[go: up one dir, main page]

US3567113A - Miniature, portable, self-powered, high speed, clinical centrifuge - Google Patents

Miniature, portable, self-powered, high speed, clinical centrifuge Download PDF

Info

Publication number
US3567113A
US3567113A US808118A US3567113DA US3567113A US 3567113 A US3567113 A US 3567113A US 808118 A US808118 A US 808118A US 3567113D A US3567113D A US 3567113DA US 3567113 A US3567113 A US 3567113A
Authority
US
United States
Prior art keywords
rotor head
miniature
centrifuge
powered
portable
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Expired - Lifetime
Application number
US808118A
Inventor
Marion J Stansell
Oskar G Langner
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
United States Department of the Air Force
Original Assignee
United States Department of the Air Force
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by United States Department of the Air Force filed Critical United States Department of the Air Force
Application granted granted Critical
Publication of US3567113A publication Critical patent/US3567113A/en
Anticipated expiration legal-status Critical
Expired - Lifetime legal-status Critical Current

Links

Images

Classifications

    • B—PERFORMING OPERATIONS; TRANSPORTING
    • B04—CENTRIFUGAL APPARATUS OR MACHINES FOR CARRYING-OUT PHYSICAL OR CHEMICAL PROCESSES
    • B04B—CENTRIFUGES
    • B04B13/00—Control arrangements specially designed for centrifuges; Programme control of centrifuges
    • B—PERFORMING OPERATIONS; TRANSPORTING
    • B04—CENTRIFUGAL APPARATUS OR MACHINES FOR CARRYING-OUT PHYSICAL OR CHEMICAL PROCESSES
    • B04B—CENTRIFUGES
    • B04B5/00—Other centrifuges
    • B—PERFORMING OPERATIONS; TRANSPORTING
    • B04—CENTRIFUGAL APPARATUS OR MACHINES FOR CARRYING-OUT PHYSICAL OR CHEMICAL PROCESSES
    • B04B—CENTRIFUGES
    • B04B5/00—Other centrifuges
    • B04B5/04—Radial chamber apparatus for separating predominantly liquid mixtures, e.g. butyrometers
    • B04B5/0407—Radial chamber apparatus for separating predominantly liquid mixtures, e.g. butyrometers for liquids contained in receptacles
    • B04B5/0414—Radial chamber apparatus for separating predominantly liquid mixtures, e.g. butyrometers for liquids contained in receptacles comprising test tubes

