U.S. patent number 3,842,440 [Application Number 05/285,749] was granted by the patent office on 1974-10-22 for implantable linear motor prosthetic heart and control system therefor.
Invention is credited to Eskil L. Karlson.
United States Patent |
3,842,440 |
Karlson |
October 22, 1974 |
IMPLANTABLE LINEAR MOTOR PROSTHETIC HEART AND CONTROL SYSTEM
THEREFOR
Abstract
Linear drive pump and control means provide pulses of fluid of
desired wave form into one or two conduits. The wave forms in two
conduits may be the same or different, and controlled if desired by
preprogrammed means. If employed as a half or whole heart sensing
means disposed within the circulatory system or the artificial
heart may be used to provide data for modifying preprogrammed data
and scanning and monitoring means and means for recharging a power
source implanted in a body may be provided.
Inventors: |
Karlson; Eskil L. (Stamford,
CT) |
Family
ID: |
23095537 |
Appl.
No.: |
05/285,749 |
Filed: |
September 1, 1972 |
Current U.S.
Class: |
623/3.19;
417/412 |
Current CPC
Class: |
A61M
60/40 (20210101); A61M 1/1053 (20130101); A61M
60/50 (20210101); A61M 60/268 (20210101); A61M
60/871 (20210101); A61M 60/148 (20210101); A61M
60/896 (20210101) |
Current International
Class: |
A61M
1/10 (20060101); A61f 001/24 () |
Field of
Search: |
;3/1,DIG.2
;128/1D,1R,DIG.3,419R,419D,419B ;417/412 |
References Cited
[Referenced By]
U.S. Patent Documents
Foreign Patent Documents
Other References
Final Report: Summary and Conclusions - Artificial Heart Program,
The Children's Hospital Medical Center, by Thermo Electron
Engineering Corp., Waltham, Mass., 1966, pages 25-26. .
"A Linear Oscillating Electromotor for Possible Application in an
Intrathoracic Artificial Heart" by W. H. Burns et al., Transactions
A.S.A.I.O., Vol. X, 1964, pages 151-153. .
"Development of an Artificial Intrathoracic Heart" by C. K. Kirby
et al., Surgery, Vol. 56, No. 4, Oct. 1964, pages 7-19-725. .
"The Cardiac Programmer to Trigger an Arterial Pump" by W. P.
Murphy, Transactions Amer. Soc. Art. Internal Organs, Vol. VII,
1961, pages 361-373..
|
Primary Examiner: Gaudet; Richard A.
Assistant Examiner: Frinks; Ronald L.
Attorney, Agent or Firm: Hoag; John W.
Claims
What I claim is:
1. A prosthetic heart adapted to be implanted within the body of a
human being or other animal, and a system for operating it,
comprising, a single collapsible chamber, having inlet and outlet
ports, adapted to be connected respectively to a vein and an
artery, means for opening the chamber to receive fluid from a vein
to which it is adapted to be connected, means for closing the
chamber and expelling pulses of fluid from it into an artery to
which it is adapted to be connected, means for controlling the
expelling means so as to provide in the artery predetermined
changes in pulse pressure, amplitude and frequency, a source of
electric power adapted to be disposed within the body, and
circuitry for connecting it to the prosthetic heart for operating
it, a source of electric power to be located outside the body, and
circuitry including, leads adapted to be implanted within the body,
and connected to said source of power to be located within the
body, leads connected to the source of power outside the body, and
separable contact members connected to said leads respectively and
adapted when physically brought together to connect the source of
electric power outside the body directly to the source of electric
power to be implanted within the body, to recharge the latter from
the former, said separable contact members including at least a
first set of contact members adapted to be disposed on teeth of the
body, and another set of contact members are sized and shaped for
mounting on teeth of the body adapted to carry said first set of
contacts, and the said leads adapted to be implanted within the
body are adapted to extend from said first set of contacts through
the root canals of the teeth intended to carry said contacts, and
the other set of contacts are connected to the said leads which are
disposed outside the body and extend to the said source of power
outside the body.
