US20150034536A1 - Medical apparatus for extracorporeal treatment of fluid and a process of calculating set flow rates in a medical apparatus for delivery or collection of fluids - Google Patents

Medical apparatus for extracorporeal treatment of fluid and a process of calculating set flow rates in a medical apparatus for delivery or collection of fluids Download PDF

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Publication number
US20150034536A1
US20150034536A1 US14/342,028 US201214342028A US2015034536A1 US 20150034536 A1 US20150034536 A1 US 20150034536A1 US 201214342028 A US201214342028 A US 201214342028A US 2015034536 A1 US2015034536 A1 US 2015034536A1
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fluid
container
flow rate
line
control unit
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Inventor
Hiram Rada
Dominique Pouchoulin
Georges Vantard
Alain Frugier
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Gambro Lundia AB
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Gambro Lundia AB
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Assigned to GAMBRO LUNDIA AB reassignment GAMBRO LUNDIA AB ASSIGNMENT OF ASSIGNORS INTEREST (SEE DOCUMENT FOR DETAILS). Assignors: FRUGIER, ALAIN, POUCHOULIN, DOMINIQUE, RADA, HIRAM, VANTARD, GEORGES
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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
    • A61M1/1601—Control or regulation
    • A61M1/1613—Profiling or modelling of patient or predicted treatment evolution or outcome
    • 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
    • A61M1/34—Filtering material out of the blood by passing it through a membrane, i.e. hemofiltration or diafiltration
    • 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
    • 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
    • A61M1/1601—Control or regulation
    • 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
    • A61M1/1601—Control or regulation
    • A61M1/1603—Regulation parameters
    • A61M1/1605—Physical characteristics of the dialysate fluid
    • 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
    • A61M1/1601—Control or regulation
    • A61M1/1603—Regulation parameters
    • A61M1/1611—Weight of the patient
    • 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
    • A61M1/34—Filtering material out of the blood by passing it through a membrane, i.e. hemofiltration or diafiltration
    • A61M1/342—Adding solutions to the blood, e.g. substitution solutions
    • 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
    • A61M1/34—Filtering material out of the blood by passing it through a membrane, i.e. hemofiltration or diafiltration
    • A61M1/342—Adding solutions to the blood, e.g. substitution solutions
    • A61M1/3424—Substitution fluid path
    • A61M1/3431—Substitution fluid path upstream of the filter
    • A61M1/3434—Substitution fluid path upstream of the filter with pre-dilution and post-dilution
    • 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
    • A61M1/34—Filtering material out of the blood by passing it through a membrane, i.e. hemofiltration or diafiltration
    • A61M1/342—Adding solutions to the blood, e.g. substitution solutions
    • A61M1/3424—Substitution fluid path
    • A61M1/3437—Substitution fluid path downstream of the filter, e.g. post-dilution with filtrate
    • 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
    • A61M1/34—Filtering material out of the blood by passing it through a membrane, i.e. hemofiltration or diafiltration
    • A61M1/342—Adding solutions to the blood, e.g. substitution solutions
    • A61M1/3441—Substitution rate control as a function of the ultrafiltration rate
    • A61M1/3451—Substitution rate control as a function of the ultrafiltration rate the difference in weight between both ultra-filtrate and substitution reservoir being used as control signal
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M1/00—Suction or pumping devices for medical purposes; Devices for carrying-off, for treatment of, or for carrying-over, body-liquids; Drainage systems
    • A61M1/36—Other treatment of blood in a by-pass of the natural circulatory system, e.g. temperature adaptation, irradiation ; Extra-corporeal blood circuits
    • A61M1/3607—Regulation parameters
    • A61M1/3609—Physical characteristics of the blood, e.g. haematocrit, urea
    • 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
    • B01D61/30—Accessories; Auxiliary operation
    • 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
    • B01D61/32—Controlling or regulating
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01F—MEASURING VOLUME, VOLUME FLOW, MASS FLOW OR LIQUID LEVEL; METERING BY VOLUME
    • G01F1/00—Measuring the volume flow or mass flow of fluid or fluent solid material wherein the fluid passes through a meter in a continuous flow
    • 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
    • A61M1/34—Filtering material out of the blood by passing it through a membrane, i.e. hemofiltration or diafiltration
    • A61M1/342—Adding solutions to the blood, e.g. substitution solutions
    • A61M1/3441—Substitution rate control as a function of the ultrafiltration rate
    • 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
    • A61M2202/00—Special media to be introduced, removed or treated
    • A61M2202/04—Liquids
    • A61M2202/0413—Blood
    • 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
    • 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
    • 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
    • A61M2205/50—General characteristics of the apparatus with microprocessors or computers
    • A61M2205/502—User interfaces, e.g. screens or keyboards
    • 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
    • A61M2205/50—General characteristics of the apparatus with microprocessors or computers
    • A61M2205/52—General characteristics of the apparatus with microprocessors or computers with memories providing a history of measured variating parameters of apparatus or patient
    • 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
    • A61M2205/75—General characteristics of the apparatus with filters

Definitions

  • the present invention relates to a medical apparatus for extracorporeal processing of fluid, such as blood, a blood component or other biological or medical fluid.
  • the present invention also relates to a process of calculating set flow rates in a medical apparatus for delivery, or collection, or for delivery and collection of fluids, such as for example in an apparatus for extracorporeal fluid processing.
  • Extracorporeal blood treatment apparatus which are typically used to extract undesirable fluids and/or solutes from the patient's blood and/or add desirable fluids and/or substances to the blood.
  • Extracorporeal blood treatment is used for treating patients unable to effectively remove excess water and undesirable substances from their blood, such as when a patient suffers temporary or permanent kidney failure. These patients may receive an extracorporeal blood treatment to add/or remove substances to their blood, to maintain an acid/base balance, and/or to remove excess body fluids, for example.
  • Extracorporeal blood treatment is typically accomplished by removing the blood from the patient in e.g.
  • a continuous flow introducing the blood into a primary chamber, also referred to as blood chamber, of a filtration unit (such as a dialyzer or an hemofilter or an hemodiafilter) where the blood is allowed to flow along a semipermeable membrane.
  • a filtration unit such as a dialyzer or an hemofilter or an hemodiafilter
  • the semipermeable membrane selectively allows matter in the blood to cross the membrane from the primary chamber into a secondary chamber and also selectively allows matter in the secondary chamber to cross the membrane into the blood in the primary chamber, depending on the type of treatment. Cleared blood is then returned to the patient.
  • a number of different types of extracorporeal blood treatments may be performed.
  • UF ultrafiltration
  • HF hemofiltration
  • the blood flows past the semipermeable membrane as in UF and desirable substances are added to the blood, typically by dispensing a fluid into the blood either via respective infusion lines before and/or after it passes through the filtration unit and before it is returned to the patient.
  • a hemodialysis (HD) treatment a secondary fluid containing desirable substances is introduced into the secondary chamber of the filtration unit. Undesirable substances from the blood may cross the semipermeable membrane by diffusion into the secondary fluid and desirable substances from the secondary fluid may cross the membrane into the blood.
  • extracorporeal blood treatment equipment may comprise a plurality of lines for delivering fluid directly to the patient or into the extracorporeal blood circuit.
  • the set values for the flow rates on each line are used to control respective pumps: in other words, a plurality of pumps are used where each pump draws fluid from or supplies fluid to a respective fluid container according to the set flow rate value for the respective line.
  • each bag/container is emptied at a respective rate of fluid because consumption for each individual bag/container usually differs from that of the other bags.
  • the consequence is that nurses or assisting operators are compelled to very frequently intervene to change a bag.
  • the number of interventions for bag changes is directly proportional to the number of bags/containers used and leads to a very cumbersome management of the blood treatment equipment.
