometimes called a third flow port) therethrough.
  • the intended downstream flow through this control is from first flow port 69 to second flow port 70, port 69 being upstream and port 70 being downstream.
  • a support 71 projects into the cavity from the dome, to which it is attached. it has a plurality of passages 72 in its wall and a central opening 73 in communication with the passages and in alignment with flow port 68.
  • a seat 74 is formed on the diaphragm surrounding the flow port and facing into chamber 66.
  • a complementary diaphragm 75 extends across the cavity adjacent to the base. It is prevented from adhering to the base by a plurality of raised buttons 77 which are molded integrally with the base.
  • Ports 69 and 70 form connectors 78, 79 by means of which the control may be coupled into the system.
  • Control 60 is shown in three different positions in FIGS. 8, 9, and 10.
  • the positions of FIGS. 8 and 9 are closed positions and that of FIG. 10 is its normal open position.
  • FIG. 11 shows an optional feature which may be incorporated in the control of FIG. 8, when it is desired to resist suction only if exerted from the downstream end.
  • a vent passage 80 is formed interconnecting the first chamber 65 to a relief chamber 81 formed between the base and the complementary diaphragm; The function of this vent passage will further be discussed below.
  • the device is shown assembled by layers of cement. 82, which are shown in dotted notation.
  • This control and all other embodiments of the invention arepreferably made out of the same material of construction, a convenient example of which is medical grade silicone rubber.
  • the parts may individually be molded and then cemented together. In some embodiments variuus of the portions may be vulcanized together without cement. It is to be understood that, in all of the drawings herein, the parts where joined together to form continuous structure are fluid-tight at their joints except as otherwise indicated. The required flexibility of certain parts is generally secured by selection of their respective thicknesses.
  • FIGS. 15 and 16 show another embodiment of the invention.
  • a control 85 has a body 86 constructed of a flat base 87 and a dome 88. These form a cavity 89 between them.
  • the cavity is divided into chambers 90, 91 which are respectively connected to first and second flow ports 92, 93. Port 93 will ordinarily be the downstream port,'although in this embodiment the selection is immaterial, because the control functions bidirectionally.
  • the base includes a dome-shaped inner surface 94, which faces convex upwardly toward a flexible diaphragm 95.
  • This diaphragm divides the cavity into the aforesaid two chambers and 91..
  • a flow port 96 (sometimes called a third flow port) passes through the diaphragm and a seat 97 extending around this port, facing into the chamber 91.
  • FIGS: 15 and 16 The device of FIGS: 15 and 16 is shown in these two figures in its actuated position with the diaphragm flexed. In its unflexedcondition, the diaphragm will assume a position midway between the two positions, and so there will be free flow between ports 92 and 93 through flow port 96. Exertion of sufficient suction at either of the two flow ports will cause the diaphragm to assume a respective one of the illustrated positions.
  • FIGS. 17 and 18 show another embodiment of the in vention wherein a control 100 has a body 101 with a base 102 and a cover 103. A cavity 105 is formed in the body. A flexible diaphragm 106 bows upwardly in the diaphragm with a chamber 107 beneath it. A bias spring 108 is placed in chamber 107 which tends to force the central portion of the diaphragm upwardly toward a first flow port 109, which is surrounded by a seat 110 that projects into chamber 111 of cavity 105. A second flow port 112 also enters chamber 111.
  • This embodiment differs from the previous embodiments in that flow does not occur through the diaphragm, but instead is always on the same side thereof.
  • the normal relaxed position of the diaphragm is that shown in FIG. 17, and its actuated position, when suction does not occur and sufficient positive pressure exists to open the control, is shown in FIG. 18, both of which will be more fully described below.
  • FIG. 19 shows still another embodiment of the invention wherein a control 120 includes a body 121 having a cavity 122 therein.
  • the cavity is vented by vent ports 123 through its wall, although if desired these may be closed and the cavity filled with a spongy or springy means for exerting a reference pressure as will later be discussed.
  • the device is a generally flat lozenge having first and second ports 124, 125 entering at its ends.
  • the ports connect to a flow chamber 126 of variable volume which is formed between a pair of diaphragms 127, 128 that are generally flat sheets of elastic resilient material which, under proper conditions of pressure and flow rates, will bow apart as shown in FIG. 1 to enlarge the flow chamber 126, or under suction conditions where closure occurs, draw together to form a closure line 129 as shown in FIG. 22.
  • FIG. 23 illustrates a portion of a diaphragm which is flexible, but not necessarily resilient in the elastic" sense of the term. Except for diaphragms such as complementary diaphragm 75, which is best made elastic, the diaphragms merely need to be movable to accomplish their purpose. Even in diaphragm 75, a spring could be substituted for the elasticity as a source of restorative force.
  • This illustrative diaphragm 135 has a fabric reinforcement 136 which will prevent stretching. However, a number of bellows-convolutions enable the seat 137 to move axially relative to the rim edge of the diaphragm. Such a construction can generally be substituted for the other diaphragms shown in the drawings.
