U.S. patent number 3,771,899 [Application Number 05/207,162] was granted by the patent office on 1973-11-13 for pulsator pump and heat exchanger for blood.
Invention is credited to Robert C. Brumfield.
United States Patent |
3,771,899 |
Brumfield |
November 13, 1973 |
PULSATOR PUMP AND HEAT EXCHANGER FOR BLOOD
Abstract
A slow variable speed drive rotates a pulsator pump and heat
exchanger which can circulate pulsed blood flow extra-corporeally
at a required blood temperature to a patient. The pump has a
cylindrical rotor shell permanently mounted in a closely fitting
internally cylindrical stator housing. The rotor has a support
shaft which is eccentrically disposed parallel to the internal axis
of symmetry of the stator housing and also to the rotor symmetry
axis. Thus the rotor shell has its exterior surface also
eccentrically disposed parallel to the rotor shaft axis of
symmetry, providing controlled laminar flow of admitted blood.
Laminar flow pumping means are provided, together with Taylor
mixing vortices. Admitted patient blood is pumped as a thin blood
film in pulsed laminar flow between the rotor and stator as the
rotor exterior surface eccentrically approaches the stator surface,
and in pulsed laminar Taylor vortex flow as the rotor surface
recedes from the stator surface. The blood is introduced into the
pump through a manifolded blood inlet having a longitudinal groove
disposed in the inner face of the stator housing, the groove
distributing blood to the annular space between the rotor and
stator. A second similar blood outlet combination includes a
longitudinal groove in the inner stator face, facilitating blood
removal from the pump. The manifolded and jacketed stator housing
provides heat transfer means for controlling the temperature of
treated-blood of the patient. CROSS-REFERENCE TO RELATED
APPLICATION This application is related to the pending U.S. Pat.
application, Ser. No. 190,800, filed Oct. 20, 1971 by the same
inventor. BACKGROUND OF THE INVENTION A patient's blood can be
mechanically pumped during advanced patient treatment and during
radical cardio-pulmonary surgery. Likewise, there can be a need to
provide a prescribed pulse in the extra corporeal blood
circulation. Apparatus for pumping blood is classified in Class 128
Subclass 258.5, and in Class 103 Subclasses 99 and 148. SUMMARY OF
THE INVENTION A slow variable speed drive rotates a pulsator pump
and heat exchanger which can circulate pulsed blood flow
extra-corporeally at a required blood temperature to a patient. The
pump has a cylindrical rotor shell permanently mounted in a closely
fitting internally cylindrical stator housing. The rotor has a
support shaft which is eccentrically disposed parallel to the
internal axis of symmetry of the stator housing and also
eccentrically disposed parallel to the rotor symmetry axis. The
rotor shell has its exterior surface also eccentrically disposed
parallel to the rotor shaft axis of symmetry, providing controlled
laminar flow of admitted blood. Laminar flow pumping means together
with Taylor mixing vortex flow are provided for the pumped blood.
Admitted patient blood is pulsatingly pumped by the exchanger pump,
between the doubly eccentrically disposed rotor and stator. The
blood flows laminarly in a thin film as a position on the
eccentrically disposed rotor surface approaches the stator surface.
Laminar Taylor vortex flow occurs as the same position on the rotor
surface recedes from the stator surface. The stator housing is
manifolded and jacketed, providing heat transfer means for
controlling the patient's circulating blood temperature. Blood
inlet and outlet conduits are conductively secured to the stator
housing. The blood is introduced into the pump through a manifolded
blood inlet having a longitudinal groove disposed in the inner face
of the stator housing, the groove distributing blood to the annular
space between the rotor and stator. A second similar blood outlet
combination also includes a longitudinal blood distribution groove
collecting blood for removal from the pump. Included in the objects
of this invention are: To provide a variable speed pump for
pulsatingly pumping patient blood extra-corporeally. To provide a
blood pump capable of extra-corporeally pumping blood during a
surgical procedure, or the like. To provide a blood pump capable of
providing a variable rate of pulsed blood flow in extra-corporeal
patient blood circulation. To provide an effective thin blood film
suitable for rapid heat exchange in a blood pump. To provide an
effective Taylor mixing vortex in a blood circulating device useful
in an extra-corporeal patient blood pump.
