U.S. patent number 3,841,515 [Application Number 05/131,803] was granted by the patent office on 1974-10-15 for apparatus for the preservation of biological substances.
This patent grant is currently assigned to Redeco, Inc.. Invention is credited to Ralph E. Schwartz.
United States Patent |
3,841,515 |
Schwartz |
October 15, 1974 |
APPARATUS FOR THE PRESERVATION OF BIOLOGICAL SUBSTANCES
Abstract
Biological substances such as blood are stored under pressure at
below 0.degree.C temperatures, in a substantially non-dilatable
vessel. Upon being introduced into the vessel, the temperature of
the vessel and the blood are reduced to 4.degree.C; when
equilibrium has been achieved the blood within the vessel is
precompressed at a controlled rate several thousand pounds per
square inch by the application of mechanical leverage to a vessel
piston. Thereafter, the vessel and blood are reduced to a final
temperature from 0.degree.C to -21.degree.C. This temperature
reduction, because of the conjunctive effect of the volumetric
expansion of the blood and non-dilation of the vessel,
self-generates a pressure from 15 to 35,000 p.s.i. The vessel may
now be stored at the final temperature and the blood within it
maintained without deleterious effects. CONTINUING DATA
Inventors: |
Schwartz; Ralph E.
(Lindenhurst, NY) |
Assignee: |
Redeco, Inc. (East Islip, L.
I., NY)
|
Family
ID: |
25046791 |
Appl.
No.: |
05/131,803 |
Filed: |
April 6, 1971 |
Related U.S. Patent Documents
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Application
Number |
Filing Date |
Patent Number |
Issue Date |
|
|
757195 |
Aug 8, 1968 |
3579999 |
May 25, 1971 |
|
|
Current U.S.
Class: |
604/403; 138/31;
220/200; 220/378 |
Current CPC
Class: |
A01N
1/0289 (20130101); A61J 1/10 (20130101); A01N
1/02 (20130101); A61M 1/0272 (20130101); A61M
1/02 (20130101) |
Current International
Class: |
A01N
1/02 (20060101); A61J 1/00 (20060101); A61M
1/02 (20060101); F25j 001/00 (); B65d 053/00 () |
Field of
Search: |
;220/3,24,24A,24.5,42C,27 ;215/83,19,59,60 ;277/165 ;251/368
;128/214R,DIG.22 ;137/538 ;138/31 |
References Cited
[Referenced By]
U.S. Patent Documents
Other References
Huffman, The Journal of Teflon, "Slipper Seals: O-Rings With Teflon
for Low Wear, May 1964, Vol. 5, No. 4, Page 7..
|
Primary Examiner: Price; William I.
Assistant Examiner: Shoap; Allan N.
Attorney, Agent or Firm: Sandoe, Hopgood & Calimafde
Parent Case Text
This application is a division of Ser. No. 757,195, filed 08/08/68
and now U.S. Pat. No. 3,579,999, issued 05/35/71.
Claims
What is claimed is:
1. A vessel for the storage of blood comprising:
a housing of material having a modulus of elasticity, yield point,
thermal coefficient of expansion and thickness able to withstand a
selected internal pressure of up to 35,000 p.s.i. and temperature
changes of between 4.degree. and -21.degree.C without appreciable
change in volume, said housing embracing a blood storage
cavity;
a piston mounted for slidable hermetic entry into said cavity;
and
leverage means for controlling the pressure within the container by
forcing said piston into said cavity, said piston surface and
internal surface of said housing at said cavity being formed of a
material inert to blood.
2. The vessel claimed in claim 1, wherein said cavity has a volume
of approximately 500 ml., and wherein said material is nickel.
3. A vessel for the storage of blood comprising:
a housing of material having a modulus of elasticity, yield point
thermal coefficient of expansion and thickness able to withstand a
selected internal pressure of up to 35,000 p.s.i. and temperature
changes of between 4.degree. and -21.degree.C without appreciable
change in volume, said housing having a blood storage cavity and
including a tubular portion communicating with said cavity;
a piston mounted for slidable hermetic travel in said tubular
portion towards and away from said cavity; and
a cap threaded upon the end of said tubular portion of said housing
for driving said piston towards said cavity thereby controlling the
pressure within said cavity.
4. A vessel for the storage of blood claimed in claim 3, further
comprising a ball interposed between said piston and said cap for
reducing the friction therebetween.