2. The device claimed in claim 1 in which one set of said contact
members are adapted for mounting on teeth of the body and are
connected by leads which extend to scanning means disposed outside
the body.
3. The device claimed in claim 1 including a mouth piece adapted to
fit over contact means adapted for mounting on teeth of the body
and having conductive means adapted to engage the contact means
with means disposed outside the body.
4. A prosthetic heart adapted to be implanted within the body of a
human being or other animal and the system for operating it which
comprises, a single housing having therein two fluid chambers,
separate movable piston-like members having heads connected to the
walls of the chambers respectively, and separate coils mounted on
said piston-like members respectively, a magnetic field in which
each of said coils is disposed, and power and control means for
energizing said coils and alternating their polarity separately,
whereby the piston-like members are separately reciprocated and the
force, amplitude and frequency of the strokes of said piston-like
members may be the same or different, and the strokes of each of
said piston-like member may be varied individually.
5. The apparatus claimed in claim 4 including a source of electric
power adapted to be implanted within the body, circuitry for
connecting the said source of power to said coils respectively, for
implanting within the body, a source of electric power to be
located outside the body, and circuitry including, leads adapted to
be implanted within the body, and connected to the source of power
to be located within the body, leads connected to the source of
power outside the body and separable contact members connected to
said leads respectively and adapted when physically brought
together to connect the source of electric power outside the body
directly to the source of electric power to be implanted within the
body, to recharge the latter from the former.
6. The apparatus claimed in claim 4 in which the control means
includes, program control means, pressure detector means and power
amplifier means, all disposed within said prosthetic heart.
7. The apparatus claimed in claim 4 in which each piston-like
member comprises a rod portion and a head portion, the rod portions
extend in opposite directions and are concentrically disposed, one
of said coils is supported around the rod portion of one of said
piston-like members, and the head portion of the other of said
piston-like members is cup-shaped and the other of said coils is
mounted around the rim of said cup-shaped head portion.
Description
FIELD OF THE INVENTION
The invention relates to a compact and efficient pump adapted to
provide pulses of fluid into a conduit or a plurality of conduits.
Pulse flow into two conduits may be provided alternately or in any
timed relation, and the wave shape of either series of pulses may
be modified as desired. The flow in the two conduits may be the
same or different fluids and the flow in either conduit may be
started or stopped without effecting the flow in the other
conduit.
The operation of the pump may be programmed for optimum operating,
and changes in the wave form or the shutting off or starting of
flow in either or both conduits may be accomplished
automatically.
The operation of the pump may be scanned and the pressure and/or
duration of the pulses in either conduit may be read and any
variance from optimum operating conditions may be remedied.
In addition to its commercial uses the pump, when made of suitable
materials, is adapted for use as a prosthetic heart, or half heart,
which can be implanted in an animal or human body, and for such use
compact power and control means, which can also be implanted in an
animal or human body, are disclosed together with means whereby
leads may be inserted into the body without leaving openings into
the body subject to infection. Contact means are provided whereby
the leads may be connected to means outside the body for recharging
the power source within the body and for monitoring the operations
of the heart.
SUMMARY OF THE DISCLOSURE
The invention may be embodied in a single or a double piston pump.
In its single piston form the pump may have one or two fluid
chambers. In each case a coil carried by a piston-like member is
energized causing the coil and member to reciprocate to alternately
open and close the chamber or chambers. In each form fluid is
expelled from one chamber or a pair of chambers in pulses of
controlled wave form.
The fluid chambers may be spaces at the ends of a pair of opposed
cylinders, the spaces being opened to receive fluid and closed to
discharge fluid, by reciprocating piston heads. As shown herein in
its form using a single piston-like member to open and close one or
two chambers a coil carrying piston-like member is reciprocable
within a magnetic field. Both the field and the coil are
constructed in a way to increase their strength and efficiency.