  • FIGS. 2428 It is a variation of the device of FIGS. 17 and 18, and illustrates that the diaphragm need not be movable freely and separately within a body cavity, but can instead be used to form a body wall for the cavity.
  • a biasing force or pressure can be derived from the body region surrounding the control, such as from pressure-contact with'fatty tissue in various regions, or even from exposure to fluids in this region.
  • Control 140 includes a body 141 having a flat, relatively rigid base 142 with a peripheral rim 143 around the top of it.
  • a flexible diaphragm 144 preferably having a fabric reinforcement 145 to reduce or eliminate stretch, is peripherally attached to the rim and sealed thereto in order to form a cavity 146 in the body.
  • the diaphragm is both a cover and a diaphragm, and its operative part for flow control is its surface which is exposed in the cavity.
  • Another fabric reinforcement 147 is cemented to the base to reduce or eliminate stretching of the base.
  • Flow port 149 rises in the cavity at the center of the cavity, and is surrounded by a seat 150 which projects into the cavity (this cavity will sometimes be called a flow chamber" in the same sense as chamber 111 in FIGS. 17 and 18).
  • Flow port 148 rises into the cavity at a point laterally spaced from the seat.
  • the diaphragm when it contacts the seat as in FIG. 25, closes the control to flow. It is open in FIG. 24.
  • FIG. 24 illustrates the relaxed condition of the control in the absence of distortive forces.
  • first sealing surface and second sealing surface are sometimes used herein.
  • the first sealing surface is a portion of a diaphragm which faces toward another sealing surface, which surfaces can make contact with one another to close the control to flow.
  • the diaphragm is imperforate outside of the area occluded when the sealing surfaces abut one another.
  • diaphragm 67 has a sealing surface 74a formed as the crown of seat 74.
  • Surface 74a is on the diaphragm and in the cavity 64.
  • Complementary diaphragm has a second" sealing surface 75a which faces first sealing surface 740.
  • the area bounded by surface 74a is occluded as a consequence of abutment of the two sealing surfaces.
  • a first sealing surface 97a is formed as the crown of seat 97, and second sealing surface 94 (the dome-shaped inner surface) is formed on the base. Both are in the cavity, and they face one another. Also, the upper surface of diaphragm faces the bottom surface of dome 88, for the same purpose. In both cases, the area occluded is defined by the outer boundary of the area of abutting contact, and the area of the diaphragm which is not occluded is imperforate. Like considerations apply to the construction of FIG. 17.
  • the first and second sealing surfaces are surfaces 127a and 128a.
  • the first sealing surface is surface 144a which is on the diaphragm and in the cavity. It faces a second sealing surface a formed as the crown of seat 150.
  • the diaphragm is imperforate outside of the area occluded when the sealing surfaces abut one another, that is-, outside of the crown.
  • the function of the system is to drain the ventricles of the brain, or whatever source region is being produced by the pump does not upset the operation of the control.
  • FIGS. 8-H The configuration of FIGS. 8-H), without the modification of FIG. 11, will first be discussed in detail.
  • diaphragms 67 and 75 will assume the positions shown in FIG. 10, and there will be free flow from flow port 69 to flow port 70. This is the preferred direction of downstream flow to be controlled, wherein flow port 69 occupies the position shown by flow port 416 in FIG. 3.
  • flow port 70 Should a downstream suction surge be exerted at flow port 70, the pressure in flow chamber 66 will drop, and it will not instantaneously be relieved by pressure from flow chamber 65.
  • the size of flow port 63 is selected so as 'to comprise a flow restriction so as to delay equalization of pressure between the two chambers. Diaphragm 67 will therefore deflect to the position shown in FIG. 8 and, depending on the resilience and fluid content of the region beneath complementary diaphragm 75, diaphragm 75 may also rise. The result will be an adherence between the seat 74 and the complementary diaphragm, thereby sealingly separating flow chambers 65 and 66 from each other.
  • control 60 can be used with its connections reversed from those described, or
  • both of the diaphragms 67 and '75 will have been brought up until they are stopped by support 71, at which time the sealingcontact is made at seat 74. Again, the negative sucfect should such be desired. Because of the dimensional relationships, it is preferably connected to the likelier source of suction at flow port 70.
  • FIG. ill wherein a vent passage 80 interconnects flow chamber to relief chamber 81 beneath complementary diaphragm 75.
  • vent passage is optional, but does provide a significant improvement in the function of the device when only uni-directional suction control is desired.
  • FIG. 15 shows a flow control 85.Its diaphragm 95 is made of flexible material which tends to occupy a position intermediate between those shown in FIGS. 15 and 16. When fluid flows at gradual rates and low suction (which is the normal situation), it flows through the control without impediment.
  • the dome in this case, is also flexible and forms, in effect, a complementary diaphragm and is shown deflected somewhat in FIG. 16.
  • FIG. '15 shows closure of the control when excessive suction is exerted at flow port 93.
  • pressure will have dropped in flow chamber 91 and, because of the fluid flow restriction through flow port 96 and past the outer edge of seat 97, pressure will have dropped in flow chamber 91 enough that diaphragm 95 will be drawn down so that seal 97 seals on domeshaped inner surface 94.
