U.S. patent number 3,850,202 [Application Number 05/280,904] was granted by the patent office on 1974-11-26 for injection site for a flow conduit.
Invention is credited to Brian E. Morgan.
United States Patent |
3,850,202 |
Morgan |
November 26, 1974 |
**Please see images for:
( Certificate of Correction ) ** |
INJECTION SITE FOR A FLOW CONDUIT
Abstract
An injection site for a fluid flow conduit which comprises a
housing and an elastomeric wall maintained within the housing under
compression, in which the wall defines a portion of the fluid flow
conduit. When a needle penetrates the wall for injection purposes,
and is later withdrawn, the compressive force provides a positive
seal capable of preventing the leakage of fluid from the conduit,
even when the fluid is under positive pressure.
Inventors: |
Morgan; Brian E. (Mount
Prospect, IL) |
Family
ID: |
23075096 |
Appl.
No.: |
05/280,904 |
Filed: |
August 15, 1972 |
Current U.S.
Class: |
138/103; 138/140;
285/93; 604/86 |
Current CPC
Class: |
A61M
39/04 (20130101); F16L 21/005 (20130101) |
Current International
Class: |
A61M
39/02 (20060101); A61M 39/04 (20060101); F16L
21/00 (20060101); F16l 011/12 (); A61m
005/00 () |
Field of
Search: |
;138/99,103,140 ;128/214
;285/423 |
References Cited
[Referenced By]
U.S. Patent Documents
Primary Examiner: Goldstein; Herbert
Attorney, Agent or Firm: Ellis; W. Garrettson Shuman; Thomas
R.
Claims
That which is claimed is:
1. In a fluid flow conduit, an injection site which comprises a
housing, and an elastomeric wall maintained under radial
compression and enclosed within said housing, said wall along its
entire length defining a portion of said fluid flow conduit, and
said compression being sufficient to prevent leakage through said
wall after said wall is punctured with a needle.
2. The injection site of claim 1 in which the natural, uncompressed
dimensions of said wall are at least 10 per cent greater than the
compressed dimensions of said wall as maintained in the
housing.
3. The injection site of claim 1 in which said wall is made of
silicone rubber.
4. In a fluid flow conduit, an injection site which comprises a
housing having a bore therein, an elastomeric tube having
uncompressed, outer, transverse dimensions greater than the
transverse dimensions of said bore, said tube along its entire
length defining a portion of said fluid flow conduit, said tube
being positioned in said bore under radial compression, and a port
in said housing exposing a portion of said compressed tube to the
exterior of said housing for access by an injection needle.
5. The injection site of claim 4 in which the uncompressed, outer,
transverse dimensions of said elastomeric tube are at least 10 per
cent greater than the compressed outer, transverse dimensions of
said tube as maintained in said housing.
6. The injection site of claim 4 in which the side of said housing
opposite and adjacent said port defines a solid wall to prevent an
injection needle in said port from passing completely through said
housing.
7. The injection site of claim 5 in which said port has a dimension
transverse to said elastomeric tube which is no more than about 60
percent of the outer transverse dimension of said tube compressed
in said housing.
8. The injection site of claim 7 in which conduits having bores of
identical diameter to the bore of the compressed elastomeric tube
are carried in each end of the bore of the housing in abutting
relation with the ends of said elastomeric tube, whereby a smooth
flow path, free of discontinuities, is defined through said
conduits and elastomeric tubes.
9. The injection site of claim 8 in which said elastomeric tube is
made of silicone rubber.
10. The injection site of claim 8 in which the uncompressed, outer,
transverse dimensions of said elastomeric tube are at least 10 per
cent greater than the compressed, outer, transverse dimensions of
said tube as maintained in said housing.
11. The injection site of claim 5 wherein said elastomeric tube is
made of latex rubber.
Description
BACKGROUND OF THE INVENTION
Parenteral solution administration equipment and blood flow
conduits for solution infusion, blood transfusion, or the
conveyance of blood between a patient and an artificial kidney or
blood oxygenator, generally require sites where an injection needle
can be inserted into the conduit to withdraw samples or to
administer medication or the like. When the injection needle is
withdrawn it is important that there be no leakage of solution or
blood through the needle puncture.