5. The vessel for the storage of blood claimed in claim 3, further
comprising means for bleeding air from the cavity.
6. The vessel for the storage of blood claimed in claim 5, wherein
said air bleeding means includes a pair of apertures in said
tubular portion, said apertures being disposed to communicate from
the outside to said cavity upon travel of said piston away from
said cavity and to be sealed by said piston upon travel towards
said cavity.
7. The vessel for the storage of blood claimed in claim 3, wherein
said piston comprises at least one sealing ring annularly seated
therein for providing a static and a dynamic piston-to-tubular
vessel portion seal.
8. The vessel for the storage of blood claimed in claim 7, wherein
said sealing ring comprises a rubber O-ring and a teflon ring
mounted circumferentially about said rubber O-ring.
Description
BACKGROUND OF THE INVENTION, GENERAL FIELD
This invention relates to the preservation of biological substances
and, in particular, to the preservation of whole blood.
The preservation of biological substances such as vaccines, sera,
enzymes, hormones, blood, bacteriological cultures of various
forms, of specimens of tissue (including foodstuffs), bone, and the
like, have represented an especially acute problem within the past
several decades. The relatively short shelf like of such
substances, coupled with their high demand, have driven their costs
to impractical levels.
With respect to blood in particular, complex systems have been
inaugurated which, because of the short duration of preservation
and high cost, have necessitated detailed arrangements of debits
and credits through blood "banks."
For the purposes of illustration, the background and inventive
descriptions will be hereinafter directed to whole blood. It will
be appreciated, however, by those skilled in the art of
preservation of biological substances, that the invention applies
with like inport to biological species other than blood with
naturally some changes in the pressure temperature parameters to be
disclosed.
In dealing with blood, the primary constituent consideration is the
erythrocytes or red cells. The red cell is globular in form and
contains a cytoplasm in a semipermeable membrane. This membrane
girds the enclosed free fluid within the cell and, although details
of the intimate structure of the erythrocyte membrane are unknown,
complex mixtures of fibrous protein, lipid, and mucopolysaccharides
are known to exist. The membrane is ductal, but is essentially
non-elastic and has a critical maximum volume beyond which rupture
occurs. Rupture of the membrane results in the release of
hemoglobin into the blood plasma where it cannot serve its primary
function of carrying oxygen and carbon dioxide. This latter or
exchange function takes place through the permeable membrane.
As the erythrocyte ages in vivo (in the circulatory system) its
composition changes. Generally, enzyme activities are higher in
younger cells and decrease as the cell ages. Normally, the red
blood cells in vivo have a life span of approximately 120 days,
after which body organs selectively eliminate the cells by breaking
them down into waste and recirculating certain waste elements for
the production of new cells in the bone marrow.
Studies of the osmotic properties of the red cell membrane have
revealed basic information on the permeability of the membrane to
certain solutes and water. Such observations have led to the
conclusion that the membrane allows the passage of water, which is
the primary constituent of the internal fluid, and the plasma. It
has been concluded that the erythrocyte membrane is impervious to
sucrose and electrolites, and that water movements across the
membrane lead to the establishment of osmotic equilibrium between
the cells and plasma.
The movement of water and hydrophilic molecules between the cell
interior and the surrounding media through the membrane conceivably
proceeds either by dissolution of the molecules in the membrane
phase and diffusion from one side of the membranes to the other, or
by diffusion or convection through channels or pores which connect
extra and intra-cellular fluid.
While knowledge of the precise nature of movement is not necessary
for an understanding of the invention, the fact that physical
displacement does take place through the membrane does establish
inertial considerations and the requirement that quick or violent
changes be avoided lest membrane rupture occur.
As previously mentioned, in the circulatory system of the body the
red cells have a life span of approximately 120 days. However, in
the in vitro state, the red blood cells deteriorate very rapidly.
In considering the factors influencing the preservation of the red
cells for purposes of replacement therapy, of extreme import is the
maintenance of its chief function, gas transport through the
erythrocyte membrane for the carrying of oxygen from the lungs to
the body cells and the return of the red cells with the carbon
dioxide.
In order to ensure maintenance of this function (cell viability),
several considerations have become paramount:
1) to avoid the tendency of the blood, while in the in vitro state,
to achieve the phenomena of clotting; 2) to slow down the metabolic
processes; and 3) the maintenance of cell integrity (this partially
overlaps area 2).
