U.S. patent number 3,766,567 [Application Number 05/173,396] was granted by the patent office on 1973-10-23 for artificial heart assembly and heart assist device.
This patent grant is currently assigned to Cutter Laboratories, Inc.. Invention is credited to Ronald C. Brown, Paul Kahn.
United States Patent |
3,766,567 |
Kahn , et al. |
October 23, 1973 |
**Please see images for:
( Certificate of Correction ) ** |
ARTIFICIAL HEART ASSEMBLY AND HEART ASSIST DEVICE
Abstract
An artificial heart assembly comprising a pair of ventricles, a
pair of atria or inflow means, a pair of sinus or outflow means for
pumped blood, and fluid pumps to drive the ventricles. In a
modification, a single ventricle is used as a ventricular assist
device. Each ventricle has a shell providing a ventricular cavity
and at least one pumping chamber in the shell. The chamber has a
flexible non-stretching wall and a rigid wall sealed to each other.
The rigid wall has an aperture to permit entry of the pumping fluid
into the chamber. A blood-compatible material covers all
blood-exposed surfaces in the cavity.
Inventors: |
Kahn; Paul (San Francisco,
CA), Brown; Ronald C. (Oakland, CA) |
Assignee: |
Cutter Laboratories, Inc.
(Berkeley, CA)
|
Family
ID: |
22631815 |
Appl.
No.: |
05/173,396 |
Filed: |
August 20, 1971 |
Related U.S. Patent Documents
|
|
|
|
|
|
|
Application
Number |
Filing Date |
Patent Number |
Issue Date |
|
|
72628 |
Sep 16, 1970 |
|
|
|
|
Current U.S.
Class: |
623/3.21;
128/DIG.3; 623/3.26; 128/899 |
Current CPC
Class: |
A61M
60/894 (20210101); A61M 60/268 (20210101); A61M
60/148 (20210101); A61M 60/122 (20210101); Y10S
128/03 (20130101); A61M 60/40 (20210101); A61M
60/857 (20210101) |
Current International
Class: |
A61F
2/24 (20060101); A61M 1/10 (20060101); A61M
1/12 (20060101); A61f 001/24 () |
Field of
Search: |
;3/1,DIG.2
;128/1R,DIG.3,334R,334C |
References Cited
[Referenced By]
U.S. Patent Documents
Foreign Patent Documents
Other References
"Orthotopic Cardiac Prosthesis: Preliminary Experiments in Animals
with Biventricular Artificial Heart" by M. E. DeBakey et al.
Cardiovascular Research Center Bulletin Vol. VII No. 4, April-June
1969, pages 127-133 and 136-138. .
"A Pseudoendocardium for Implantable Blood Pumps" by D. Liotta et
al. Trans. Amer. Soc. Artif. Fnt. Organs, Vol. XII, 1966, pages
129-134. .
"A Prosthetic Heart with Hemispherical Ventricles designed for Low
Hemolytic Action" by C. Kwan - Gett et al.. Trans. Amer. Soc.
Artif. Int. Organs, Vol. XVI, Apr. 1970, pages 409-415. .
"A Time and Volume Controlled Extracorporeal Pump" by J. R.
Hinglais et al., Trans. Amer. Soc. Artif. Int. Organs, Vol. XIII,
1967, pages 317-321..
|
Primary Examiner: Gaudet; Richard A.
Assistant Examiner: Frinks; Ronald L.
Parent Case Text
CROSS REFERENCE TO RELATED APPLICATION
This application is a continuation in part of application Ser. No.
72,628, filed Sept. 16, 1970 now abandoned.
Claims
What is claimed is:
1. An improved artificial ventricle including in combination:
a generally rigid ventricle shell means providing a ventricular
cavity and having inlet means and outlet means for blood, said
verticle shell means comprising an outer shell and an inner
shell,
pumping means providing at least two pumping chambers within said
cavity and comprising a diaphragm for each pumping chamber secured
between said inner and outer shells and dividing the pumping
chamber from a blood-flow chamber in said cavity, each said
diaphragm being a flexible, non-stretching, impervious membrane,
said inner shell having aperture means enabling entrance of pumping
fluid into said pumping chambers, said inner shell being sealed at
its back side to each said diaphragm and to said outer shell,
blood-compatible material covering all blood-exposed surfaces of
said ventricle shell and said diaphragm, and
conduit means connected to said aperture means for conducting
pumping flow to said chamber,
said pumping chambers enabling central flow of blood in said blood
flow chamber.