Definitions

  • the energizing means for the motor is capable of being charged by a removable charger. Operation of the centrifuge rotates the rotor head at a high speed thereby separating blood cells from blood plasma within a capillary tube located within said rotor head. A timer regulates the length of time the: centrifuge is in operag tion.
  • This invention relates generally to centrifuges, and more particularly to a miniature, portable, hand-carried, selfpowered, high-speed clinical centrifuge capable of performing rapid hematocrit determinations and plasma preparation.
  • Blood consists of two major fractions, a fluid portion and a cellular portion.
  • the fluid portion (plasma) is made up of proteins, carbohydrates, lipids (fats), nonprotein nitrogenous material, and salts; the cellular portion contains erythrocytes (red blood cells), leukocytes '(white blood cells), and platelets.
  • erythrocytes red blood cells
  • leukocytes '(white blood cells) erythrocytes
  • platelets erythrocytes
  • the cellular elements are included in the clot and the remaining fluid is the serum, which differs from plasma only by the loss of fibrinogen (a protein) utilized in the process of clotting.
  • Blood is a dynamic tissue, the measure of which at any given time represents a balance between the rate of formation and the rate of utilization, storage, or excretion of all of its elements.
  • the cellular elements are formed in the bone marrow and lymph nodes. They are destroyed primarily in the spleen or elsewhere in the reticuloendothelial system of the body. In the presence of disease, these cellular elements may be destroyed at a rapid rate.
  • the dissolved substances of the plasma similarly represent a balance between the amount of materials ingested or formed in the various organs of the body, especially the liver, and the rate of disappearance.
  • the volume occupied by the packed cellular elements of the blood, in relation to the total volume, is referred to as the hematocrit.
  • the normal range for men is 42-52 percent, for women 37-47 percent. Variations fromthe normal usually parallel the hemoglobin and erythrocyte values, but in pernicious anemia the hematocrit (and therefore the color index) is disproportionate. In general, anemias exhibit a low hematocrit value, whereas polycythemias or dehydration reveal high values. Calculation of cellular indices is made possible by relating the hematocrit values to the number of erythrocytes and the hemoglobin concentration. This information is of value in the diagnosis of the many types of erythrocytic disorders, particularly pernicious anemia, other macrocytic anemias, congenital hemolytic anemia, and the secondary anemias.
  • the instant invention overcomes the problems heretofore encountered and as set forth above.
  • the invention is a miniabody constituents.
  • the centrifuge of this invention contains a series string of rechargable nickel-cadmium cells so that it can perform over separate centrifugations before recharging, if necessary. Furthermore, the centrifuge is equipped with a carrying handle so that it may be hand carried'during operation.
  • the unit is also equipped with an automatic timer, a brake button for rapid deceleration, a rotor head which accommodates a plurality of sizes of capillary tubes, a built-in surge resistor to prevent initial current surge and thus prolong battery life and motor commutator life, and its own lightweight, detachable, charger base which can be plugged into a variety of line voltages of varying frequency;
  • the centrifuge of this invention is of high value in conducting measurements during aeromedical evacuation operations, on flight lines free of external power sources, in combat areas, in hospital wards, at the bedside, in clinical laboratories or under any conditions where rapid hematocn't determinations are desired or where plasma is needed immediately for chemical analysis.
  • the centrifuge of the instant invention is completely contained and requires no external power source for prolonged periods.
  • the charger unit by using a 6i) Hz. transformer can be used on either 60 Hz. or 400 Hz. By simple circuit modification, the charger can operate on 24 to 28 volts DC or on any other available power source.
  • the centrifuge furthermore, features a high speed (up to 18,000 r.p.m.) motor, thus permitting especially short (30 sec.) centrifugation durations.
  • the unit also has a thermal surge resistor which minimizes initial current surge, thus adding greatly to battery charge life and motor commutator life.
  • a spring return, momentary contact, brake switch is utilized to bring the centrifuge to a rapid stop.
  • the brake shorts the armature winding, and the reverse EMF creates an opposing magnetic field which brings the centrifuge rotor to a total stop from full 'speed in approximately 12 seconds.
  • the internal nickel-cadmium cells, arranged radially about the motor can'be recharged hundreds of times and their physical arrangement lends stability to the centrifuge.
  • the centrifuge has its own handle permitting it to be carried while in operation and an O-ring seal is located between its body and its hinged lid. It also has vent holes connecting the rotor chamber to the outside thereby facilitating partial evacuation of the rotor chamber thus permitting a greater top angular velocity.
  • a miniature hematocrit reading scale and a simple magnifying lens can be attached to and carried with the centrifuge of the instant invention.
  • FIG. 1 represents a front elevational view of the clinical centrifuge and charger of this invention in cross section;
  • FIG. 2 represents a schematic diagram of the electrical cir' cuitry of the clinical centrifuge and charger of this invention
  • HO. 3 represents an isometric view of the clinical centrifuge of this invention showing the rotor head cover in its removed position;
  • FIG. 4 is a cross-sectional view taken along line 4-4 of FIG. 3 in a reduced scale.
  • FIG. 1 of the drawing numeral represents the clinical centrifuge of this invention about to be inserted within its charger 12.