With respect to area (2) supra, it is known that the exchange of
gases through the cell is probably due to concentration gradients
and does not require energy expenditure. Further, the cell appears
to synthesize little protein or lipid after it matures, and its
hemoglobin is already completely formed. The circulating cell must,
however, maintain its shape, its internal ionic composition, and
its structural integrity. It must also keep its hemoglobin in its
produced form. All of these tasks require energy and, hence, the
viabile erythrocyte must produce energy. In the in vitro state this
energy production results in the red cell carrying on a metabolic
process until the blood sugar is depleted and is converted to
lactic acid. This results in lowering of the Ph of the plasma to an
unsatisfactory level and the osmotic balance between the intra and
extra cellular material is soon destroyed.
With respect to cell integrity, consideration area (3) above, cell
viability is reflected by cell hemolysis tests and osmotic
fragility. Hemolysis is the destroying of the integrity of the cell
membrane while osmotic fragility is the stressing of the cell to a
degree where it will be removed by either the spleen or the liver.
All loss is directly measurable by what is known as a hematacrit, a
device which centrifuges the blood and gives the ratio of plasma to
cells.
BACKGROUND OF INVENTION, CONVENTIONAL TECHNIQUES
Indirect transfusion (transfusion other than directly from donor to
donee) became possible with the introduction of a citrate solution
as an anticoagulant. Modification of this citrate solution by
acidification and the addition of glucose (acid-citrate-dextrose),
yielded ACD, which as an additive in the ratio of approximately 15
grams per 100 grams of blood provided a solution, which under
adequate refrigeration (approximately 4.degree.C), was safe for
transfusion for a period of approximately 21 days. The temperature
of 4.degree.C was selected as above freezing yet sufficiently low
so that the blood solution could be maintained in the liquid phase
with a substantially reduced metabolic rate.
Aside from the modification of the citric solution, as
aforementioned (and a still newer anticoagulant CPD which will be
discussed) and the concept of reduced-temperature liquid-phase
storage, very little progress has been made in recent years in
improving the maintenance of the viability of red cells during
storage.
While there are very real practical objectives for prolonging the
safe storage period of red cells in the best possible functional
state, and these include the conservation of an inventory of rare
blood types and the elimination of wastage through outdating
(presently blood is discarded at 21 days of age), no process other
than that described above has proven adaptable to convenient and
economical stock piling of human blood in unit amounts
(approximately 500 ml.).
The successful revival of fish trapped in ice for extended periods
has produced, over the years, a great concentration of effort
directed to solid phase (frozen) storage. However, unprotected
blood, when cooled to temperatures below freezing, show massive red
cell damage.
Three theories have been advanced to explain the damage: 1) that
the extracellular ice crystals exert a physical grinding action on
the cells; 2) that the water crystallization occurs in a pure state
leaving behind local concentrations of salt causing a combined
protein de-naturing effect and intracellular hypertonicity; and 3)
a disruption of spatial relationships within the cell.
These theories in turn have each generated methods for the lowering
of temperatures below the freezing point without cell damage. One
method suggests the replacement of the free intracellular material
by an additive such as glycerol or dimethyl sulfoxide which
penetrates the cells. While such an arrangement protects the red
cells from damage during ice crystallization, the chemicals
themselves must be removed before the blood can be transfused.
Accordingly, such processes, as well as the apparatus for
effectuating them, have been proved to be extremely expensive.
Alternative arrangements suggest rapid freezing in the presence of
non-penetrating or slowly penetrating additives such as PVP
(polyvinylpyrrolidone) dextrin, gelatin, sucrose, lactose or
glucose. These additives, however, raise the same problems as those
just discussed.
More sophisticated and esoteric arrangements involving the droplet
freezing of blood in moving streams of liquid nitrogen and the
aqueous bathing of the droplets in specific solutions have also
been suggested, however, all of these more sophisticated
arrangements are completely beyond the pale of competence of the
normal hospital technician, and, consequently, are undependable and
unreliable. Further, they introduce almost insurmountable sterility
problems.
The use of high pressure to avoid freezing has been generally
rejected due to the alleged cytotoxic effect of the pressure itself
on the red cells and due to "shell" freezing (to be described)
which inevitably takes place destroying an inordinate number of red
cells.