2. The ventricle of claim 1 wherein said pumping chambers are so
disposed that when fully expanded the flexible membranes do not
touch each other, thereby minimizing red cell trauma.
3. The ventricle of claim 1 wherein said pumping chambers are
disposed to diverge from each other upwardly and outwardly from a
lower end of said shell means.
4. The ventricle of claim 1 wherein said shell means is made from
stiff silicone rubber.
5. The ventricle of claim 1 wherein said shell means is made from
glass fiber cloth impregnated with epoxy resin.
6. The ventricle of claim 1 wherein said shell means is made from
metal.
7. The ventricle of claim 1 wherein said blood-exposed surfaces are
all covered with Dacron velour.
8. The ventricle of claim 1 wherein said flexible membrane is of
flexible silicone rubber.
9. The ventricle of claim 1 wherein said flexible membrane is of
elastomer-impregnated non-expandable cloth.
10. The ventricle of claim 1 having valves in both said inlet and
outlet means.
11. The ventricle of claim 1 having an artificial atrium detachably
connected to said inlet means.
12. The ventricle of claim 11 having an artificial sinus detachably
connected to said outlet means.
13. The ventricle of claim 12 wherein both said detachable
connections comprise a pair of rings, one rotatably mounted to said
ventricle, the other being secured in one instance to said sinus
and in the other instance to said atrium, each ring of each pair
having a flange with suture openings therethrough, the rotatable
mounting of said one ring of each pair enabling alignment of its
suture openings with those of the other ring of that pair.
14. The ventricle of claim 13 wherein a valve is seated by press
fit in an annular shouldered recess in each said ring that is
mounted to said ventricle.
15. An artificial heart assembly comprising in combination:
a. a pair of ventricles,
b. a pair of atria, one connected to each said ventricle,
c. a pair of sinus, one connected to each said ventricle,
d. means to provide pumping fluid to said assembly,
e. outflow means for pumped blood, including a valve for each
ventricle,
f. intake means for blood to be pumped, including a valve for each
ventricle,
g. each said ventricle comprising:
1. a rigid outer shell providing a ventricular cavity,
2. at least two pumping chambers disposed in said cavity and having
one flexible nonstretching diaphragm wall separating each said
pumping chamber from a blood-flow chamber in said cavity and a more
rigid inner shell sealed to each said diaphragm and secured to said
outer shell,
3. said inner shell having an aperture therein to permit entry of
pumping fluid into said pumping chamber,
4. blood-compatible material covering all blood-exposed surfaces in
said cavity; and
5. means to conduct pumping fluid to said pumping chamber,
6. said chambers being of predetermined capacity.
16. The assembly of claim 15 wherein said blood-compatible material
is Dacron velour.
17. The assembly of claim 15 wherein each said ventricle has two
connectors, each having a body with an annular shouldered recess,
and a stiff radial flange rotatably mounted to said body and having
circumferentially spaced holes therethrough, one said valve being
seated and held in each said recess, a connector for each atrium
and each sinus mated with a connector on said ventricle and each
having a radial flange with circumferentially spaced holes
therethrough and alignable with those of a flange on the
ventricle's connector, by rotation of the flange on the ventricle's
connector, for suturing said flanges together.
18. The assembly of claim 17 wherein each said valve is a
low-profile valve having an annular housing press fitted into said
recess.
