Method and apparatus for calculating fluid flow rate

• US 7,896,831 B2
• Filed: 03/06/2009
• Issued: 03/01/2011
• Est. Priority Date: 10/23/1998
• Status: Active Grant

• Current Assignee: Gambro Lundia AB (Baxter International Inc.)
• Original Assignee: Gambro Lundia AB (Baxter International Inc.)
• Inventors: Asbrink, Perry, Nilsson, Eddie, Mishkin, Gary Joel, Sternby, Jan Peter
• Primary Examiner(s): Deak; Leslie R
• Application Number:
  US12/399,792
• Publication Number:
  US 20090171261A1
• Time in Patent Office: 725 Days
• Field of Search: 604/4.01, 604/5.01, 604/5.04, 604/6.1, 604/6.09, 210/646, 210/645, 210/739, 422/44, 137/601.05, 137/15.21, 137/896, 137/597, 137/625.43, 251/228, 251/298, 251/304
• US Class Current: 604/6.09
• CPC Class Codes: A61M 1/16 with membranes
• CPC Class Codes: A61M 1/1607 before use, i.e. upstream of dialyser
• CPC Class Codes: A61M 1/1609 after use, i.e. downstream of dialyser
• CPC Class Codes: A61M 1/361 before treatment
• CPC Class Codes: A61M 1/3656 Monitoring patency or flow at connection sites; Detecting disconnections
• CPC Class Codes: A61M 1/3658 Indicating the amount of purified blood recirculating in the fistula or shunt
• CPC Class Codes: A61M 1/3663 Flow rate transducers; Flow integrators
• CPC Class Codes: A61M 2202/0498 Urea
• CPC Class Codes: A61M 2205/15 Detection of leaks
• CPC Class Codes: A61M 2205/3317 Electromagnetic, inductive or dielectric measuring means
• CPC Class Codes: A61M 2205/3324 PH measuring means
• CPC Class Codes: A61M 2205/3331 Pressure; Flow
• CPC Class Codes: G01F 9/00 Measuring volume flow relative to another variable, e.g. of liquid fuel for an engine

Abstract

A switch valve for use in an extracorporeal blood flow circuit comprises a valve housing having a chamber, four openings communicating with the chamber, and a valve member located in the valve chamber. A first opening is to be connected to a patient via an arterial cannula, a second opening is to be connected to a patient via an venous cannula, a third opening is to be connected to a first inlet/outlet of a blood treatment device, and a fourth opening is to be connected to a second inlet/outlet of a blood treatment device. The valve member is movable within the valve housing to fluidly connect the first opening to either the third or the fourth opening and to fluidly connect the second opening to either the third or the fourth opening. The width of the valve member is smaller than a peripheral dimension of the openings.

Claims

1. A method of estimating fluid flow rate (Qa) in a fluid flow access, comprising:

in a normal position, removing a first fluid flow from said access at a removal position to an external flow circuit comprising a dialyzer having a semipermeable membrane, said first fluid flow passing along said membrane at one side thereof and a dialysis fluid being emitted from the other side thereof, and returning said first fluid flow from said external flow circuit to said access at a return position downstream of said removal position;

measuring a first conductivity of the dialysis fluid emitted from the dialyzer in said normal position;

in a reversed position wherein the removal position and the return position are reversed, removing a second fluid flow and measuring a second conductivity of the dialysis fluid emitted from the dialyzer in said reversed position; and

calculating the fluid flow rate (Qa) in said flow access utilizing said measured first and second conductivities.

2. The method of claim 1, wherein calculating the fluid flow rate (Qa) in said flow access takes place by the formula:

Cd norm/Cd rev=1+K/Qa

in which Cd norm and Cd rev are values proportional to the conductivity of the dialysis fluid in the normal and reversed positions, respectively, and K is the clearance of the dialyzer and Qa is the access flow rate, wherein conductivity of the dialysis fluid is measured as the conductivity difference between dialysis fluid at the dialyzer outlet and dialysis fluid at the dialyzer inlet.

