US20100089807A1 - Dialysis machine - Google Patents
Dialysis machine Download PDFInfo
- Publication number
- US20100089807A1 US20100089807A1 US12/460,427 US46042709A US2010089807A1 US 20100089807 A1 US20100089807 A1 US 20100089807A1 US 46042709 A US46042709 A US 46042709A US 2010089807 A1 US2010089807 A1 US 2010089807A1
- Authority
- US
- United States
- Prior art keywords
- pump
- cartridge
- dialysate
- blood
- flow
- 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.)
- Abandoned
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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
- A61M1/00—Suction or pumping devices for medical purposes; Devices for carrying-off, for treatment of, or for carrying-over, body-liquids; Drainage systems
- A61M1/14—Dialysis systems; Artificial kidneys; Blood oxygenators ; Reciprocating systems for treatment of body fluids, e.g. single needle systems for hemofiltration or pheresis
- A61M1/16—Dialysis systems; Artificial kidneys; Blood oxygenators ; Reciprocating systems for treatment of body fluids, e.g. single needle systems for hemofiltration or pheresis with membranes
- A61M1/1692—Detection of blood traces in dialysate
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- A61M1/00—Suction or pumping devices for medical purposes; Devices for carrying-off, for treatment of, or for carrying-over, body-liquids; Drainage systems
- A61M1/14—Dialysis systems; Artificial kidneys; Blood oxygenators ; Reciprocating systems for treatment of body fluids, e.g. single needle systems for hemofiltration or pheresis
- A61M1/16—Dialysis systems; Artificial kidneys; Blood oxygenators ; Reciprocating systems for treatment of body fluids, e.g. single needle systems for hemofiltration or pheresis with membranes
- A61M1/1694—Dialysis systems; Artificial kidneys; Blood oxygenators ; Reciprocating systems for treatment of body fluids, e.g. single needle systems for hemofiltration or pheresis with membranes with recirculating dialysing liquid
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- A61M1/15—Dialysis systems; Artificial kidneys; Blood oxygenators ; Reciprocating systems for treatment of body fluids, e.g. single needle systems for hemofiltration or pheresis with a cassette forming partially or totally the flow circuit for the treating fluid, e.g. the dialysate fluid circuit or the treating gas circuit
- A61M1/152—Details related to the interface between cassette and machine
- A61M1/1524—Details related to the interface between cassette and machine the interface providing means for actuating on functional elements of the cassette, e.g. plungers
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- A61M1/154—Dialysis systems; Artificial kidneys; Blood oxygenators ; Reciprocating systems for treatment of body fluids, e.g. single needle systems for hemofiltration or pheresis with a cassette forming partially or totally the flow circuit for the treating fluid, e.g. the dialysate fluid circuit or the treating gas circuit with sensing means or components thereof
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- A61M1/155—Dialysis systems; Artificial kidneys; Blood oxygenators ; Reciprocating systems for treatment of body fluids, e.g. single needle systems for hemofiltration or pheresis with a cassette forming partially or totally the flow circuit for the treating fluid, e.g. the dialysate fluid circuit or the treating gas circuit with treatment-fluid pumping means or components thereof
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- A61M1/156—Constructional details of the cassette, e.g. specific details on material or shape
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- A61M1/1696—Dialysis systems; Artificial kidneys; Blood oxygenators ; Reciprocating systems for treatment of body fluids, e.g. single needle systems for hemofiltration or pheresis with membranes with recirculating dialysing liquid with dialysate regeneration
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- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M2205/00—General characteristics of the apparatus
- A61M2205/12—General characteristics of the apparatus with interchangeable cassettes forming partially or totally the fluid circuit
- A61M2205/128—General characteristics of the apparatus with interchangeable cassettes forming partially or totally the fluid circuit with incorporated valves
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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
- A61M2205/00—General characteristics of the apparatus
- A61M2205/33—Controlling, regulating or measuring
- A61M2205/3306—Optical measuring means
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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
- A61M2205/00—General characteristics of the apparatus
- A61M2205/33—Controlling, regulating or measuring
- A61M2205/3331—Pressure; Flow
- A61M2205/3334—Measuring or controlling the flow rate
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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
- A61M2205/00—General characteristics of the apparatus
- A61M2205/33—Controlling, regulating or measuring
- A61M2205/3375—Acoustical, e.g. ultrasonic, measuring means
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
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- A61M2205/00—General characteristics of the apparatus
- A61M2205/33—Controlling, regulating or measuring
- A61M2205/3379—Masses, volumes, levels of fluids in reservoirs, flow rates
- A61M2205/3382—Upper level detectors
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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
- A61M2205/00—General characteristics of the apparatus
- A61M2205/33—Controlling, regulating or measuring
- A61M2205/3379—Masses, volumes, levels of fluids in reservoirs, flow rates
- A61M2205/3386—Low level detectors
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- B—PERFORMING OPERATIONS; TRANSPORTING
- B01—PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
- B01D—SEPARATION
- B01D2313/00—Details relating to membrane modules or apparatus
- B01D2313/44—Cartridge types
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Abstract
A disposable cartridge for use in a hemodialysis machine has a blood flowpath for carrying a volume of blood to be treated in a dialyseer and a dialysate flowpath, isolated from the blood flowpath, for delivering a flow of dislysate solution through the dialyser. The cartridge is received in an engine section of the machine. The engine section has first and second platens which close when the cartridge is inserted to retain the cartridge. Actuators and sensors arranged on the second platen control operation of the cartridge.
Description
- This application is a continuation of U.S. application Ser. No. 11/919,694, filed Oct. 31, 2007, which in turn is a U.S. national stage application of International Application No. PCT/GB2006/001668 with an International filing date of May 8, 2006 and a priority date of May 6, 2005.
- The present invention relates to dialysis machines and in particular, but not exclusively, to a disposable cartridge for use in hemodialysis machine.
- Dialysis is a treatment which replaces the renal function of removing excess fluid and waste products, such as potassium and urea, from blood. The treatment is either employed when renal function has deteriorated to an extent that uremic syndrome becomes a threat to the body's physiology (acute renal failure) or, when a longstanding renal condition impairs the performance of the kidneys (chronic renal failure).
- There are two major types of dialysis, namely hemodialysis and peritoneal dialysis.
- In peritoneal dialysis treatment, a dialysate solution is run through a tube into the peritoneal cavity. The fluid is left in the cavity for a period of time in order to absorb the waste products, and is subsequently removed through the tube for disposal.
- It is common for patients in the early stages of treatment for a longstanding renal condition to be treated by peritoneal dialysis before progressing to hemodialysis at a later stage.
- In hemodialysis, the patient's blood is removed from the body by an arterial line, is treated by the dialysis machine, and is then returned to the body by a venous line. The machine passes the blood through a dialyser containing tubes formed from a semipermeable membrane. On the exterior of the: semipermeable membrane is a dialysate solution. The semipermeable membrane filters the waste products and excess fluid from the blood into the dialysate solution. The membrane allows the waste and a controlled volume of fluid to permeate into the dialysate whilst preventing the loss of larger more desirable molecules, like blood cells and certain proteins and polypeptides.
- The action of dialysis across the membrane is achieved primarily by a combination of diffusion (the migration of molecules by random motion from a region of higher concentration to a region of lower concentration), and convection (solute movement that results from bulk movement of solvent,’ usually in response to differences in hydrostatic pressure).
- Fluid removal (otherwise known as ultrafiltration) is achieved by altering the hydrostatic pressure of the dialysate side of the membrane, causing free water to move across the membrane along the pressure gradient.