  • the equipment, and thereby treatment delivery must be stopped to give the operator time to substitute the container with a new one, thus leading to frequent interruptions with inefficient and discontinuous delivery of the treatment.
  • Another object of the invention is to offer a medical apparatus for the treatment of fluid and a process for calculating set flow rates in said apparatus capable of reducing treatment interruptions and bag or container changes without however compromising the prescribed treatment dose delivery.
  • Another object is an apparatus capable of controlling operating parameters in a safe manner.
  • At least one of the above objects is substantially reached by an apparatus according to one or more of the appended apparatus claims.
  • One or more of the above objects is also substantially reached by a process according to any one of the appended process claims.
  • a 1 st aspect concerns an apparatus for extracorporeal treatment of blood comprising a filtration unit having a primary chamber and a secondary chamber separated by a semi-permeable membrane; a blood withdrawal line connected to an inlet of the primary chamber, and a blood return line connected to an outlet of the primary chamber said blood lines being configured for connection to a patient cardiovascular system; a blood pump configured to control the flow of blood through the blood lines; an effluent fluid line connected to an outlet of the secondary chamber; at least two further fluid lines selected in the group comprising:
  • control unit is further configured to control said means for regulating the flow of fluid based on said set values of the fluid flow rates.
  • the control unit uses the calculated set values of the fluid flow rates for e.g. controlling the rotational pump of the pumps or the position of the regulating valves used on the fluid lines.
  • a memory is provided storing a plurality of mathematical relations correlating fluid flow rates selected in said group, said control unit being connected to said memory.
  • control unit is further configured to calculate the set values at least of the second and third fluid flow rates by applying said prescribed dose value D set and the set value of the first fluid flow rate entered by the operator to said mathematical relations.
  • control unit is further configured to allow the user to select at least two of said relations and to calculate the set values of at least the second and third of said fluid flow rates by applying the set value of the prescribed dose and the set value of the first fluid flow rate entered by the operator to the mathematical relations selected by the user.
  • the convection-diffusion relation defines a first ratio R 1 dividing the total fluid flow rate Q rep1 +Q rep2 +Q pbp through said infusion fluid lines by the fluid flow rate Q dial through said dialysis fluid line.
  • the blood pre-dilution relation defines a second ratio R 2 dividing the flow rate of blood or of plasma Q BLOOD , Q PLASMA by the sum of fluid flow rates Q rep1 +Q pbp infused in the blood withdrawal line through said pre-dilution infusion fluid line and through said pre-blood pump infusion line.
  • the pre-post relation defines a third ratio R 3 dividing the sum of the fluid flow rates Q rep1 +Q pbp through said pre-blood pump infusion line and pre-dilution infusion line by the fluid flow rate Q rep2 through said post-dilution infusion line.
  • control unit is further configured to: store a preset value or preset range for each one of said first, second and third ratios R 1 , R 2 , R 3 .
  • control unit is further configured to allow entry by an operator of a set value or a set range for each one of said first, second and third ratios R 1 , R 2 , R 3 .
  • the blood pump is active in correspondence of a segment of the blood withdrawal line and the apparatus comprises the following fluid lines:
  • the blood pump is active in correspondence of a segment of the blood withdrawal line and the apparatus comprises the following fluid lines:
  • said prescribed dose value D set comprises a prescribed value for a flow rate or a combination of flow rates.
  • said prescribed dose value D set comprises a prescribed value for one selected in the group including:
  • control unit is configured to correct the selected one of the above defined doses to take into account a predilution effect, when a fluid replacement or infusion line is present and delivers fluid upstream the treatment unit, by multiplying the dose value times a dilution factor F dilution , which is ⁇ then 1, as per the following formula:
  • said first fluid flow rate is the fluid removal rate Q pfr from the patient and wherein the control unit is configured to receive the set value of the patient fluid removal rate Q pfr and to calculate the fluid flow rate Q dial through the dialysis liquid fluid line and the fluid flow rate Q rep1 , Q pbp , Q rep2 through the infusion fluid line or lines using at least two of said mathematical relations.
  • control unit is further configured to allow entry by an operator of the set value for a blood flow Q BLOOD through the blood withdrawal or blood return line.
  • control unit is configured to calculate the set value for the blood flow based on a sensed value of a patient parameter selected in the group comprising:
  • control unit is configured to control the blood pump using either the entered or the calculated set value for the blood flow Q BLOOD .
  • control unit is further configured to calculate the set value for the fluid flow rate Q pbp through said pre-blood pump infusion line as a function of:
  • the apparatus further comprises a graphic user interface connected to said control unit, said control unit being configured to:
  • the means for regulating the flow of fluid through said fluid lines comprises a pre-dilution pump for regulating the flow through said pre-dilution fluid line and a post-dilution pump for regulating the flow through said post-dilution fluid line.
  • a dialysis fluid line is connected to the inlet of the secondary chamber, and the means for regulating the flow of fluid through said fluid lines comprises at least a dialysis fluid pump for regulating the flow through said dialysis fluid line.
  • said one or more infusion fluid lines comprise: a pre-blood pump infusion line connected to the blood withdrawal line in a region of this latter which is positioned in use upstream the blood pump, the means for regulating the flow of fluid through said fluid lines comprises at least a pre-blood infusion pump for regulating the flow through said pre-blood pump infusion line.
  • the apparatus further comprises a memory storing a one or a plurality of optimization criteria, said control unit being connected to said memory and being further configured to calculate the set values at least one of the second and third fluid flow rates by applying the optimization criteria.
  • the apparatus includes a waste container connected to an end of the effluent fluid line.
  • the apparatus includes a first container of fresh fluid connected to an end of the pre-dilution infusion fluid line.
  • the apparatus includes a second container of fresh fluid connected to an end of the post-infusion fluid line.
  • the apparatus includes a third container of fresh fluid connected to an end of the dialysis liquid fluid line.
  • the apparatus includes a fourth container of fresh fluid connected to an end of the pre-blood pump infusion fluid line.
  • the optimization criteria comprises a first optimization criterion imposing that an emptying time of at least two among the containers of fresh fluid and, optionally, a filling time of the waste container are multiple of a same reference time.
  • the optimization criteria comprises a first optimization criterion imposing that an emptying time of at least one among the containers of fresh fluid and/or a filling time of the waste container is substantially same as or multiple of the emptying time of one or more of the other containers of fresh fluid.
  • the optimization criteria comprises a second optimization criterion imposing that fluid consumption through said fluid lines is minimized.
  • the optimization criteria comprises a third optimization criterion imposing that a life time of said filtration unit is maximized.
  • the optimization criteria comprises a fourth optimization criterion imposes that urea clearance or dialysance of a given solute is maximized.
  • control unit is configured to allow the user selecting one or more of said criteria and calculate said at least second and third flow rate using said selected criteria.
  • a 39 th aspect according to any one of the preceding aspects from the 27 th to the 37 th allow the user selecting one or more of said criteria and one or more of said mathematical relations and to calculate said at least second and third flow rate using said selected criteria and said selected mathematical relations.
  • control unit is configured to determine if said selected criteria and said selected mathematical relations are compatible or conflicting and then:
  • control unit may be configured combine the use of the flow rate set-up procedure with the use of one or more optimization criteria.
  • control unit may be configured to:
  • a 41 st aspect relates to an apparatus for extracorporeal treatment of fluid comprising:
  • a filtration unit having a primary chamber and a secondary chamber separated by a semi-permeable membrane; a blood withdrawal line connected to an inlet of the primary chamber, and a blood return line connected to an outlet of the primary chamber said blood lines being configured for connection to a patient cardiovascular system; a blood pump configured to control the flow of blood through the blood lines; an effluent fluid line connected, at one end thereof, to an outlet of the secondary chamber and, at its other end, optionally connected to a waste container; at least two further fluid lines selected in the group of fluid lines comprising:
  • each fresh fluid line e.g. the following:
  • control unit is configured to:
  • control unit is configured to:
  • control unit is configured to use at least two reference times T r1 and T r2 .