  • the centrifuge 10 has a housing 14 made up of cylindrical side portion 16 and base portion 18.
  • any suitable motor 20 such as a high-speed 24 volt DC motor fixedly secured to inner housing wall 22 and motor mounting plate 23.
  • Surrounding motor 20 is a plurality of rechargable batteries, 24, shown more clearly in FIG. 4.
  • the batteries 24 may be of the nickel-cadmium type and are connected in series.
  • the total no-load voltage available from five such batteries is over 30 volts. This voltage stabilizes at near 25 volts DC during operation with the surge resistor shown in the circuit of FIG. 5.
  • a rotor head 26 is secured to the rotor shaft 28 of motor 20 by any suitable securing means such as by key 30 fixedly secured to shaft 28.
  • the rotor head 26 has a plurality of grooves 32 (shown clearly in FIG. 3) therein of various sizes for holding capillary tubes.
  • the rotor head 26 further has a raised lip 34 around its periphery.
  • the lip 34 and grooves 32 are lined with a thin resilient substance 36 such as neoprene, thus obviating breakage of the capillary tubes (not shown) placed in the rotor head grooves 32.
  • the grooves 32 are of various sizes to accommodate microhematocrit capillary tubes as well as larger capillary tubes (heparinized) used to prepare volumes of plasma for chemical analysis.
  • a rotor head cover 38 screws onto the rotor shaft 28. The cover 38 holds the capillary tubes in place within grooves 32 during operation of the centrifuge 10.
  • a knurled knob 40 permits easy removal of the cover 38 when the rotor head grooves 32 are to be exposed.
  • a space 42 surrounds the rotor head 26. This space is partially evacuated during operation through the pumping action of the rotating rotor head 26. This evacuation minimizes air turbulence and permits higher rotor speeds.
  • FIG. 2 There is a layer 44 of insulatory material at the bottom and at the top of batteries 24.
  • Upper vent holes 46 permit evacuation of the rotor head chamber 42 while bottom vent holes 48 establish continuity with the upper vent holes 46, facilitating evacuation of air through the bottom of the centrifuge 10.
  • a lid 54 has a hinge 56 on one side and a lockingtype clasp means 58 on the other side (see FIG. 3).
  • An O-ring 60 provides a tight joint between the centrifuge housing 14 and lid 54.
  • numeral 12 designates the nickelcadmium cell charger.
  • the charger 12 has a space 62 into which the centrifuge base portion 18 fits when it is to be charged or operated from external power.
  • a charger plug 64 having an insulation 66 and terminals 68 is imbedded within the charger base 69.
  • the terminals 68 mate with terminals 70 of the charger jack 52.
  • Appropriate polarity is assured by means of a projection 72 on the centrifuge base portion 18 which mates with a slot 74 in the sidewall of charger base 69.
  • a space 76 within the charger 12 houses an appropriate stepdown transformer and diode rectifiers, etc.
  • FIG. 4 shows in more detail the position of batteries 24 within housing 14 surrounding charger jack 52.
  • the timerforming part of timer mechanism 78 is located within chamber 84.
  • the circuit diagram 86 of the centrifuge 10 is shown clearly irTFIG. 2.
  • a blood sample is obtained by means of capillary puncture (e.g. finger stick) or venipuncture.
  • the heparinized capillary tube not shown is filled from one-half to three-fourths full with t e blood. he blood is moved back and forth within the tube to promote mixing with the anticoagulant. The tube is then blocked at one end with a minute piece of clay or other pliable inert material.
  • the sealed tube is placed into an appropriately sized rotor head groove 32, the rotor head cover 38 is screwed in place and the lid 54 is shut and locked.
  • the automatic timer mechanism 78 is set for the desired period of centrifugation (normally 30 seconds). While the centrifuge is operating, it may be carried or set aside onto most any irregular surface. After the timer switch opens, braking can be greatly increased by depressing the red brake button 80. The brake shorts the armature winding, and the reverse EMF creates an opposing magnetic field which brings the centrifuge rotor to a total stop from full speed in approximately 12 seconds.
  • the lid 54 is opened, the rotor head cover 38 is unscrewed, and the capillary tube is removed. The tube is then placed onto a microhematocrit reading scale and the percent packed cell volume is read off directly.
  • the centrifuge 10 can be conveniently placed on its charger 12 so that the ni-cad cells 24 are always in a fully charged state and the centrifuge 10 will be always ready for a self-powered mission wherever it may be needed.
  • a miniature, portable, self-powered, high-speed clinical centrifuge comprising a housing, a motor means fixedly secured to said housing, a means for energizing said motor means adjacent thereto, a rotor head having a plurality of grooves therein operably connected to said motor means, a rotor head cover removably secured to said motor means and proximate said rotor head, a lid removably secured to said housing for covering said rotor head and rotor head cover, said housing having a base portion, said base portion having a charger jack mounted therein and operably connected with said energizing means, and a removable charger having a charger plug thereon capable of being inserted within said charger jack for charging said energizing means, whereby energizing of said motor means operates to rotate said rotor head at a high speed thereby separating blood cells from blood plasma within a capillary tube located within said grooves.
  • a miniature, portable, self-powered, high-speed clinical centrifuge as defined in claim 1 further comprising a timer mechanism within said housing and operably associated with said motor means for regulating the operation thereof.
  • a miniature, portable, self-powered, high-speed clinical centrifuge as defined in claim 2 further comprising a brake within said housing and operably associated with said motor means for quickly bringing said rotor head to a total stop.

