US3778369A - Hemodialyzer with tapered slit blood ports and baffles - Google Patents

Hemodialyzer with tapered slit blood ports and baffles Download PDF

Info

Publication number
US3778369A
US3778369A US00223270A US3778369DA US3778369A US 3778369 A US3778369 A US 3778369A US 00223270 A US00223270 A US 00223270A US 3778369D A US3778369D A US 3778369DA US 3778369 A US3778369 A US 3778369A
Authority
US
United States
Prior art keywords
tubes
blood
hemodialyzer
casing
baffles
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Expired - Lifetime
Application number
US00223270A
Other languages
English (en)
Inventor
F Markley
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
US Atomic Energy Commission (AEC)
Original Assignee
US Atomic Energy Commission (AEC)
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by US Atomic Energy Commission (AEC) filed Critical US Atomic Energy Commission (AEC)
Application granted granted Critical
Publication of US3778369A publication Critical patent/US3778369A/en
Anticipated expiration legal-status Critical
Expired - Lifetime legal-status Critical Current

Links

Images

Classifications

    • B—PERFORMING OPERATIONS; TRANSPORTING
    • B01—PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
    • B01D—SEPARATION
    • B01D63/00—Apparatus in general for separation processes using semi-permeable membranes
    • B01D63/06—Tubular membrane modules
    • B—PERFORMING OPERATIONS; TRANSPORTING
    • B01—PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
    • B01D—SEPARATION
    • B01D61/00—Processes of separation using semi-permeable membranes, e.g. dialysis, osmosis or ultrafiltration; Apparatus, accessories or auxiliary operations specially adapted therefor
    • B01D61/24—Dialysis ; Membrane extraction
    • B01D61/28—Apparatus therefor
    • B—PERFORMING OPERATIONS; TRANSPORTING
    • B01—PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
    • B01D—SEPARATION
    • B01D2313/00—Details relating to membrane modules or apparatus
    • B01D2313/08—Flow guidance means within the module or the apparatus
    • B01D2313/086—Meandering flow path over the membrane