- The correction of uremic acidosis of the blood is achieved by use of a bicarbonate buffer. The bicarbonate buffer also allows the correction of the blood bicarbonate level.
- The dialysis solution consists of a sterilized solution of mineral ions. These ions are contained within an acid buffer which is mixed with the serilised water and bicarbonate base prior to delivery to the dialyser.
- Dialysate composition is critical to successful dialysis treatment since the level of dialytic exchange across the membrane, and thus the possibility to restore adequate body electrolytic concentrations and acid-base equilibrium, depends on the composition.
- The correct composition is accomplished primarily by formulating a dialysate whose constituent concentrations are set to approximate normal values in the body.
- However, achieving the correct composition of dialysate requires the accurate control of low volumes of liquid and at present this is achieved by the provision of complex fluid paths, including multiple pumping and valving components on the dialysis machine.
- This presents the disadvantage of a complex and costly dialysis machine which is at increased risk of failure by virtue of its complexity. Increased maintenance is also a problem since it is essential to minimize machine downtime in order to most efficiently treat the patient.
- A further problem with known hemodialysis machines is that the blood and dialysate solution lines require careful mounting onto the dialysis machine before the treatment can commence. This presents a risk that the lines are not correctly installed, a risk which is particularly relevant to those patients who dialyse at home.
- This method of dialysis also presents an increased risk of cross-infection between patients since the disposable blood and dialysate lines come into contact with the dialysis machine.
- It is an object of the present invention to provide a hemodialysis system which at least mitigates some of the problems described above.
- According to a first aspect of the invention there is provided a disposable cartridge for use in a hemodialysis machine, the cartridge comprising a blood flowpath for carrying a recirculating volume of blood to be treated in a dialyser and a dialysate flowpath, isolated from the blood flowpath, for delivering a flow of dialysate solution through the dialyser.
- Preferably, the cartridge has a first mixing pump and a second mixing pump, the second mixing pump accepting a homogoneous mix of sterile water and a first dialysate solution base from the first mixing pump and introducing a further dialysate solution base.
- Preferably, the dialysate pathway includes a first three-way valve upstream of the first dialysate solution mixing pump, the first three-way valve controlling delivery of the first dialysate solution base into the first mixing pump.
- Preferably, the first three-way valve has a mixing pump outlet port, a dialysate solution reservoir inlet port and a positive displacement pump port.
- Preferably, the first three-way valve acts to permit a volume of a first dialysate solution base into the first dialysate solution mixing pump on each and every stroke of the pump.
- Preferably, the dialysate pathway includes a second three-way valve upstream of the second dialysate solution mixing pump.
- Preferably, the cartridge includes a dialysate solution reservoir, more preferably a first reservoir immediately downstream of the first mixing pump and a second reservoir immediately downstream of the second mixing pump.
- Preferably, the blood and dialysate fluid pathways pass between a first outwardly facing surface of the cartridge and a second outwardly facing surface of the cartridge.
- Preferably, at least some parts of the first and second outwardly facing surfaces of the cartridge body are covered with a deformable membrane.
- Preferably, the valves and pumps on the cartridge are actuable by deformation of the membrane by the dialysis machine.
- Preferably, the blood and dialysate solution fluid pathways are at least partially defined by upwardly standing walls projecting outwardly from the upper and lower surfaces of the cartridge.
- Preferably, the upstanding walls are enclosed by the deformable membranes.
- Preferably, the mixing pumps are membrane pumps.
- Preferably, the blood flow path is provided with at least one blood bubble trap, more preferably, the or each blood bubble trap is provided with a level sensor.
- Preferably, the level sensor is an optical level sensor, or an ultrasonic level sensor.
- Preferably, the blood bubble trap is provided with an upper and a lower level sensor.
- Preferably, the blood bubble trap is provided with a hydrophilic membrane for removing or adding a volume of air to the blood bubble trap.
- Preferably, the cartridge is provided with a positive displacement pump plunger acting in combination with the three-way valve to deliver a measured volume of dialysate solution base into the dialysate solution mixing pumps.
- Preferably, the cartridge is provided with an endotoxin filter, preferably a single use endotoxin filter.
- Preferably, the dialysate solution fluid pathway is provided with an ultra-sonic flow sensor for detecting the flow rate through the dialysate solution path.
- Preferably, the cartridge defines a series of apertures interlinking the portion of fluid pathways defined on the upper surface of the cartridge with the portion of fluid pathways defined on the lower surface of the cartridge.
- According to a second aspect of the invention there is provided adialysis machine adapted to receive the dialysis cartridge of the first aspect of the invention, the machine including at least one platen arranged in use to hold the cartridge in position on the machine.
- The invention will now be described, by way of example only, and with reference to the following drawings, in which:
-
FIG. 1 is an isometric view of the dialysis machine and cartridge of the current invention, -
FIG. 2 is an isometric view of the engine portion of the machine ofFIG. 1 , -
FIG. 3 is an isometric view of the cartridge of the present invention, -
FIG. 4 is a front view of the cartridge ofFIG. 3 , -
FIG. 5 is a front view of the pumping portion of the cartridge ofFIG. 3 showing partial hidden detail, -
FIG. 6 is a front view of the cartridge ofFIG. 3 showing the dialyser cover removed, -
FIG. 7 is a rear view of the pumping portion of the cartridge ofFIG. 3 , -
FIG. 8 is a top view of the cartridge ofFIG. 3 , -
FIG. 9 is an end view of the cartridge ofFIG. 3 , and -
FIG. 10 is a schematic representation of a dialysate solution base delivery system according to the present invention. - In
FIG. 1 a dialysis machine 1 is shown having acover 2 which opens to reveal astorage compartment 3. The machine has anengine section 4 which receives adialysis cartridge 10. - Referring now to
FIG. 2 , theengine section 4 is shown in further detail to include first andsecond platens cartridge 10 into the machine to retain the cartridge in position in use. Theengine 4 haspneumatic actuators 7 and sensors (indicated generally at 8 inFIG. 2 ) arranged on the second platen to control operation of thecartridge 10 as will be described in further detail shortly. - In
FIGS. 3 and 4 adialysis cartridge 10 is shown having a pumping portion 12 (to the right of dashed line I-1 inFIG. 4 ) and a dialysis portion 14 (to the left of dashed line I-I inFIG. 4 ). The pumpingportion 12 has the form of a fiat rectangle. Thedialysis portion 14 has adialyser cover 15 which is shaped so as to contain a dialyser as will be described in further detail shortly. - Referring briefly to
FIG. 8 , the pumpingportion 12 of thedialysis cartridge 10 has anupper surface 16 and alower surface 18. Theupper surface 16 and alower surface 18 are covered by adear membrane upper surface 16 and alower surface 18, respectively by way of adhesive or similar known method. - Referring now to
FIG. 4 , theupper surface 16 defines a series of upstanding walls indicated, for example, as 24. Theupstanding walls 24 define a system of flow channels as will be described in further detail shortly. The channels are enclosed at the outermost part of theupper surface 16, by thefirst membrane 20. Accordingly, theupper surface 16 defines a series of fluid channels for carrying either the blood to be dialysed, or the Dialysate solution. - The
cartridge 10 also defines the series of apertures, indicated generally for example at 26 inFIG. 4 . These apertures provide a fluid pathway through thecartridge 10, the purpose of which will now be described. - Referring to