3. The method as claimed in claim 2, wherein said flow access is a blood flow access in a mammal.

4. The method as claimed in claim 3, wherein said flow access is a hemodialysis access in the nature of an arterio-venous shunt or fistula, and wherein the dialyzer clearance K is replaced by the effective dialyzer clearance Keff obtained by taking into account a cardiopulmonary recirculation.

5. The method of claim 4, wherein said Keff is obtained by the equation

Keff=Qd*Cd/Cs

where Qd is the flow of dialysis fluid emitted from the dialyzer, Cd is the conductivity of the dialysis fluid and Cs is the conductivity of systemic venous blood, wherein conductivity of the systemic venous blood is measured as the conductivity difference between systemic venous blood at the dialyzer inlet and dialysis fluid at the dialyzer inlet.

6. The method of claim 5, wherein the conductivity of the systemic venous blood is measured by:

stopping the blood flow in the external flow circuit for a time period sufficient to allow the cardiopulmonary circulation to equalize;

starting the blood flow in the external flow circuit with a slow speed to fill the arterial line with fresh blood before the measurement;

measuring the equalized conductivity of the dialysis fluid at a low dialysate flow rate or at isolated ultrafiltration.

7. An apparatus for extracorporeal blood treatment comprising:

a dialyzer having first and second compartments separated by a semi-permeable membrane;

a blood circuit having;

a blood removal line for connecting, in a normal condition, an inlet of the first compartment to a blood access of a patient at a first connecting point, and a blood return line for connecting, in the normal condition, an outlet of the first compartment to the blood access of the patient at a second connecting point;

a reversal means for switching the connection of the blood removal line and the blood return line to the blood access so that, in a reverse condition, the first connecting point is in fluid communication with the outlet of the first compartment and the second connecting point is in fluid communication with the inlet of the first compartment;

a dialysis liquid circuit having;

a dialysis liquid line for supplying a dialysis liquid to an inlet of the second compartment, and a dialysate line for draining a dialysate from an outlet of the second compartment;

a sensor connected to the dialysate line for measuring, in the normal condition, a first conductivity of the dialysate, and for measuring, in the reverse condition, a second conductivity of the dialysate;

a calculating means for calculating a fluid flow rate (Qa) in the blood access from the first and second conductivities and from a clearance of the dialyzer.

8. The apparatus of claim 7, wherein the calculating means calculates the fluid flow rate (Qa) in the blood access by the formula:

Cd norm/Cd rev=1+K/Qa

in which Cd norm and Cd rev are values proportional to the conductivities of said dialysate in the normal and reversed conditions, respectively, and K is the clearance of the dialyzer and Qa is the access flow rate, wherein conductivity of the dialysate is measured as the conductivity difference between dialysate at the dialyzer outlet and dialysis liquid at the dialyzer inlet.

9. The apparatus as claimed in claim 8, wherein the blood access is a hemodialysis access in the nature of an arterio-venous shunt or fistula, and wherein the dialyzer clearance K is replaced by the effective dialyzer clearance Keff obtained by taking into account a cardiopulmonary recirculation.

10. The apparatus of claim 9, wherein said clearance Keff is obtained by the equation Keff=Qd*Cd/Cs

where Qd is the flow of dialysate, Cd is the conductivity of said dialysate and Cs is the conductivity of systemic venous blood, wherein conductivity of the systemic venous blood is measured as the conductivity difference between systemic venous blood at the dialyzer inlet and dialysis liquid at the dialyzer inlet.

11. The apparatus of claim 10, further comprising means for measuring the conductivity of the systemic venous blood, including:

means for stopping a blood flow in the blood circuit for a time period sufficient to allow the cardiopulmonary circulation to equalize;

means for starting the blood flow in the external blood circuit with a slow speed to fill the blood removal line with fresh blood before the measurement;

means for measuring an equalized conductivity of the dialysate at a low dialysate flow rate or at isolated ultrafiltration.