Inventors: |
Brumfield; Robert C. (Laguna
Beach, CA) |
Family
ID: |
22769442 |
Appl.
No.: |
05/207,162 |
Filed: |
December 13, 1971 |
Current U.S.
Class: |
415/90;
128/DIG.1; 415/178; 128/DIG.3; 415/900 |
Current CPC
Class: |
A61M
60/216 (20210101); A61M 60/36 (20210101); A61M
60/33 (20210101); A61M 60/109 (20210101); F04D
5/001 (20130101); A61M 60/827 (20210101); A61M
60/546 (20210101); A61M 60/32 (20210101); A61M
1/265 (20140204); A61M 1/267 (20140204); A61M
60/825 (20210101); A61M 60/422 (20210101); A61M
60/113 (20210101); A61M 60/829 (20210101); Y10S
415/90 (20130101); A61M 2205/366 (20130101); A61M
60/50 (20210101); A61M 60/818 (20210101); Y10S
128/03 (20130101); A61M 60/40 (20210101); A61M
60/562 (20210101); A61M 2205/3334 (20130101); Y10S
128/01 (20130101); A61M 60/205 (20210101) |
Current International
Class: |
A61M
1/10 (20060101); F04D 5/00 (20060101); A61M
1/26 (20060101); A61M 1/16 (20060101); F04 ();
F03 () |
Field of
Search: |
;128/DIG.2,DIG.3,1D
;415/DIG.4,90,178,180 |
References Cited
[Referenced By]
U.S. Patent Documents
Foreign Patent Documents
Other References
Publication Medical Societies-New Inventions Feb. 1959 Page
347..
|
Primary Examiner: Raduazo; Henry F.
Claims
I claim:
1. In an apparatus for pumping extra-corporeal patient blood, said
apparatus having a right cylinder rotor secured on a rotor shaft,
an internally cylindrical stator housing cylindrically enclosing
said rotor, and means providing cooperative bearing support for
said rotor shaft, the blood transport pump combination
comprising:
a rigid cylindrical rotor shell having its rotational axis of
symmetry precisely displaced parallel to the rotor axis of
symmetry, said rotor shell and said rotor shaft being positively
secured together, said rotor shaft adaptively disposed in said
stator housing, said shell having an external diameter precisely
less than said internal diameter of said stator housing.
a pair of rotor shaft bearing supports, each one of said pair of
bearing supports disposed adjacent one shaft terminus, said bearing
supports secured to precise positions on said rotor shaft,
a pair of eccentricity adapters, each one of said adapters
cooperatively securing one of said pair of bearing supports,
disposing said rotor shaft in a precisely fixed resultant
eccentricity parallel with the internal axis of symmetry of said
internally cylindrical stator housing,
a blood laminar flow arc sector precisely disposed between said
rotor and said stator housing, said resultant eccentricity
cooperatively fixing the laminar flow arc sector value, said arc
sector providing blood pumping means during rotation of said rotor,
and
a blood Taylor vortex flow arc sector precisely disposed between
said rotor and said stator housing, said resultant eccentricity
cooperatively fixing said Taylor vortex arc sector value, said arc
sector providing blood film mixing means during rotation of said
rotor;
whereby the rotating said rotor provides pulsed laminar blood flow
in said laminar flow arc sector and provides pulsed laminar
transitional and Taylor vortex flow in the remainder of the pump
arc sector.
2. An apparatus in accordance with claim 1 wherein a heat transfer
shell jacket covers the external cylinder face of said stator
housing, said jacket having a fluid inlet conduit and a fluid
outlet conduit secured to said jacket, said inlet conduit, said
jacket and said outlet conduit together providing a serial
passageway for a heat transfer fluid suitable for controlling
patient blood temperature.