  • This solution may be adopted when the apparatus includes at least four of the fluid lines selected in said group of fluid lines specified in aspect 41 .
  • the control unit is configured to calculate set values (Q iset ) of two or more of:
  • the apparatus would include a relevant number of lines bringing and or withdrawing fluid from the blood circuit and leading to respective fresh fluid containers or waste containers, it may be possible to synchronize the emptying/filling of the containers in 3 or more groups where each group of containers is synchronized relative to a respective reference time.
  • control unit is further configured to control said means for regulating based on said calculated set values, either automatically or after receipt of a confirmation signal.
  • the apparatus comprises at least the following fluid lines:
  • control unit is configured to calculate the set value for the fluid flow rate through each of the infusion fluid lines and dialysis fluid line by imposing that the emptying time of each given of said first, second and third containers is multiple of the same reference time T r .
  • control unit is configured to calculate the set value for the fluid flow rate through each of the infusion fluid lines and dialysis fluid line by imposing that the emptying time of each given of said first, second and third containers is same as or multiple of the emptying time of one or more other of said first, second and third containers.
  • the blood pump is active in correspondence of a segment of the blood withdrawal line
  • the pre-dilution infusion fluid line is connected to the blood withdrawal line between the blood pump segment and the filtration unit
  • a pre-blood pump infusion fluid line is connected to the blood withdrawal line in a region of this latter which is positioned between the blood pump segment and an end of the blood withdrawal line opposite the end connected to the filtration unit.
  • control unit is configured to calculate the set value for the fluid flow rate through each of the infusion fluid lines and dialysis fluid line by imposing that the emptying time of each given of said first, second, third, and fourth containers is multiple of the same reference time T r .
  • control unit is configured to calculate the set value for the fluid flow rate through each of the infusion fluid lines and dialysis fluid line by imposing that the emptying time of each given of said first, second, third, and fourth containers is same as or multiple of the emptying time of one or more other of said first, second, third, and fourth containers.
  • the waste line is connected to the waste container and the control unit is configured to calculate the set value for the fluid flow rate through each of the fluid lines by imposing that the emptying time of each given of said containers of fresh fluid and the filling time of the waste container are multiple of the same reference time T r and are optionally same as or multiple of the emptying time of one or more other containers of fresh fluid or filling time of the waste container.
  • control unit is configured to store in a memory connected to the control unit the volume or weight of fluid which may be contained in each container of fresh fluid and optionally in said waste container.
  • said volume or weight of fluid is detected by a sensor associated to each respective container and connected to the control unit, or said volume or weight of fluid is entered by an operator for each respective container through a user interface connected to the control unit.
  • said volume or weight of fluid is determined by the control unit associating an identification code on each respective container to a respective volume.
  • said volume or weight of fluid is pre-stored in said memory.
  • control unit is further configured to receive, for instance by allowing a corresponding selection by an operator, at least one set value for a treatment time T.
  • control unit is further configured to receive, for instance by allowing a corresponding selection by an operator, at least one set value for a treatment dose D set to be delivered to the patient during the treatment.
  • the set value for the treatment dose comprises a prescribed value for one selected in the group including:
  • control unit is further configured to receive, for instance by allowing a corresponding selection by an operator, at least one set value for one or more of:
  • the apparatus comprises one or more scales weighing one or more of said containers.
  • the apparatus comprises a corresponding scale for each respective of said containers, said one or more scales being connected to the control unit and sending to the control unit corresponding weight signals.
  • control unit is configured to:
  • control unit is configured to:
  • control unit is configured to:
  • the weighing coefficient c i for each respective container is calculated as a function of an intermediary factor b i obtained by dividing either the dose or the sum of said proposed values Q i of the flow rates by the respective proposed value Q i optionally wherein the weighing coefficient c i for each respective container is calculated using formula:
  • control unit is configured to:
  • a 67 th aspect relates to an apparatus for extracorporeal treatment of fluid comprising:
  • a filtration unit having a primary chamber and a secondary chamber separated by a semi-permeable membrane; a blood withdrawal line connected to an inlet of the primary chamber, and a blood return line connected to an outlet of the primary chamber said blood lines being configured for connection to a patient cardiovascular system; a blood pump configured to control the flow of blood through the blood lines; an effluent fluid line connected, at one end thereof, to an outlet of the secondary chamber and, at its other end, optionally connected to a waste container; at least two further fluid lines selected in the group comprising:
  • control unit is configured to
  • control unit is configured to:
  • control unit configured to:
  • control unit is configured to receive one set value set by an operator for one fluid flow rate selected in the group comprising:
  • control unit is configured to compute the reference time T r by:
  • c i is an weighing coefficient to be multiplied by the initial weight or volume of each container
  • c i is the weighing coefficient to be multiplied by the initial weight or volume of each container.
  • the apparatus comprises a separate scale detecting the weight of each respective container.
  • control unit is configured to receive a weight W i of one or more of said containers as measured by a corresponding scale associated to each container, wherein the weight of each respective container W i used for the calculation of the set values of the fluid flow rates is determined either at the beginning of the treatment or at a prefixed checkpoint during treatment or responsive to a user input.
  • control unit is configured to compare the detected weight of each container of fresh fluid to a respective threshold and to determine that a fresh fluid container is empty if the detected weight is below the respective threshold.
  • control unit is configured to compare the detected weight of the waste fluid container a respective threshold and to determine that the waste container is full if the detected weight is above the threshold.
  • the threshold may be fixed or the control unit may be configured to calculate as threshold a set value (V eff-change ) of the waste container reference volume or weight, at which the control unit considers that the waste container is full, by imposing that the filling time of the waste container is substantially same as, proportional to, or multiple of the emptying time of one or more of the other containers of fresh fluid.
  • control unit is configured to generate an empty container signal when the weight of one or more containers of fresh fluid is below the respective threshold and to generate a full container signal when the weight of said waste container is above the respective threshold.
  • the means for regulating the flow of fluid through said fluid lines comprises a pre-dilution pump for regulating the flow through said pre-dilution fluid line and a post-dilution pump for regulating the flow through said post-dilution fluid line,
  • control unit is further configured to:
  • control unit is configured to allow entry of:
  • the fluid removal rate Q pfr from the patient or of b) the treatment time T and of the weight loss WL to be imposed over said treatment time T.
  • the fluid removal rate may be calculated as ratio between WL and T.
  • control unit is further configured to calculate the set values (Q iset ) of the fluid flow rates through said fluid lines by imposing that:
  • all containers of fresh fluid comprise a fluid having a same composition.
  • the fourth container of fresh fluid comprises a fluid having a composition different from that of the other containers of fresh fluid, for example said fourth container contains an anticoagulant (heparin or a regional anticoagulant such as a citrate solution): in this case the control unit is configured to calculate the set value of fluid flow rate through the pre-blood pump infusion line based on a predefined algorithm: e.g. the flow rate through the pre-blood pump infusion line may be set to be proportional to the set or calculated value of the blood pump flow rate.
  • an anticoagulant heparin or a regional anticoagulant such as a citrate solution
  • the apparatus comprises the fourth container which includes a regional anticoagulant, for example a citrate based solution
  • the second container leading to said post-dilution infusion fluid line includes an ionic balance solution, for example calcium ion based solution: in this case the control unit is configured to calculate the fluid flow rate through said pre-blood pump infusion fluid line and through said post-dilution infusion fluid line based on pre-defined algorithm(s).
  • the apparatus comprises one or two syringe lines leading to respective syringe containers (S) including an anticoagulant solution or a ionic balance solution, the control unit being configured to calculate the fluid flow rate through said syringe line or lines based on pre-defined algorithm(s).
  • control unit is configured to check if the calculated set value for the fluid flow rate through the post-dilution infusion line is higher than a prefixed fraction of the blood flow rate.