FIG. 7 , thelower surface 18 also defines a series ofupstanding walls 24, which collectively define a labyrinth of fluid channels enclosed by thesecond membrane 22. - In combination therefore the
upper surface 16,lower surface 18 and the first andsecond membranes portion 12. This labyrinth of fluid flowing pathways will now be described in further detail. - The
first membrane 20 is bonded to theupper surface 16, and similarly thesecond membrane 22 bonded to thelower surface 18, so as to contain the fluids within their respective channels. - The
dialyser cartridge 10 defines two primary fluid pathways, firstly, a flow path for blood and secondly a flow path for the dialysate solution. The blood pathway is formed as follows. - The patient's blood enters the
dialysis cartridge 10 via anarterial port 28. The blood then passes from theupper surface 16 to thelower surface 18 via anarterial port aperture 30 where it is then carried by anarterial port channel 32 from thearterial aperture 30 to an arterialblood bubble trap 34. The arterialblood bubble trap 34 has aninlet lip 36 for directing the incoming blood towards the bottom of the trap. Arranged at the bottom of the trap is a bloodbubble trap exit 38 which carries the blood from the arterialblood bubble trap 34 to an arterial bloodbubble trap aperture 40 viachannel 42. - The purpose of the arterial
blood bubble trap 34 is to remove from the arterial blood supply any gas bubbles which may be contained therein. Gas bubbles may impair the performance of dialyser, and furthermore, present a risk to the patient if they were reintroduced back into the body via the venous blood line. Theblood bubble trap 34 is also provided with an upperlevel sensor port 44 and a lower level sensor port 46. Thelevel sensor ports 44, 46 are arranged to coincide with corresponding optical level sensors arranged on the dialysis machine. Accordingly, the level sensors are able to optically interrogate the arterialblood bubble trap 34 so as to ensure that the level in the blood bubble trap is above the level of the lower level sensor port 46 and below the level of the upperlevel sensor port 44. It is important to ensure that the blood level remains between these two levels so that there always remains a volume of air in the blood level trap into which any gas bubbles carried in the blood can migrate. - Having passed through the arterial blood
bubble trap aperture 40 the blood is carried on theupper surface 16 to a blood pump inlet valve 48 (seeFIG. 4 ). - Referring to
FIG. 4 , the bloodpump inlet valve 48 is operable between a closed condition and an open condition as follows. Thevalve 48 has an outer annularupstanding wall 50 and an inner annularupstanding wall 52. Arranged inwardly of the inner upstandingannular wall 52 is avalve aperture 54. The inner upstandingannular wall 52 is recessed from the outer upstandingannual wall 50 in a direction towards thecartridge 10. Arranged between the inner and outer upstandingannual wall sector aperture 56 which acts as an outlet from thevalve 48. Accordingly, thevalve 48 has a valve inlet in the form ofvalve aperture 54 and an outlet in the form of thesector aperture 56. As discussed previously, thelower surface 18 has its outer service covered by adeformable membrane 22. Thedeformable membrane 22 rests against the outwardly facing surface of the outer upstandingannular wall 50 where the valve is in the un-actuated, open state. In order to change the condition of thevalve 48 from the open state to the closed state, the dialysis machine applies a positive pressure to the exterior surface of thesecond membrane 22 in order to drive the inner surface of the membrane on to the outwardly facing surface of the inner upstandingannular wall 50. This doses the inlet to the valve thereby preventing flow through the valve. - With the blood
pump inlet valve 48 in the open state, the blood flows through the arterial bloodbubble trap aperture 40 over the inner upwardly standingwall 50 and through thesector aperture 56 so as to exit the bloodpump inlet valve 48. From thesector aperture 56 the blood then flows down a bloodpump inlet channel 58 and into ablood pump 60 via ablood pump inlet 62. - The blood pump is defined by a dome shaped
pump cavity 64 into which theblood pump inlet 62 opens. Arranged at the centre of thepump chamber 64 is apump outlet 66. The outer edge of thepump chamber 64 is defiled by an annularupstanding wall 68, the outwardly facing surface of which is in contact with the inner surface of thesecond membrane 22. A volume of blood is drawn into thepump chamber 64, through the open bloodpump inlet valve 48 as follows. - The dialysis machine generates a negative pressure on the outside surface of the
second membrane 22 in order to deform the membrane outwardly away from thelower surface 18. With thepump chamber 64 full, and the pump at full stroke, the bloodpump inlet valve 48 is closed by the dialysis machine generating positive pressure on the outside surface of thesecond membrane 22 in order to dose thevalve aperture 54. Thepump chamber 64 is then evacuated by the dialysis machine applying a positive pressure to the outside surface of thesecond membrane 22 in order to drive the blood contained within thepump chamber 64 through thepump outlet 66. Thepump outlet 66 is in fluid communication with a bloodpump outlet valve 70 which is identical in form to the bloodpump inlet valve 48. It follows that with the blood pump inlet valve closed, and theblood pump 60 being driven by the dialysis machine to evacuate thepump 64, the bloodpump outlet valve 70 is in an open state in order to permit the flow of blood past thevalve 70 and through a blood pumpoutlet valve aperture 72. - Accordingly, the
blood pump 60 is in combination with the bloodpump inlet valve 48 and the bloodpump outlet valve 70. Specifically, the bloodpump inlet valve 48 opens when the blood pump is in the expansion stroke in order to admit blood into the pump chamber, whilst the bloodpump outlet valve 70 remains closed in order to prevent back-flow of blood through the system. Theinlet valve 48 then closes at the same time as theoutlet valve 70 is opened in order to allow the compression stroke of the flow pump to drive the blood from thepump chamber 64 and through the blood pumpoutlet valve aperture 72. - From the
aperture 72, the blood then flows through apressure sensor chamber 74. As the blood flows through thechamber 74, the fluid pressure causes a force to be applied to thefirst membrane 20 which in turn causes a deflection in the membrane. This deflection is detected by a sensor provided in the dialysis machine and this measured deflection is calibrated to generate a blood pressure reading for within the cartridge. - From the
pressure sensor chamber 74 the blood then passes through adialyser blood port 76. - Referring now to
FIG. 6 , the blood flows from thedialyser blood port 66 down adialyser blood line 78 and into the bottom end of adialyser 80 of known design. Thedialyser 80 contains multiple axially extending semi-permeable tubes through which the blood passes. Upon exiting thedialyser 80 the blood travels down a dialyserreturn blood line 82 before passing into a venousblood bubble trap 86 via a dialyserblood return Port 84. - The venous
blood bubble trap 86 is similar in design to the arterialblood bubble trap 34 in that it has aninlet lip 88, anoptical level sensor 90 and ahydrophilic membrane 94 to allow the hydrolysis machine withdraw or administer a volume of air to or from the bubble trap in order to maintain a constant blood level within the bubble trap. The venousblood level trap 86 is further provided with anultrasonic level sensor 92 the design of which will be described in further detail shortly. At the bottom end of the valve trap is athrombus filter 96 for trapping blood dots within the bubble trap. The Thrombus filter may be of conical form as in known thrombus filters or may be wedge shaped. Having passed through thethrombus filter 96, the blood passes through an ultrasonicflow rate sensor 98 which will be described in further detail shortly. The blood is then returned to the patient via avenous port 100. - The blood therefore completes its passage through the