Preferably two magnetic fields of opposite polarity act
simultaneously on a coil mounted on a reciprocating piston-like
member. A source of electrical power fed to a pulse generator
connected to the coil continually changes the polarity of the coil
causing reciprocation of the coil carrying piston-like member. One
or both ends of the piston-like member are extended laterally and
attached in any suitable manner to the opposed face or faces of the
collapsible chamber or chambers. Each of the chambers has an inlet
port and a discharge port each controlled by a check valve. As a
chamber is collapsed by the movement of the piston-like member
fluid is expelled from it through its discharge port into a
communicating conduit, and in its two chamber form, the other
chamber is expanded and fluid is drawn into the other chamber
through its inlet valve. If desired the reciprocation of the
piston-like member may be controlled so that its stroke in one
direction is not the same as its stroke in the other direction,
thus providing flow of different wave form in the conduits.
In the double piston embodiment of the invention two separate coil
carrying piston-like members are provided extending in opposite
directions and with their rod portions preferably disposed
concentrically to conserve space. In this embodiment both
piston-like members are reciprocable within the same magnetic field
and their heads are respectively attached to opposed surfaces of a
pair of collapsible chambers but the coils which are mounted on the
piston-like members respectively are separately powered and
controlled so that the time and frequency as well as the speed and
duration of the stroke of one piston-like member may be different
from that of the other and modified as may be required.
If a device embodying the invention is to be used as a substitute
for all or one-half of a living heart the materials used,
particularly for the interior of the collapsible chambers, must be
compatible with blood. The development or identification of such
materials forms no part of this invention. A vast amount of work
has been done to provide such materials and the results of this
work may be found in many reference sources including for
example:
U.S. Pat. No. 3,449,767, June 17, 1969 and long list of artificial
hearts and chambers set forth therein; U.S. Pat. 3,409,913, Nov.
12, 1968 and references therein to arterial graft sections for
attachment to the open ends of auxiliary ventrical means, and to
connector means described therein, including connector means made
of Medical Silastic 372 supplied by Dow Corning Corporation,
Midland, Mich.; also Transactions Of The Americal Society Of
Artificial Internal Organs; also references cited during
prosecution of U.S. Pat. No. 3,327,322, June 27, 1967; also
pamphlet of Avco Everett Research Laboratory, "Development of Blood
- Compatible Elastomers, Theory, and Practice And In Viro
Performance," by Emery Nyilas.
For use as an artificial heart the one way valves of a collapsible
chamber or chambers will respectively communicate through suitable
connectors to veins and arteries of the animal or human body which
have been severed when removing the original, damaged heart. In a
full prosthetic heart the inlet valve of one chamber will
communicate with the vein bringing the blood back from all parts of
the body to the heart, and the outlet valve of the chamber will
communicate with the artery leading from the heart to the lungs.
The inlet valve of the other chamber will communicate with the vein
bringing the blood from the lungs to the heart, and the outlet
valve of the chamber will communicate with the artery (aorta) which
carries and distributes the blood from the heart to all parts of
the body.
The source of power illustrated herein for each coil employed is a
storage battery preferably implanted in the body adjacent the
implanted pump which is the artificial heart, and connected to the
coil power and control circuitry, preferably housed in the same
casing as the pump, by leads also within the body. Each battery may
be recharged from time to time from means outside the body through
leads disposed within the body. Such leads may also be employed for
reading and recording the operation of the heart pump and
conditions within the body such as blood pressure at selected
points, and for the input to a programmed memory bank of further
instructions to correct or improve the recorded operations.
Preferably the leads extend through tooth root canals of the animal
or human being, to contacts provided as fillings or inlays. Three
such contacts are provided in this way with a pair of said leads
extending from the contacts to the power source, and a pair of said
leads extending to scanning means, preferably disposed within the
power source housing.
An inter-connector means is provided which can be readily inserted
into and removed from a subject's mouth and is adapted to fit over
the teeth having the contact forming fillings or inlays, the
inter-connector means in turn having contacts adapted to register
with the teeth supported contacts and to be connected to monitoring
means as well as to a power supply for recharging the battery means
within the body. When this connector means is placed over the
contact forming inlays or fillings the battery means within the
body may be recharged and the operation of the artificial heart may
be monitored as well as certain conditions within the body for
which detector means connected with the power control system have
been provided, and commands may be transmitted to the control means
within the body to change or modify the control means and thereby
overcome malfunctions or deficiencies disclosed by the monitor.