Landscapes

  • Centrifugal Separators (AREA)

Abstract

A portable, miniature, self-powered, high-speed, clinical centrifuge having a housing, a motor, an energizing means, a rotor head and a rotor head cover. The energizing means for the motor is capable of being charged by a removable charger. Operation of the centrifuge rotates the rotor head at a high speed thereby separating blood cells from blood plasma within a capillary tube located within said rotor head. A timer regulates the length of time the centrifuge is in operation.

Description

United States Patent [72] Inventors [2 l] Appl. No. [22] Filed [45] Patented [73] Assignee Marion J. Stansell;
Oskar G. Langner, San Antonio, Tex. 808,118
Mar. 18, 1969 Mar. 2, 1971 the United States of America as represented by the Secretary of Air Force [54] MINIATURE, PORTABLE, SELF POWERED, HIGH SPEED, CLINICAL CENTRIFUGE 5 Claims, 4 Drawing Figs.
[52] US. Cl 233/24, 233/26 [51] Int. Cl B04b 9/04 [50] Field of Search 233/24, 26
[5 6] References Cited UNITED STATES PATENTS 7 2,783,938 3/1957 Grela et al. 233/26X 2,789,757 l/i957 Melton 233/26 3,168,473 2/1965 Goda et al.. 233/26 3,233,825 2/1966 Lomb 233/26 FOREIGN PATENTS 521,880 6/1940 Great Britain 233/24 Primary Examiner--William 1. Price Attorneys-Harry A. Herbert, Jr. and Jacob N. Erlich ABSTRACT: A portable, miniature, self-powered, high-speed, clinical centrifuge having a housing, a motor, an energizing means, a rotor head and a rotor head cover. The energizing means for the motor is capable of being charged by a removable charger. Operation of the centrifuge rotates the rotor head at a high speed thereby separating blood cells from blood plasma within a capillary tube located within said rotor head. A timer regulates the length of time the: centrifuge is in operag tion.
MINIATURE, PORTABLE, SELF POWERED, HIGH SPEED, CLINICAL CEN'IRIFUGE BACKGROUND OF THE INVENTION This invention relates generally to centrifuges, and more particularly to a miniature, portable, hand-carried, selfpowered, high-speed clinical centrifuge capable of performing rapid hematocrit determinations and plasma preparation.
Blood consists of two major fractions, a fluid portion and a cellular portion. The fluid portion (plasma) is made up of proteins, carbohydrates, lipids (fats), nonprotein nitrogenous material, and salts; the cellular portion contains erythrocytes (red blood cells), leukocytes '(white blood cells), and platelets. When blood clots, the cellular elements are included in the clot and the remaining fluid is the serum, which differs from plasma only by the loss of fibrinogen (a protein) utilized in the process of clotting.
Blood is a dynamic tissue, the measure of which at any given time represents a balance between the rate of formation and the rate of utilization, storage, or excretion of all of its elements. The cellular elements are formed in the bone marrow and lymph nodes. They are destroyed primarily in the spleen or elsewhere in the reticuloendothelial system of the body. In the presence of disease, these cellular elements may be destroyed at a rapid rate. The dissolved substances of the plasma similarly represent a balance between the amount of materials ingested or formed in the various organs of the body, especially the liver, and the rate of disappearance.
The volume occupied by the packed cellular elements of the blood, in relation to the total volume, is referred to as the hematocrit. The normal range for men is 42-52 percent, for women 37-47 percent. Variations fromthe normal usually parallel the hemoglobin and erythrocyte values, but in pernicious anemia the hematocrit (and therefore the color index) is disproportionate. In general, anemias exhibit a low hematocrit value, whereas polycythemias or dehydration reveal high values. Calculation of cellular indices is made possible by relating the hematocrit values to the number of erythrocytes and the hemoglobin concentration. This information is of value in the diagnosis of the many types of erythrocytic disorders, particularly pernicious anemia, other macrocytic anemias, congenital hemolytic anemia, and the secondary anemias.
l'leretofore, it was either impossible or required long, tedious and laborious medical operations to perform rapid hematocrit determinations and plasma preparation. The circumstances under which these determinations and preparations usually had to be performed included aeromedical evacuation operations, rugged combat zone operations, bedside operations or on flight lines and staging areas. In many instances, there is no external power available and there is no flat laboratory benches available on which to place the instruments which perform these determinations. Furthermore, the apparatus heretofore in use for performing'hematocrit determinations and plasma preparation were cumbersome and therefore not easily lifted or carried. Thus, in many instances proper medical assistance could not be carried out and many lives were needlessly lost.
SUMMARY OF THE INVENTION The instant invention overcomes the problems heretofore encountered and as set forth above. The invention is a miniabody constituents.
The centrifuge of this invention contains a series string of rechargable nickel-cadmium cells so that it can perform over separate centrifugations before recharging, if necessary. Furthermore, the centrifuge is equipped with a carrying handle so that it may be hand carried'during operation. The unit is also equipped with an automatic timer, a brake button for rapid deceleration, a rotor head which accommodates a plurality of sizes of capillary tubes, a built-in surge resistor to prevent initial current surge and thus prolong battery life and motor commutator life, and its own lightweight, detachable, charger base which can be plugged into a variety of line voltages of varying frequency; The centrifuge of this invention is of high value in conducting measurements during aeromedical evacuation operations, on flight lines free of external power sources, in combat areas, in hospital wards, at the bedside, in clinical laboratories or under any conditions where rapid hematocn't determinations are desired or where plasma is needed immediately for chemical analysis.
The centrifuge of the instant invention is completely contained and requires no external power source for prolonged periods. The charger unit, by using a 6i) Hz. transformer can be used on either 60 Hz. or 400 Hz. By simple circuit modification, the charger can operate on 24 to 28 volts DC or on any other available power source. The centrifuge, furthermore, features a high speed (up to 18,000 r.p.m.) motor, thus permitting especially short (30 sec.) centrifugation durations. The unit also has a thermal surge resistor which minimizes initial current surge, thus adding greatly to battery charge life and motor commutator life. A spring return, momentary contact, brake switch is utilized to bring the centrifuge to a rapid stop. The brake shorts the armature winding, and the reverse EMF creates an opposing magnetic field which brings the centrifuge rotor to a total stop from full 'speed in approximately 12 seconds. The internal nickel-cadmium cells, arranged radially about the motor can'be recharged hundreds of times and their physical arrangement lends stability to the centrifuge. The centrifuge has its own handle permitting it to be carried while in operation and an O-ring seal is located between its body and its hinged lid. It also has vent holes connecting the rotor chamber to the outside thereby facilitating partial evacuation of the rotor chamber thus permitting a greater top angular velocity. A miniature hematocrit reading scale and a simple magnifying lens can be attached to and carried with the centrifuge of the instant invention.
It is therefore an object of this invention to provide a miniature, clinical centrifuge which will permit rapid hematocrit determinations and plasma preparation.
It is another object of this invention to provide a miniature, clinical centrifuge which eliminates the need for external power for prolonged periods of time.
It is a further object of this invention to provide a miniature, clinical centrifuge which is readily transportable and which can be easily lifted with one hand and carried by its own handle.