Problems can arise with leakage of blood and solution, particularly
when the conduit is under elevated pressure, as in the case of
certain blood oxygenation and artificial kidney blood conduits, and
in the case of the pressurized administration of parenteral
solution or blood to a patient. In this circumstance, the
conventional infusion sites, which are commonly latex tubes or
bulbs which fit over the respective ends of vinyl conduit tubing,
have been known to pop off, causing blood or parenteral solution to
spurt out. In the same circumstance, blood and parenteral solution
may tend to leak out through the needle punctures of the injection
site. Similarly, air may leak through a needle puncture into the
blood or solution line if the line is under reduced pressure.
Injection sites in blood or parenteral solution conduits are
generally made of natural latex, which has good self-sealing
properties, and thus has tended to partially compensate for the
disadvantages of the prior art injection sites. However, natural
latex is a relatively thrombogenic material, and is undesirable for
use in blood flow conduits.
In accordance with this invention, a new injection site is provided
having reliable sealing of needle punctures through materials such
as silicone rubber, rather than latex or other materials having
more pronounced blood clotting tendencies or other biologic
incompatibilities.
Furthermore, an improved and more reliable injection site which
does not pop apart under internal pressure can be provided by this
invention.
Basically, while the prior art latex injection sites have been
stretched over vinyl conduits or the like, the needle puncture site
used in this invention is not stretched, but is placed under
compression in a housing and abutted in an end-to-end relationship
with the remaining fluid flow conduit to provide a more reliable
high pressure injection site. This injection site can have the
added advantage of a smooth bore, free of discontinuities, which
discontinuities tend to cause blood to clot, or cause accentuated
hemolysis. Furthermore, because of the compressive action in the
present invention, blood-compatible, elastomeric materials can be
utilized as the needle puncture member, even though their
self-sealing capabilities are not the equal of the less
biologically compatible latex materials.
DESCRIPTION OF THE INVENTION
The injection site for a fluid flow conduit of this invention
comprises a housing, and an elastomeric wall maintained within the
housing under compression, the wall defining a portion of the fluid
flow conduit. When a needle penetrates the elastomeric wall, for
adding a medicament or withdrawing fluid sample, and then is
withdrawn, the compression of the elastomeric wall provides a
positive seal of the needle puncture.
The injection site can be designed to seal effectively against a
wide range of pressures using a wide range of elastomeric
materials, depending upon the degree of the compressive force on
the elastomeric wall.
Preferably, the elastomeric wall is made of silicone rubber, or
similar biocompatible, antithrombogenic, and elastomeric material
which does not readily "creep" into permanent deformation under
compression.
In the drawings:
FIG. 1 is an elevational view of a preferred embodiment of the
fluid flow conduit of this invention.
FIG. 2 is a magnified elevational view of the conduit of FIG. 1
with portions broken away and shown in section.
FIG. 3 is a sectional view taken along line 3--3 of FIG. 2.
Referring to the drawings, fluid conduit 10 is shown. This conduit
might be used as part of the system to connect a patient's artery
to a blood oxygenator or artificial kidney, or it may also be used
as a connection between the aforesaid oxygenator or kidney and a
vein of a patient. Similarly, the blood flow conduit might be used
as part of the blood flow path in an organ perfusion device, such
as the VIACELL.sup.TM organ perfusion system sold by Travenol
Laboratories, Inc. of Morton Grove, Ill.
Flow conduit 10 comprises elastomeric tubing 12, 14, which can
optionally be terminated with flanges 15 to assist in connecting
tubing 12, 14 in sealing, abutting, end-to-end relationship with
similarly flanged tubing by means of couplers of the type shown in
Argentine Pat. No. 188,952 or U.S. Pat. No. 3,456,965.
Lengths of tubing 12, 14 which are typically made of
non-thrombogenic plasticized polyvinyl chloride, have ends 16, 18
conventionally secured by solvent or heat sealing within tubular
housing 20, which is typically made of ABS plastic or another
strong, generally rigid plastic.
Elastomeric tube 22 is positioned within the bore of housing 20.