The invention will be best understood if the following description
is read in connection with the drawings in which;
FIG. 1 is an elevational view partly in cross section of a single
piston two chamber pump in which the piston-like member carries a
specially constructed coil which is reciprocated through a
specially devised magnetic field,
FIG. 1a is a detail of one of the irom shims used singly or in
groups, between successive portions of the coil winding to improve
the strength of the field and so that a more efficient magnetic
coupling is made.
FIG. 2 shows schematically drive and control means for the single
piston pump,
FIG. 3 shows a two chamber and double piston pump which when made
of suitable material may be used as a heart pump, comprising two
coils carried by the piston-like members respectively and
reciprocated independently within the same magnetic field,
FIG. 4 is similar to FIG. 3 but shows a single chamber and single
piston pump which may be used as one-half a heart,
FIG. 5 is a schematic view of a control system for the pumps shown
in FIGS. 3 or 4 including means for modifying and adjusting coil
driving power in response to data from detector means disposed at
selected points, and/or in response to data from a recording or
preprogrammed memory bank,
FIG. 6 is a schematic view of a power supply and distribution
system for energizing the power transmitting, modifying and
adjusting means as shown in FIG. 5 including connections through
which the power source may be recharged and data may be transmitted
from data scanning to recording means, and input data may be
supplied to a memory bank.
FIG. 7 is a detail schematic view showing teeth inlay contacts and
leads extending from them within the body,
FIG. 8 is a side elevation showing relative location of artificial
heart, battery and tooth supported contact means within a human
body, and
FIG. 9 is a schematic view of a mouth piece interconnector, adapted
when inserted in a subject's mouth to fit over the teeth contacts,
and of connections from the interconnector to battery recharging
means, and to means for recording and sequentially reading data
from data scanner means and for handling input data for the memory
bank.
DESCRIPTION
In FIG. 1 a reciprocating single piston pump is shown and in FIG. 3
a double piston pump is shown and in FIG. 4 is shown a single
chamber and single piston pump which is adapted to serve as
one-half a heart.
In the embodiment of the invention shown in FIG. 1 a casing 10
encloses a pair of spaced stationary magnetic field assemblies, 12
and 13, comprising respectively, an annular magnet 14 and two field
portions 16 and 18 which are spaced apart and in contact
respectively with the two poles of magnet 14 so that portions 16
and 18 are of different polarity, and an annular magnet 15 and two
field portions 17 and 19 which are spaced apart and in contact
respectively with the two poles of magnet 15 so that portions 17
and 19 are of different polarity. As shown, portion 16 is in
contact with the north pole of magnet 14, and portion 18, through
its laterally extended base portion 18a, is in contact with the
south pole of magnet 14, and portion 17 is in contact with the
south pole of magnet 15, and portion 19 is in contact with the
north pole of magnet 15 through its laterally extended base portion
19a.
Portions 18 and 19 are axially and concentrically disposed within
the open centers of magnet 14 and field portion 16, and magnet 15
and field portion 17 respectively, and radially spaced from their
inner surfaces sufficiently to leave space between them and it
within which a piston-like member 22, which may comprise four
parallel spaced rods, and a coil 20, which is wound around it and
carried by it, may be axially reciprocated. Base members 18a and
19a are apertured at a to provide spaces through which the rods
comprising member 22 may reciprocate. Portions 18 and 19 of the two
magnetic fields are spaced apart by a non-magnetic spacing member
21.
Portions 16, 18 and 18a, and 17, 19 and 19a, are made of iron to
provide a strong magnetic field.
The piston-like coil support means 22, spaces apart and
interconnects collapsible chambers 30 and 32, which are made of
material selected on the basis of being suitable for, and
compatible with, the fluid passing through them. The ends of the
member 22 may be attached, as by screws 24, to piston cross members
or heads 26 and 28 which in turn are attached in any suitable way
as by adhesive to the opposed surfaces of members 30 and 32.