Definitions

  • Baies are placed across the width of the tubes from one side wall of the casing forcing the blood to flow around the ba-les across the tubes a multiple number of times in passing through the hemodialyzer.
  • the baliles are made from epoxy resin strips placed across the width of each tube.
  • the new blood ports extend across the width of the side of the casing near its ends. The ports have an end adjacent the edge of the casing which defines an opening from the exterior of the hemodialyzer which leads to a tapered slit opening to the interior of the hemodialyzer, this slit tapering to a smaller width as the distance from the exterior opening increases and tapering to a close at the edge of the casing opposite the exterior opening.
  • This invention relates to an improved apparatus for use in the cleansing of impurities from the blood by hemodialysis.
  • Hemodialyzers commonly referred to as artificial kidneys have been used for many years to treat patients suifering from kidney malfunction or kidney disease. Recent development work on hemodialyzers has been directed toward increasing the eiciency of hemodialyzer units, lowering the expense involved in dialysis treatment, and making dialysis treatment available to more of those in need of such treatment.
  • the hemodialyzers presently being used fail to fully satisfy the needs of the vast number of kidney patients in several important respects.
  • Hemodialyzer machines presently used are expensive to produce and hence require a large initial investment for the basic machine and other associated equipment.
  • a blood pump is required because of the ilow resistance caused by the large size of the present machines, which size also often makes a blood transfusion necessary because of the loss of blood to the blood priming volume of the machine.
  • In-hospital treatment or the ⁇ presence of trained medical personnel is also necessary swellas the essential rebuilding of the hemodialyzer unit under sterile conditions following each hemodialyzer treatment. Partially resulting from these mentioned considerations, the costs of continuing hemodialysis treatment is prohibitive to many patients in need of such periodic treatment.
  • the number of hemodialyzer units available is also severely limited in relation to the vast number of those suiiering from kidney disorders.
  • a hemodialyzer which has a plurality of flattened semipermeable membrane tubes which are arranged in parallel in a stack within a rectangular casing.
  • the hemodialyzer has associated therewith means for passing dialysate iiuid uid through the hemodialyzer within the flattened tubes and means for passing blood through the hemodialyzer across the between the iiattened tubes.
  • the eiciency of the hemodialyzer is increased by incorporating one or more bales which extend from a side wall of the casing across the width of each of the flattened tubes and terminate at the edges of the tubes at a point just short of the opposite side wall of the casing.
  • Each blood port has an end adapted fornaking the appropriate connections and defining a blood inlet or outlet opening 3 BRIEF DESCRIPTION OF THE DRAWINGS
  • FIG. 1 is a longitudinal section of the hemodialyzer taken along the line 1-1 of FIG. 2.
  • FIG. 2 is an enlarged view taken along the line 2--2 of FIG. 1 with the tubes partially broken away to expose a feature of the blood ports of the hemodialyzer.
  • FIG. 3 is a transverse cross-sectional view taken along line 3-3 of FIG. 1.
  • FIG. 4 is a view taken along broken line 4-4 of FIG. l.
  • the two portions of the flattened tubes between the generally vflattened surfaces can be referred to as the two edges of the tubes, the parallel tubes being stacked so that the edges of the tubes are aligned to define the two sides of the stack of tubes.
  • the edges of the flattened tubes and the sides of the stack of tubes face the two sides of the casing 1.
  • a dialysate inlet 3 and a dialysate outlet 4 located on opposite ends of casing 1 and leading respectively to and from the interior of the hemodialyzer.
  • Dialysate duid, flowing through the inlet 3 has access to the interior of tubes 2 through the openings in the ends of the tubes 2 adjacent the inlet 3 but is prevented from flowing about the exterior of the tubes 2 by barrier 5 near the ends of the tubes 2 adjacent the inlet 3 which seals the tubes to each other and to the casing 1.
  • barrier 6 near the opposite ends of tubes 2 adjacent the outlet 4 prevents dialysate fluid, flowing from the interior of the tubes 2 through the openings in the ends of the tubes 2 adjacent the outlet 4, from flowing back about the exterior of the tubes 2.
  • Dialysate flow is seen to be from the inlet 3, through the interior of tubes 2, and to the outlet 4 from which it exits from the hemodialyzer.
  • a blood inlet port 7 and a blood outlet port 8 located on opposite sides and at opposite ends of casing 1.
  • the structure of the blood ports is described in more detail below.
  • the barriers 5 and 6 also serve to seal the blood from the ends of the tubes 2 and prevent intermingling of blood and dialysate fluid. Blood flow is therefore exterior to the allattend tubes 2 and in general is between the tubes 2 across their width.