  • control unit configured to activate a correction procedure comprising:
  • control unit is configured to:
  • a 87 th aspect concerns a process of setting up a medical apparatus for the delivery and/or collection of fluids, the apparatus comprising:
  • the apparatus comprises:
  • a filtration unit having a primary chamber and a secondary chamber separated by a semi-permeable membrane; a blood withdrawal line connected to an inlet of the primary chamber, and a blood return line connected to an outlet of the primary chamber said blood lines being designed to be connected to a patient cardiovascular system; a blood pump configured to control the flow of blood through the blood lines; an effluent fluid line connected, at one end thereof, to an outlet of the secondary chamber and, at its other end, optionally connected to a waste container; at least two fluid lines selected in the group comprising:
  • the apparatus comprises:
  • a filtration unit having a primary chamber and a secondary chamber separated by a semi-permeable membrane; a blood withdrawal line connected to an inlet of the primary chamber, and a blood return line connected to an outlet of the primary chamber said blood lines being designed to be connected to a patient cardiovascular system; a blood pump configured to control the flow of blood through the blood lines; an effluent fluid line connected, at one end thereof, to an outlet of the secondary chamber and, at its other end, optionally connected to a waste container; at least two fluid lines selected in the group comprising:
  • each fresh fluid line e.g. the following:
  • the apparatus comprises at least the following three fluid lines:
  • the emptying time of each given of said first, second, third and fourth containers and/or the filling time of the waste container is substantially the same as, or multiple of, the emptying time of one or more other of said first, second, third and fourth containers, said set value for the fluid flow rate through each of the above-listed three fluid lines being calculated dividing said weight or volume W i , V i of the respective container by the value of reference time T r .
  • the calculation of reference time T r may be made as disclosed in connection with the above apparatus aspects.
  • the process comprises to:
  • a 96 th aspect concerns a process of setting up a medical apparatus for the delivery or collection of fluid, the apparatus comprising:
  • a filtration unit having a primary chamber and a secondary chamber separated by a semi-permeable membrane; a blood withdrawal line connected to an inlet of the primary chamber, and a blood return line connected to an outlet of the primary chamber said blood lines being designed to be connected to a patient cardiovascular system; a blood pump configured to control the flow of blood through the blood lines; an effluent fluid line connected to an outlet of the secondary chamber; at least two fluid lines selected in the group comprising:
  • said means for regulating the flow of fluid are controlled based on said set values of the fluid flow rates.
  • said mathematical relations stored in said memory comprise one or more of the following:
  • the process comprises selecting at least two of said relations and calculating the set values of at least the second and third of said fluid flow rates by applying the set value of the prescribed dose and the set value of the first fluid flow rate entered by the operator to the selected mathematical relations.
  • the convection-diffusion relation defines a first ratio R 1 dividing the total fluid flow rate Q rep1 +Q rep2 +Q pbp through said infusion fluid lines by the fluid flow rate Q dial through said dialysis fluid line,
  • the blood pre-dilution relation defines a second ratio R 2 dividing the flow rate of blood or of plasma Q BLOOD , Q PLASMA by the sum of fluid flow rates Q rep1 +Q pbp infused in the blood withdrawal line through said pre-dilution infusion fluid line and through said pre-blood pump infusion line
  • the pre-post relation defines a third ratio R 3 dividing the sum of the fluid flow rates Q rep1 +Q pbp through said pre-blood pump infusion line and pre-dilution infusion line by the fluid flow rate Q rep2 through said post-dilution infusion line.
  • the process may include selection of optimization relations as disclosed in connection with the above apparatus aspects.
  • the apparatus comprises one or more scales weighing one or more of said containers, optionally wherein a corresponding scale is provided for each respective of said containers, said scales being connected to the control unit and sending to the control unit corresponding weight signals, wherein the control unit is configured to receiving the initial weight W i of one or more of said containers from one or more of said scales.
  • a data carrier comprising instructions which when executed by the control unit of an apparatus according to any one of the preceding apparatus aspects render said control unit configured to execute the respective steps described in the preceding aspects.
  • FIG. 1A shows a chart, relative to the emptying profiles of bags in accordance with a state of the art solution; the vertical axis represents the weight of each one of three bags and the horizontal axis represents the emptying time;
  • FIG. 1B shows a chart, relative to the set flow rates as a function of time for the three pumps withdrawing fluid from respective bags in order obtain the emptying profiles shown in FIG. 1A ;
  • FIG. 2A shows a chart, relative to the emptying profiles of bags in accordance with aspects of the invention, where the vertical axis represents the weight of each one of three bags and the horizontal axis represents the emptying time;
  • FIG. 2B shows a chart, relative to the set flow rates as function of time for the three pumps withdrawing fluid from respective bags in order obtain the emptying profiles shown in FIG. 2A ; as it may be seen although the initial weight of each bag is different all bags are emptied at the same time thus minimizing the number of times the equipment must be stopped for proceeding with bag substitution;
  • FIG. 3A shows a chart, relative to the emptying profiles of bags in accordance with aspects of the invention, where the vertical axis represents the weight of each one of three bags and the horizontal axis represents the emptying time diagram of a blood treatment apparatus according to one aspect of the invention;
  • FIG. 3B shows a chart, relative to the set flow rates as a function of time for the three pumps withdrawing fluid from respective bags in order obtain the emptying profiles shown in FIG. 3A ;
  • FIGS. 4-7 show schematic representations of blood treatment apparatuses according to aspects of the invention.
  • FIG. 8 is a flowchart of a process of calculating set flow rates in a medical apparatus for delivery or collection of fluids, according to an aspect of the invention.
  • FIG. 9 relates to a flowchart showing calculation of set flow rates in a medical apparatus, e.g. of the type of FIGS. 4-7 , according to a further aspect of the invention.
  • FIG. 10 shows a chart, relative to the emptying profiles of three bags/containers in a case where certain flow rates have been imposed for each one of the lines leading to the three bags/containers; the vertical axis in FIG. 10 represents the weight of each one of three bags/containers and the horizontal axis represents the emptying time;
  • FIG. 11 shows a chart, relative to the emptying profiles of three bags/containers in accordance with the flowchart of FIG. 9 , where the vertical axis represents the weight of each one of three bags/containers and the horizontal axis represents the emptying time; and
  • FIG. 12 is a flowchart showing calculation of set flow rates in a medical apparatus, e.g. of the type of FIGS. 4-7 , according to another aspect of the invention.
  • FIGS. 4-7 show exemplifying embodiments of apparatus for extracorporeal treatment of blood according to aspects of the invention. Note that same components are identified by same reference numerals in the figures. Also note that—although the present invention is described with specific reference to blood treatment apparatuses—the invention may also refer to apparatuses for handling a plurality of medical fluids, such as nutrients, replacement solutions, serum, or other fluids which need to be controllably injected into or withdrawn from a patient's body.
  • a plurality of medical fluids such as nutrients, replacement solutions, serum, or other fluids which need to be controllably injected into or withdrawn from a patient's body.
  • FIG. 4 shows an extracorporeal blood treatment apparatus 1 which is designed for delivering any one of treatments like hemodialysis, hemofiltration, hemodiafiltration, ultrafiltration.
  • the apparatus 1 comprises a filtration unit 2 having a primary chamber 3 and a secondary chamber 4 separated by a semi-permeable membrane 5 ; depending upon the treatment the membrane of the filtration unit may be selected to have different properties and performances.
  • a blood withdrawal line 6 is connected to an inlet of the primary chamber 3 , and a blood return line 7 is connected to an outlet of the primary chamber 3 .
  • the blood withdrawal line 6 and the blood return line 7 are connected to a needle or to a catheter or an implanted port or other access device (not shown) which is then placed in fluid communication with the patient vascular system, such that blood may be withdrawn through the blood withdrawal line, flowed through the primary chamber and then returned to the patient's vascular system through the blood return line.