dialysis cartridge 10 from thearterial port 28 through the arterialblood bubble trap 34, the bloodpump inlet valve 48 and into theblood pump 60. Fromblood pump 60 the blood is driven past the bloodpump outlet valve 70 and into thedialyser 80 via the crossmembrane pressure sensor 74. Upon exit from thedialyser 80, the blood is returned to thedialysis cartridge 10 via the dialyserblood return port 84. Upon exit from theport 84 the blood enters the venousblood bubble trap 86, passes through thethrombus filter 96 andflow sensor 98 before being returned to the patient via thevenous port 100. - A
syringe 71 is provided which introduces a volume of an anti-coagulant drug such as heparin into the blood line between the bloodpump outlet valve 70 and thedialyser 80. The syringe plunger 73 is driven by the machine engine as shown inFIG. 2 . - As described above, dialysis occurs across a semi-permeable membrane, in this instance the semi-permeable tubes provided within the
dialyser 80. As described, the blood flows through the centre of the semi-permeable tubes and it therefore follow that the dialysate solution flows in the space within thedialyser 80 between the tubes. The mixing of the dialysate solution on the cartridge at the correct concentration will now be described in detail. - The
pump portion 12 defines the dialysate flow path in addition to the blood flow path as described above. - Accordingly, the
dialysis cartridge 10 provides for the mixing into a sterile water supply of a small volume of concentrated bicarbonate solution and a small volume of acid solution. The resulting dialysate solution is pumped from the pumping portion to deliver the solution to the dialyser. The cartridge further allows for the accurate sensing of dialysate solution concentration, dialysate flow rate and dialysate pressure. - Sterile water enters the
dialysis cartridge 10 via asterile water inlet 102. The sterile water is then mixed with a controlled volume of bicarbonate solution base as follows. Thecartridge 10 defines achamber 104, for receiving the plunger of a positive displacement pump (not shown for clarity inFIGS. 3 to 9 ). The pump acts in combination with a three-way valve 106 of known design. The pump and three-way valve 106 are operated by the dialysis machine to micro-dose a controlled volume of bicarbonate solution into abicarbonate pump 108. Thebicarbonate pump 108 is of similar design to theblood pump 60 with the exception that thebicarbonate pump 108 is additionally provided with aninlet 110 from the three-way valve 106. Thebicarbonate pump 108 is controlled in exactly the same manner to theflow pump 60 in order to draw a volume of sterile water through the sterile port at 102 and past abicarbonate inlet pump 112 whilst a bicarbonatepump outlet valve 114 remains closed. At the same time as a volume of sterile water is drawn into the pump a small volume of saturated bicarbonate solution is injected into thebicarbonate pump 108 by a positive displacement pump. The body of the positive displacement pump is defined by the cartridge body. The saturated bicarbonate solution is drawn from a reservoir on the dialysis machine. The solution is delivered to the pump via abicarbonate inlet channel 105 and three-way valve 106. - The action of drawing the water into the pump chamber by means of applying a negative pressure to the outer surface of the
first membrane 20 generates a turbulent flow within the pump chamber which causes the sterile water and bicarbonate solution to be mixed thoroughly within the pump chamber. Accordingly, at the point where the bicarbonatepump inlet valve 112 is closed, and theoutlet valve 114 opens in order to drive a solution from the pump chamber, a thorough homogoneous mixing has been achieved. - The bicarbonate and water solution is pumped out of the pump chamber via a
pump exit 116 from which it flows past thepump outlet valve 114 and into a water-bicarbonate solution reservoir 118. The volume of the water-bicarbonate reservoir 118 is approximately four times the volume of the bicarbonate pump chamber and performs two functions. Firstly, it further ensures that the mixture is homogenous, and secondly acts as a fluid buffer within the dialysate solution flow path, the purpose of which will be described in further detail shortly. - The
bicarbonate solution reservoir 118 is provided with aconductivity sensing probe 120 and atemperature sensing probe 122, anupper level sensor 124 and alower level sensor 126. - The conductivity and temperature sensor probes are provided to contact with conductivity and temperature sensors in the dialysis machine. The measurements are used to deduce the concentration of the water-bicarbonate solution in the
reservoir 118. The resevoir also acts as buffer to allow for the various system pumps being out of phase. Accordingly, the level in the resevoir is able to rise and fall thereby averaging out pressure spikes in the system. - From the water-
bicarbonate resevoir 118, the solution is drawn into anacid pump 128 past an open acidpump inlet valve 130. Coupled to theacid pump 128 is an acidpump outlet valve 132. The purpose of theacid pump 128 is to introduce a small volume of acid solution base into the water-bicarbonate solution. This process is achieved using the same valuing and pumping methodology as employed for thebicarbonate pump 108. Specifically, asecond chamber 107 is provided for receiving the plunger of a second positive displacement pump. A volume of acid solution base is thereby dispensed down aacid inlet channel 109 to a second 3-way valve 111. Under the action of thepump 128, water-bicarbonate solution is drawn into the pump chamber. The the acid solution base is injected into the pump by a second positive displacement pump. The fluids are thoroughly mixed in the turbulent flow within the pump chamber before being dispensed passed theoutlet valve 132 into a water-bicarbonate-acid reservoir 138. - The water-bicarbonate-
acid reservoir 138 is provided with aconductivity sensing probe 144 and atemperature sensing probe 146, anupper level sensor 140 and alower level sensor 142, in common with the water-bicarbonate reservoir 118. - From the water-bicarbonate-
acid reservoir 138, the solution flows through a resevoir exit 147 (seeFIG. 7 ) into a flowbalance inlet channel 148. The solution is thereby delivered to theflow balancer 150. - The purpose of the
flow balancer 150 is to ensure that the volume of dialysate solution pumped into the dialyser is the same as that withdrawn from thedialyser 80. The purpose of matching the flow into and out of the dialyser is to match the osmotic potential of the dialysate solution within the dialyser to the osmotic potential of the blood. This ensures that the volume of the fluid removed from the blood, or transferred to the blood, can be carefully controlled. This is critical to ensuring that the patient is not hydrated or dehydrated to a dangerous extent during the dialysis treatment. - The
flow balancer 150 is provided with a firstflow balance pump 152 and a secondflow balance pump 154. The first and second flow balance pumps 152,154 have a similar mode of operation to theblood pump 60, and the mixing pumps 108, 128. However, the flow path for delivering fluid to each of the flow balance pumps 152, 154 is rather more complex due to the way in which theflow balancer 150 achieves the controlled fluid flow input and output from thedialyser 80. - In principal, the
flow balancer 150 operates by using the firstflow balance pump 152 to pump dialysate solution into the dialyser, and the secondflow balance pump 154 to withdraw the dialysate solution from the dialyser, for a period of time, before switching the secondflow balance pump 154 to pump dialysate solution into the dialyser, and the firstflow balance pump 152 withdrawing dialysate solution from the dialyser. The purpose of this mode of operation is to eliminate the effect of manufacturing tolerances in generating a mismatch in the volume of the pump chamber in each of the flow balance pumps 152, 154. For example, were the firstflow balance pump 152 used permanently to pump dialysate solution into the dialyser, and the secondflow balance pump 154 used to withdraw dialysate solution from the dialyser, then over a period of time even the very small discrepency in the pump chamber volume of the pumps would lead to a dangerous imbalance in the volume of dialysate solution being pumped into, and withdrawn from, the dialyser. - By switching the first and second flow balance pumps 152,154, any errors in the chamber volume are averaged over time, thereby ensuring a balance in the flow across the dialyser.