19. An artificial heart ventricle assembly comprising in
combination:
a. a ventricle,
b. an atrium separate from said ventricle and separately attachable
to a patient's atrial remnant before attachment to said
ventricle,
c. an atrioventricular valve enclosed between said atrium and said
ventricle upon attachment of said atrium to said ventricle,
d. a sinus separate from said ventricle and separately attachable
to a patient's aorta or pulmonary artery before attachment to said
ventricle,
e. a sinuventricular valve enclosed between said sinus and said
ventricle upon attachment of said sinus to said ventricle,
f. means for providing pumping fluid for said ventricle,
each said ventricle comprising:
1. a rigid shell providing a ventricular cavity,
2. at least two pumping chambers disposed in said cavity each
having one flexible nonstretching wall and one rigid wall sealed to
each other,
3. each said rigid wall secured to said shell and having an
aperture for entry of pumping fluid into said chamber,
4. each said flexible wall dividing said pumping chamber from a
blood-flow chamber in said cavity,
5. blood-compatible material covering all blood-exposed surfaces in
said cavity; and
6. means for conducting said pumping fluid to said pumping
chamber,
7. said chambers being of predetermined capacity.
20. The assembly of claim 19 wherein said blood-compatible material
is Dacron velour.
21. The assembly of claim 19 wherein said atrium and said sinus
each have a female connector having an annular socket receptacle
and a radial flange having a plurality of spaced openings
therethrough and said ventricle has two male connectors each
pluggable into a said socket receptacle and having a radial flange
mounted rotatably to said male connector and having a plurality of
spaced openings therethrough like those of said flange of said
female connector alignable therewith by rotation relative to said
male connector, for suturing together of said mating
connectors.
22. The assembly of claim 21 wherein each said male connector has
an annular shouldered recess, one receiving said atrioventricular
valve and one receiving said sinuventricular valve for press fit
therewith.
23. A heart assist device, comprising in combination
a. an artificial ventricle comprising
1. a rigid shell providing a ventricular cavity,
2. at least two pumping chambers disposed in said cavity, each
having one flexible nonstretching wall and one rigid wall sealed to
each other,
3. each said rigid wall secured to said shell and having an
aperture for entry of pumping fluid into said chamber,
4. said flexible wall dividing said pumping chamber from a
blood-flow chamber in said cavity,
5. blood-compatible material covering all blood-exposed surfaces in
said cavity,
6. means for conducting said pumping fluid to each said pumping
chamber,
7. inflow and outflow valves for blood flowing to and from said
blood-flow chamber,
b. an apex connector, covered with blood-compatible material,
having means enabling suture of said connector to a patient's heart
and providing a channel for removal of blood from that heart,
and
c. conduit means for connecting said apex connector to said
artificial ventricle and for connecting said ventricle to the
patient's descending aorta.
24. The device of claim 23 wherein said conduit means comprises
arterial graft tubing.
25. The device of claim 23 wherein each said conduit means is
connected to said ventricle by a connector assembly comprising a
male connector and a female connector, each having a body and a
radial flange with identically spaced perforations therethrough,
one said radial flange being rotatable relative to its said
body.
26. The device of claim 23 wherein said apex connector comprises a
rigid tube lined exteriorly and interiorly with blood compatible
material and having a terminal radial flange for engaging the
interior wall of the patient's heart, and a radial sewing flange
spaced away from said terminal flange and suturable to the heart
muscles.
27. The device of claim 26 wherein said rigid tube has a radial
flange to which said sewing flange is sutured.
Description
BACKGROUND OF THE INVENTION
This invention relates to an artificial heart assembly that is
implantable in a human being or an animal for functioning similarly
to the natural heart, and also relates to a heart assist device for
supporting a natural heart. Either assembly can function over an
extended period of time, providing controllable pressure, volume,
and rate control. Both assemblies are blood-compatible and require
little, if any, anticoagulation. Implantation is relatively easy
and convenient.
Devices are known which use pneumatic or hydraulic pressure as a
motive force to activate an artificial heart or heart assist. The
single ventricle of the assist or each of the two ventricles used
in a total prosthesis usually has comprised a double walled chamber
with an inner bladder representing the ventricular cavity, pressure
being applied in the outer chamber. The outer wall, whether rigid
or flexible, has had a tubulation for transmission of the gas or
fluid medium, but there has been no specific control of the pump
volume, and the expansion and elasticity of the pneumatic or
hydraulic chamber has required excessive pumping and relief time,
due to expansion of the outer chamber and compressibility of the
medium. The atrial connection chambers have usually been attached
to the ventricles, and the ventricles have been connected in a way
that has tended to cause difficulties in the surgical procedure for
installation of the artificial heart.