  • An air separator such as a bubble trap 8 , may be present on the blood return line; moreover, a safety clamp 9 controlled by a control unit 10 may be present on the blood return line downstream the bubble trap 8 .
  • a bubble sensor 8 a for instance associated to the bubble trap 8 or coupled to a portion of the line 7 between bubble trap 8 and clamp 9 may be present: if present, the bubble sensor is connected to the control unit 10 and sends to the control unit signals for the control unit to cause closure of the clamp 9 in case one or more bubbles are detected.
  • the blood flow through the blood lines is controlled by a blood pump 11 , for instance a peristaltic blood pump, acting either on the blood withdrawal line (as shown e.g. in FIG. 1 ) or on the blood return line.
  • An operator may enter a set value for the blood flow rate Q BLOOD through a user interface 12 and the control unit 10 , during treatment, is configured to control the blood pump based on the set blood flow rate.
  • the blood pump 11 may be automatically controlled with no need of user input: in that case control unit may control the blood pump at a prefixed flow rate or at a flow rate calculated based on other parameters such as, for instance, pressure detected upstream the blood pump; if the blood pump 11 is controlled based on the pressure signal detected upstream the blood pump then a pressure sensor 6 b is present in the tract 6 a of bloodline upstream the blood pump 11 : for instance the control unit 10 may be designed to drive the blood pump in a manner to keep the pressure detected by pressure sensor 6 b within a prefixed range, or below a prefixed threshold.
  • an effluent fluid line 13 is connected, at one end, to an outlet of the secondary chamber 4 and, at another end, to an effluent fluid container 14 collecting the fluid extracted from the secondary chamber.
  • the embodiment of FIG. 1 also presents a pre-dilution fluid line 15 connected to the blood withdrawal line: this line 15 supplies replacement fluid from an infusion fluid container 16 connected at one end of the pre-dilution fluid line.
  • a post-dilution fluid line 25 may also be present connecting an infusion fluid container 26 to the blood return line, for instance in correspondence of bubble trap 8 .
  • each infusion fluid line may be connected to a respective infusion fluid container or the two infusion fluid lines could receive infusion fluid from a same infusion fluid container or other fluid source.
  • An effluent fluid pump 17 operates on the effluent fluid line under the control of said control unit 10 to regulate the flow rate Q eff across the effluent fluid line.
  • an infusion pump 18 operates on the infusion line 15 to regulate the flow rate Q rep1 through the pre-dilution fluid line 15 .
  • each fluid line 15 , 25 may cooperate with a respective infusion pump 18 , 27 to regulate the flow rate Q rep1 and Q rep2 through the respective lines.
  • the apparatus of FIG. 4 further includes a dialysis fluid line 19 connected at one end with a dialysis fluid container 20 and at its other end with the inlet of the secondary chamber 4 of the filtration unit.
  • a dialysis pump 21 works on the dialysis fluid line 19 under the control of said control unit 10 , to supply fluid from the dialysis liquid container to the secondary chamber at a flow rate Q dial .
  • the dialysis fluid pump 21 , the infusion fluid pump 18 (or pumps 18 , 27 ) and the effluent fluid pump 17 are part of means for regulating the flow of fluid through the respective lines and, as mentioned, are operatively connected to the control unit 10 which controls the pumps as it will be in detail disclosed herein below.
  • the control unit 10 is also connected to a memory 10 a and to user interface 12 , for instance a graphic user interface, which receives operator's inputs and displays the apparatus outputs.
  • the graphic user interface 12 may include a touch screen, a display screen and/or hard keys for entering user's inputs or a combination thereof.
  • FIG. 5 shows an alternative apparatus 1 where the same components described for the embodiment of FIG. 1 are also present and are identified by same reference numerals and thus not described again.
  • the apparatus 1 shown in FIG. 2 presents a further infusion line connected, at one end, with a tract 6 a of the blood withdrawal line 6 positioned upstream the blood pump 11 and, at its other end, with a further infusion fluid container 23 , which for instance may contain a drug, or a regional anticoagulant such as a citrate solution, or a nutrients solution or other.
  • This further infusion line is herein referred to as pre-blood pump infusion line 22 .
  • the means for regulating comprises a pump 24 , for instance a peristaltic pump controlled by control unit 10 , acting on a segment of the pre-blood pump infusion line to regulate a pre-blood pump infusion rate Q pbp .
  • the apparatus of FIG. 5 may also present a post-dilution line 25 similar to that of the apparatus of FIG. 4 : the infusion line 25 in FIG. 2 is connected to the blood return line 7 in a location between the bubble trap 8 and the exit of the filtering unit 2 ; alternatively the infusion line may be directly connected to bubble trap 8 .
  • the apparatus of FIG. 6 is similar to that of FIG. 4 but includes only either the post-dilution line 25 with its pump 27 and infusion fluid container 26 or the pre-dilution line 15 with its pump and container (see phantom line).
  • FIG. 7 A further embodiment is shown in FIG. 7 .
  • a line switch 101 operates (such as a 3-way valve or a clamp mechanism) on the dialysis fluid line 19 which allows the dialysis line to be selectively coupled either to the inlet of the second chamber 4 or to the return line 7 : in this latter case the dialysis line would work as a post-dilution line.
  • a further line switch 100 operates on the infusion line 15 which allows the infusion line 15 to be selectively coupled either to the blood withdrawal line or to the blood return line.
  • a further post-dilution line 27 may or may not be present.
  • the above apparatuses may also include a syringe pump provided with a container S connected via a respective line to one of the blood lines 6 and 7 and with a plunger P for displacing the fluid in the container.
  • the syringe pump is connected via syringe line 50 to the blood withdrawal line 6 , downstream the blood pump.
  • Syringe line 50 may be used to inject medicaments, anticoagulants or other fluids.
  • the circuits shown in FIGS. 5 and 7 may include a syringe line 50 with respective container S and plunger P connected either to the blood withdrawal line and/or to the blood return line.
  • the means for regulating have been described as one or more pumps (in particular of the peristaltic type); however it is not to be excluded that other flow regulating means such as valves or combinations of pumps and valves may be used. Moreover, in case of syringe lines, the plunger P acts as a flow regulating means.
  • dose refers to a flow rate or to a combination of flow rates.
  • one of the following magnitudes may be used as dose:
  • the above defined doses could be corrected to take into account the predilution effect, when a fluid replacement line is present upstream the treatment unit, such as lines 15 and 22 in the enclosed drawings.
  • Each of the above defined doses could be corrected multiplying the dose value times a dilution factor F dilution :
  • the dilution factor F dilution may be defined according to one of the following:
  • Q pre is the total predilution infusion rate (where two infusion lines are present upstream the treatment unit, as lines 15 and 22 , Q pre combines PBP infusion 15 and pre-replacement infusion 22 )
  • the control unit 10 is connected to the various sensors, to the means for regulating the flow rate through the various lines (in the above examples this means comprises the pumps active on the lines and the switch valves) and to the user interface.
  • the control unit 10 may comprise a digital processor (CPU) and necessary memory (or memories), an analogical type circuit, or a combination thereof.
  • CPU digital processor
  • an analogical type circuit or a combination thereof.
  • the control unit is “configured” or “programmed” to execute certain steps: this may be achieved in practice by any means which allow configuring or programming the control unit.
  • a program may be stored in an appropriate memory containing instructions which, when executed by the control unit, cause the control unit to execute the steps herein described.
  • the circuitry of the control unit may be designed to include circuitry configured in use to execute the steps herein disclosed.
  • control unit 10 may be configured to calculate set values of fluid flow rate Q rep1 through the pre-dilution infusion fluid line 15 , of fluid flow rate Q rep2 through the post-infusion fluid line 25 , and of fluid flow rate Q dial through the dialysis fluid line 27 , by imposing that an emptying time of the containers of fresh fluid 16 , 20 , 26 is either identical to, or proportional to, or multiple of the emptying time of one of the other containers of fresh fluid.