  • the control is locked andremains locked. This effect is also helped by any upstream pressure which continues to exert a locking downward pressure on the diaphragm, and the pressure cannot by-pass the seat to relieve the suction.
  • This differential pressure (which must, of course, be sufficient to overcome any springiness in the diaphragm) will prevent the control from opening until the suction is relieved.
  • FIG. 16 illustrates locking of the device should sufficient suction be exerted at flow port 92.
  • pressure in flow chamber will have dropped so as to draw down the dome and draw up diaphragm 94 to make a seal between them, thereby separating the two flow chambers and preventing flow until the suction is again relieved.
  • the closure remains, as in FIG. 15, except that in the condition of FIG. 16 there is a small additional differential pressure to be considered on the surface bounded by the seat.
  • FIGS. 17 and 18 show still another flow control which is intended for operation at somewhat higher pressures than the other embodiments.
  • FIG. 17 shows the device in its normally closed condition. It is also the condition which would occur when sufficient suction is exerted at flow port 109.
  • flow port 109 In the event that strong suction exists in flow port 109, its negative force on the diaphragm caused by an abrupt drop in cavity pressure, combined with the mechanical force of the spring, will close the valve unless and until unusually high pressures are exerted in flow port 112. Should, however, there be no excessive suction, and there be normal drainage pressure at flow port 112, the effect is to build up sufficient force over the diaphragm outside the seat 110 to move the diaphragm to the position shown in FIG. 18, thereby opening the valve to flow as shown.
  • the device of FIG. 19 comprises a pair of housing parts that enclose a pair of contiguous flat, resilient sheets. These sheets in repose act as diaphragms that tend to lay against one another, and which will be bowed apart by sufficient pressure exerted between them. Should there be enough pressure at the upstream end and an absence of excessive suction at the downstream end,- then a flow chamber 126 will open up, as shown in FIGS. 19 and 21, and a continuous channel will be formed between the two flow ports. If, however, a sufficient suction is exerted at the downstream port, then the lesser pressure will cause the diaphragms to move together and seal to form a closure plane between them, along which fluid will not flow.
  • This closure canbeovercome only by a very substantial upstream pressure which must overcome not only the ambient surrounding pressure that tends to force the diaphragms together, but also to peel them apart where they are pressed together ,by the differential between suction and ambient pressure.
  • the practical effect in a shunt installed in a human body is that the device remains closed so long as suction is exerted downstream and is not opened by practical levels of upstream pressure.
  • the effectiveness of this device may also be improved by providing means to vary the force which tends to bias the diaphragms together.
  • Vents 123 admit body fluids under ambient pressures, and the device could also be packed with springy sponge-like material, or even with springs, which would exert a restorative force tending to keep the device closed against incoming pressures and to amplify the effect of downstream suction.
  • FIGS. 24-28 operates like that of FIGS. 17 and 18. Instead of a bias spring, it utilizes force derived from the surrounding region such as body tissue to resist movement of the diaphragm away from the seat. Normally, it leaves a small-area flow channel above the seat, and the outside force and inside fluid forces about balance in order to permit slow flow. In the event excessive suction is applied downstream, the lowered pressure at the center of the diaphragm will pull it down to close the control as shown in FIG. 25, and the control tends to remain closed because the outer annular region retains about the same pressure relationship between inside and outside as it had before, but the central portion is under a strong closing force. Of course, this can be overcome by a sufficient upstream pressure, but it must be substantial, and by the time it is exerted, the user will probably have changed his position and relieved the suction.
  • FIG. 25 some yielding of the rim has been shown to illustrate means whereby the flexible diaphragm, although drawn fairly tightly across the rim, can move down to close the seat even though there may be little, if any, stretch in the diaphragm itself.
  • control should be built so that its normal tendency, absent any differential pressure through it, is to be open.
  • relative flow port sizes may be selected to provide restrictions which delay change of pressure in respective flow chambers so as to make the operation of the valve even more reliable. This is an optional consideration for the designers use.
  • this device provides a means for preventing over-drainage of source regions in the human body, thereby providing a system which drains to a datum level and no farther, and providing the individual with a constant livable condition rather than one which varies from time to time in a manner which might upset him.
  • a suction control for a physiological drain wherein the control closes in response to excessive downstream suction comprising: a body having an internal cavity, a first and a second flow port through the body into the cavity, a flexible diaphragm extending across the cavity; a first sealing surface in said cavity on said diaphragm; and a second sealing surface in the cavity adapted to make a closure with the first sealing surface between the flow ports as a consequence of the exertion of sufficient suction at one of said ports to cause at least one of said sealing surfaces to move toward and against the other, the diaphragm being imperforate throughout its entire area which lies outside of that portion of the second sealing surface which is c cluded when the said sealing surfaces abut one another.
  • a suction control according to claim 1 in which the diaphragm 41 across the cavity to divide it into two chambers, there being a third flow port through said diaphragm interconnecting the chambers, and in which the first sealing surface surrounds the third flow port, and the-second sealing surface comprises a wall of one of the chambers, each of the first and second flow ports entering a different respective flow chamber outside the area bounded by a sealing surface.