The coil 20 is made up of a series of coils separated by magnetic
laminations. Discontinuous shim-like members 34, preferably in
bundles of three to 10 members depending upon the shim thickness,
are inserted between at evenly spaced intervals between turns of
the coil to increase magnetic coupling when the coil is energized.
The shim-like members 34 are made of soft magnetic iron with an
insulating coating. The members 34 are made with radially extending
gaps 36 to avoid short circuiting the coil or creating an induced
voltage as it moves through the magnetic field.
As shown in FIG. 1 collapsible chamber 30 communicates with a
conduit 40 through intake check valve 42, normally held in closed
position by spring 43, and communicates with a conduit 44 through
discharge check valve 46, normally held in closed position by
spring 47.
Similarly collapsible chamber 32 communicates with intake conduit
48 through check valve 50, normally held in closed position by
spring 51, and communicates with discharge conduit 52 through
discharge check valve 54 normally held in closed position by spring
55.
When the movable coil 20 is energized it will move in one direction
or the other depending upon the voltage polarity fed to the coil
and because of the disposition of the magnetic polarity of the two
magnetic fields it will be simultaneously pulled and pushed by said
fields and thus can be moved with considerable force. When coil 20
moves toward chamber 30 between the annularly spaced north and
south poles of the magnetic field 12, it causes the piston-like
coil carrying means 22 to move with it thus opening valve 46 and
collapsing chamber 30 and thereby forcing its contents, as a pulse
of fluid, into conduit 44. During the collapsing of chamber 30
valve 42 remains closed. However upon the return stroke of the coil
assembly, due to change in the polarity of the fed voltage the coil
controlled by the driving power source, chamber 30 is opened, valve
46 closes, and valve 42 opens, and fluid from conduit 40 flows into
chamber 30.
While chamber 30 is being expanded and filled with fluid, chamber
32 is being collapsed, valve 54 opens, and fluid within chamber 32
is discharged in pulse form into conduit 52, valve 50 being held in
closed position during the collapsing of chamber 32 but opening
again to admit fluid from conduit 48 into chamber 32 when the
stroke of the coil assembly is again reversed.
It should be noted that by control of the power source the opposite
strokes of the coil assembly may be made with the same force and
timing thus delivering alternately into conduits 44 and 52 pulses
of fluid having the same wave form, or the coil assembly may be
made to move in one direction with greater force and speed than in
the other direction by having a higher voltage pulse for one
direction of travel. This result may be desired for example in
installations where it is important to conserve space and weight
and to deliver fluid through separate conduits in different wave
form.
Flap valves 56 are provided in the wall of casing 10 to dissipate
heat generated within the pump, and the liquid passing through
chambers 30 and 32 may also serve to cool the interior of the
pump.
The pump shown in FIG. 1 may be driven and controlled by the
operation of the well known full wave SCR cycloconverter control
system shown in FIG. 2 which is desirable because of its low cost
to build and operate.
Power from a 60 Hz voltage power source is fed into the system at
A, having the necessary voltage and current to match the impedence
of the pump drive coil 20. The required frequency signal input is
fed into the system at B, and the size and frequency of this signal
may be varied and programmed to produce the required pumping
changes to give the required pressure pulse curve and rate. The
power source is modulated to produce the necessary frequency and
wave form by the action of the cycloconverter.
The cycloconverter comprises, a full wave bridge 58 comprising four
triac bilateral solid state switches, Q1, Q2, Q3 and Q4; connected
respectively to control bridges BR-1, BR-2, BR-3 and BR-4; photon
couplers PC-1, PC-2, PC-3 and PC-4 each comprising a light emitting
diode D; a trigger control amplifier E; a trigger capacitor F; and
a phase splitter transformer G.