It is still another object of this invention to provide a miniature, clinical centrifuge which utilizes conventional, currently available components that lend themselves to standard massproducing manufacturing techniques.
For a better understanding of the present invention, together with other and further objects thereof, reference is made to the following description taken in connection with the accompanying drawing and its scope will be pointed out in the appended claims:
DESCRIPTION OF THE DRAWING FIG. 1 represents a front elevational view of the clinical centrifuge and charger of this invention in cross section;
FIG. 2 represents a schematic diagram of the electrical cir' cuitry of the clinical centrifuge and charger of this invention;
HO. 3 represents an isometric view of the clinical centrifuge of this invention showing the rotor head cover in its removed position; and
FIG. 4 is a cross-sectional view taken along line 4-4 of FIG. 3 in a reduced scale.
Referring now to FIG. 1 of the drawing, numeral represents the clinical centrifuge of this invention about to be inserted within its charger 12. The centrifuge 10 has a housing 14 made up of cylindrical side portion 16 and base portion 18. Located within housing 14 is any suitable motor 20 such as a high-speed 24 volt DC motor fixedly secured to inner housing wall 22 and motor mounting plate 23. Surrounding motor 20 is a plurality of rechargable batteries, 24, shown more clearly in FIG. 4. The batteries 24 may be of the nickel-cadmium type and are connected in series. The total no-load voltage available from five such batteries is over 30 volts. This voltage stabilizes at near 25 volts DC during operation with the surge resistor shown in the circuit of FIG. 5.
Referring to FIGS. 1 and 3, a rotor head 26 is secured to the rotor shaft 28 of motor 20 by any suitable securing means such as by key 30 fixedly secured to shaft 28. The rotor head 26 has a plurality of grooves 32 (shown clearly in FIG. 3) therein of various sizes for holding capillary tubes. The rotor head 26 further has a raised lip 34 around its periphery. The lip 34 and grooves 32 are lined with a thin resilient substance 36 such as neoprene, thus obviating breakage of the capillary tubes (not shown) placed in the rotor head grooves 32. The grooves 32 are of various sizes to accommodate microhematocrit capillary tubes as well as larger capillary tubes (heparinized) used to prepare volumes of plasma for chemical analysis. A rotor head cover 38 screws onto the rotor shaft 28. The cover 38 holds the capillary tubes in place within grooves 32 during operation of the centrifuge 10. A knurled knob 40 permits easy removal of the cover 38 when the rotor head grooves 32 are to be exposed. A space 42 surrounds the rotor head 26. This space is partially evacuated during operation through the pumping action of the rotating rotor head 26. This evacuation minimizes air turbulence and permits higher rotor speeds.
There is a layer 44 of insulatory material at the bottom and at the top of batteries 24. Upper vent holes 46 permit evacuation of the rotor head chamber 42 while bottom vent holes 48 establish continuity with the upper vent holes 46, facilitating evacuation of air through the bottom of the centrifuge 10. There is a space 50 located under motor 20 to accommodate wire leads from charger jack 52 and the surge resistor (shown in FIG. 2). A lid 54 has a hinge 56 on one side and a lockingtype clasp means 58 on the other side (see FIG. 3). An O-ring 60 provides a tight joint between the centrifuge housing 14 and lid 54.
Referring again to FIG. 1, numeral 12 designates the nickelcadmium cell charger. The charger 12 has a space 62 into which the centrifuge base portion 18 fits when it is to be charged or operated from external power. A charger plug 64 having an insulation 66 and terminals 68 is imbedded within the charger base 69. The terminals 68 mate with terminals 70 of the charger jack 52. Appropriate polarity is assured by means of a projection 72 on the centrifuge base portion 18 which mates with a slot 74 in the sidewall of charger base 69. The centrifuge 10, therefore, can be fit into the charger 12 in only one way. A space 76 within the charger 12 houses an appropriate stepdown transformer and diode rectifiers, etc.
FIG. 4 shows in more detail the position of batteries 24 within housing 14 surrounding charger jack 52. The timerforming part of timer mechanism 78 is located within chamber 84. The circuit diagram 86 of the centrifuge 10 is shown clearly irTFIG. 2.
MODE OF OPERATION A blood sample is obtained by means of capillary puncture (e.g. finger stick) or venipuncture. The heparinized capillary tube not shown is filled from one-half to three-fourths full with t e blood. he blood is moved back and forth within the tube to promote mixing with the anticoagulant. The tube is then blocked at one end with a minute piece of clay or other pliable inert material.
' The sealed tube is placed into an appropriately sized rotor head groove 32, the rotor head cover 38 is screwed in place and the lid 54 is shut and locked. The automatic timer mechanism 78 is set for the desired period of centrifugation (normally 30 seconds). While the centrifuge is operating, it may be carried or set aside onto most any irregular surface. After the timer switch opens, braking can be greatly increased by depressing the red brake button 80. The brake shorts the armature winding, and the reverse EMF creates an opposing magnetic field which brings the centrifuge rotor to a total stop from full speed in approximately 12 seconds. When the centrifuge rotor head 26 comes to a complete stop, the lid 54 is opened, the rotor head cover 38 is unscrewed, and the capillary tube is removed. The tube is then placed onto a microhematocrit reading scale and the percent packed cell volume is read off directly.
During storage periods, the centrifuge 10 can be conveniently placed on its charger 12 so that the ni-cad cells 24 are always in a fully charged state and the centrifuge 10 will be always ready for a self-powered mission wherever it may be needed.
Although the invention has been described with reference to a particular embodiment, it will be understood to those skilled in the art that the invention is capable of a variety of alternative embodiments within the spirit and scope of the appended claims:
We claim:
1. A miniature, portable, self-powered, high-speed clinical centrifuge comprising a housing, a motor means fixedly secured to said housing, a means for energizing said motor means adjacent thereto, a rotor head having a plurality of grooves therein operably connected to said motor means, a rotor head cover removably secured to said motor means and proximate said rotor head, a lid removably secured to said housing for covering said rotor head and rotor head cover, said housing having a base portion, said base portion having a charger jack mounted therein and operably connected with said energizing means, and a removable charger having a charger plug thereon capable of being inserted within said charger jack for charging said energizing means, whereby energizing of said motor means operates to rotate said rotor head at a high speed thereby separating blood cells from blood plasma within a capillary tube located within said grooves.
2. A miniature, portable, self-powered, high-speed clinical centrifuge as defined in claim 1 further comprising a timer mechanism within said housing and operably associated with said motor means for regulating the operation thereof.
3. A miniature, portable, self-powered, high-speed clinical centrifuge as defined in claim 2 further comprising a brake within said housing and operably associated with said motor means for quickly bringing said rotor head to a total stop.
4. A miniature, portable, self-powered, high-speed clinical centrifuge as defined in claim 3 wherein said motor means is provided with a shaft secured thereto, said rotor head being fixedly secured to said shaft and said rotor head cover being removably secured to said shaft.
5. A miniature, portable, self-powered, high-speed clinical centrifuge as defined in claim 4 wherein said rotor head further has a raised lip around its periphery, said lip and said grooves being lined with a thin resilient substance to prevent breakage of capillary tubes placed therein.