  • a suction control according to claim 2 in which a third sealing surface is provided which comprises a wall of the other of said chambers.
  • a suction control in which the diaphragm extends across the cavity to divide it into two chambers, there being a third flow port through said diaphragm interconnecting the chambers, in which the first sealings'urface surrounds the third flow port, each of the first and second flow ports entering a different respective flowchamber outside the area bounded by a sealing surface, in which a flexible complementary diaphragm-extends across the cavity in one of said flow chambers, with one of the first and second flow ports entering the flow chamber between the two diaphragms, a surface of said complementary diaphragm forming a sealing surface, and a support member in the other flow chamber supporting the diaphragm away from the wall of the cavity.
  • a suction control according to claim 5 in which the support is tubular, axially aligned with the third flow port, and perforated to permit flow inside the support and through its wall.
  • a suction control according to claim 5 in which a vent passage interconnects the flowchamber entered by the other of said first and second flow ports to a relief chamber located between the complementary diaphragm and the wall of the cavity.
  • a suction control according to claim 7 in which the support is tubular, axially aligned with the third flow port, and perforated to permit flow inside the support and through its wall.
  • a suction control according to claim din which spacer means prevent adherence of the complementary diaphragm to the wall of the cavity.
  • a suction control according to claim 10 in which bias spring means is mounted in the chamber which does not receive the flow ports, and biases the sealing surface toward the first-named flow port.
  • a suction control according to claim 1 in which a pair of said diaphragms is provided, said diaphragms being substantially flat sheets laid against one another and sealed to each other to form an internal flow chamber when fluid pressure is exerted between the diaphragms, the flow ports opening into said flow chamber at linearly spaced-apart locations, each of said diaphragms carrying one of said sealing surfaces.
  • a suction control according to claim 12 in which a body surrounds said diaphragms to form a cavity receiving the same and permitting their distention by insertion of fluid underpressure.
  • a physiological drainage system provided with a control for resisting over-drainage as a consequence of downstream suction comprising: a drainage catheter adapted to drain fluid from a source region; a shunt tube to dispose of fluid collected by said catheter; and a suction control comprising: a body having an internal cavity, a first and a second flow port through the body into the cavity, a flexible diaphragm extending across the cavity; a first sealing surface in said cavity on said diaphragm; and a second sealing surface in the cavity adapted to make a closure'with the first sealing surface between the flow ports as a consequence of the exertion of sufficient suction at one of said ports to cause at least one of said sealing surfaces to move toward and against the other, the catheter being connected to one flow port and the shunt tube to the other; the diaphragm being imperforate throughout its entire area which lies outside of that portion of the second sealing surface which is occluded when the said sealing surfaces abut one another.
  • a physiological drainage system in which the shunt tube is provided with a check valve at a location removed from its connection to the control.
  • a physiological drainage system in which a pump is connected into the system between-the catheter and the control.
  • a physiological drainage system in which the shunt tube is provided with a check valve at a location removed from its connection to the control.
  • a physiological drainage system in which the diaphragm extends across the cavity to divide it into two chambers, there being a third flow port through said diaphragm interconnecting the chambers, and in which the first sealing surface-surrounds the third flow port, and the second sealing surface comprises awall of one of the chambers, each of the first and second flow ports entering a different respective flow chamber outside the area bounded by a sealing surface.
  • a physiological drainage system in which the diaphragm extends across the cavity to divide it into two chambers, there being a third flow port through said diaphragm interconnecting the chambers, in which the first sealing surface surrounds the third flow port, each of the first and second flow ports entering a different respective flow chamber outside the area bounded by a sealing surface, in which a flexible complementary diaphragm extends across the cavity in one of said flow chambers, with one of the said first and second flow ports entering the flow chamber between the two diaphragms, a surface of said complementary diaphragm forming a sealing surface, and a support in the other flow chamber supporting the diaphragm away from the wall of the cavity.
  • a physiological drainage system in which a vent passage interconnects the flow chamber entered by the other of said first and second flow ports to a relief chamber located between the complementary diaphragm and the wall of the cavity.
  • a physiological drainage system in which the diaphragm extends across the cavity to divide it into two chambers, its sealing surface facing one of said flow ports and adapted to close the same, the other of said flow ports entering the same chamber as the other of the said flow ports.
  • a physiological drainage system in which a pair of said diaphragms is provided, said diaphragms being substantially flat sheets laid against one another and sealed to each other to form an internal flow chamber when fluid pressure is exerted between the diaphragms, the flow ports opening into said flow chamber at linearly spaced-apart locations, each of said diaphragms carrying one of said sealing surfaces.
  • a suction control according to claim 24 in which the control is generally circular in plan view, and in which a seat surrounds the second flow port at the center of the control, the diaphragm overlaying the said seat and the entry of the first flow port into the cavity.
  • a suction control according to claim 14 in which the diaphragm forms a bounding wall of said cavity, and is so disposed and arranged as to shut off flow between the flow ports as a consequence of exertion of sufficient suction on the control.