The triac switches Q-1Q-4 will be triggered in the proper sequence
to convert a 60 Hz input wave into a low frequency wave form which
will, with proper filtering, replicate the low frequency input
signal. Triggering is accomplished through the photon couplers
which receive their signals from the trigger control amplifier
which receives its signal from the input of the phase splitter
transformer G.
The light transmitting diode D of each photon coupler is normally
"on" and causes a short circuit across its related trigger
capacitor F which prevents the triac from triggering. When the
light transmitting diode is turned off the capacitor will charge to
32 volts at which point the bilateral switch will change state and
trigger the triac switch.
The trigger control amplifier E operates with a 0-6 volt signal.
The signal will cause trigger on either the positive or negative
half of the 60 hertz input voltage, depending upon the polarity of
the input signal. Q1 and Q4 will trigger when the control signal
and the 60 hertz signal are in phase, and Q2 and Q3 will trigger
when the signals are 180.degree. out of phase.
The phase splitter transformer G provides the proper polarity
relationship between the input and output signals.
Pulsing the wave with a square wave form may be obtained using a
d.c. on-off electronic switch, such for example as the
cycloconverter, for low power consumption.
The double piston pump shown in FIG. 3 comprises a casing 60
enclosing a stationary annular magnet 62 and a magnetic field
comprising the annular portion 63 which is in contact with the
north pole of magnet 62, and a field portion 66 which is in contact
with the south pole of magnet 62. From the base 66 portions 64 and
65 extend upwardly on opposite sides of field portion 63. Portion
64 is tubular and extends up from the center of base 66. Portion 65
is formed by an upwardly extending cup-shaped extension of base 66.
Portions 64 and 65 are shaped and disposed so as to provide annular
spaces between themselves and portion 63 within which a pair of
coils 68 and 70, and the two piston-like members 72 and 82 by which
they are respectively carried, may reciprocate.
The member 72 comprises a tubular portion 74 and the curved head
portion 76 which is attached in any suitable manner to the opposed
face of fluid chamber 30a. Projecting radially from tubular portion
74 in axially spaced relation are the flanges 78 and 80, and coil
68 is wound around the said tubular portion 74 between flanges 78
and 80. It will be noted that magnetic field portion 64 is tubular
and is disposed within the tubular portion 74 of member 72. Coil 68
is thus disposed between magnetic field portions 63 and 64.
Member 82 comprises the rod portion 84 which is disposed for
reciprocation within the concentrically disposed tubular field
portion 64 and the surrounding piston-like member 74, and the
central head portion 86 is attached in any suitable way to the
opposed face of fluid chamber 32a. The heat portion 86 is extended
outwardly forming the cup-shaped flange 88 which extends close to
chamber 30a and coil 70 is disposed around the rim of the flange,
between portions 63 and 65 of the magnetic field. The rod portion
84 is guided for linear movement with magnetic field portion 64 by
the bearing 90 disposed therein.
Circuitry for controlling the pump, such for example as is shown in
FIG. 5, may be disposed within the pump, as in the annular housing
100 secured in place by means of screws 102 shown extending from
magnetic field member 66 through the magnet 62 and field member
63.
Because of its flexibility and compactness the pump disclosed
herein is adapted for many uses as for example to supply two
liquids in unequal and variable amounts, or to administer two drugs
at a changing rate controlled by a patient's temperature and heart
rate. For such uses chambers 30a and 32a may be connected to inlet
and outlet conduits in the manner shown for the collapsible
chambers of the single piston pump shown in FIG. 1.
One of the uses particularly contemplated for the double piston
pump is as a heart pump, a prosthetic substitute for a whole human
or animal heart and in FIG. 3 the inlet and outlet of each chamber
30a and 32a is shown provided with connector means suitable for
connecting the chamber to veins and arteries of a living body which
were previously connected to the heart which has been removed.
Chamber 30a is connected through inlet valve 92 and the connector
106 to the blood vessel which returns blood from the lungs to the
heart; and is connected through outlet valve 94 and the connector
108 to the main artery, the aorta, which delivers blood from the
heart to the rest of the body.