Claims (5)

1. A miniature, portable, self-powered, high-speed clinical centrifuge comprising a housing, a motor means fixedly secured to said housing, a means for energizing said motor means adjacent thereto, a rotor head having a plurality of grooves therein operably connected to said motor means, a rotor head cover removably secured to said motor means and proximate said rotor head, a lid removably secured to said housing for covering said rotor head and rotor head cover, said housing having a base portion, said base portion having a charger jack mounted therein and operably connected with said energizing means, and a removable charger having a charger plug thereon capable of being inserted within said charger jack for charging said energizing means, whereby energizing of said motor means operates to rotate said rotor head at a high speed thereby separating blood cells from blood plasma within a capillary tube located within said grooves.
2. A miniature, portable, self-powered, high-speed clinical centrifuge as defined in claim 1 further comprising a timer mechanism within said housIng and operably associated with said motor means for regulating the operation thereof.
3. A miniature, portable, self-powered, high-speed clinical centrifuge as defined in claim 2 further comprising a brake within said housing and operably associated with said motor means for quickly bringing said rotor head to a total stop.
4. A miniature, portable, self-powered, high-speed clinical centrifuge as defined in claim 3 wherein said motor means is provided with a shaft secured thereto, said rotor head being fixedly secured to said shaft and said rotor head cover being removably secured to said shaft.
5. A miniature, portable, self-powered, high-speed clinical centrifuge as defined in claim 4 wherein said rotor head further has a raised lip around its periphery, said lip and said grooves being lined with a thin resilient substance to prevent breakage of capillary tubes placed therein.
US808118A 1969-03-18 1969-03-18 Miniature, portable, self-powered, high speed, clinical centrifuge Expired - Lifetime US3567113A (en)

Applications Claiming Priority (1)

Application Number Priority Date Filing Date Title
US80811869A 1969-03-18 1969-03-18

Publications (1)

Publication Number Publication Date
US3567113A true US3567113A (en) 1971-03-02

Family

ID=25197912

Family Applications (1)

Application Number Title Priority Date Filing Date
US808118A Expired - Lifetime US3567113A (en) 1969-03-18 1969-03-18 Miniature, portable, self-powered, high speed, clinical centrifuge

Country Status (1)

Country Link
US (1) US3567113A (en)

Cited By (26)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US3906890A (en) * 1973-05-24 1975-09-23 Corning Glass Works Blood smeared slide centrifuge
US4193538A (en) * 1977-05-17 1980-03-18 Compur-Electronic Gesellschaft Mit Beschrankter Haftung Apparatus for separating and measuring sample components
US4202487A (en) * 1978-02-22 1980-05-13 Beckman Instruments, Inc. Lipoprotein rotor lid
US4412830A (en) * 1982-06-24 1983-11-01 Beckman Instruments, Inc. Cover for centrifuge rotor
FR2565941A1 (en) * 1984-06-15 1985-12-20 Jouan SEALED CLOSURE DEVICE FOR A CONTAINER, IN PARTICULAR A CENTRIFUGER NACELLE
US4738655A (en) * 1987-06-17 1988-04-19 Utah Bioresearch, Inc. Apparatus and method for obtaining a rapid hematocrit
EP0334453A2 (en) * 1988-03-21 1989-09-27 Shell Internationale Researchmaatschappij B.V. A process for preparing non-porous, selective membrane layers
US5924972A (en) * 1998-03-24 1999-07-20 Turvaville; L. Jackson Portable D.C. powered centrifuge
US6536937B1 (en) * 2000-02-14 2003-03-25 Telios Orthopedic Systems, Inc. Self-contained base for a surgical cement mixing system, binding material mixing base, and surgical bone cement mixing system
US20030220181A1 (en) * 2002-05-21 2003-11-27 Kendro Laboratory Products, Lp Centrifuge rotor lid holder device
US20100184056A1 (en) * 2009-01-12 2010-07-22 Molecular Sensing, Inc. Sample collection and measurement in a single container by back scattering interferometry
US20100188665A1 (en) * 2009-01-12 2010-07-29 Molecular Sensing, Inc. Methods and systems for interferometric analysis
US20100291700A1 (en) * 2009-05-04 2010-11-18 Molecular Sensing, Inc. Analysis of membrane component interactions
US8502985B2 (en) 2007-12-10 2013-08-06 Molecular Sensing, Inc. Microfluidic systems
WO2013160668A2 (en) 2012-04-24 2013-10-31 Magna Parva Limited Miniaturised centrifugation apparatus
US20140371047A1 (en) * 2013-06-18 2014-12-18 L.U.M. Gmbh Centrifuge rotor
US20160030952A1 (en) * 2013-03-14 2016-02-04 Centricycle, Inc. Centrifuge device
US9273949B2 (en) 2012-05-11 2016-03-01 Vanderbilt University Backscattering interferometric methods
US9562853B2 (en) 2011-02-22 2017-02-07 Vanderbilt University Nonaqueous backscattering interferometric methods
US9638632B2 (en) 2010-06-11 2017-05-02 Vanderbilt University Multiplexed interferometric detection system and method
WO2017127248A1 (en) * 2016-01-18 2017-07-27 The Board Of Trustees Of The Leland Stanford Junior University Paperfuge: an integrated paper-based centrifugation and microfluidics platform for low-cost diagnostics
US10261013B2 (en) 2015-01-23 2019-04-16 Vanderbilt University Robust interferometer and methods of using same
US20190271683A1 (en) * 2012-04-09 2019-09-05 Western New England University Centrifuge
US10627396B2 (en) 2016-01-29 2020-04-21 Vanderbilt University Free-solution response function interferometry
US20200289738A1 (en) * 2019-03-11 2020-09-17 ABC Med Tech Corp. Centrifuge and method of use
US10900961B2 (en) 2007-09-20 2021-01-26 Vanderbilt University Free solution measurement of molecular interactions by backscattering interferometry