It is the object of this invention to provide a method for the
storage of biological substances for extended periods of time,
including months and years, which at the end of such periods,
exhibit the same or better cell viability (where the biological
material was living) and characteristics as those observed after
short periods of conventional storage.
It is another object of this invention to provide a method as
previously described, which is particularly applicable to the
storage of whole blood and which maintains the highest percentage
of the erythrocyte viability for the storage period.
It is a further object of this invention to provide a method for
the storage of whole blood in unit volumes which is adaptable to
conventional sterilization techniques.
It is another object of this invention to provide a method and
apparatus for the storage of whole blood which is relatively simple
to implement and use, which may be accomplished with personnel of
minimal training.
It is a still further object of this invention to provide an
apparatus for the storage of whole blood which is particularly
adaptable to blood units.
It is a still further object of this invention to provide an
apparatus for the storage of whole blood which accomplishes the
foregoing objects in a manner which is self-generative and which,
once the process is under way,
achieves the desired optimum condition.
SUMMARY OF THE INVENTION
Briefly, the invention is predicated upon the careful control of
temperature and pressure in such a manner as to maintain
characteristics of the biological substance by the avoidance of
freezing shocks as well as the phenomena of freezing itself. With
blood this permits the maintenance of the integrity of the
erythrocyte and its membrane, while lowering its metabolic rate
sufficiently to obviate deterioration. It has been discovered, for
example, that by precompressing whole blood at a temperature above
freezing, and carefully controlling the pressure to ensure minimal
shell-freezing shocks as the temperature is lowered, it is possible
to lower the temperature to a point where the metabolic rate is
negligible, without deleterious effects.
It has further been ascertained that by applying this
precompression at the maximum density point of blood and then
containing the blood in a non-yielding vessel, that the volumetric
expansion of the blood as it undergoes temperature decrease will,
depending upon the precompression pressure, automatically maintain
the foregoing functional requisites to a predetermined final
storage temperature.
The above mentioned and other features and objects of this
invention and the manner of attaining them will become more
apparent and the invention itself will best be understood by
reference to the following description of an embodiment of the
invention taken in conjunction with the accompanying drawings
wherein:
FIG. 1 graphically illustrates permissible precompression versus
final storage temperature parameters in p.s.i. and degrees
centigrade, respectively;
FIG. 2 is a sectional illustration of one embodiment of a storage
vessel according to the invention; and
FIG. 2a is a detail of the piston rings in FIG. 2.
DETAILED DESCRIPTION OF THE INVENTION
As previously discussed, the solid phase storage of frozen blood is
not feasible for widespread use, and the use of high pressures to
avoid crystal formation has been rejected and expressly described
by authorities as impractical and cytotoxic to the red cells from
the pressure itself.
There is, however, a relationship which has not been completely
explored and which, while it may be only theorized, is completely
supported in the laboratory. Blood is approximately 90 percent
water and, consequently, its static, dynamic, and physical
characteristics are such that its behavior may be anticipated by
the water analogy in several important respects. For example, both
water and blood achieve maximum density at 4.degree.C (actually
3.98.degree.C, however, since the figure is not critical to the
second decimal point, an approximation of 4.degree.C will be
adhered to hereinafter). Accordingly, both above and below
4.degree.C water (blood) will expand.
Also analogous is the phenomenon of freezing. During freezing, an
expansion of from 7 percent to 13 percent in volume occurs
(depending upon freezing temperature and pressure). Because of an
almost unavoidable temperature gradient between the center of the
containing vessel and the outer walls, freezing necessarily takes
place in laminar stages or shells, and as each stage freezes (a
stage may represent only 1,000th of an inch) its volume expands
from 7 percent to 13 percent. If the space is confined or the
volume otherwise fixed, a pressure shudder will be transmitted
throughout the fluid. Recalling the previously explained character
of the erythrocyte membrane, while it is permeable and ductal,
sudden changes do not permit maintenance of an equilibrium between
extra and intracellular fluid. Accordingly, if shell freezing is
permitted to take place, hemolysis will occur, or, if insufficient
to completely destroy the integrity of the membrane, the osmotic
fragility will be so low that upon being transfused the affected
red cells will be removed from circulation. The free expansion of
water and blood when freezing at, for example, one atmosphere and
0.degree.C is 9 percent, but the compressibility of water and blood
at this temperature and pressure, due to the change in state, is
only 4.2 percent. Thus, when the rapid expansion takes place in a
controlled volume, ice would form to a total amount of expansion to
cause a change of 4.2 percent of the volume beyond which no more
ice could form at that temperature.