  • the tubes 2 are of smaller length and width than the interior dimensions of the casing 1, leaving space on the sides and at the ends to permit distribution of the blood and dialysate fluids respectively.
  • One or more ballles extend across the width of the tubes to direct blood flow and consequently increase the efliciency of the hemodialyzer.
  • alternate baflles extend from opposite sides of the casing, the bales being equally spaced so as to divide the interior of the hemodialyzer into equal segments.
  • the two blood ports are located at opposite ends of the casing and are located on the same side of the casing if there are an odd number of baflles and on opposite sides of the casing if there are an even number of baflles, their relative location being determined by the number of baflles and the blood flow path around the baffles.
  • baflles 9 and 10 there are two such baflles 9 and 10 and the blood ports are located on opposite sides of the casing 1 as pictured in the drawings.
  • the first baille 9, located nearest the blood inlet 7 extends from the interior side wall 11 of the casing 1 on the same side of the casing 1 as the blood inlet 7.
  • Ballle 9 extends across the width of the flattened tubes 2 and terminates at the edges of the tubes 2 near to but not touching the opposite interior side wall 12 of the casing 1. As is more clearly seen from FIGS.
  • baille 9 comprises a narrow vertical band 13 along the height of one side of the stack of tubes at the edges of tubes 2 and a series of fingers 14 connected by and extending horizontally from band 13 across the width of the tubes 2 to the edges of the tubes opposite the band 13, one finger 14 extending between each two adjacent tubes 2 and also between the tubes 2 and the top and bottom of casing 1.
  • the narrow vertical band 13 fills the space between the edges of the tubes 2 and the interior side wall 11.
  • baille 9 extends from the interior side wall 11 between each of the tubes 2 and forces blood to flow across the tubes around its end at the end of its fingers 14 at the opposite edges of the tubes 2 adjacent the interior side wall 12.
  • the similar second baille 10 is located nearest the blood outlet 8 and extends from the opposite interior side wall 12 of the casing 1 on the same side of the casing 1 as the blood outlet 8. Batlle 10 extends from interior side wall 12 across the width of the flattened tubes 2, terminating at the edges of the tubes near to but not touching interior side wall 11. Blood is therefore forced to flow around baille 10 at its end at the edges of the tubes adjacent interior side wall 11.
  • Blood flow through the dialyzer is from the blood inlet 7 across the width of the tubes 2 around the end of baille 9 near the interior side wall 12 opposite blood inlet 7 and continues across the width of tubes 2 a second time around the end of baille 10 near the interior side wall 11 opposite the blood outlet 8 and across the tubes 2 a third time to the blood outlet 8.
  • the blood is thereby caused by the bales to flow across the width of the tubes three times rather than just once.
  • the blood ports both blood inlet port 7 and blood outlet port 8, are of identical structure and provide for better blood flow distribution in the dialyzer. Referring to FIG. 4 for a detailed description of the blood ports, it should be understood that the blood outlet port Sis identical in structure with the blood inlet port 7 and in fact the two are interchangeable, it being inconsequential which is connected as the inlet at the beginning of hemodialysis treatment.
  • a tubular conduit 20 is mounted transversely across a side of the casing 1 on the outside and near an end of the casing, conduit 20 being perpendicular to the flattened tubes 2 and extending along a side of the stack of tubes.
  • the tubular conduit 20 has one end 21 projecting beyond the edge of casing 1, which end is adapted for connection to tubing conducting the blood from the patients artery.
  • the end 21 of tubular conduit 20 defines an opening indicated at 22 which leads to the interior of the tubular conduit 20.
  • the tubular conduit 20 further has a tapered slit 23 along its length on one side thereof at its junction with the casing 1, tubular conduit 20 and casing 1 being sealed together at their junction. Tapered slit 23 is aligned with and opens to an identical tapered slit 24 in the casing 1, not seen in FIG. 4 but apparent in FIG. 2 where the tubes 2 have been partially broken away to reveal the slit 24.
  • Tapered slits 23 and 24 are widest at a point in the side of casing 1 adjacent opening 22 and tapered to a close at the edge of casing 1 opposite opening 22.
  • Blood entering tubular conduit '20 through opening 22 in end 21 passes from the interior of tubular conduit 20 to the interior of hemodialyzer casing 1 through the aligned tapered slits 23 and 24 which act to distribute the blood evenly along the height of the stack gf tubes 2 for better blood ilow distribution between all the tubes.
  • the circular opening blood tends to ilow through the spaces between the tubes immediately facing the opening rather than distribute along the entire stack.
