초록 ▼

A method and apparatus for optimizing parameters of a hollow membrane filter results in a relatively small filter when a predetermined, substantially constant, driving pressure drop is applied between the inlet and the outlet of the filter. The method includes simultaneous solution of a set of equat

A method and apparatus for optimizing parameters of a hollow membrane filter results in a relatively small filter when a predetermined, substantially constant, driving pressure drop is applied between the inlet and the outlet of the filter. The method includes simultaneous solution of a set of equations to specify fiber length, number and internal diameter. A system including a computer can make optimized filters in response to the determined parameters.

대표청구항 ▼

In a blood filtration system comprising a hollow fiber membrane device for separating filtrate from blood comprising a housing having a blood inlet port, a blood outlet port, and a filtrate outlet port, the membrane device including a preselected number (N) of hollow fiber membrane elements carried

In a blood filtration system comprising a hollow fiber membrane device for separating filtrate from blood comprising a housing having a blood inlet port, a blood outlet port, and a filtrate outlet port, the membrane device including a preselected number (N) of hollow fiber membrane elements carried within the housing, each element having a preselected length (L) and a preselected internal diameter (D), and apparatus associated with the hollow fiber membrane device for conveying blood having a determinable hematocrit (Hi) and viscosity (mi) of blood through the blood inlet port of the membrane device, second means for establishing a flow rate (Qi) of filtrate from the filtrate outlet port of the membrane device, and third means for conveying filtrate-poor blood from the blood outlet port of the membrane device, a method of operating the system subject to a selected safety factor for red blood cell hemolysis (HSF) comprising the step of simultaneously obtaining the following performance relationships: Performance Relationships(1) Qf=K1, QxN(1-x)L(1-y)D(1-3x) where K1=0.0002206 [ln (95/Hi)]zII(1-x)(8/15)x and x=0.9141; y=0.3619; z=0.8528; Q is the average blood flow rate through the device defined as the blood flow rate through the blood inlet port (Qi) minus one-half the filtrate flow rate through the filtrate outlet port, or Qi-Qf/2; and Hi is the hematocrit (expressed in %) of the blood entering the blood inlet port of the device; PerformanceRelationship(2) [Figure] where m3.236206/[(1-Hi)/1001.440442; Lp is the potting length of the fibers, expressed in cm; P is the pressure drop across the device expressed in mmHg; and [Figure] (theapplicableconversionfactorforconsistentunits); and PerformanceRelationship(3) [Figure] where (TMP)h= [Figure] rp is the average pore radius of the membrane; (-20 mmHg) is the assumed filtrate collection chamber pressure; and [Figure] is the shear rate for hemolysis.