- In selective fluid communication with the first
flow balance pump 152 are a first flow balance pumpfirst inlet valve 156, a first flow balance pumpsecond inlet valve 158, a first flow balance pumpfirst outlet valve 160 and a first flow balance pump second outlet valve 162. Similarly, in selectable fluid communication with the secondflow balance pump 154 are a second flow balance pumpfirst inlet valve 164, a second flow balance pumpsecond inlet valve 166, a second flow balance pumpfirst outlet valve 168 and a second flow balance pumpsecond outlet valve 170. - The first mode of operation of the
flow balancer 150 will now be described in detail. In the first mode of operation, the first flow balance pumpfirst inlet valve 156, first flow balance pump second outlet valve 162, second flow balance pumpsecond inlet valve 166 and second flow balance pumpfirst outlet valve 168 are all held in the closed position by the dialysis machine applying a positive pressure to the outside surface of thefirst membrane 20 in the region of each of the valves. Accordingly, the first mode of operation the secondflow balance pump 154 is operated to pump dialysate solution into the dialyser, and the firstflow balance pump 152 is operated to withdraw dialysate solution from the dialyser. - With the first flow balance pump
first inlet valve 156 in the closed position, dialysate solution passing out of thebicarbonate acid reservoir 138 flows past the first flow balance pumpfirst inlet valve 156 along a flowbalance inlet channel 148. The dialysate solution then passes from thelower surface 18 toupper surface 16 via anaperture 172. With the second flow balance pumpfirst inlet valve 164 in its open position, the secondflow balance pump 154 is able to draw a volume of dialysate solution into the pump chamber under the action of the dialysis machine generating a negative pressure on the outward facing surface of thefirst membrane 20. - As soon as the second
flow balance pump 154 is at full capacity, the second flow balance pumpfirst inlet valve 164 is closed, and the second flow balance pumpsecond outlet valve 170 is opened. Thepump 154 is then actuated to discharge the dialysate solution through anaperture 174 and the dialysate solution then flows alongchannel 176 as shown inFIG. 10 . The dialysate solution then passes through anendotoxin filter 178 before passing through adialyser output port 180 viachannel 182. - Referring now to
FIG. 6 , from thedialysate outlet port 180, dialysate solution passes along adialysate inlet pipe 180 before passing along thedialyser 80 from top to bottom as shown inFIG. 9 . In order to return the dialysate solution from thedialyser 80 to the pumpingportion 12, adialysate outlet pipe 184 carries dialysate solution to adialysate inlet port 186. Upon return to the pumpingportion 12, the dialysate solution passes through acolour sensor portion 188 in order to allow a colour sensor arranged on the dialysis machine to interrogate the dialysate solution to detect for blood leakage into the dialysate solution within thedialyser 80. On exit from thecolour sensor portion 188, the dialysate solution passes throughaperture 190 and from there into a flowbalance return channel 192. - Since the second flow balance pump
second inlet valve 166 is closed, the dialysate solution flowspast aperture 194 towards the first flow balance pumpsecond inlet valve 158. With thevalve 158 in the open position, the firstflow balance pump 152 is able to draw in to the pump chamber a volume of dialysate solution through theinlet valve 158 under the action of a positive pressure generating by the dialysis machine on the outwardly facing surface of the-first membrane 20. The first flow balance pumpsecond inlet valve 158 then doses, the first flow balance pumpfirst outlet valve 160 opens, and thepump 152 drives the dialysate solution from the fluid chamber through theoutlet valve 160. Theoutlet valve 160 is then closed, theinlet valve 158 opened and thepump 152 driven to draw in a further volume of dialysate solution ready for dispensing in the next pump cycle. - Having been delivered past the
outlet valve 160, the dialysate solution flows throughaperture 196 since the second flow balance pumpfirst outlet valve 168 is closed during the mode of operation. The dialysate solution then passes through anultrasonic flow sensor 198 which will be described in further detail shortly, before exiting thedialysis cartridge 10 by way ofdialysate solution drain 200. - In the second mode of operation, the roles of the first and second flow balance pumps 152, 154 are reversed. In other words, the first flow balance pump
second inlet valve 158 and first flow balance pumpfirst outlet valve 160 are held closed whilst thefirst inlet valve 156 and second outlet valve 162 are operated to control the flow of Dialysate solution into and out for the valve chamber. Similarly, with reference to the secondflow balance pump 154, the second flow balance pumpfirst inlet valve 164 and second flow balance pumpsecond outlet valve 170 are held in a closed position whilst the second flow balance pumpsecond inlet valve 166 and second flow balance pump andfirst outlet valve 168 are operated to control the flow of the acid solution into and out of the pump chamber. - The technique of flow balancing, as described above, is provided to ensure that exactly the same volume of dialysate solution is pumped into the
dialyser 80 as is removed from it. However, in certain dialysis treatments there is a requirement to either remove excess fluid from the blood, or to transfer fluid back into the blood. This is achieved by the process of ultra-filtration in which the flow balance circuit is placed slightly out of balance by either introducing or removing a small volume of liquid to or from the diayslate solution. In the dialysis cartridge of the present invention this is achieved by an ultra-filtration three-way valve 206 which acts in combination with a positive displacement pump received inchamber 208 on the cartridge. This combination of three-way valve and positive displacement pump is identical to that used to introduce the bicarbonate solution into thebicarbonate pump 108. The positive displacement pump plunger is received within thechamber 208 and is positioned by a drive, for example a stepper motor, on the dialysis machine. - The
cartridge 10 has adrainage channel 202 for draining excess fluid from the water-bicarbonate reservoir 118 and the water-bicarbonate-acid reservoir 138. The drainage channel carries excess fluid from thereservoirs drainage port 204 which is in fluid communication with a drainage port in the dialysis machine. - Accordingly, the
dialysis cartridge 10 provides two distinct flow paths, firstly for blood, and secondly for dialysate solution. The provision of anupper surface 16 and alower surface 18, with apertures therebetween allows the transfer of fluid from the outwardly facing surface of the upper surface to be on the facing surface of the lower surface. The blood flow path and the dialysate solution flow path are maintained discrete from one another by upstanding walls extending from the upper surface and lower surface. The outer surface of the upstanding walls abuts a deformable membrane in order to seal the flow path. - It will be appreciated that the apertures provided in the first and
second cartridge bodies - In an alternative embodiment of cartridge, the arterial
blood bubble trap 34 and venousblood bubble trap 86 have a collapsible element in the form of a concertina section of plastic material so as to limit the area of blood/air interface. This is particularly advantageous in that the reduced blood/air interface reduces the risk of clotting and/or separation of the blood. - A further alternative feature of the bubble trap is to replace the
hydrophilic membrane 94 with a membrane pump similar to theblood pump 60. Accordingly, instead of air being added or removed to the bubble trap by way of the transfer of air across the hydrophilic membrane, the transfer of air can be achieved by the displacement of the membrane by the application of either a positive or negative pressure on the outwardly facing surface of the membrane. Furthermore, the extent of actuation of the membrane could be monitored in order to detect where an excessive volume of air is either being added to the reservoir or removed from the reservoir. - In a further alternative embodiment, each of the valves, for example 48, 106, 112, 114, 164 etc are provided with rigid disks which have the diameter equal to or slightly greater than the diameter of the inner upwardly standing wall. The rigid disk is arranged between the inner upwardly standing wall and the membrane. The purpose of the rigid disc is to minimise the deformation required in the membrane in order to seal the valve. In other words, the membrane acts on the rigid disc which in turn forms a valve seat on the inner upwardly standing wall. The result of the reduced deformation of the membrane is that the transient shock waves generated in the valve by virtue of the switching between open and closed is reduced since the valve is closed at a lower peak pressure than would be necessary if the rigid disc were not present. A further benefit in addition to the reduction in pressure spiking observed in the valve body is the reduced blood damage achieved by smoother operation of the valve between its open and closed state.