The above difficulties are overcome by the device of the present
invention, and other advantages will become apparent from the
description which follows. For instance, the ventricle of the
present invention provides a precise and predetermined pump volume;
the pumping chamber walls are flexible and non-elastic and as a
result provide a more constant and uniform supply of blood under
controllable pressure and at a controlled rate. The atria and
sinuses as part of the prostheses are detachable from the
ventricles so that at the time of surgery, attachment of these
parts to the atrial remnants and arteries after removal of the
heart or to the apex of the left ventricle (in the case of the
assist) is more readily accomplished. The blood-contacting surfaces
of this new device are blood-compatible with minimal embolic
risk.
BRIEF SUMMARY OF THE INVENTION
The present invention provides an artificial heart assembly or a
heart assist device which can be implanted in an animal or human
body and which provides a constant and uniform pulsing flow of
blood, with minimal risks of coagulation, embolism or infection,
and with optimal ease of installation and use.
The invention provides a ventricle containing one or more pumping
chambers. A means for introducing a fluid, either gas or liquid, is
provided for each pumping chamber. A prosthetic heart assembly
includes one or two such ventricles while a heart assist uses a
single ventricle. The pumping fluid is kept separated from the
blood, and there is means for connecting the blood outlet from each
ventricle to one of the body's arterial systems. An atrium connects
the ventricle to the patient's venous system in the total heart
device. In the heart assist, a special connection joins the
patient's left ventricle to the assist device. In both devices,
there are inflow and outflow valves located in the inflow and
outflow means, respectively.
Each pumping chamber comprises a rigid outer wall and a flexible,
non-stretching diaphragm wall, the two walls being secured together
at or adjacent their edges, as by sutures or by cement or by
compression seal, to define a generally ovoid bladder when
inflated. When deflated, the flexible membrane lies against the
rigid wall while the central space or blood-flow chamber of the
ventricle, in which the pumping space is disposed, fills with the
blood to be pumped. The walls of the blood-flow chamber and any
other surfaces of the device or assembly which are exposed to blood
are provided with a blood-compatible covering, advantageously
Dacron velour. The rigid wall is made of a physiologically
compatible material such as stiffened silicone rubber,
resin-impregnated glass-fiber cloth, or a suitable plastic or
metal.
The present invention provides separate impervious non-stretching
pumping chambers of the exact size desired. While a single chamber
may be used, two pumping chambers are preferably used for each
ventricle, in order to economize size and movement and to provide
central flow of blood in the ventricle. One side of each chamber --
the outer side -- is made rigid to force expansion to take place
only in the desired direction, which is inwardly. Fluid or gas
passages are provided in this rigid shell so that the movable
diaphragm is uncomplicated in form in the interest of extending
flexural fatigue life. The diaphragm membrane is non-stretching and
is impervious to liquid and gas, to provide controlled pressure,
volume, and position in the ventricle and to separate the pumping
fluid from the blood by separating the pumping chamber from the
blood-flow chamber. Prefabrication of the pumping chambers enables
their pretesting to assure freedom from leaks.
The pumping chambers are assembled into the ventricle, usually
being placed at an angle to give the most economical use of space,
and to prevent their touching opposing walls when fully expanded to
minimize red cell trauma. This enables control of the volume and
pressure. When more than one expansion or pumping chamber is used
in a single ventricle, the expansion or pumping chambers are
preferably interconnected at the base or tip of the ventricle to a
common gas or liquid conduit. A separate conduit is provided for
each ventricle. The ventricle is preferably shaped to be round or
oval laterally, to accommodate the expansion or pumping chambers in
the side wall or walls, and the inflow and outflow valves fit
naturally into the spaces at the top of the ventricle. The entire
ventricle is lined with an impervious lining, such as velour,
especially Dacron velour, or other blood-compatible material.
The atria and sinus, which may be part of the inflow and outflow
means, may be fabricated separately, so that the ventricle may be
attached to them by suitable connectors which mate with connectors
on top of the ventricle. This attachment is done after the atria
and sinus are surgically attached to the patient or animal. This
technique results in easier surgical insertion and
manipulation.