3. A blood transport pulsator pump combination comprising:
a slow speed drive and a rotor shaft means coaxially secured
together,
a cylindrical pump rotor having its cylindrical axis of symmetry
precisely displaced parallel to the rotor axis of symmetry, said
rotor mounted on and secured to said rotor shaft means, together
providing a blood pump rotor means,
an internally cylindrical stator pump housing fitting around and
cylindrically enclosing said pump rotor, said rotor shaft means
being eccentrically disposed parallel to the internal axis of
symmetry of said stator pump housing, said pump housing and said
pump rotor proportioned and cylindrically axially copositioned
providing a substantial thin annular laminar flow arc area during
rotor rotation, and cooperatively providing a substantial Taylor
vortex flow arc sector area during rotor rotation,
means providing cooperative bearing support, securing said rotor
shaft means and said stator housing,
means providing cooperative blood sealing support, securing said
rotor shaft means and said stator housing,
means providing heat transfer control disposed in the wall of said
stator pump housing, providing temperature control of blood
pumped,
means conductively secured to said stator housing, adjacent to said
area of laminar flow of blood, providing a blood inlet conduit,
means conductively secured to said stator housing disposed in said
area of laminar flow of blood, providing a blood outlet
conduit,
whereby the rotating said rotor provides laminar blood flow in said
laminar flow arc sector and provides laminar transitional and
Taylor vortex flow in the remainder of the pump arc sector.
Description
Other objects and advantages of this invention are taught in the
following description and claims.
BRIEF DESCRIPTION OF THE DRAWINGS
The description of this invention is to be read in conjunction with
the following drawings:
FIG. 1 is an elevational sectional and partial perspective view of
the blood pump.
FIG. 2 is an enlarged perspective partial sectional view through
2--2 of FIG. 1.
FIG. 3 is a cross sectional view through 3--3 of FIG. 1
illustrating the overall cross sectional configuration of the blood
pump.
FIG. 4 schematically illustrates in cross section the configuration
of the stator axis of symmetry, rotor axis of symmetry and the
rotor shaft axis of symmetry which are required to produce the
pulsatingly pumped blood flow.
FIG. 5 is a further schematic partial axial view of the cross
section of FIG. 4, illustrating the pumping mechanism of the blood
pump of FIGS. 1 and 3.
DESCRIPTION OF THE PREFERRED EMBODIMENT
Refer to FIG. 1, FIG. 2 and FIG. 3 in detail as required. In FIG. 1
the blood transport pulsator pump 10 is shown in side elevational
sectional view detail, having rotor shaft 11 eccentrically disposed
substantially throughout a major fraction of the length of pump 10.
A rotative drive pulley 13 and shaft key 13a are secured adjacent a
first shaft terminus 16. A pair of rotor shaft bearing supports 21
and 22 are each adjacently disposed to shaft terminus 16 and 17
respectively. The bearing supports 21 and 22 are secured in precise
positions on the rotor shaft 11, each said bearing support being
removably securely locked to the shaft 11 by conventional means. A
rigid tubular pump base 23 has a precise internal diameter 35
adaptively providing an internal cylindrical stator housing for the
pump 10. Precisely ground guide pin screws 24 and 25 are shown
threaded into precision threaded apertures 28 and 29 respectively
in the pump base 23, through the precisely located apertures 26 and
27 respectively in the bearing supports 21 and 22. As in
conventional precision bearing supports, a second pair of ground
guide pin screws secure the pair of bearing supports 21 and 22 on
opposed bases of bearing supports, not shown. The pair of unseen
ground guide pin screws likewise are precisely screwed into
threaded apertures in the pump base 23, precisely locating unseen
opposed apertures in the bearing supports 21 and 22 respectively,
providing precise location of 21 and 22.