- Referring now to
FIG. 10 , the positive displacement pump and three-way valve on the current invention are shown schematically in further detail. The three-way valve is indicated generally at 106. It will be appreciated that the three-way valve 106 is identical to the valve in communication with thepump 128 and theultra-filtration valve 206. The detailed description of three-way valve 106 therefore applies equally to the other two three-way valves provided on the dialysis cartridge. - The
bicarbonate mixing pump 108 is connected via a fluid line to anoutput 250 of the three-way valve 106. The three-way valve also has areservoir inlet 252 and apump inlet 254. Thereservoir inlet 252 is connected to abicarbonate solution reservoir 255. Thereservoir 255 is provided on the dialysis machine, or attached thereto, and does not form part of the cartridge itself. The positive displacement pump is indicated generally at 258. The positive displacement pump includes apneumatic cylinder 260 which drives apiston arm 262 in a reciprocating manner. At the opposite end of the piston arm to the piston cylinder is aplunger 264 which acts within the cartridge chamber 104 (seeFIG. 10 ). - On the return stroke indicated at A in
FIG. 10 , theplunger 264 is moved within thechamber 104 to draw in to the chamber a measured volume of dialysate solution from thebicarbonate solution reservoir 255. This transfer of fluid is achieved by the closure of the three-way valve output 250, with the reservoir inlet and pumpinlet piston arm 262 is withdrawn in direction A until anabutment 268 provided on thepiston arm 262 comes into contact with amoveable end stop 270. - Upon the
abutment 268 hitting themoveable end stop 270, thepneumatic cylinder 268 is driven in direction B in order to dispense the dialysate solution from thechamber 104 into thebicarbonate mixing pump 108. This transfer of fluids is achieved by the closure of thereservoir inlet 252, and the opening of the three-way valve output 250. Thepneumatic cylinder 260 drives thepiston ring 264 in direction B until the piston ring abuts the extreme left hand end of thechamber 104. Accordingly, by reciprocating the movement of thecylinder piston arm 262 in a known manner, a quantity of bicarbonate solution is repeatedly dispensed into thebicarbonate mixing pump 108. Furthermore, by adjusting the position of theremovable end stop 270, the volume of fluid dispensed can be accurately set. Themoveable end stop 270 is positioned by a stepper motor or similar accurate positioning drive system. - The advantage of this system is that the
pneumatic cylinder 260 provides the speed of the reciprocating movement required to deliver discrete volumes of fluid into the mixingpump 108 at the required rate. A stepper motor which is extremely accurate but not able to provide the speed reciprocation required, is therefore only used to set the dispense volume of fluid by positioning the moveable end-stop accurately. - It will be appreciated that the
bicarbonate mixing pump 108, three-way valve 106, andchamber 104 are provided on the cartridge. However, the remainder of the components described in respect ofFIG. 10 is provided on the dialysis machine. Importantly therefore, the pneumatic cylinder, stepper motor and moveable lens stop are provided on the machine, not the cartridge. - It will be appreciated that the cartridge of the current invention provides the significant advantage of delivering a homogenous mix of dialysis solution on each and every stroke of the first and second flow balance pumps 152, 154. This feature is critical to delivering a stable dialysis treatment. Furthermore, all of the fluid pathways, pumps and valves required to achieve a homogenous mix are arranged on the cartridge itself. This provides significant advantage since the cartridge contains all of the fluid pathways.
- It is conceivable within the scope of the invention that where the provision of a membrane is not necessary to contain flow within a channel, it is conceivable within the scope of invention that such a section of membrane could be removed from the
dialysis cartridge 10 following the application of the membrane sheet on to the outwardly facing surface of the cartridge. - Additionally, it is conceivable within the scope of invention that certain sections of flow channel may be strengthened for example, by the thickening of the upwardly standing walls, in order to reduce any flexing in the flow channels resulting from the varied hydrostatic pressure in the fluids.
Claims (30)
1-30. (canceled)
31. A disposable cartridge for use in a hemodialysis machine, the cartridge comprising a blood flowpath for carrying a volume of blood to be treated in a dialyser and a dialysate flowpath, isolated from the blood flowpath, for delivering a flow of dialysate solution through the dialyser.
32. The disposable cartridge of claim 31 , wherein in use the dialysate flowpath forms part of a recirculating dialysate loop including the dialyser and a regenerative filter.
33. The disposable cartridge of claim 31 , wherein in use the dialysate flowpath forms part of a continuous dialysate line including a sterile water supply inlet from the hemodialysis machine, the dialyser and a waste fluid outlet, said waste fluid outlet downstream of the dialyser.
34. The disposable cartridge of claim 33 , wherein the cartridge includes the dialyser or is adapted to be attachable to the dialyser.
35. The disposable cartridge of claim 33 , wherein the cartridge fully encloses the blood flowpath and the dialysate flowpath.
36. The disposable cartridge of claim 33 , wherein the cartridge comprises a rigid body.
37. The disposable cartridge of claim 36 , wherein the rigid body has a first outwardly facing surface and a second outwardly facing surface, each of the outwardly facing surfaces being enclosed by a deformable membrane.
38. The disposable cartridge of claim 37 , wherein the first and second outwardly facing surfaces collectively define a blood flow channel and a dialysate flow channel, the deformable membranes enclosing the flow channels to form the blood flowpath and the dialysate flowpath.
39. The disposable cartridge of claim 38 , wherein at least part of the blood flowpath is formed on each of the first and second outwardly facing surfaces.
40. The disposable cartridge of claim 39 , wherein at least part of the dialysate flowpath is formed on each of the first and second outwardly facing surfaces.
41. The disposable cartridge of of claim 37 , wherein, in use, the rigid body is held in place in the hemodialysis machine by at least one moveable platen which engages one of the first or second outwardly facing surfaces.
42. The disposable cartridge claim 41 , wherein the dialysate flow path includes a sterile water inlet to admit sterile water onto the cartridge from the hemodialysis machine.
43. The disposable cartridge of claim 42 , wherein the dialysate flow path includes a first mixing pump having a pump chamber for receiving a predetermined volume of sterile water, and a dispenser for dispensing into the pump chamber a predetermined volume of a first dialysate solution base, the first mixing pump operable to form and pump the resulting homogeneous mixture of sterile water and first dialysate solution base out of the pump chamber.
44. The disposable cartridge of claim 43 , wherein the dialysate flow path includes a second mixing pump downstream of the first mixing pump, the second mixing pump having a second pump chamber for receiving a predetermined volume of the mix of sterile water and first dialysate solution base from the first mixing pump, the dialysate flow path further including a dispenser for dispensing into the second pump chamber a predetermined volume of a second dialysate solution base, the second mixing pump operable to pump the resulting dialysate solution of sterile water and first and second dialysate solution bases out of the second pump chamber.
45. The disposable cartridge of claim 43 , wherein the first dialysate solution base is a bicarbonate solution.
46. The disposable cartridge of claim 44 , wherein the second dialysate solution base is one of an acid and acetate solution.
47. The disposable cartridge of claim 44 , wherein the operation of each of the first and second mixing pumps is achieved by displacement of the deformable membrane by way of pneumatic actuation.