  • the pressure and momentum of the blood passing into the port from the tubing from the patient tends to carry it past the first several openings between the tubes in the stack, causing more blood to ilow around the tubes in the stack further from the opening and less blood to ilow around the tubes adjacent the opening.
  • the eiciency of the hemodialyzer is also increased by the above-described bailles. Without batlles, blood ilowing through the hemodialyzer at any given ilow rate will cross the width of the tubes one time in passing through the hemodialyzer. With two bailles, as described above for the disclosed embodiment, blood flowing through the hemodialyzer at the same given total ilow rate will cross the width of the tubes three times in passing through the hemodialyzer. Since the blood ilow path is greater by a factor of three, the velocity of the blood across the tubes must also increase by a factor of three. This increase in velocity causes a mixing of the blood and improves dialysis eiliciency as the impurities throughout the blood are brought into contact with the membrane by the mixing action.
  • the blood With a low blood ilow velocity, the blood is in laminar ilow and impurities in the center of the blood stream must diffuse through the blood to the membrane surface in order to be removed from the blood.
  • the increased velocity disrupts the laminar ilow and causes mixing which carries the impurities directly to the surface of the membrane.
  • This increase in velocity of the blood has also beenfound to reduce the tendency of brin to deposit or settle out on the membrane surface which deposit not only increases the thickness of the layer through which the impurities must diiluse to pass from the blood but wln'ch also is the initial stages of undesirable and very dangerous blood clots.
  • the bailles are formed from a series of epoxy resin strips across the Width of each of the tubes, each of the epoxy resin strips sealed to the tube above and below the strip. These strips are joined to each other and sealed to one side wall of the casing by an epoxy band along the side of the stack of tubes, the strips extending only to the opposite edges of the tubes leaving space between the opposite edges of the tubes and the opposite side wall of the casing for blood ilow around the end of the baille.
  • the epoxy resin bailles are easily formed as the hemodialyzer is constructed by placing a strip of epoxy resin across the width of each tube as the tubes are arranged in the stack.
  • the hemodialyzer of the present invention has increased eiliciency in dialysis and improved blood flow distribution.
  • a hemodialyzer comprising: a rectangular casing containing a plurality of -attened semipermeable membrane tubes arranged in parallel in a stack therein; a dialysate inlet and a dialysate outlet located on opposite ends of said casing; means associated with said dialysate inlet and outlet for passing dialysate fluid through said hemodialyzer within said flattened tubes; a blood inlet port located on a side of the casing at one end thereof and a blood outlet port located on a side of the casing at the opposite end thereof; means associated with said blood inlet port and outlet port for passing blood through said hemodialyzer across and between said flattened tubes; and at least one baille extending from a side wall of said casing across the width of each 0f the ilattened tubes and terminating at the edges of the tubes near to but not touching the opposite side wall of the casing, each such bafle being formed by a series of epoxy resin strips extending from a side wall of the casing across the width of each
  • a hemodialyzer wherein a plurality of flattened semipermeable membrane tubes are arranged in parallel in a stack and wherein the dialysate lflows within the tubes while the blood flows across and between the flattened tubes transverse to the dialysate
  • the improvement therein comprising: two battles extending from the opposite side walls of the hemodialyzer across the width of each of the flattened tubes and terminating at the edges of the tubes near to but not touching the opposite side wall of the hemodialyzer, each such bale being formed from epoxy resin strips extending from one side wall of the hemodialyzer across the width of each of the :attened tubes, said strips being sealed together and sealed to a side wall of the casing by an epoxy resin band between said side wall and the edges of the tubes on the side of the stack of tubes adjacent said side wall, whereby the blood owing through the hemodialyzer must flow around the battles and across the ilattened tubes a multiple number of times.
  • a method of forming a bull in a hemodialyzer which contains a plurality of ilattened semipermeable membrane tubes arranged in parallel in a stack within a casing, comprising: placing a strip of epoxy resin across the width of each tube as the tubes are arranged in the stack, said epoxy resin strips aligned with each other in the stack; joining together said aligned epoxy resin strips by placing an epoxy resin strip along one edge of the stack of tubes; lling the space between the epoxy resin strips along the edge of the stack and the hemodialyzer casing with a band of epoxy resin; and curing the epoxy resin to hardness.