A pair of first pump eccentricity adapters 30 and 31 are adaptively
disposed between the pair of bearing supports 21 and 22
respectively and the rigid tubular pump base 23. The first pump
eccentricity adapters 30 and 31 are secured by the respective guide
pin screws 24 and 25, disposing the rotor shaft 11 in a precisely
fixed first eccentricity value E.sub.1 parallel with the internal
axis of symmetry 33 of the precision diameter 35 of the internally
cylindrical stator housing 23. The first pump eccentricity adapters
30 and 31 can be metal shims; they can also be equivalent well
known means for precisely fixing the first eccentricity value
E.sub.1 of shaft 11 with respect to the axis of symmetry 33 of the
pump stator housing 23. Thus the first eccentricity E.sub.1 of
shaft 11 is displaced vertically upward. The first eccentricity can
equivalently be disposed along any internal radius of the
360.degree. arc of the pump stator housing 23, for the purpose of
positioning the shaft 11 in a pre-determined first eccentricity
value E.sub.1 or the equivalent. Other securing means can be used,
replacing shims as shaft eccentricity adapters, such as securing
indexing pins, precisely machined lands or grooves, or the
like.
The rigid cylindrical rotor shell 34 is also eccentrically disposed
on the rotor shaft 11, represented by the second eccentricity
E.sub.2. The values of E.sub.1 and E.sub.2 are not separately
represented on FIG. 3, due to their small size. The resultant pump
overall eccentricity, which is a vector sum E, of E.sub.1 + E.sub.2
= E , is the eccentricity value 32, illustrated in FIG. 3.
The system schematic 140 of FIGS. 4 and 5 together illustrate on an
exaggerated scale the stator 141, the rotor 142, and the shaft 143.
The typical relative positions of the stator center 146, the rotor
center 147, and the shaft center 148 are equivalent to the pump
configuration illustrated in detail in FIG. 3. The schematic blood
inlet is 144 and the blood outlet is 145. The resultant
eccentricity 32 of FIG. 3 is also equivalent to the resultant
eccentricity E of FIG. 4, and provides pump pulsed transport of
blood with laminar flow throughout the pump cycle.
Since turbulent blood flow in mechanically pumped extra-corporeal
blood circulation is known to be destructive to formed blood
elements, such as corpuscles and the like, it is very desirable to
provide a blood pump which has a laminar flow pumping cycle. The
blood laminar flow arc sector 75 in FIG. 3 is provided by disposing
the rotor shell 34 in the resultant eccentricity 32, providing a
thin laminar blood pumping means 76. The means 76 is formed between
the stator 23 and the rotor 34 over the arc 75. Further, laminar
flow of blood in the pump 10 or the like is maintained over the
remainder of the pump arc by providing laminar flow with Taylor
vortices over the pumping arc 78. The arcs 111 and 112 respectively
denote transition into and transition out of the pumping means 76.
The significance of the laminar flow with Taylor vortices is
disclosed in detail below.
Referring again to FIGS. 4 and 5 in detail, the pump can be
operated in the Taylor number (Ta) range of
41 < Ta < 400
where
Ta = U.sub.i d/.mu. .sqroot.d/R.sub.i ,
and
U.sub.i = peripheral velocity of rotor 142,
R.sub.1 = radius 150
d = radius 149 - radius 150
.mu. = viscosity of blood
as referenced by Schlichting, H., Boundary Layer Theory, N.Y.,
McGraw-Hill, 1968.
Turbulent flow develops at the high Taylor number Ta = 1715,
corresponding to a Reynolds number R = 3960. Below the above Taylor
number, the generated Taylor vortices 152 have axes which locally
rotate in alternate opposite directions, such as the vortices 152
of FIG. 5. The Taylor vortices 152 provide excellent mixing means,
promoting high rates of heat transfer. Similarly, the Taylor
vortices 152 and the like equivalent vortices can promote a high
rate of mass transfer across the blood membrane pump
cross-referenced in U.S. Ser. No. 190,800, filed Oct. 20, 1971, by
the same applicant.