  • an emptying time of the containers of fresh fluid 16 , 20 , 26 is either identical to, or proportional to, or multiple of the emptying time of one of the other containers of fresh fluid.
  • control unit 10 may be configured to calculate set values of fluid flow rate Q rep1 through the pre-dilution infusion fluid line 15 , of fluid flow rate Q rep2 through the post-infusion fluid line 25 , of fluid flow rate Q dial through the dialysis fluid line 27 , and of Q pbp through line 22 by imposing that an emptying time of the containers of fresh fluid 16 , 20 , 23 , 26 is either identical to or multiple of or proportional to the emptying time of one of the other containers of fresh fluid.
  • an emptying time of the containers of fresh fluid 16 , 20 , 23 , 26 is either identical to or multiple of or proportional to the emptying time of one of the other containers of fresh fluid.
  • control unit 10 may be configured to calculate set values of fluid flow rate Q rep2 through the post-infusion fluid line 25 , of fluid flow rate Q dial through the dialysis fluid line 27 by imposing that an emptying time of one of the containers of fresh fluid 20 , 26 is either identical to or multiple of or proportional to the emptying time of the other container of fresh fluid 26 , 20 .
  • the control unit 10 may be configured to calculate set values of fluid flow rate Q rep1 through the pre-dilution infusion fluid line 15 , of fluid flow rate Q dial through the dialysis fluid line 27 , and of Q pbp through line 22 by imposing that an emptying time of the containers of fresh fluid 16 , 20 , 23 is either identical to or proportional to or multiple of the emptying time of one of the other containers of fresh fluid.
  • the control unit may be configured to calculate the set flow rates through the various lines of fresh fluid such as to either synchronize the emptying time of all containers (e.g.
  • control unit may also be configured to calculate the set value of the fluid flow rate Q eff through the effluent fluid line 13 , by imposing that the filling time of the waste container 14 is substantially same as, proportional to, or multiple of the emptying time of one or more of the other containers of fresh fluid.
  • the control unit may calculate a set value (V eff-change ) of the waste container volume or weight at which the control unit considers that the waste container is full (which is basically a calculated threshold as opposed to a prefixed threshold): this set value (V eff-change ) may be calculated by imposing that the filling time of the waste container 14 is substantially same as, proportional to, or multiple of the emptying time of one or more of the other containers of fresh fluid.
  • the control unit is configured to trigger a signal, e.g. to user interface, requesting a waste container change.
  • this alternative solution may add significant synchronization in bag changes while normally losing little volume in the waste container (namely while only shortly anticipating the waste container change).
  • control unit may be configured to ask, or wait, for a confirmation which may be entered by the user, e.g. through action onto the user interface 12 .
  • the control unit is designed to control the means for regulating the flow rate based on the calculated set values either automatically (i.e. with no need of any action on the part of an operator), or after the appropriate confirmation is entered and a confirmation signal received at the control unit.
  • the control unit 10 may be configured to store, e.g. in a memory connected to the same control unit, the maximum volume of fluid which may be contained in each container of fresh fluid.
  • the control unit may also be configured to store in a memory connected to the same control unit the maximum volume of fluid which may be contained in said waste container.
  • the volume each container may host may be detected by a sensor associated to each respective container and connected to the control unit, or may be entered by an operator for each respective container through a user interface connected to the control unit, or determined by the control unit associating an identification code (indicia such as a bar code, an RFID or other identification means may be associated to the container) on each respective container to a respective volume, or said volume may be pre-stored in said memory.
  • an identification code indicia such as a bar code, an RFID or other identification means may be associated to the container
  • the control unit may be configured to generate an alarm signal and/or to stop the treatment when the maximum quantity of fluid in one fresh fluid container (i.e. in one among the infusion fluid containers 16 , 23 , 26 and the dialysis fluid container 20 ) is reached, corresponding to a “empty container” threshold.
  • the user knows that he is supposed to substitute all fresh fluid containers (if the emptying is simultaneous on all bags as shown in FIGS. 2A , 2 B) or at least to substitute a known number of the fresh fluid containers (if the emptying of the bags or containers is synchronized to happen for two or more containers at prefixed intervals, as shown in FIG. 3 A, 3 B).
  • the control unit may also be configured to generate an alarm signal and/or to stop the treatment when the maximum quantity of fluid has been reached in the effluent fluid container (corresponding to a “full container” threshold).
  • treatment stop it is meant a condition where the control unit is configured to stop at least the pumps delivering fresh fluid (namely pumps 18 , 21 , 24 , 27 , 17 in the embodiments of FIGS. 5 and 7 ; pumps 18 , 21 , 27 , 17 in the embodiment of FIG. 4 ; pumps 21 , 27 , 17 or 21 , 18 , 17 in the embodiment of FIG. 6 ) and optionally also the blood pump 11 .
  • a respective scale (or other force sensor) is associated to the support of each container for detecting in real time the actual weight, and thus the current volume of fluid, of each container.
  • the control unit which is connected to the scales, may determine when the volume of fluid in each respective container is approaching or passing the respective thresholds (empty or full) as above described.
  • sensors e.g. level sensors depending upon the circumstances and or the structure of the containers.
  • control unit 10 is configured to allow selection by an operator of a set value for the treatment dose D set to be delivered to the patient during the treatment (step 200 ).
  • the set value of the dose may be received through an external channel or be pre-stored in a memory connected to the control unit.
  • This set value may be for instance an effluent dose flow rate D eff — set , which is the prescribed mean value of the flow rate through the effluent line, or a convective dose flow rate D conv — set , which is the prescribed mean value of the sum of the flow rates Q rep1 , Q pbp , Q rep2 through any infusion fluid line and the patient fluid removal rate Q pfr , or a diffusive dose flow rate D dial — set , which is the prescribed mean value of the flow rate through the dialysis fluid line Q dial .
  • the control unit also receives the readings of the scales and thus knows the values W, of the initial weights of each container (step 201 ). Alternatively the control unit may read or know the initial volume V, of each container. In the description
  • the set value Q iset namely the flow rate to be set in each fluid line is calculated (step 202 ).
  • control unit is configured to calculate a reference time value T r in different ways, namely:
  • control unit is configured to determine the fluid flow rate in each one of the fresh fluid lines by dividing a weight W, of the respective container by the value of reference time T r (step 204 ).
  • FIGS. 3A and 3B show a second solution where the time required for emptying one of the bags is twice that required for the other 2 bags.
  • c i is an integer: when all c i values are imposed to be equal to 1 then all containers empty at the same time, while if for instance, as in FIG. 3A , one of the c i values is imposed to be equal to 2 and the others equal to 1, then two bags empty twice as faster than the other.
  • c i (normally equal to 1, 2, 3, or 4 or 5) may be used to customize the control by allowing the emptying times of the various bags to be one multiple of one the remaining bags.
  • T r would be calculated as follows:
  • T r ( ⁇ W i ⁇ c i )/Dose
  • the control unit may issue a signal to the user interface 12 requesting a confirmation ( 206 ) from the user before actually applying the calculated values of Q iset to control the pumps.
  • the control unit 10 may be configured to work in a situation where a number of proposed values Q i for the flow rates through each one of the lines are available. This may happen before start of the treatment or at a certain moment during the treatment.
  • the proposed Q i values could be values set by the user (step 400 ), or values calculated by the control unity to accomplish targets other than synchronization of the emptying of the fluid bags.
  • the set value of the treatment dose D set to be delivered to the patient during the treatment may be either calculated by the control unit based on the flow rates Q i or set by the user and communicated by to the control unit (step 401 ).
  • the set value of the dose may be received through an external channel or be pre-stored in a memory connected to the control unit.