Hence, the ability of water or blood to convert to the solid stage
depends upon its compressibility. I have discovered that if this
compressibility can in some manner be accounted for,
crystallization or freezing of a portion can be avoided. In the
case of human blood, this avoids the hemolysis of the cells under
the surge of pressures accompanying crystallization. Specifically,
I have found that a sufficient amount of "precompression" may be
applied to the blood to take up the available compressibility,
thereby eliminating or controlling these surges of pressure.
As will be appreciated by those skilled in the art, the freezing
point of a liquid will depend upn the prevailing temperature and
pressure. Thus, at pressure p, the freezing point would be t, but
at p.sub.2 where p.sub.2 > p.sub.1, the freezing temperature
would be at t.sub.2, a lower temperature than t.sub.1.
"Precompression" may be defined for the purpose of this disclosure
and invention as the mechanical application of positive pressure at
any temperature above the freezing point of the substance being
worked upon.
Precompression may be applied in a unitary manner at one
temperature (see, for example, the embodiment described herein) or
it may be applied in stages with the introduction of defined
pressure increases at predetermined temperature points (e.g. 5,200
p.s.i. at 4.degree.C, 3,000 p.s.i. at -5.degree.C, and 2,000 p.s.i.
at -8.degree.C, and so on.).
As mentioned, the precompression may be applied at any temperature
above freezing; however, in order to define its magnitude, the
precompression pressure will be measured at maximum density; for
blood this is 4.degree.C. To determine precompression pressure the
temperature need only be brought to 4.degree. C and the pressure
increased. For example, assume that is a non-yielding vessel, 4,000
p.s.i. (absolute is to be inferred in all pressure values) pressure
is applied at a temperature of 5.degree.C. Since blood will
thereafter contract to 4.degree.C, the "precompression pressure"
will be 4,000 p.s.i. minus the pressure drop due to the volumetric
contraction of blood to 4.degree.C. The same contraction principle
would apply if pressure were introduced at 3.degree.C and the
precompression pressure would be 4,000 p.s.i. minus the pressure
drop due to contraction.
From observed, data it has been found that even a slight degree of
pressure has a marked effect on the temperature at which the rapid
expansion necessary to allow ice to form will occur.
Additional pressure after or between precompressions, I have found,
can be self-generating. When water or an aqueous solution is
contained in a vessel having a sufficiently high modulus of
elasticity and yield point so as to reduce to an almost negligible
amount the radial displacement of the vessel when the temperature
is lowered below 4.degree.C, a pressure is generated due to the
attempt of the liquid to expand. The result is that the point of
rapid expansion at which ice is formed (normally at 0.degree.C at
one atmosphere of pressure; lower when precompressed) will be
lowered until the forces acting upon the fluid and tending towards
ice overcome the pressure.
It bears mentioning that while it is theoretically desirable (from
the point of view solely of freezing) to put sufficient
precompression on the blood to account for all compressibility,
this requires a pressure of about 12,000 p.s.i. placed on about
4.degree.C. Tests have shown, however, that this much pressure
applied at one time induces undesirable cell wall deformation so
that body rejection upon transfusion may be presumed. This can be
avoided by applying the pressure in stages, it having been
discovered that cell damage is a function of pressure and
temperature. However, seldom is freezing the sole consideration
and, accordingly, as will be explained, the best pressure and
temperature relationship is guided by several factors.
FIG. 1 illustrates the safe and unsafe division of precompression
versus final storage temperature. For example, a precompression
pressure of 5,000 p.s.i. yields a final safe storage temperature
(assuming negligible dilation of the containing vessel) of
-12.degree.C or higher. A precompression of 3,000 p.s.i. on the
other hand, would require a storage temperature of approximately
-3.5.degree.C or higher. Below these temperatures hemolysis due to
shell freezing is too severe to give good transfusable results.
While theoretically the lowest possible safe storage temperature on
the graph would appear to achieve the best possible reduced
metabolic rate, at any given temperature there is a limit to the
amount of pressure that blood can be subjected to. Membrane
distortion is also a function of pressure and, accordingly, within
the safe area shown in FIG. 1, there are varying percentages of
cells which hemolyze, and, hence, for each precompression value the
lowest possible "safe" temperature is not necessarily the best. I
have found a precompression of between 4,000 and 6,000 p.s.i. to
give the most satisfactory results, and since the slope of the
curve between these pressures is a minimum, offers the greatest
latitude or selection in storage temperatures.