  • a physiological drainage system in which the control is generally circular in plan view, and in which a seat surrounds the second flow port at the center of the control, the diaphragm overlaying the said seat and the entry of the first flow port into the cavity.

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US00183463A 1971-09-24 1971-09-24 Physiological drainage system with closure means responsive to downstream suction Expired - Lifetime US3769982A (en)

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Cited By (61)

* Cited by examiner, † Cited by third party
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US3889687A (en) * 1974-01-31 1975-06-17 Donald L Harris Shunt system for the transport of cerebrospinal fluid
US3894541A (en) * 1974-02-27 1975-07-15 El Shafei Ismail Lotfy Method of treating hydrocephalus
US3901245A (en) * 1973-03-15 1975-08-26 Bio Medical Res Ltd Bio-medical pressure control device
US3910283A (en) * 1973-10-09 1975-10-07 Harry H Leveen Process for treatment of ascites and device to accomplish same
US3964484A (en) * 1975-03-03 1976-06-22 Sorenson Research Co., Inc. Antiocoagulant metering device and method
US3991768A (en) * 1973-03-16 1976-11-16 Portnoy Harold D Shunt system resistant to overdrainage and siphoning and valve therefor
US3999553A (en) * 1973-03-15 1976-12-28 Bio-Medical Research, Ltd. Bio-medical pressure control device
US4103689A (en) * 1976-12-13 1978-08-01 Stephen Beecher Leighton Tissue pressure reference for cerebrospinal fluid shunting device
US4364395A (en) * 1981-06-30 1982-12-21 American Heyer-Schulte Corporation Low profile shunt system
FR2539299A1 (fr) * 1983-01-14 1984-07-20 Descartes Paris V Universite R Dispositif de traitement de l'hydrocephalie avec filtre a impedance variable
US4464168A (en) * 1981-06-30 1984-08-07 American Hospital Supply Corporation Low profile shunt system
EP0117050A1 (en) * 1983-02-17 1984-08-29 Cordis Corporation Intercranial pressure regulator valve
US4540400A (en) * 1983-02-17 1985-09-10 Cordis Corporation Non-invasively adjustable valve
US4552553A (en) * 1983-06-30 1985-11-12 Pudenz-Schulte Medical Research Corp. Flow control valve
US4557721A (en) * 1983-11-29 1985-12-10 Cordis Corporation Servo valve
EP0163897A1 (en) * 1984-05-08 1985-12-11 Cordis Corporation Three stage intracranial pressure relief valve having single-piece valve stem
US4560375A (en) * 1983-06-30 1985-12-24 Pudenz-Schulte Medical Research Corp. Flow control valve
US4568333A (en) * 1983-04-12 1986-02-04 Sawyer Philip Nicholas Valve arrangement especially suitable for preventing introduction of air into vascular systems
EP0156974A3 (en) * 1983-12-08 1986-06-11 Cordis Corporation Three-stage valve for the flow control of body fluids
US4634427A (en) * 1984-09-04 1987-01-06 American Hospital Supply Company Implantable demand medication delivery assembly
US4636194A (en) * 1983-06-30 1987-01-13 Pudenz-Schulte Medical Research Corp. Burr-hole flow control valve
EP0220431A1 (de) * 1985-09-05 1987-05-06 Fresenius AG Vorrichtung zur Einstellung eines Flusses einer Körperflüssigkeit eines Patienten
US4675003A (en) * 1985-12-23 1987-06-23 Cordis Corporation Three stage pressure regulator valve
US4676772A (en) * 1985-12-23 1987-06-30 Cordis Corporation Adjustable implantable valve having non-invasive position indicator
US4681559A (en) * 1985-12-23 1987-07-21 Cordis Corporation Plural valve three stage pressure relief system
US4714459A (en) * 1985-12-23 1987-12-22 Cordis Corporation Three stage intracranial pressure control valve
US4714458A (en) * 1985-12-23 1987-12-22 Cordis Corporation Three stage valve with flexible valve seat
US4722725A (en) * 1983-04-12 1988-02-02 Interface Biomedical Laboratories, Inc. Methods for preventing the introduction of air or fluid into the body of a patient
US4729762A (en) * 1985-12-23 1988-03-08 Cordis Corporation Three stage implantable pressure relief valve with adjustable valve stem members
EP0276356A1 (en) * 1987-01-29 1988-08-03 Pudenz-Schulte Medical Research Corporation Siphon control device
US4769002A (en) * 1983-02-17 1988-09-06 Cordis Corporation Intercranial pressure regulator valve
US4776838A (en) * 1983-12-08 1988-10-11 Cordis Corporation Three stage valve
US4776839A (en) * 1986-10-21 1988-10-11 Cordis Corporation Three stage implantable pressure relief valve with improved valve stem member
US4781672A (en) * 1986-10-21 1988-11-01 Cordis Corporation Three stage implantable flow control valve with improved valve closure member
US4787886A (en) * 1987-02-05 1988-11-29 Cosman Eric R Pressure sensor controlled valve
US4861331A (en) * 1988-03-24 1989-08-29 Pudenz-Schulte Medical Research Corp. Implantable shunt system and method of assembly
US4867741A (en) * 1983-11-04 1989-09-19 Portnoy Harold D Physiological draining system with differential pressure and compensating valves