Tube 22 has an uncompressed outer diameter which is greater than
the bore of housing 20, so that when tube 22 is positioned in the
bore of housing 20, as shown in the drawings, it is under radial
compression. For example, housing 20 may have an outer diameter of
0.375 inch and an inner diameter of 0.298 inch. Tube 22 may have,
prior to compression within bore 20, an outer diameter of 0.330
inch and an inner diameter of 0.210 inch, resulting in an
uncompressed wall thickness of 0.060 inch. When tube 22 is made of
silicone rubber and housing 20 is a rigid material such as ABS
plastic, the above specifically designed arrangement will prevent
leakage from a needle puncture in the presence of fluid pressures
inside conduit 10 of up to about 25 p.s.i.. Preferably, the
uncompressed outer diameter of tube 22 should be at least 10 per
cent greater than the inner diameter (bore diameter) of housing 20,
which, of course, governs and is equal to the compressed outer
diameter of tube 22.
The bore diameter of compressed tube 22 is equal to the bore
diameters of tubing 12, 14, to provide a smooth fluid flow path
free of discontinuities.
Tubular housing 20 and elastomeric tube 22 are typically of
circular cross-section, but equivalent structural parts having oval
or polygonal cross-sections are contemplated to be within the scope
of the invention.
Port 24 in housing 20 provides needle access to tube 22. It is
desirable that the dimension of port 24 which is transverse to tube
22 be no more than about 60 percent of the outer transverse
dimension (outer diameter) of tube 22, so that the portion of the
tube which is exposed by port 24 does not lose an excessive amount
of compression by compressive relief provided by port 24. If
housing 20 is made of polyethylene, vinyl plastic, or the like,
port 24 can be omitted in those cases in which housing 20 is thin
enough to permit the needle to penetrate directly through the
housing wall, as well as the wall of tube 22.
As an added advantage, housing 20 can be fabricated to prevent
injection needles from accidentally passing entirely through the
injection site, as frequently happens with the present latex tube
sites. This is achieved when port 24 is adjacent a solid,
needle-stopping wall 25 on the opposite side of housing 20.
The injection site of this invention can be theoretically designed
to prevent leakage from a hypodermic needle injection puncture in
tube 22 over a wide range of fluid pressures within bore 21,
utilizing a wide range of materials for constructing tube 22,
including natural latex, if desired.
The capacity of the injection site of this invention to seal
against pressurized fluid after puncture is largely dependent upon
the degree of compression of tube 22. The minimum degree of
compression needed to seal against any given pressure can be
expressed as a minimum difference between the outer diameter of the
uncompressed tube 22 and the inner diameter of housing 20 (such
difference being defined as the variable D) which provides sealing
of a needle puncture at a given internal pressure P within bore 21.
This value of D at any given value of P can be approximated by
solving the following equation:
D.congruent. bP/E.sub.1 (C.sup.2 + b.sup.2 /C.sup.2 - b.sup.2 +
.mu..sub.1)+bP/E.sub.2 (b.sup.2 + a.sup.2 /b.sup.2 - a.sup.2 -
.mu..sub.2)
in which a is the radius of the bore of tube 22, b is the radius of
the bore of housing 20, and c is the outer diameter of housing 20
(as illustrated in FIG. 3). E.sub.1 is the modulus of elasticity of
the material of housing 20, E.sub.2 is the modulus of elasticity of
the material of tube 22, .mu..sub.1 is Poisson's ratio of the
material of housing 20, and .mu..sub.2 is Poisson's ratio of the
material of tube 22.
As stated above, this equation approximates the limiting pressures
at which leakage just begins for a compressed tube and housing
arrangement made of given materials and having specified dimensions
and a specific degree of compression. At significantly lower
pressures of P than that used in the equation, there shall be no
leakage, either out of hypodermic needle puncture sites or along
the surface defined between housing 20 and tube 22. The effect of
port 24 is not included in the calculation; it would of course
lower the limiting pressure at which leakage would just begin.
Further details on the above equation can be found in the book
entitled "Mechanical Engineering Design," by J. E. Shigley,
published by McGraw Hill Publishers, N.Y. (1963), pp. 563-565.
Thus, injection sites for fluid flow conduits can be provided in
accordance with this invention to resist leakage in the presence of
almost any maximum fluid pressure desired. Furthermore, blood
contacting portions of the injection site can be made of
anti-thrombogenic material to provide the most favorable possible
environment for blood which is being passed extracorporeally.
The above has been offered for purposes of illustration only, and
is not to be considered as limiting the invention, which is defined
in the claims below.
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