48. The disposable cartridge of claim 43 , wherein operation of the first mixing pump is such that the predetermined volume of first dialysate solution base is delivered into the pump chamber at the same time as the pump is actuated to draw into the pump chamber a volume of sterile water such that every stroke of the pump delivers a homogoneous mix of sterile water and first dialysate solution base.
49. The disposable cartridge of claim 44 , wherein operation of the second mixing pump is such that the predetermined volume of the second dialysate solution base is delivered into the pump chamber at the same time as the pump is actuated to draw into the pump chamber a volume of homogoneous mix of sterile water and first dialysate solution base such that every stroke of the second mixing pump delivers a homogoneous dialysate solution.
50. The disposable cartridge of claim 31 , wherein the cartridge includes a flow balancer for achieving a balance of dialysate solution flow volume observed at the dialyser inlet and at the dialyser outlet outlet over the course of a treatment.
51. The disposable cartridge of claim 50 , wherein the flow balancer comprises a first flow balance pump and a second flow balance pump, the balance pumps operable between two modes of operation, a first mode of operation in which the first flow balance pump is arranged in a dialysate line, said first flow balance pump downstream of the first and second mixing pumps and upstream of the dialyser and the second flow balance pump is arranged in said dialysate line, said second flow balance pump downstream of the dialyser, and a second mode of operation in which the second flow balance pump is arranged in the dialysate line, said second flow balance pump downstream of the first and second mixing pumps and upstream of the dialyser and the first flow balance pump is arranged in the dialysate line, said first flow balance pump downstream of the dialyser.
52. The disposable cartridge of claim 43 , wherein the cartridge includes a delivery pump for delivering heparin into the blood flowpath.
53. A hemodialysis machine adapted to receive the dialysis cartridge of claim 31 , the machine including at least one platen arranged in use to hold the cartridge in position on the machine.
54. The hemodialysis machine of claim 53 , wherein the at least one platen includes one or more level sensors arranged to sense the level of fluid on the cartridge.
55. The hemodialysis machine of claim 53 , wherein the at least one platen includes one or more pressure sensors arranged to sense the fluid pressure on the cartridge.
56. The hemodialysis machine of claim 53 , wherein the at least one platen includes one or more flow sensors arranged to sense the flow rate of one or more fluids on the cartridge.
57. The hemodialysis machine of claim 53 , wherein the at least one platen includes one or more colour sensors arranged to detect blood leaks on the cartridge.
58. The hemodialysis machine of claim 53 , wherein the at least one platen includes one or more conductivity sensors, each sensor arranged to measure the concentration of the dialysate solution within the cartridge.
59. The hemodialysis machine of claim 53 , wherein the machine comprises a pair of platens which come together in use to hold the cartridge in position.
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US13/488,830 US8685244B2 (en) | 2005-05-06 | 2012-06-05 | Dialysis machine |
US14/195,601 US20140251885A1 (en) | 2005-05-06 | 2014-03-03 | Dialysis Machine |
US15/604,491 US20170252498A1 (en) | 2005-05-06 | 2017-05-24 | Dialysis machine |
US15/782,501 US10456516B2 (en) | 2005-05-06 | 2017-10-12 | Dialysis machine |
US16/666,326 US20200268958A1 (en) | 2005-05-06 | 2019-10-28 | Dialysis machine |
US17/478,569 US20220001087A1 (en) | 2005-05-06 | 2021-09-17 | Dialysis machine |
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US12/460,427 US20100089807A1 (en) | 2006-05-08 | 2009-07-17 | Dialysis machine |
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US13/488,830 Continuation US8685244B2 (en) | 2005-05-06 | 2012-06-05 | Dialysis machine |
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US14/195,601 Abandoned US20140251885A1 (en) | 2005-05-06 | 2014-03-03 | Dialysis Machine |
US15/604,491 Abandoned US20170252498A1 (en) | 2005-05-06 | 2017-05-24 | Dialysis machine |
US15/782,501 Active US10456516B2 (en) | 2005-05-06 | 2017-10-12 | Dialysis machine |
US16/666,326 Abandoned US20200268958A1 (en) | 2005-05-06 | 2019-10-28 | Dialysis machine |
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US14/195,601 Abandoned US20140251885A1 (en) | 2005-05-06 | 2014-03-03 | Dialysis Machine |
US15/604,491 Abandoned US20170252498A1 (en) | 2005-05-06 | 2017-05-24 | Dialysis machine |
US15/782,501 Active US10456516B2 (en) | 2005-05-06 | 2017-10-12 | Dialysis machine |
US16/666,326 Abandoned US20200268958A1 (en) | 2005-05-06 | 2019-10-28 | Dialysis machine |
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Cited By (14)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
ITBO20110224A1 (en) * | 2011-04-26 | 2012-10-27 | Bellco Srl | GROUP FOR MONITORING A CASSETTE OF A DIALYSIS MACHINE |
WO2013110906A1 (en) * | 2012-01-26 | 2013-08-01 | Quanta Fluid Solutions Ltd. | Dialysis machine |
WO2014011543A3 (en) * | 2012-07-10 | 2014-05-22 | Lifeline Scientific, Inc. | Perfusion apparatus with reduced pressure fluctuations, and bubble trap |
US20150343133A1 (en) * | 2014-04-29 | 2015-12-03 | Michael Edward HOGARD | Dialysis system and methods |
WO2020086540A1 (en) * | 2018-10-25 | 2020-04-30 | Diality Inc. | Dual reservoir hemodialysis system |
US10881775B2 (en) | 2015-10-28 | 2021-01-05 | Quanta Dialysis Technologies Ltd. | Dialysis machine and ultrafiltration |
USD907211S1 (en) | 2017-09-28 | 2021-01-05 | Quanta Dialysis Technologies Ltd. | Dialysis machine |
US11365728B2 (en) | 2017-02-24 | 2022-06-21 | Quanta Dialysis Technologies Ltd. | Testing rotor engagement of a rotary peristaltic pump |
US11534537B2 (en) | 2016-08-19 | 2022-12-27 | Outset Medical, Inc. | Peritoneal dialysis system and methods |
US11571499B2 (en) | 2015-12-30 | 2023-02-07 | Quanta Dialysis Technologies Ltd. | Dialysis machine |
US11583618B2 (en) | 2014-06-02 | 2023-02-21 | Quanta Dialysis Technologies Limited | Method of heat sanitization of a haemodialysis water circuit using a calculated dose |
US11660382B2 (en) | 2016-12-23 | 2023-05-30 | Quanta Dialysis Technologies Limited | Valve leak detection system |
US11724013B2 (en) | 2010-06-07 | 2023-08-15 | Outset Medical, Inc. | Fluid purification system |
USRE49881E1 (en) | 2013-03-28 | 2024-03-26 | Quanta Fluid Solutions Ltd. | Re-use of a hemodialysis cartridge |