Similarly chamber 32a is connected through inlet valve 96 and the
connector 110 to the blood vessel which returns blood from the body
to the heart, and is connected through outlet valve 98 and the
connector 112 to the main artery, which leads from the heart to the
lungs.
In FIG. 4 a single chamber pump is shown which is adapted for use
as one-half of a human or animal heart. It will be seen that FIG. 4
is similar to the upper portion of FIG. 3 and for convenience like
parts are identified by like numerals, but it will be understood
that the single chamber may be connected in this manner as shown
for either chamber of the pump shown in FIG. 3. The casing of the
pump shown in FIG. 4 is identified by the numeral 60.
Since the optimum fluid pulse output of each chamber varies in
accordance with the condition and needs of the body or other system
in which the pump is used, each coil is connected to its source of
power through a power amplifier or switching circuit, the output of
which may be modified to provide great flexibility to the stroke of
the piston it drives and thereby provide the desired output pulses
of blood from the chamber controlled by that piston.
In FIGS. 5 and 6 means are indicated for driving a coil from a
single storage battery source of power in accordance with
prerecorded programmed data modified by data signalled from various
points within the body and within a prosthetic heart implanted
therein. It will be understood that the circuitry will be repeated
for driving a second coil. The prerecorded program data which
supplies the basic control pressure wave form to the fluid and
controls the rates of the pulses leaving the collapsible chambers
30a and 32a respectively, is shown supplied by a memory bank 120
which is part of a bidirectional multiple and monitoring system
incorporated into the mechanical heart's electronic control system.
Sensing means in the form of a detector 122 is disposed in the
discharge conduit, which when the pump is used as a mechanical
heart is the aorta, to supply a pressure data signal. A second
detector 124 is shown in contact with the carotid nerve to provide
command data to the memory 120. It will be understood that other
sensing means may be disposed at other points, such as 126, 127 and
128, along the circulation system of a body in which the mechanical
heart is implanted and at points within the pump itself to provide
information as to the pressure, temperature or other conditions at
such places, and that such data may be employed to modify the basic
wave form and rate of the pulses delivered from the pump in
response to the programmed controlled data.
As shown, power for driving a coil is supplied from a storage
battery power source 130 to a power amplifier 132 and also to the
data handling preamplifiers 134 and 136, and to programmer
amplifier 138 and the data scanner 140.
Each coil is driven by a power amplifier 132 which is driven by the
driver amplifier 134 and a feedback loop 144. The driver amplifier
134 controls the feedback loop 144 and is driven by the
differential amplifier 136 with the data signal from the
preprogrammed data signal modified by the pressure wave form
supplied from the detector means 122 in the aorta through the
pressure control pre-amplifier 142. In addition, the signal
produced by the carotid nerve through detector 124 feeds into
memory 120 through pre-amplifier 146 to adjust the memory signal in
such a manner as to produce sufficient blood pressure for the brain
of the patient.
The data scanner 140 is connected by leads 148 and 150 to contacts
154 and 156 through which connection may be made to means 160 for
reading and recording data from the scanner 140 and through which
new input data may be supplied to the memory 120.
As shown in FIG. 6 and 7 a third contact 158 is provided, and the
power source 130 is connected through leads 150 and 152 to contacts
156 and 158 through which, as by the means illustrated in FIG. 9
the power source 130 may be recharged.
In FIG. 7 contacts 154, 156 and 158 are shown as inlays or fillings
in three teeth of the user of the heart pump and the leads 148, 150
and 152 extend from the inlay contacts respectively through the
root canals of the teeth and preferably within a teflon conduit 164
within the body, to the power source 130 and to the data scanner
140.
For convenience in connecting the inlay contacts 154, 156 and 158
to a battery charger 166 and to a means 160 for recording data from
the scanner system and handling memory input data, an
interconnecting means 170 may be employed, adapted to fit over the
inlay contact carrying teeth and having contacts 172, 174 and 176
disposed to register with the inlay contacts, the contacts of the
interconnecting means being in turn connected with the battery
recharger means 166 and the recorder and input data handling means
160.
* * * * *