Citations (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
GB521880A (en) * 1937-11-30 1940-06-03 Hermes Patentverwertungs Gmbh Improvements in or relating to electrical drives for centrifuges particularly for use in plant for the production and/or treatment of explosive material
US2783938A (en) * 1954-11-15 1957-03-05 Internat Equipment Company Centrifuge for capillary tubes
US2789757A (en) * 1956-01-18 1957-04-23 William L Melton Oil testing centrifuge
US3168473A (en) * 1961-12-04 1965-02-02 Clay Adams Inc Microhematocrit reader for centrifuges
US3233825A (en) * 1963-02-11 1966-02-08 Lomb Paul Self-contained centrifuge

Patent Citations (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
GB521880A (en) * 1937-11-30 1940-06-03 Hermes Patentverwertungs Gmbh Improvements in or relating to electrical drives for centrifuges particularly for use in plant for the production and/or treatment of explosive material
US2783938A (en) * 1954-11-15 1957-03-05 Internat Equipment Company Centrifuge for capillary tubes
US2789757A (en) * 1956-01-18 1957-04-23 William L Melton Oil testing centrifuge
US3168473A (en) * 1961-12-04 1965-02-02 Clay Adams Inc Microhematocrit reader for centrifuges
US3233825A (en) * 1963-02-11 1966-02-08 Lomb Paul Self-contained centrifuge