  • the blood pump flow rate may be set by the user (step 400 ) or calculated by the control unit (see below section “Blood pump setting”).
  • the control unit also receives the readings of the scales and thus knows the values W, of the initial weights of each container (step 402 ). Note that the volumes V, of each of the containers may be used as an alternative to the weights also for this third solution.
  • c i for each respective container may be calculated as a function of an intermediary factor b i obtained (see step 404 ) by dividing either the dose or the sum of said proposed values Q i of the flow rates by the respective proposed value Q i .
  • each weighing coefficient c i for each respective container is calculated (step 405 ) using formula:
  • c i Round [b i /min(b i . . . b n )], where “min(b 1 . . . b n )” is a function selecting the minimum among the b i factors, and “Round” is a function determining the natural number nearest to the result of quotient b i /min(b i . . . b n ).
  • the control unit may issue a signal to the user interface 12 requesting a confirmation ( 407 ) from the user before actually applying the calculated values of Q iset to control the pumps.
  • the operator may set the fluid flow rate Q rep1 through the pre-dilution infusion fluid line 15 , or the fluid flow rate Q rep2 through the post-infusion fluid line 25 , or the fluid flow rate Q pbp through the pre-blood pump infusion fluid line 21 , a fluid flow rate Q dial through the dialysis liquid fluid line 27 .
  • the setting may be done through the user interface or via any other input.
  • control unit may be configured to execute a synchronization algorithm able to combine the use of proposed values for the set flow rates (for instance initially set by the user or calculated using one or more of the mathematical relations, as above described) with at least a certain degree of synchronization in the emptying of the containers; in other words, a purpose of the algorithm is to minimize the number of user interventions while keeping the flow rates in ‘proximity’ of some initial settings (which may be manual or computed settings). In practice this algorithm is designed to change according to a certain set percentage the initially set or calculated flow rates in order to reduce as possible the number of container/bag changes across a certain time period, e.g. 24 hours, without substantially changing the initially set or calculated flow rates.
  • the starting point of the algorithm is the knowledge of:
  • the blood flow rate setting for the blood pump may be entered or calculated by the control unit, see step 500 .
  • An optional step of calculating a set dose value as sum of the proposed flow rates Q i may be present at step 501 .
  • an allowed adjustment parameter ‘A’ is defined as maximum relative change allowed on bag/container change periods in order to optimize bag synchronization and reduce number of user interventions (step 503 A).
  • the algorithm also considers ‘ratios of interest’ R0 k which are parameters defined in the algorithm as ratios between change periods (time between one container change and the next change of the same container) of pairs of containers (step 503 B). Ratios of interest are defined for each pair of lines and respective containers.
  • K is an integer which may vary from 1 to M, and M may be pre-stored in the control unit memory or the control unit may be configured to receive it from a user input.
  • the algorithm takes into account that more interventions (container changes) are saved when identifying a ‘1 to 1’ container synchronization ratio between two lines (because in that case the containers of the two lines are changed at the same time), than when having a ‘1 to 4’ ratio.
  • Next table 1 provides the list of the optimum ratios of interest when considering all synchronization ratios up to ‘order 5’ in relation with a pair of containers indicated as bag1 and bag2.
  • the first 8 R0 k values are used in some examples reported at the end of the detailed description.
  • control unit may be configured to execute the following steps, after the value of A has been selected or predefined (at step 503 , see FIG. 13 ):
  • the effluent line flow rate may verify condition a fluid balance equation; moreover the syringe line(s) may have a fixed flow rate; the N ⁇ 2 other lines are infusion or dialysate lines leading to respective containers having fixed volume.
  • the associated bag change periods are also fixed and the N ⁇ 2 bag change periods for the other lines remain to be defined.
  • the selection of the NF ratios R ij (step 509 above) providing for the highest number of saved bag changes considers also the ‘degrees of freedom’ issue.
  • control unit 10 may be configured to display the calculated set values.
  • control unit may also be configured to ask, or wait, for a confirmation which may be entered by the user, e.g. through action onto the user interface 12 .
  • the control unit 10 is designed to control the means for regulating the flow rate based on the calculated set values either automatically (i.e. with no need of any action on the part of an operator), or after the appropriate confirmation is entered and a confirmation signal received at the control unit.
  • the control unit may be configured to calculate the fluid flow rate through said syringe line or lines based on a pre-defined algorithm so that basically there are one or two degree of freedom less and thus 2 flow rates less to calculate left with the algorithm for synchronization of the containers emptying.
  • the syringe delivery may be controlled based on said predefined algorithm while the emptying of any other container may be fully or partially synchronized with the emptying of the syringe container(s) using one of the synchronization methods above described.
  • the control unit may be configured to calculate the fluid flow rate through said pre-blood pump infusion fluid line 21 and through said post-dilution infusion fluid line 25 based on a pre-defined algorithm.
  • the delivery through lines 21 and 25 may be controlled based on said a predefined algorithm while the emptying of any other container may be fully or partially synchronized with the emptying of the second and/or fourth container using one of the synchronization methods above described.
  • the equipment comprises three fresh fluid containers 16 , 20 , 26 .
  • the control unit may be configured to adopt the emptying profiles shown in FIG. 2A , thereby synchronizing the emptying of the three containers.
  • the scales inform the control unit about the quantity of fluid present in each bag.
  • Each pump flow rate is then calculated as:
  • control unit may alternatively be configured to adopt the emptying profiles shown in FIG. 3A , thereby synchronizing the emptying of two of containers after a first interval and synchronizing the emptying of all three containers after a second interval.
  • the scales inform the control unit about the quantity of fluid present in each bag.
  • an overall dose D eff of 3000 ml/h is received by the control unit and a first reference time T r calculated as sum of the weights of the bags divided by the total dose:
  • c 1 , c 2 and c 3 are weighing factors in this case respectively set equal to 1, 1 and 2.
  • Each container 20 , 16 and 26 is a 5 L bag, and the set dose is the sum of the above Q i values, namely 3000 ml/h
  • c 1 , c 2 and c 3 are calculated as follows:
  • control unit calculates intermediary parameters B, using the formula:
  • c i The value of c i are obtained by normalizing the values of b i with respect to their minimum and rounding the result to the closest natural number, using the formula:
  • Q BLOOD and the proposed Q i values are set by the user or calculated by the control unit at step 500 .
  • the patient fluid removal rate Q PFR is fixed or entered by the user at 100 ml/h.
  • the dose value is set or calculated (step 501 ) and the volume of the of each bag detected or entered by the user (step 502 ).
  • step 503 The following parameters are selected or preprogrammed:
  • the apparatus comprises a circuit similar to that of FIG. 2 with a syringe pump connected to the blood return line instead of infusion line 25 .
  • Effluent and Syringe bag/container volumes are fixed.
  • the T values are calculated and ranked by the control unit.
  • Table 2 below recaps the initial flow rates Q i (2 nd column), the bag volumes (3 rd column), the change bag periods T, (4 th column) using the initial Q i values and the corresponding number of daily bag changes (5 th column).
  • Table 3 below ranks the change bag periods Ti from the shortest to the longest.
  • the control unit compares the R ij ratios to the ratios of interests R0 k of table 1 creating the ratios R ij /R0 k .
  • Table 5 shows the ratios R ij /R0 k ;
  • the control unit table 5 also checks the ratios R ij /R0 k which stay within the ‘A’ criterion, namely those which verify the condition: (1 ⁇ A) ⁇ R0 k ⁇ R ij ⁇ (1+A) ⁇ R0 k .
  • table 5 also includes an identification of ratios which result within ‘A’ criterion (see cells with underlined values, namely those which verify the condition: (1 ⁇ A) ⁇ R0 k ⁇ R ij ⁇ (1+A) ⁇ R0 k ).
  • step 507 the control unit computes the degrees of freedom NF.