Landscapes

  • Chemical & Material Sciences (AREA)
  • Chemical Kinetics & Catalysis (AREA)
  • Health & Medical Sciences (AREA)
  • Urology & Nephrology (AREA)
  • Engineering & Computer Science (AREA)
  • Water Supply & Treatment (AREA)
  • External Artificial Organs (AREA)
  • Separation Using Semi-Permeable Membranes (AREA)
US00223270A 1972-02-03 1972-02-03 Hemodialyzer with tapered slit blood ports and baffles Expired - Lifetime US3778369A (en)

Applications Claiming Priority (1)

Application Number Priority Date Filing Date Title
US22327072A 1972-02-03 1972-02-03

Publications (1)

Publication Number Publication Date
US3778369A true US3778369A (en) 1973-12-11

Family

ID=22835782

Family Applications (1)

Application Number Title Priority Date Filing Date
US00223270A Expired - Lifetime US3778369A (en) 1972-02-03 1972-02-03 Hemodialyzer with tapered slit blood ports and baffles

Country Status (11)

Country Link
US (1) US3778369A (enrdf_load_stackoverflow)
JP (1) JPS5217680B2 (enrdf_load_stackoverflow)
AU (1) AU470383B2 (enrdf_load_stackoverflow)
BE (1) BE784557A (enrdf_load_stackoverflow)
CA (1) CA961775A (enrdf_load_stackoverflow)
CH (1) CH540697A (enrdf_load_stackoverflow)
DE (1) DE2232938A1 (enrdf_load_stackoverflow)
FR (1) FR2171043B1 (enrdf_load_stackoverflow)
GB (1) GB1331896A (enrdf_load_stackoverflow)
IT (1) IT956072B (enrdf_load_stackoverflow)
SE (1) SE398709B (enrdf_load_stackoverflow)

Cited By (8)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4033878A (en) * 1975-05-12 1977-07-05 Universal Oil Products Company Spiral wound membrane module for direct osmosis separations
US4038191A (en) * 1975-10-14 1977-07-26 Davis Harold R Manifold for ultra filtration machine
US4124509A (en) * 1976-04-21 1978-11-07 Asahi Medical Co., Ltd. Haemodialyzer employing hollow fibers
US4202776A (en) * 1975-07-28 1980-05-13 Nippon Zeon Co., Ltd. Hollow-fiber permeability apparatus
US4225439A (en) * 1977-10-17 1980-09-30 Gambro Dialysatoren Gmbh & Co. Kg Apparatus for selective separation of matter through semi-permeable membranes
US4278542A (en) * 1977-10-19 1981-07-14 Medical Development S.A. Method for manufacturing multi-layer hemodialyzers and improved multi-layer hemodialyzer obtained thereby
WO1981002705A1 (en) * 1980-03-24 1981-10-01 Baxter Travenol Lab Forming diffusion membrane units with joined capillary membrane tubes
US5391163A (en) * 1992-01-31 1995-02-21 Inpaco Corporation Pouch for administering medical fluids

Families Citing this family (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JPS5595743U (enrdf_load_stackoverflow) * 1974-01-18 1980-07-03
US4219426A (en) * 1976-03-19 1980-08-26 Organon Teknika B.V. Dialysis device
DE2833966A1 (de) * 1977-08-08 1979-02-22 Us Energy Haemodialysator
US4212742A (en) * 1978-05-25 1980-07-15 United States Of America Filtration apparatus for separating blood cell-containing liquid suspensions
DE2836192C2 (de) * 1978-08-18 1983-12-22 Fresenius AG, 6380 Bad Homburg Verfahren zur Herstellung eines Dialysators
DE2847945C2 (de) * 1978-11-04 1984-01-12 Fresenius AG, 6380 Bad Homburg Künstliche Niere und Verfahren zu ihrer Herstellung

Family Cites Families (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US3019853A (en) * 1958-06-30 1962-02-06 Bell Telephone Labor Inc Separation of gases by diffusion
US3370710A (en) * 1966-05-11 1968-02-27 Research Corp Compact blood dialyzer with a pleated membrane therein
NL163125C (nl) * 1967-02-13 1980-08-15 Cordis Dow Corp Semipermeabel membraansamenstel.
US3522885A (en) * 1968-04-18 1970-08-04 Atomic Energy Commission Parallel flow hemodialyzer
US3547271A (en) * 1968-06-04 1970-12-15 Miles Lowell Edwards Membrane fluid diffusion exchange device
US3565258A (en) * 1969-06-06 1971-02-23 Atomic Energy Commission Parallel flow hemodialyzer