US4867740A (en) * 1988-03-24 1989-09-19 Pudenz-Schulte Medical Research Corp. Multiple-membrane flow control valve and implantable shunt system
US4883461A (en) * 1987-05-15 1989-11-28 Interface Biomedical Laboratories Corp. Safety needle sheath in anti-reflux catheter having novel valve means
US4898583A (en) * 1988-05-18 1990-02-06 Baxter Healthcare Corporation Implantable patient-activated fluid delivery device and outlet valve therefor
US4898585A (en) * 1988-05-18 1990-02-06 Baxter Healthcare Corporation Implantable patient-activated fluid delivery device with bolus injection port
US4898584A (en) * 1988-05-18 1990-02-06 Baxter Healthcare Corporation Implantable patient-activated fluid delivery device
US4931039A (en) * 1988-10-21 1990-06-05 Baxter International Inc. Ventricular catheter introducer
US4950232A (en) * 1987-08-11 1990-08-21 Surelab Superior Research Laboratories Cerebrospinal fluid shunt system
US5147332A (en) * 1991-05-17 1992-09-15 C.R. Bard, Inc. Multi-valve catheter for improved reliability
US5160325A (en) * 1986-10-06 1992-11-03 C. R. Bard, Inc. Catheter with novel lumens shapes
WO1993020862A1 (en) * 1992-04-17 1993-10-28 Science Incorporated Liquid delivery apparatus
FR2721216A1 (fr) * 1994-06-21 1995-12-22 Bruno Chene Traitement de l'hydrocéphalie.
US5662600A (en) * 1995-09-29 1997-09-02 Pudenz-Schulte Medical Research Corporation Burr-hole flow control device
WO2002036193A1 (en) * 2000-10-30 2002-05-10 Technovobis Ab System and method for physiological drainage
US20040082900A1 (en) * 2002-02-23 2004-04-29 Luttich Edward H. Proportional control device for a hydrocephalus shunt
US20060111664A1 (en) * 2002-06-24 2006-05-25 Ilan Samson Breast pump
US7282040B2 (en) 2002-12-24 2007-10-16 Vygon Us, Llc Gravitational pressure regulating mechanism
WO2012125449A1 (en) * 2011-03-11 2012-09-20 Seaver Chad Systems and methods of controlling flow of bodily fluids
WO2013123021A1 (en) 2012-02-13 2013-08-22 Watson David A Improved shunt valve for controlling siphon effect
US20140236129A1 (en) * 2012-11-29 2014-08-21 Boehringer Laboratories Llc Gastric sizing systems including instruments for use in bariatric surgery
US8870809B2 (en) 2009-12-23 2014-10-28 Christoph Miethke Gmbh & Co Kg Implantable hydrocephalus shunt system
US9649481B2 (en) 2013-03-14 2017-05-16 Siddharth Sadanand Shunt flow monitor
US9662478B2 (en) 2010-03-19 2017-05-30 University Of Washington Body fluid drainage system
US10413710B2 (en) 2014-01-16 2019-09-17 University Of Washington Pressure reference assemblies for body fluid drainage systems and associated methods
US10932937B2 (en) 2012-11-29 2021-03-02 Boehringer Laboratories Llc Gastric sizing systems including instruments for use in bariatric surgery

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DE10046651A1 (de) * 2000-09-20 2002-04-04 Fresenius Medical Care De Gmbh Ventil
JP2020157059A (ja) * 2019-03-22 2020-10-01 川澄化学工業株式会社 灌流用チューブ

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US3503402A (en) * 1966-03-23 1970-03-31 Rudolf R Schulte Shunt device
US3601128A (en) * 1968-12-26 1971-08-24 Salomon Hakim Ventriculoatrial shunt accumulator

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US3111125A (en) * 1961-11-06 1963-11-19 Rudolf R Schulte Drainage device
US3492996A (en) * 1966-02-09 1970-02-03 Dow Corning Ventriculo-atrial shunt
US3503402A (en) * 1966-03-23 1970-03-31 Rudolf R Schulte Shunt device
US3601128A (en) * 1968-12-26 1971-08-24 Salomon Hakim Ventriculoatrial shunt accumulator

Cited By (83)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US3901245A (en) * 1973-03-15 1975-08-26 Bio Medical Res Ltd Bio-medical pressure control device
US3999553A (en) * 1973-03-15 1976-12-28 Bio-Medical Research, Ltd. Bio-medical pressure control device
US3991768A (en) * 1973-03-16 1976-11-16 Portnoy Harold D Shunt system resistant to overdrainage and siphoning and valve therefor
US3910283A (en) * 1973-10-09 1975-10-07 Harry H Leveen Process for treatment of ascites and device to accomplish same
US3889687A (en) * 1974-01-31 1975-06-17 Donald L Harris Shunt system for the transport of cerebrospinal fluid
US3894541A (en) * 1974-02-27 1975-07-15 El Shafei Ismail Lotfy Method of treating hydrocephalus
US3964484A (en) * 1975-03-03 1976-06-22 Sorenson Research Co., Inc. Antiocoagulant metering device and method
US4103689A (en) * 1976-12-13 1978-08-01 Stephen Beecher Leighton Tissue pressure reference for cerebrospinal fluid shunting device
US4364395A (en) * 1981-06-30 1982-12-21 American Heyer-Schulte Corporation Low profile shunt system
EP0068815A1 (en) * 1981-06-30 1983-01-05 BAXTER INTERNATIONAL INC. (a Delaware corporation) Low profile shunt system
US4464168A (en) * 1981-06-30 1984-08-07 American Hospital Supply Corporation Low profile shunt system
FR2539299A1 (fr) * 1983-01-14 1984-07-20 Descartes Paris V Universite R Dispositif de traitement de l'hydrocephalie avec filtre a impedance variable