  • Table 6 indicates the number of degrees of freedom (NF).
  • control unit calculates and optionally stores the flow rates.
  • Table 8 provides a summary of selected R ij ratios and flow rate relations obtained using below Equations:
  • FIG. 4 Reference is made to an apparatus as shown in FIG. 4 , provided with 4 fluid pumps (Dialysate pump 21 , Replacement pump 27 , Replacement pump 15 , Effluent pump 17 ) and thus capable of running a HDF therapy.
  • 4 fluid pumps Dialysate pump 21 , Replacement pump 27 , Replacement pump 15 , Effluent pump 17 .
  • the control unit 10 then computes the flow rates as follows:
  • the issue in this case is the choice of the ‘allowed adjustment’ parameter A, since a specific flow rate
  • control unit compares the R ij ratios to the ratios of interests R0 k of table 1 creating the ratios R ij /R0 k and also checks the ratios R ij /R0 k which stay within the ‘A’ criterion, namely those which verify the condition: (1 ⁇ A) ⁇ R0 k ⁇ R ij ⁇ (1+A) ⁇ R0 k .
  • the operator may select a prescribed dose value.
  • the prescribed dose value may also be calculated at the beginning of the treatment by the control unit or it may be pre-stored in a memory connected with the control unit.
  • the control unit may determine the set flow rates on each line in order to achieve the desired level of emptying/filling synchronization.
  • the control unit may receive a set flow rate for one of the fluid lines 15 , 19 , 22 , 25 and the value of the weighing coefficients c i , and then determine the set flow rates on each line in order to achieve the desired level of emptying/filling synchronization.
  • a treatment time T may be entered which is then used to calculate T r and then the flow rates in each line based on T r and c i .
  • the control unit may also allow entry by an operator of the set value for a blood flow Q BLOOD through the blood withdrawal or blood return line, and/or it may be configured to calculate the set value for the blood flow to be set (see below section “Blood pump setting”).
  • control unit is configured to allow entry of the fluid removal rate (Q pfr ) from the patient, or of the treatment time (T) and of the weight loss (WL) to be imposed over said treatment time (T).
  • the apparatus may be very easily initialized and treatment may start with the emptying of the containers or bags duly synchronized.
  • control unit is configured to receiving weight signal corresponding to the weight W, as measured by a corresponding scale associated to each container: the weight of each respective container W, used for the calculation of the set values of the fluid flow rates is usually determined at the beginning of the treatment or subsequent to each bag-substitution before restarting the treatment; however, each weight may also be determined at prefixed checkpoints during treatment or responsive to a user input, such that the control unit may be designed to be able to synchronize the emptying of the bags at any time.
  • the blood pump may be controlled by the control unit 10 using a set value of the blood flow rate Q BLOOD entered by the user. More in general, the control unit 10 may allow entry by an operator of the set value for a blood flow Q BLOOD through the blood withdrawal or blood return line, or it may be configured to calculate the set value for the blood flow to be set.
  • the calculated value for the set blood flow could be calculated based on the value of the flow rate determined in one of the fluid lines: for instance the blood flow rate could be calculated to be proportional to calculated value of the flow rate through pre-blood pump infusion line (or viceversa the pre-blood pump infusion line flow rate could be calculated to be proportional to Q BLOOD )
  • the blood flow rate may be calculated based on a sensed value of a patient parameter or of a treatment parameter, e.g.
  • the pressure sensed by pressure sensor 6 b in tract 6 a of the blood withdrawal line a measured blood recirculation fraction re-circulating from the blood return line 7 into the blood withdrawal line 6 , a measured value of hemo-concentration measured in correspondence of one of the blood lines 6 , 7 , a measured value of transmembrane TMP pressure across the filter semipermeable membrane 5 .
  • control unit 10 may control the blood pump using either the entered or the calculated set value for the blood flow Q BLOOD
  • control unit may be designed to include some safety features: indeed it the filtration fraction is an important factor to be considered. Since the flow rates may be automatically set by the control unit 10 , it is possible to ensure that all pumps infusing in post-dilution will not cause an excessive filtration fraction (e.g. post-dilution flow rate >20% of blood flow rate). In this respect the control unit 10 may be configured to check if the calculated set value for the fluid flow rate through the post-dilution infusion line is higher than a prefixed fraction of the blood flow rate and in the affirmative activate a correction procedure.
  • the control unit 10 may be configured to check if the calculated set value for the fluid flow rate through the post-dilution infusion line is higher than a prefixed fraction of the blood flow rate and in the affirmative activate a correction procedure.
  • the correction procedure may comprise issuing a warning to the user interface, or it may comprise issuing a command to stop the treatment, or it may comprise correcting the delivery of fluid through one or more of the other lines, or (in case for instance the blood treatment apparatus includes a switch on the post-dilution line) issuing a command to switch 100 and/or 101 to temporary connecting a post-dilution fluid line to the blood withdrawal line.
  • the control unit could switch one or more pumps infusing in post-dilution to pre-dilution or dialysate mode.
  • the switch could be accompanied by majoring the flow rate of the pump(s) that have been switched and reducing the other pump flow rates.
  • control unit 10 configured to maintain the post-dilution pump as such but rather decrease its flow rate such that the emptying time is differed by adjusting its weighting factor.
  • All containers of fresh fluid may comprise a fluid (e.g. a replacement solution) having a same composition.
  • a fluid e.g. a replacement solution
  • the fact that the flow rates are not set individually implies that if the same type of composition is used during the treatment for containers there is no unexpected outcome regarding the electrolytic balance and/or acid-base equilibrium of the patient.
  • a container of fresh fluid comprises a fluid having a composition different from that of the other containers of fresh fluid: for instance the fourth container may contain an anticoagulant, such as a citrate solution; in this case the control unit 10 is configured to calculate the set value of fluid flow rate through the pre-blood pump infusion line to be proportional to the set or calculated value of the blood pump flow rate for achieving an adequate anticoagulation level.
  • the other pump flow rates are adjusted so as to become empty at the same time as the citrate bag.
  • the control unit could use the citrate bag in a way that it is not synchronized with the emptying of the other fluid bags and is thus managed separately (e.g. flow rate is proportional to blood flow rate).
  • fourth bag emptying is synchronized with the other bags and the blood pump flow rate setting is adjusted so as to be proportional to the citrate pump flow rate.
  • all infusion bags used be citrate-containing bags: in this case synchronization may be made with no problems.
  • the fourth bag includes a regional anticoagulant, e.g. a citrate based solution
  • one post-dilution line including a calcium ion based solution may be present: for instance referring to FIG. 2 container 23 may include a citrate based solution and container 26 a calcium ion solution.
  • lines 22 and 27 may be associated with a bag container and cooperate with a peristaltic pump (as shown in FIG. 2 ) or may include a syringe delivery system.
  • One other advantage is a positive impact on the treatment since lesser interruptions help in providing more continuous and accurate treatment.
  • One further positive aspect which may be provided by certain aspects of the present invention is a simplification in setting of treatment prescription.

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US10668199B2 (en) 2020-06-02
WO2013030643A1 (fr) 2013-03-07
CA2847053C (fr) 2019-12-03
CN103889479B (zh) 2015-09-16
CA2847053A1 (fr) 2013-03-07
EP2564884A1 (fr) 2013-03-06
AU2012300546A1 (en) 2014-03-13
PL2564884T3 (pl) 2014-11-28
US20180207341A1 (en) 2018-07-26
AU2012300546B2 (en) 2016-06-23
CN103889479A (zh) 2014-06-25
US11207451B2 (en) 2021-12-28
KR20140065432A (ko) 2014-05-29
US20200246529A1 (en) 2020-08-06
KR102013468B1 (ko) 2019-08-22
EP2564884B1 (fr) 2014-06-18
ES2497215T3 (es) 2014-09-22

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