Cited By (42)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US3906890A (en) * 1973-05-24 1975-09-23 Corning Glass Works Blood smeared slide centrifuge
US4193538A (en) * 1977-05-17 1980-03-18 Compur-Electronic Gesellschaft Mit Beschrankter Haftung Apparatus for separating and measuring sample components
US4202487A (en) * 1978-02-22 1980-05-13 Beckman Instruments, Inc. Lipoprotein rotor lid
US4412830A (en) * 1982-06-24 1983-11-01 Beckman Instruments, Inc. Cover for centrifuge rotor
FR2565941A1 (en) * 1984-06-15 1985-12-20 Jouan SEALED CLOSURE DEVICE FOR A CONTAINER, IN PARTICULAR A CENTRIFUGER NACELLE
EP0169099A1 (en) * 1984-06-15 1986-01-22 JOUAN, Société Anonyme dite Sealing closure for a container, especially for a centrifugal bucket
AU600574B2 (en) * 1987-06-17 1990-08-16 Separation Technology, Inc. Apparatus and method for obtaining a rapid hematocrit
EP0295771A2 (en) * 1987-06-17 1988-12-21 Separation Technology, Inc. Apparatus and method for obtaining a rapid hematocrit
EP0295771A3 (en) * 1987-06-17 1990-01-24 Separation Technology, Inc. Apparatus and method for obtaining a rapid hematocrit
US4738655A (en) * 1987-06-17 1988-04-19 Utah Bioresearch, Inc. Apparatus and method for obtaining a rapid hematocrit
EP0334453A2 (en) * 1988-03-21 1989-09-27 Shell Internationale Researchmaatschappij B.V. A process for preparing non-porous, selective membrane layers
EP0334453A3 (en) * 1988-03-21 1990-09-26 Shell Internationale Researchmaatschappij B.V. A process for preparing non-porous, selective membrane layers
US5924972A (en) * 1998-03-24 1999-07-20 Turvaville; L. Jackson Portable D.C. powered centrifuge
US6536937B1 (en) * 2000-02-14 2003-03-25 Telios Orthopedic Systems, Inc. Self-contained base for a surgical cement mixing system, binding material mixing base, and surgical bone cement mixing system
US7090633B2 (en) * 2002-05-21 2006-08-15 Thermo Electron Laboratory Equipment Llc Centrifuge rotor lid holder device
US20030220181A1 (en) * 2002-05-21 2003-11-27 Kendro Laboratory Products, Lp Centrifuge rotor lid holder device
US10900961B2 (en) 2007-09-20 2021-01-26 Vanderbilt University Free solution measurement of molecular interactions by backscattering interferometry
US8502985B2 (en) 2007-12-10 2013-08-06 Molecular Sensing, Inc. Microfluidic systems
US20100184056A1 (en) * 2009-01-12 2010-07-22 Molecular Sensing, Inc. Sample collection and measurement in a single container by back scattering interferometry
US20100188665A1 (en) * 2009-01-12 2010-07-29 Molecular Sensing, Inc. Methods and systems for interferometric analysis
US20100291700A1 (en) * 2009-05-04 2010-11-18 Molecular Sensing, Inc. Analysis of membrane component interactions
US9638632B2 (en) 2010-06-11 2017-05-02 Vanderbilt University Multiplexed interferometric detection system and method
US9562853B2 (en) 2011-02-22 2017-02-07 Vanderbilt University Nonaqueous backscattering interferometric methods
US20190271683A1 (en) * 2012-04-09 2019-09-05 Western New England University Centrifuge
US10697957B2 (en) * 2012-04-09 2020-06-30 Western New England University Evaluation of hematocrit with manually-operated centrifuge
WO2013160668A2 (en) 2012-04-24 2013-10-31 Magna Parva Limited Miniaturised centrifugation apparatus
US9273949B2 (en) 2012-05-11 2016-03-01 Vanderbilt University Backscattering interferometric methods
US20160030952A1 (en) * 2013-03-14 2016-02-04 Centricycle, Inc. Centrifuge device
US9839921B2 (en) * 2013-03-14 2017-12-12 Sisu Global Health, Inc. Modular centrifuge devices and methods
US10335803B2 (en) * 2013-03-14 2019-07-02 Sisu Global Health, Inc. Modular centrifuge devices and methods
US20190314829A1 (en) * 2013-03-14 2019-10-17 Sisu Global Health, Inc. Modular centrifuge devices and methods
US10792675B2 (en) * 2013-03-14 2020-10-06 Sisu Global Health, Inc. Modular centrifuge devices and methods
US20140371047A1 (en) * 2013-06-18 2014-12-18 L.U.M. Gmbh Centrifuge rotor
US10261013B2 (en) 2015-01-23 2019-04-16 Vanderbilt University Robust interferometer and methods of using same
US11293863B2 (en) 2015-01-23 2022-04-05 Vanderbilt University Robust interferometer and methods of using same
WO2017127248A1 (en) * 2016-01-18 2017-07-27 The Board Of Trustees Of The Leland Stanford Junior University Paperfuge: an integrated paper-based centrifugation and microfluidics platform for low-cost diagnostics
US11331665B2 (en) 2016-01-18 2022-05-17 The Board Of Trustees Of The Leland Stanford Junior University Paperfuge: An integrated paper-based centrifugation and microfluidics platform for low-cost diagnostics
US10627396B2 (en) 2016-01-29 2020-04-21 Vanderbilt University Free-solution response function interferometry
US11143649B2 (en) 2016-01-29 2021-10-12 Vanderbilt University Free-solution response function interferometry
US20200289738A1 (en) * 2019-03-11 2020-09-17 ABC Med Tech Corp. Centrifuge and method of use
US11964092B2 (en) * 2019-03-11 2024-04-23 ABC Med Tech Corp. Portable centrifuge and method of use
US20240238498A1 (en) * 2019-03-11 2024-07-18 ABC Med Tech Corp. Portable Centrifuge Device and Method of Use

Similar Documents

Publication Publication Date Title
US3567113A (en) Miniature, portable, self-powered, high speed, clinical centrifuge
US4738655A (en) Apparatus and method for obtaining a rapid hematocrit
US4846974A (en) Centrifuge system and fluid container therefor
US3239136A (en) Centrifuge and centrifuge head for separating constituents of a liquid and a liner therefor
US4981585A (en) Centrifuge system and fluid container therefor
JPH11506828A (en) Determination of erythrocyte sedimentation velocity and erythrocyte volume fraction
ES8707799A1 (en) Liquid level adjusting and filtering device.
Kahn et al. Optimum centrifugation conditions for the preparation of platelet and plasma products
GB1351371A (en) Methods and apparatus for determining the volume of colloidal particles suspended in a liquid
GB1357231A (en) Test apparatus for use in testing a liquid
RU95113187A (en) METHOD FOR DETERMINING SYSTEM INFLAMMATION
AU2005203033B2 (en) Apparatus and method for obtaining rapid creamatocrit and caloric content values of milk
US10697957B2 (en) Evaluation of hematocrit with manually-operated centrifuge
US20210316317A1 (en) Devices and methods for portable and compact centrifugation
JPS62273065A (en) Device and method for sorting and separating fine solid granular substance suspended in liquid
US3240425A (en) Relatively small casing for a high speed miniature centrifuge
JPS60237368A (en) Biochemical analyzer
Blackwell et al. Simplified preparation of blood hemolysates for hemoglobin electrophoresis
CN211527987U (en) Reagent and sample processing equipment
CN116585756B (en) A device suitable for single molecule sampling equipment and sample storage
CN221982713U (en) Portable medical centrifuge
US20220347699A1 (en) Ultracompact Centrifuge, Specimen Container, and Methods of Use
GB2049930A (en) Multi-cell centrifugal analyser ring
Norberg et al. A hematocrit centrifuge
SU125340A1 (en) The method of defibrinating blood