EP0115973A1 (fr) * 1983-01-14 1984-08-15 Universite Rene Descartes, (Paris V) Dispositif de traitement de l'hydrocéphalie avec filtre à impédance variable
US4605395A (en) * 1983-01-14 1986-08-12 Universite Rene Descartes (Paris V) Hydrocephaly treatment device including a variable impedance filter
EP0117050A1 (en) * 1983-02-17 1984-08-29 Cordis Corporation Intercranial pressure regulator valve
US4540400A (en) * 1983-02-17 1985-09-10 Cordis Corporation Non-invasively adjustable valve
US4769002A (en) * 1983-02-17 1988-09-06 Cordis Corporation Intercranial pressure regulator valve
US4722725A (en) * 1983-04-12 1988-02-02 Interface Biomedical Laboratories, Inc. Methods for preventing the introduction of air or fluid into the body of a patient
US4568333A (en) * 1983-04-12 1986-02-04 Sawyer Philip Nicholas Valve arrangement especially suitable for preventing introduction of air into vascular systems
US4560375A (en) * 1983-06-30 1985-12-24 Pudenz-Schulte Medical Research Corp. Flow control valve
US4636194A (en) * 1983-06-30 1987-01-13 Pudenz-Schulte Medical Research Corp. Burr-hole flow control valve
US4552553A (en) * 1983-06-30 1985-11-12 Pudenz-Schulte Medical Research Corp. Flow control valve
US4867741A (en) * 1983-11-04 1989-09-19 Portnoy Harold D Physiological draining system with differential pressure and compensating valves
US4557721A (en) * 1983-11-29 1985-12-10 Cordis Corporation Servo valve
US4776838A (en) * 1983-12-08 1988-10-11 Cordis Corporation Three stage valve
EP0156974A3 (en) * 1983-12-08 1986-06-11 Cordis Corporation Three-stage valve for the flow control of body fluids
EP0163897A1 (en) * 1984-05-08 1985-12-11 Cordis Corporation Three stage intracranial pressure relief valve having single-piece valve stem
US4627832A (en) * 1984-05-08 1986-12-09 Cordis Corporation Three stage intracranial pressure relief valve having single-piece valve stem
US4634427A (en) * 1984-09-04 1987-01-06 American Hospital Supply Company Implantable demand medication delivery assembly
EP0220431A1 (de) * 1985-09-05 1987-05-06 Fresenius AG Vorrichtung zur Einstellung eines Flusses einer Körperflüssigkeit eines Patienten
US4681559A (en) * 1985-12-23 1987-07-21 Cordis Corporation Plural valve three stage pressure relief system
US4714458A (en) * 1985-12-23 1987-12-22 Cordis Corporation Three stage valve with flexible valve seat
US4729762A (en) * 1985-12-23 1988-03-08 Cordis Corporation Three stage implantable pressure relief valve with adjustable valve stem members
US4714459A (en) * 1985-12-23 1987-12-22 Cordis Corporation Three stage intracranial pressure control valve
US4676772A (en) * 1985-12-23 1987-06-30 Cordis Corporation Adjustable implantable valve having non-invasive position indicator
US4675003A (en) * 1985-12-23 1987-06-23 Cordis Corporation Three stage pressure regulator valve
US5160325A (en) * 1986-10-06 1992-11-03 C. R. Bard, Inc. Catheter with novel lumens shapes
US4776839A (en) * 1986-10-21 1988-10-11 Cordis Corporation Three stage implantable pressure relief valve with improved valve stem member
US4781672A (en) * 1986-10-21 1988-11-01 Cordis Corporation Three stage implantable flow control valve with improved valve closure member
US4795437A (en) * 1987-01-29 1989-01-03 Pudenz-Schulte Medical Research Corporation Siphon control device
EP0276356A1 (en) * 1987-01-29 1988-08-03 Pudenz-Schulte Medical Research Corporation Siphon control device
US4787886A (en) * 1987-02-05 1988-11-29 Cosman Eric R Pressure sensor controlled valve
US4883461A (en) * 1987-05-15 1989-11-28 Interface Biomedical Laboratories Corp. Safety needle sheath in anti-reflux catheter having novel valve means
US4950232A (en) * 1987-08-11 1990-08-21 Surelab Superior Research Laboratories Cerebrospinal fluid shunt system
US4867740A (en) * 1988-03-24 1989-09-19 Pudenz-Schulte Medical Research Corp. Multiple-membrane flow control valve and implantable shunt system
US4861331A (en) * 1988-03-24 1989-08-29 Pudenz-Schulte Medical Research Corp. Implantable shunt system and method of assembly
US4898583A (en) * 1988-05-18 1990-02-06 Baxter Healthcare Corporation Implantable patient-activated fluid delivery device and outlet valve therefor
US4898584A (en) * 1988-05-18 1990-02-06 Baxter Healthcare Corporation Implantable patient-activated fluid delivery device
US4898585A (en) * 1988-05-18 1990-02-06 Baxter Healthcare Corporation Implantable patient-activated fluid delivery device with bolus injection port
US4931039A (en) * 1988-10-21 1990-06-05 Baxter International Inc. Ventricular catheter introducer
US5147332A (en) * 1991-05-17 1992-09-15 C.R. Bard, Inc. Multi-valve catheter for improved reliability
WO1993020862A1 (en) * 1992-04-17 1993-10-28 Science Incorporated Liquid delivery apparatus
AU667377B2 (en) * 1992-04-17 1996-03-21 Science Incorporated Liquid delivery apparatus
FR2721216A1 (fr) * 1994-06-21 1995-12-22 Bruno Chene Traitement de l'hydrocéphalie.