Cited By (9)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4033878A (en) * 1975-05-12 1977-07-05 Universal Oil Products Company Spiral wound membrane module for direct osmosis separations
US4202776A (en) * 1975-07-28 1980-05-13 Nippon Zeon Co., Ltd. Hollow-fiber permeability apparatus
US4038191A (en) * 1975-10-14 1977-07-26 Davis Harold R Manifold for ultra filtration machine
US4124509A (en) * 1976-04-21 1978-11-07 Asahi Medical Co., Ltd. Haemodialyzer employing hollow fibers
US4225439A (en) * 1977-10-17 1980-09-30 Gambro Dialysatoren Gmbh & Co. Kg Apparatus for selective separation of matter through semi-permeable membranes
US4278542A (en) * 1977-10-19 1981-07-14 Medical Development S.A. Method for manufacturing multi-layer hemodialyzers and improved multi-layer hemodialyzer obtained thereby
WO1981002705A1 (en) * 1980-03-24 1981-10-01 Baxter Travenol Lab Forming diffusion membrane units with joined capillary membrane tubes
US4346006A (en) * 1980-03-24 1982-08-24 Baxter Travenol Laboratories, Inc. Diffusion membrane units with adhered semipermeable capillaries
US5391163A (en) * 1992-01-31 1995-02-21 Inpaco Corporation Pouch for administering medical fluids

Also Published As

Publication number Publication date
IT956072B (it) 1973-10-10
JPS4887698A (enrdf_load_stackoverflow) 1973-11-17
SE398709B (sv) 1978-01-16
FR2171043B1 (enrdf_load_stackoverflow) 1977-12-23
AU4314972A (en) 1973-12-13
DE2232938A1 (de) 1973-08-09
FR2171043A1 (enrdf_load_stackoverflow) 1973-09-21
GB1331896A (en) 1973-09-26
CH540697A (de) 1973-08-31
AU470383B2 (en) 1973-12-13
BE784557A (fr) 1972-10-02
CA961775A (en) 1975-01-28
JPS5217680B2 (enrdf_load_stackoverflow) 1977-05-17

Similar Documents

Publication Publication Date Title
US3778369A (en) Hemodialyzer with tapered slit blood ports and baffles
US3522885A (en) Parallel flow hemodialyzer
US3743098A (en) Spiral mass transfer device with low flow resistance and fluid volume
US3728256A (en) Crossflow capillary dialyzer
US4038191A (en) Manifold for ultra filtration machine
EP1741458B1 (de) Vorrichtung zur Behandlung von Blut in einem extrakorporalen Blutkreislauf
GB1363794A (en) Compact dialyzer
JPH06509733A (ja) 体外における血液酸素化のための装置及び方法
ES456859A1 (es) Perfeccionamientos aportados a la construccion de filtros para sangre y similares.
US10124105B2 (en) Device for the extracorporeal oxygenation of the blood of a patient
EP1397196A1 (en) Hemodialyzer headers
US3660280A (en) Dialysis apparatus
US3682817A (en) Dialyzer
DE3923692A1 (de) Medizinisches geraet fuer den stoff- und/oder waermeaustausch
CA1122536A (en) Twin pack hemodialyzer
DE2632044C3 (de) Vorrichtung zur Diffusion von Substanzen zwischen zwei Flüssigkeiten
US3510004A (en) Artificial kidney
GB1282338A (en) Parallel flow hemodialyzer
CN116942940A (zh) 一种双滤式血液净化透析装置
CN207270524U (zh) 一种可快速过滤的医用血液过滤装置
CN208864911U (zh) 一种新型防感染的血液透析器
EP0369418A2 (en) Hemofilter
GB2010121A (en) Device for treating renal insufficiency
CN221906514U (zh) 去除内毒素的中空纤维过滤装置
CN208711060U (zh) 临床中药煎煮用的药液浓缩装置