Families Citing this family (6)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US8114276B2 (en) | 2007-10-24 | 2012-02-14 | Baxter International Inc. | Personal hemodialysis system |
PE20161123A1 (en) | 2014-02-27 | 2016-11-23 | Easydial Inc | PORTABLE HEMODIALYSIS MACHINE AND DISPOSABLE CARTRIDGE |
US10172989B2 (en) | 2014-09-12 | 2019-01-08 | Easydial Inc. | Portable hemodialysis machine and disposable cartridge with blood leak sensor |
US10980929B2 (en) | 2014-09-12 | 2021-04-20 | Diality Inc. | Hemodialysis system with ultrafiltration controller |
US10912875B2 (en) | 2014-10-09 | 2021-02-09 | Fresenius Medical Care Holdings, Inc. | Sensing negative pressure with a pressure transducer |
JP7387644B2 (en) * | 2018-05-17 | 2023-11-28 | ガンブロ・ルンディア・エービー | Processing apparatus and method with level control of gas separation devices |
Citations (5)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US3744762A (en) * | 1970-09-19 | 1973-07-10 | Alfa Laval Bergedorfer Eisen | Homogenizing method and apparatus |
US4161264A (en) * | 1977-06-17 | 1979-07-17 | Johnson Bryan E | Fluid metering and mixing device having inlet and outlet valves |
US5421823A (en) * | 1993-03-03 | 1995-06-06 | Deka Products Limited Partnership | Peritoneal dialysis methods that emulate gravity flow |
US20040206703A1 (en) * | 1999-11-02 | 2004-10-21 | Gambro Hospal (Schweiz) Ag | Method and a device for preparing a medical liquid |
US20050020961A1 (en) * | 2001-05-24 | 2005-01-27 | Burbank Jeffrey H. | Fluid processing systems and methods using extracorporeal fluid flow panels oriented within a cartridge |
Family Cites Families (4)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US3774762A (en) | 1971-01-20 | 1973-11-27 | E Lichtenstein | Analogue fluid flow programming structures |
CS248305B1 (en) | 1984-06-18 | 1987-02-12 | Miroslav Skala | Blood cleaning instrument |
US5591344A (en) * | 1995-02-13 | 1997-01-07 | Aksys, Ltd. | Hot water disinfection of dialysis machines, including the extracorporeal circuit thereof |
DE10224750A1 (en) | 2002-06-04 | 2003-12-24 | Fresenius Medical Care De Gmbh | Device for the treatment of a medical fluid |
-
2009
- 2009-07-17 US US12/460,427 patent/US20100089807A1/en not_active Abandoned
-
2012
- 2012-06-05 US US13/488,830 patent/US8685244B2/en active Active
-
2014
- 2014-03-03 US US14/195,601 patent/US20140251885A1/en not_active Abandoned
-
2017
- 2017-05-24 US US15/604,491 patent/US20170252498A1/en not_active Abandoned
- 2017-10-12 US US15/782,501 patent/US10456516B2/en active Active
-
2019
- 2019-10-28 US US16/666,326 patent/US20200268958A1/en not_active Abandoned
Patent Citations (5)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US3744762A (en) * | 1970-09-19 | 1973-07-10 | Alfa Laval Bergedorfer Eisen | Homogenizing method and apparatus |
US4161264A (en) * | 1977-06-17 | 1979-07-17 | Johnson Bryan E | Fluid metering and mixing device having inlet and outlet valves |
US5421823A (en) * | 1993-03-03 | 1995-06-06 | Deka Products Limited Partnership | Peritoneal dialysis methods that emulate gravity flow |
US20040206703A1 (en) * | 1999-11-02 | 2004-10-21 | Gambro Hospal (Schweiz) Ag | Method and a device for preparing a medical liquid |
US20050020961A1 (en) * | 2001-05-24 | 2005-01-27 | Burbank Jeffrey H. | Fluid processing systems and methods using extracorporeal fluid flow panels oriented within a cartridge |
Cited By (24)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US11724013B2 (en) | 2010-06-07 | 2023-08-15 | Outset Medical, Inc. | Fluid purification system |
EP2517741A3 (en) * | 2011-04-26 | 2013-04-03 | Bellco S.r.l. | An assembly for monitoring a cassette of a dialysis machine |
ITBO20110224A1 (en) * | 2011-04-26 | 2012-10-27 | Bellco Srl | GROUP FOR MONITORING A CASSETTE OF A DIALYSIS MACHINE |
EP3228340A1 (en) * | 2012-01-26 | 2017-10-11 | Quanta Fluid Solutions Ltd | Dialysis machine |
WO2013110906A1 (en) * | 2012-01-26 | 2013-08-01 | Quanta Fluid Solutions Ltd. | Dialysis machine |
US20150076053A1 (en) * | 2012-01-26 | 2015-03-19 | Quanta Fluid Solutions Limited | Dialysis Machine |
US9833553B2 (en) * | 2012-01-26 | 2017-12-05 | Quanta Fluid Solutions Ltd. | Dialysis machine |
WO2014011543A3 (en) * | 2012-07-10 | 2014-05-22 | Lifeline Scientific, Inc. | Perfusion apparatus with reduced pressure fluctuations, and bubble trap |
US9565853B2 (en) | 2012-07-10 | 2017-02-14 | Lifeline Scientific, Inc. | Perfusion apparatus with reduced pressure fluctuations, and bubble trap |
EP3501279A1 (en) * | 2012-07-10 | 2019-06-26 | Lifeline Scientific, Inc. | Bubble trap and perfusion appparatus comprising such a bubble trap |
EP4285957A3 (en) * | 2012-07-10 | 2024-03-13 | Lifeline Scientific, Inc. | Perfusion apparatus with reduced pressure fluctuations, and bubble trap |
JP2015522072A (en) * | 2012-07-10 | 2015-08-03 | ライフライン サイエンティフック インコーポレイテッドLifeline Scientific, Inc. | Perfusion device with reduced pressure fluctuation and bubble trap |
USRE49881E1 (en) | 2013-03-28 | 2024-03-26 | Quanta Fluid Solutions Ltd. | Re-use of a hemodialysis cartridge |
US20150343133A1 (en) * | 2014-04-29 | 2015-12-03 | Michael Edward HOGARD | Dialysis system and methods |
US11305040B2 (en) * | 2014-04-29 | 2022-04-19 | Outset Medical, Inc. | Dialysis system and methods |
US11583618B2 (en) | 2014-06-02 | 2023-02-21 | Quanta Dialysis Technologies Limited | Method of heat sanitization of a haemodialysis water circuit using a calculated dose |
US10881775B2 (en) | 2015-10-28 | 2021-01-05 | Quanta Dialysis Technologies Ltd. | Dialysis machine and ultrafiltration |
US11571499B2 (en) | 2015-12-30 | 2023-02-07 | Quanta Dialysis Technologies Ltd. | Dialysis machine |
US11534537B2 (en) | 2016-08-19 | 2022-12-27 | Outset Medical, Inc. | Peritoneal dialysis system and methods |
US11951241B2 (en) | 2016-08-19 | 2024-04-09 | Outset Medical, Inc. | Peritoneal dialysis system and methods |
US11660382B2 (en) | 2016-12-23 | 2023-05-30 | Quanta Dialysis Technologies Limited | Valve leak detection system |
US11365728B2 (en) | 2017-02-24 | 2022-06-21 | Quanta Dialysis Technologies Ltd. | Testing rotor engagement of a rotary peristaltic pump |
USD907211S1 (en) | 2017-09-28 | 2021-01-05 | Quanta Dialysis Technologies Ltd. | Dialysis machine |
WO2020086540A1 (en) * | 2018-10-25 | 2020-04-30 | Diality Inc. | Dual reservoir hemodialysis system |
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US20120292237A1 (en) | 2012-11-22 |
US20200268958A1 (en) | 2020-08-27 |
US20180154059A1 (en) | 2018-06-07 |
US10456516B2 (en) | 2019-10-29 |
US20170252498A1 (en) | 2017-09-07 |
US20140251885A1 (en) | 2014-09-11 |
US8685244B2 (en) | 2014-04-01 |
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