US5662600A (en) * 1995-09-29 1997-09-02 Pudenz-Schulte Medical Research Corporation Burr-hole flow control device
US5800376A (en) * 1995-09-29 1998-09-01 Medtronic, Inc. Burr-hole flow control device
AU2002212884B2 (en) * 2000-10-30 2006-06-29 Technovobis Ab System and method for physiological drainage
US20040087887A1 (en) * 2000-10-30 2004-05-06 Nilsson Per Erik System and method for physiological drainage
WO2002036193A1 (en) * 2000-10-30 2002-05-10 Technovobis Ab System and method for physiological drainage
CN1299780C (zh) * 2000-10-30 2007-02-14 泰克诺沃比斯股份公司 用来进行生理引流的系统
US7476211B2 (en) 2000-10-30 2009-01-13 Technovobis Ab System and method for physiological drainage
US20040082900A1 (en) * 2002-02-23 2004-04-29 Luttich Edward H. Proportional control device for a hydrocephalus shunt
US20060111664A1 (en) * 2002-06-24 2006-05-25 Ilan Samson Breast pump
US7413557B2 (en) * 2002-06-24 2008-08-19 Ilan Sampson Breast pump
US7282040B2 (en) 2002-12-24 2007-10-16 Vygon Us, Llc Gravitational pressure regulating mechanism
US8870809B2 (en) 2009-12-23 2014-10-28 Christoph Miethke Gmbh & Co Kg Implantable hydrocephalus shunt system
US9662478B2 (en) 2010-03-19 2017-05-30 University Of Washington Body fluid drainage system
US11247030B2 (en) 2010-03-19 2022-02-15 University Of Washington Body fluid drainage system
US10166375B2 (en) 2010-03-19 2019-01-01 University Of Washington Body fluid drainage system
CN103561799A (zh) * 2011-03-11 2014-02-05 查德·西弗 控制体液流动的系统和方法
WO2012125449A1 (en) * 2011-03-11 2012-09-20 Seaver Chad Systems and methods of controlling flow of bodily fluids
CN103561799B (zh) * 2011-03-11 2016-03-30 查德·西弗 控制体液流动的系统和方法
US9393388B2 (en) 2011-03-11 2016-07-19 Arkis, Llc Systems and methods of controlling flow of bodily fluids
EP2838583A4 (en) * 2012-02-13 2016-03-09 David A Watson ENHANCED BYPASS VALVE TO REGULATE SIPHON EFFECT
WO2013123021A1 (en) 2012-02-13 2013-08-22 Watson David A Improved shunt valve for controlling siphon effect
US10646625B2 (en) * 2012-11-29 2020-05-12 Boehringer Laboratories, Inc. Gastric sizing systems including instruments for use in bariatric surgery
US10932937B2 (en) 2012-11-29 2021-03-02 Boehringer Laboratories Llc Gastric sizing systems including instruments for use in bariatric surgery
US20140236129A1 (en) * 2012-11-29 2014-08-21 Boehringer Laboratories Llc Gastric sizing systems including instruments for use in bariatric surgery
US11511030B2 (en) 2012-11-29 2022-11-29 Boehringer Laboratories Llc Gastric sizing systems including instruments and methods of bariatric surgery
US11857445B2 (en) 2012-11-29 2024-01-02 Boehringer Laboratories Llc Gastric sizing systems including instruments for use in bariatric surgery
US9649481B2 (en) 2013-03-14 2017-05-16 Siddharth Sadanand Shunt flow monitor
US10881841B2 (en) 2013-03-14 2021-01-05 Siddharth Sadanand Shunt flow monitor
US10413710B2 (en) 2014-01-16 2019-09-17 University Of Washington Pressure reference assemblies for body fluid drainage systems and associated methods

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