Turning now to FIG. 2, an apparatus for performing the described
inventive method as well as an exemplary blood preservation process
will now be described.
The vessel in which the blood will be stored must be made of a
material of high yield point sufficient to withstand internal
pressures of the order of 20,000 p.s.i. It must also have a Young's
modulus of elasticity sufficiently high so that in the range of use
these internal pressures will produce negligible dilation or radial
displacement. The thermal coefficeint of expansion, on the other
hand, must be such so that its effect over the intended temperature
range will either increase pressure or will be compensated by the
elastic dilation due to pressure. Desirably, the vessel should also
be easily adaptable to autoclaving type sterilization and have its
internal surface non-wetting with blood and capable of assuming a
mirror-like finish (for reducing red cell injuries).
The most practical vessel material discovered to date is nickel.
Preferably, the vessel is formed by electroforming the nickel upon
a mandrel of spherical shape and of blood unit volume. The mandrel
is coated with silver or another suitable electrode material and
polished to a micro-finish. It is then placed into an electrolytic
bath where it is agitated or rotated. While one electrode is
affixed to the mandrel, the other electrode (the anode) of pure
nickel is suspended distally in the bath. Electroplating takes
place anode to cathode, depositing nickel ions and slowly building
up the vessel to the form shown in the figure. A wall thickness of
approximately 0.125 inches has been found sufficient to withstand
the internal stresses which will obtain during the described mode
(5,900 p.s.i. precompression).
One end of the vessel has a pair of apertures 11 and 12, drilled
therethrough for a purpose to be explained, while the other end is
threaded internally to take a conventional pressure gauge 13.
Slidably received at the end opposite the pressure gauge is a
follower piston 14 which is machined to close tolerances and
includes a pair of spaced annular slots 15 and 15' for reception of
sealing rings.
Each sealing ring is, as shown in the detail of FIG. 2a,
constituted of two parts. The first comprises a medical grade
silicone rubber O-ring 16 of circular cross-section which acts as a
mechanical bias inside a rectangular cross-section O-ring 22 of
teflon. This combination, which effectuates the liquid seal, is
non-wetting with blood and is easily autoclaved. The second sealing
ring 15' serves the fail safe function. It is made up of similar
parts (16' and 22') in juxtaposed relationship rather than in
tandem in order to reduce sliding friction which has been found to
be too stiff where both seals are made like sealing ring 15.
The external surface of the follower piston should have a finish
fulfilling the same functional requisites as the inside of the
vessel and rings. That is, it must be non-wetting with blood,
easily autoclaved, and non-injurious to red cells. A stainless
steel piston has proven satisfactory. For purposes of sealing and
applying pressure within the vessel a steel cap 17 is threaded to
vessel end 18. The pitch of the threads is optional, and the thread
depth must be sufficient to withstand the anticipated internal
pressures. Considerations governing the thread pitch are the means
to be employed for angularly displacing the cap of the vessel
during precompression. A pitch of seven threads per inch has been
found suitable for use with a torque wrench having a lever arm of
18 inches in length.
Steel ball 19 serves as an antifriction device between the cap 17
and the piston 14. As shown, both the cap and piston include
spherical depressions for better ball seating. With this
arrangement the piston may be driven rectilinearly with little
angular moment upon advancement of the steel cap. In order to
permit easy removal of the piston an internal thread 20 may be
provided for engagement by an extractor (not shown).
While the pressure gauge 13 shown in the figure will give rather
precise indications of precompression and final pressures, such
gauges will only be necessary as a spot check and the end of the
vessel shown receiving the gauge may be sealed by a pressure limit
indicator (e.g., a colorcoded piston) or may be eliminated
entirely. This may be achieved simply by precisely controlling the
internal size of the vessel and thread pitch, and by properly
marking the cap and external parts of the vessel so that the
relationship of turns to internal pressure may be established for
the operator. Thus, for example, a vessel having an internal
configuration sufficient to contain a pint of blood and having a
3/4 inch diameter piston will require approximately 11/4 inches of
piston travel at 4.degree.C to apply 4,000 pounds of
precompression. The relationship of piston travel to pressure at
4.degree.C may, therefore, be indexed on the cap and vessel.