When a single ventricle is used as a heart assist device, the
patient's own heart is left intact in this application. A suitable
connector is placed in the apex of the left ventricle to draw blood
out of the patient's left ventricle into the artificial ventricle
via a flexible plastic tube such as a Dacron tube. The artificial
ventricle or heart assist may be placed in the abdominal cavity,
inferior to the diaphragm or it may be left outside the body. The
artificial ventricle then pumps blood through a suitable flexible
tube into the descending aorta. Valves are located at the top of
the artificial ventricle. This device relieves the load on a
patient's own heart for an indefinite period of time permitting his
own heart to recover sufficiently to resume its full capacity.
Other objects and advantages of the invention will appear from the
following description of some preferred embodiments.
BRIEF DESCRIPTION OF THE DRAWINGS
FIG. 1 is a partially exploded view in side elevation of an
artificial heart ventricle, embodying the principles of the
invention, with a prosthetic valve and an atrium shown ready for
insertion and attachment. A detachable sinus and outflow prosthetic
valve are shown connected. The attachment to a pump is broken and
is shown partly diagrammatically.
FIG. 2 is a view in section, taken along the line 2--2 in FIG. 1,
with the pumping chambers collapsed.
FIG. 3 is a view similar to FIG. 2 with the pumping chambers
expanded to a maximum.
FIG. 4 is a view in section, taken along the line 4--4 in FIG. 1,
with the pumping chambers expanded as in FIG. 3.
FIG. 5 is a view in perspective of two of the ventricles of FIG. 1
attached to each other to provide a complete heart prosthesis.
FIG. 6 is an exploded enlarged fragmentary view in section of a
portion of the apparatus showing the connectors and a valve between
the atrium and the ventricle.
FIG. 7 is a view similar to FIG. 6 with the parts assembled.
FIG. 8 is a fragmentary view partially in section of a heart assist
device embodying the principles of the invention, completely
connected to the patient's heart and descending aorta.
FIG. 9 is a view in section of an apex connector used with the
heart assist device.
DESCRIPTION OF SOME PREFERRED EMBODIMENTS
An entire totally artificial heart 10 (see FIG. 5) of this
invention comprises two identical artificial ventricles 11 and 12,
two atria 13 and 14 serving as blood inflow means into their
respective ventricles 11 and 12, and two sinus 15 and 16 serving as
the outflow means for blood from the respective ventricles 11 and
12.
Each of the two identical ventricles 11 and 12 has an air bleeder
line 17 (see FIG. 1) and gas or fluid lines 18 or 19 for the
pumping fluid, leading to a pump 20 (FIG. 1). Between each atrium
13, 14 and its ventricle 11, 12 is an inflow or atrioventricular
valve 21, located where a flanged connector 22 on the atrium 13
meets and mates with a flanged connector 23 on the ventricle 11.
The atrium 13 has a wall 24 at its other end for attachment to the
patient's residual atrial walls after removal of the recipient's
heart. Between each ventricle 11, 12 and its sinus 15 or 16 is an
outflow or sinuventricular valve 25 housed in similar flanged
connectors 26 and 27. The sinus 15 and 16 also have tubulation 28
for connection to the patient's aorta or pulmonary artery. The
flanged connectors 22, 23 and 26, 27 greatly ease the technical
problem of insertion of the prosthesis 10 at the time of surgery,
since the atrium 13 and sinus 15 can be surgically installed
individually, unencumbered by the ventricle 11. Connection of the
ventricle 11 to its atrium 13 and sinus 15 is simplified in that
one merely "plugs" the parts together, securing the flanges to one
another with sutures threaded into holes provided in the flanges as
described below. After the prosthetic heart 10 is fully assembled,
it is filled with blood, and any air is removed via the bleeder
line 17, which is then sealed. The gas or fluid line 18 (or 19) is
brought out through the body wall 29 and connected to a suitable
power source or pump 20 for continued operation of the device.
Individual power sources are used for each ventricle 11, 12 since
the pressure requirements for the arterial and pulmonary
circulations are different.