Again in FIGS. 4 and 5, the offset shaft radius 151 is rotated in
the direction 157, generating the laminar pumping means 153, and
providing a Taylor vortex arc 154, with the incoming transition
region 155 and the exiting transition region 156.
The pump parameters limiting pulsed blood flow are defined by
E E.sub.1 > o, .sub.2 = o no pulsing of blood positive blood
pumping and E E.sub.1 = o, .sub.2 > o positive blood pulsing no
blood pumping
Hence the shape of the pressure distribution curve 110 of FIG. 3 is
determined by the restraints placed on E.sub.1 and E.sub.2. The
shape of the pulse is accordingly modified. The pump provides a
single lobe rotor which impresses a repetitive pressure peak on the
blood output flow, as the double eccentric type of lobe approaches
the outlet conduit 86 or its equivalent 145, on each pump
revolution. By varying the pump RPM, the blood pulse rate or
pressure peak can be varied as desired.
Again referring to FIGS. 1 and 2 in detail, a pair of removable
circular end plates 44 and 45 are respectively disposed at opposed
rotor shell end 38 and end 43. The rotor shell 34 is operationally
sealed against blood leakage by the pair of O-rings 40 and 66,
which are respectively compressively disposed in the pair of O-ring
grooves 39 and 67, located at the shell ends 38 and 43
respectively. The shell 34 has an external diameter 36, a precisely
fixed value less than the internal diameter 35 of the stator
housing 23, as will be discussed later. The precise diameter 36 of
the rotor shell 34 is cooperatively related to the internal
precision diameter 35 of the tubular base 23. A very smooth
exterior surface is disposed on the cylindrical rotor shell 34
exterior face 37.
Each of the end plates 44 and 45 precisely fit respectively into
the rotor end 38 and rotor end 43, also coaxially sealed by the
pair of compressible gaskets 41 and 42 respectively. Two pairs of
removable securing bolts, the pair of bolts 46 and 47 together with
the pair 48 and 49 are shown securing the removable circular end
plates 44 and 45 respectively. The pair of bolts 46 and 47 together
with the pair of bolts 48 and 49 are shown threaded into the fixed
inlet plates 62 and 63, as will be discussed later. Obviously each
removable end plate 44 and 45 can be secured with the required
number of removable securing bolts as is necessary to secure the
rotor shell end fluid tight.
To maintain the removable end plates 44 and 45 fluid tight during
rotation, a pair of removable fluid seals 50 and 51 are
respectively secured against the plates 44 and 45. Securing means
52 and 53 applied against the pair of removable fluid seals 50 and
51 respectively are disposed internally in the tubular stator
housing 23. Typically the securing means 52 consists of an annular
support ring 54 precisely disposed in the tubular stator housing
23, the support ring 54 being locked in position by a removable
retainer ring 56, which in turn holds multiple spring guide pins
58, each guide pin 58 being loaded by one of multiple expansion
springs 60. In a similar manner the removable fluid seal 51 is
secured in position by the means 53. The means 53 comprising as
above, the annular rigid support ring 55 located in position by the
removable retainer ring 57, which in turn positions the multiple
spring guide pins 59, each one of the guide pins having a single
expansion spring 61 disposed thereon.
The fixed circular end plate 62 and the fixed circular outlet plate
63 are permanently coaxially secured in position on the rotor shaft
11, providing a pair of precisely fixed index support positions.
The fixed inlet plate 62 is disposed inside a rotor end 38 and the
fixed outlet plate 63 is disposed inside a rotor end 43. The plate
62 is secured to the shaft 11 as by the weldment 64, and the outlet
plate 63 is secured to the shaft 11 by the weldment 65.