Needless to say that the distance between the apertures 11 and 12
and the vessel portion 21 where it begins to flare must be
sufficient to allow a piston travel equivalent to the greatest
precompression pressures desired during the process.
Blood may be collected from the donee either directly into the
vessel (which has been sterilized) or indirectly into an enclosed
plastic system and then to the vessel. In either case, either the
plastic system or the vessel will contain the anticoagulant in
sufficient amount. With ACD (trisodium citrate, dextrose, cytric
acid) as the anticoagulant, the ratio would be 15 ml. of
anticoagulant per 100 ml. of blood. With the newer CPD (trisodium
citrate, cytric acid, monobasic sodium phosphate, dextrose) a new
and perhaps preferable anticoagulant, the ratio would be 14 ml. per
100 ml. of blood. In either event, the blood is introduced to the
vessel with the piston retrograded to expose the apertures to the
interior. The vessel is maintained at approximately 45.degree. to
60.degree. attitude with the apertures vertically located with
respect to one another and the blood is introduced into the lower
aperture to completely fill the container (which will become
apparent when the blood becomes visible at the higher
aperture).
The piston is then surfaced on the blood and the cap threaded on
the vessel. The temperature of the vessel is then brought as
quickly as possible to 4.degree.C. This may be most expeditiously
accomplished by means of a constant temperature bath into which the
vessel is inserted. As the temperature within the vessel reduces
the blood volume will contract. The piston is free moving in the
contraction direction and, accordingly, the piston-blood contact
will be maintained. When the temperature of vessel and blood has
stabilized at 4.degree.C, the steel cap is then rotated until, for
example, 5,900 pounds of positive pressure (precompression) is
applied to the blood. This is a precompression of approximately 3.4
percent of the volume. At this temperature and pressure the net
increase in the vessel volume was found to be less than one-tenth
of one percent. This increase reflects the strain introduced by the
pressure less the contraction due to reducing the temperature to
4.degree.C.
The prescribed precompression pressure is applied in a controlled
manner, preferably at 1,000 p.s.i. or less per minute. The pressure
is increased as linearly as possible to avoid pressure transients
which would result in membrane rupture upon the inability of the
cell to achieve equilibrium. The application of a linear pressure
increase may be accomplished by maintaining the displacement of the
cap at a substantially constant angular velocity. It has been found
that this may be accomplished within suitable limits manually with
a torque wrench.
Once the 5,900 p.s.i. has been introduced, the vessel is brought to
-13.degree.C in a controlled bath. The temperature change is again
brought about as quickly as possible, but this time with one
caveat. The temperature must not change so quickly that the
tendency of the blood to increase its volume will result in
pressure increases at a rate greater than that which will rupture
the membrane (1,000 p.s.i. per minute has been found satisfactory).
From the graph it may be seen that a temperature of -14.degree.C is
the minimum safe temperature at the chosen pressure. Thus,
-13.degree.C is sufficiently within the safe portion of the curve
and yet is as low as possible to decrease the metabolic rate. The
blood is now stored at this temperature for any period from one
week to several years.
When the blood is ready for use, the procedure is reversed. The
temperature is brought up to 4.degree.C whereupon the
precompression is removed again at a rate preferably about 1,000
p.s.i. per minute. When removed from storage and tested, blood
stored according to the inventive process for a long as 6 months
yields transfusable results which, when tested by a hematacrit,
examined as to osmotic fragility and given all the available tests
for determining erythrocyte viability, give results substantially
the same as blood stored employing conventional techniques at
4.degree.C for several days. Thus far, tests in excess of six
months have not been attempted, however, normal principles of
extrapolation make it reasonable to suggest that several years
storage will also yield transfusable blood.
While the principles of the invention have been described in
connection with the specific apparatus and a specific biological
substance, it is to be clearly understood that this description is
made only by way of example and not as a limitation to the scope of
the invention as set forth in the objects thereof and in the
accompanying claims. For example, those skilled in the art will
immediately recognize from the foregoing disclosure that many
biological substances have either great water content or include as
a primary constituent a fluid having a freezing point above or
close to the desired storage temperature. In such cases, the
inventive method with variations in FIGS. 1 and 2 dependent upon
the substance (and any fluid added as a perservative) will be
particularly applicable.
* * * * *