The ventricle 11 shown in FIGS. 1-4 has an outer shell 30 made of
rigid material, preferably fiberglass-reinforced epoxy resin,
though it may be made from other rigid plastics, or from metal, so
long as these are biologically compatible, or the shell 30 may be
made so biologically compatible by covering or coating a rigid
material with a compatible material such as stiff silicone rubber.
The shell 30 provides a ventricular cavity 31, and, disposed within
the cavity 31 is at least one pumping chamber, preferably two
pumping chambers 32 and 33 connected to respective gas passages 34
and 35. The chambers 32 and 33 are separated from the blood by two
fluid impervious membranes 36 and 37, preferably made from silicone
rubber impregnated Dacron fabric or other suitable non-stretching,
flexible material. The membranes 36 and 37 are preferably wrapped
around the edges and bonded to the back surfaces of inner shells 38
and 39 respectively. These inner shells are preferably made of
material similar or identical to that of the outer shell 30.
Openings 40 and 41 are provided in the inner shells 38 and 39 to
enable fluid to enter the chambers 32 and 33.
The enclosed pumping chambers 32 and 33 are thus bounded partly by
the inner shell 38 and 39 and partly by the fluid-impervious but
flexible diaphragms or membranes 36 and 37. The blood exposed
surfaces of the diaphragms 36 and 37 and of the outer shell 30 are
covered by a blood compatible material 42 such as Dacron velour, by
impregnating one side of the velour -- without filling the pile on
the other side -- with a suitable medical rubber impregnant and
then adhesively attaching the velour 42 to the diaphragms 36 and 37
and the shell 30. Also the tube 18 which connects the power source
20 to the gas passages 34 and 35, preferably via a Y-shaped
connector 43, is preferably exteriorly coated with Dacron velour
44.
The pressure chambers 32 and 33 are preferably placed so as to be
on a slight angle to the vertical centerline of the ventricular
cavity 31 -- that is, they diverge from each other and from the
blood flow chamber 45 upwardly and outwardly from the lower end 46
of the shell 30 -- so that when the chambers 32 and 33 are fully
expanded, their flexible diaphragm walls 36 and 37 do not touch
each other, minimizing blood trauma. The pumping chambers 32 and 33
may be placed in position and affixed to the interior surface of
the outer shell 30, for example, by cementing the inner shells 38
and 39 to the outer shell 30 with a medical rubber cement.
At the top of ventricle 11 is a blood inlet area 47 and a blood
outlet area 48. FIGS. 6 and 7 show the configurations of the
connectors 22,23 between the ventricle 11 and the atrium 13, and
the connectors 26 and 27 are substantially the same as the
connectors 22 and 23. The body 50 of the ventricular or male
connector 23 can be an integral part of the ventricle shell 30 or
can be made from another piece and bonded or welded to the shell
30. An annular recess 51 with a shoulder 52 is provided in the body
50 of the connector 23 in which the valve 21 is seated and is
mechanically locked in position by press fit. The valve 21 is
preferably a Wada-Cutter tilting disc valve but may be any suitable
prosthetic or tissue valve. The blood compatible lining 42 is
continued right up to the valve 21. The atrial or female connector
22 has a body 53 with an annular receptacle 54 having a cylindrical
wall 55 and a shoulder 56, against which end wall 57 of the body 50
abuts, the bodies 50 and 53 nesting together tightly.
Against a shoulder 61 of the body 50, a flange 60 is mounted so
that it can be rotated relatively to the body 50, and the flange 60
mates with a flange 62 on the body 53, preferably fixed to the body
53. These flanges 60 and 62 are made of rigid material such as
stainless steel or other suitable material such as rigid plastic or
fiberglass-reinforced epoxy resin. The flanges 60 and 62 each have
a spaced series of holes 63 and 64 respectively, distributed around
the peripheries of the flanges 60 and 62 so that the two flanges 60
and 62 can be sutured together, thereby firmly securing the two
connectors 22 and 23 together. The flange 60 can be rotated about
the vertical axis so as to align the holes 63 and 64. The generally
cone-shaped atrium 13 is preferably constructed from silicone
rubber sheet 65 (which may be reinforced with fabric) and along
with a blood compatible lining 66, preferably Dacron velour, is
bonded to the body 53 of the connector 22. The connectors 26 and 27
between the sinus 15 and the ventricle 11 are identical to the
connectors 22 and 23 except that the outflow valve 25 is a
flipped-over valve 21 so as to function properly.