Referring to FIGS. 1 and 3 together in detail, a blood inlet
conduit 80 is shown conductively secured to a blood inlet manifold
81. The manifold 81 in turn is permanently secured to a heat
transfer shell jacket 82 which cylindrically encircles the rigid
tubular pump base 23 over that length of the pump base 23 which
comprises the stator housing. The multiple blood inlet vents 83 are
radially disposed through the heat transfer jacket 82 and the
stator housing 23 providing sealed vents 83 from the blood manifold
81 into the inlet blood groove 108 distributing blood into the
blood laminar flow arc sector 75, shown in FIG. 3. Thus patient
blood can be conductively flowed through the conduit 80, serially
through the blood inlet manifold 81, then through the multiple
blood inlet vents 83 and inlet groove 108, into the blood laminar
flow arc sector 75. When the rotor shell 34 rotates in the
direction of the arrow 77, blood laminar pumping means 76 are
generated over the blood laminar flow arc sector 75 for the length
of the rotor shell 34.
The blood manifold outlet 87 conductively secured to the blood
outlet conduit 86, is in turn disposed parallel along the external
surface of the heat transfer jacket 82, as is the blood inlet
manifold 81. The multiple blood outlet vents 88 are similarly
disposed through the heat transfer jacket 82 venting into the
outlet groove 109. The pair of heat transfer fluid inlet and outlet
conduits 89 and 90 respectively are attached to the jacket 82 as
shown in FIG. 3. The conduits 89 and 90 permit the desired heat
transfer fluid to be circulated in the jacket 82, as will be later
discussed, maintaining the patient's blood at the desired
temperature.
Further details of the blood pump construction are outlined below.
The O-ring groove 91 is disposed in the fixed inlet plate 62,
sealed by the O-ring 93. The snap retaining ring 95 fits in the
retaining ring groove 96, providing an index position for the rotor
shell 34. At the opposed end of the pump 10 a second O-ring groove
98 is filled by the O-ring 100, providing a seal preventing blood
leakage. The snap retaining ring 101 is disposed in the retaining
ring groove 102, which in turn is located in the rotor shell 34,
providing a second indexing position for the shell 34. Conventional
O-rings and groove combinations 103 and 104 are disposed in the
seals 50 and 51 respectively, providing sealing means. The stator
housing extension 106 can be that length which is required to
provide a working platform for the assembly and dis-assembly of the
pump 10. The internal cylindrical surface of stator housing 23,
defined by the stator diameter 35, can be coated with a
polyurethane coating physiologically compatible with patient blood.
The support base 107, extending the length of the stator housing
provides a support base for the pump.
Typically the rotor shell 34, the O-rings 40 and 66, and the pair
of compression gaskets 41 and 42 are assembled at a factory, ready
for placement in a pump 10 as required. The subcombination is to be
used as required in a medical procedure and then discarded, the
remainder of the pump cleaned as necessary, and a second
subcombination replaces the first subcombination.
A pump 10 having a rotor 34 whose diameter 36 is approximately 4
inches and whose length is proportioned to pump the required blood
flow rate for an adult patient, can typically operate in the range
of 60 to 100 RPM, supplying a needed pulsed blood flow. Such a
machine can also be used as a blood pump for perfusion of an organ,
such as a heart or kidney, prior to surgical transplant procedure.
When required, as in transplant procedure or the like, a
refrigerant such as water or a Freon as is necessary, can be used
to cool blood and organs to temperatures typically 28.degree.C or
less for hypothermia. Likewise warmer water can be provided to warm
patients and patient's blood as becomes necessary. The machine
stores small amounts of patient's blood during medical procedures
and has the advantage of decreasing patient blood loss under
critical conditions.
The pump 10 can be a permanent apparatus suitable for use in
medical procedures, with a replaceable essentially single use
plastic rotor shell. The shell can be separately prepared in a
factory for use as required in a specific medical procedure.
Many modifications and variations in the improvement in a pulsator
blood transport pump can be made in the light of my teaching. It is
therefore understood that within the scope of the appended claims,
the invention may be practiced otherwise than as has specifically
been described.
* * * * *