In surgery the surgeon connects to the patient an external
heart-lung machine to maintain the patient's circulation and
oxygenation while the operation is in progress. By one method, he
takes out the patient's natural heart and puts in the first or
lower atrium 13, suturing it to an atrial remnant. The second
atrium 14 is then sutured to the other atrial remnant. The arterial
graft tubing 28 attached to the sinus 15 is sutured to the
pulmonary artery, and the second sinus 16 is attached to the aorta
via additional arterial graft tubing 28. The connectors 23 and 27
of the ventricles 11 and 12 are then "plugged" into the atrial and
sinus connectors 22 and 26, securing them by sutures through the
holes 63 and 64 in the connector flanges 60 and 62. The ventricles
11 and 12 are then attached to each other by straps 67 of silicone
impregnated Dacron cloth, which are bonded to each ventricle and
are then sewn to each other.
In another embodiment, a single ventricle 11 can be used as a heart
assist device. FIG. 8 shows the configuration of the attachment to
the patient's left ventricle 70 and his descending aorta 71. Blood
is removed from the apex 72 of the heart 73 via a suitable apex
connector 74.
This apex connector 74 (see also FIG. 9) is provided with an
internal radial extension 75 for positioning the apex connector 74
flush with the inner surface of the heart 73. The apex connector 74
also has another radial extension, a sewing flange 76 for suturing
the apex connector 74 to the heart muscle.
As shown in FIG. 9, the apex connector 74 preferably has a thin
metal or plastic tube 77 for stiffening the apex connector 74. The
inner and outer surfaces of the tube 77 are covered with adhesive
78 such as silicone rubber, to bond to it an exterior sleeve 80 of
blood compatible material and an inner sleeve 81 of
blood-compatible material, both sleeves preferably being Dacron
velour. The radial extensions 75 and 76 may have fillers 82 and 83,
such as silicone rubber sheet, to provide bulk. The sewing flange
76 may be attached to the body of the apex connector 74 by suturing
through holes 84 provided around the periphery of a flange 85 that
is part of the rigid tubing 77. A tubular extension 86 is provided
for attachment by suture to arterial graft tubing 87.
This tubing 87 is, in turn, sutured to a heart assist inflow
adapter 88, which, like a heart assist outflow adapter 89, is
constructed essentially from the same materials as the atrium 13
and sinus 15, i.e., silicone rubber sheeting lined with blood
compatible material, preferably Dacron velour. Built into the
assist adapters 88 and 89 are connectors 90 and 91 like the
connector 22 of FIGS. 6 and 7 for easy attachment to the connectors
23 and 27 on the ventricle 11. As in the total heart 10, inflow and
outflow valves are housed inside the connectors 23 and 27 on top of
the venricle 11. Arterial graft tubing 92 is sewn onto the heart
assist outflow adapter 89 and to the patient's descending aorta 71.
Both arterial graft tubings 87 and 92 are made of flexible,
non-collapsing materials, for example, spirally wound metal wire
covered with silicone with an interior bonded covering of Dacron
velour.
At the time of surgery a hole is punctured in the apex 72 of the
patient's heart 73, and the apex connector 74 is inserted. The
sewing flange 76 is sutured to the heart muscle. Holes 93 and 94
are cut in the patient's diaphragm 95, and the arterial graft tubes
87 and 92 are inserted through these holes 93 and 94. The tube 87
is sutured to the apex connector 74, and the tube 92 is sutured to
the descending aorta 71. The assist adapters 88 and 89 may be
attached by suturing to the tubes 87 and 92 at this point, or they
may have been sutured prior to surgery. The connectors 23 and 27 of
the ventricle 11 are then "plugged" into the connectors 90 and 91
of the adapters 88 and 89 and secured by sutures. The fluid
pressure line 18 is brought out through the body wall 29 as in FIG.
1 and is attached to the power source 20 as described
previously.
The above specific description and the drawings have been furnished
for illustrative purposes only, and variations and modification can
be made without departing from the spirit and scope of the
invention.
* * * * *