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Biomedical circuits and systems torecuperate neuromuscular functions
Mohamad Sawan, P. Eng., Ph.D., FCAE,Canadian Research Chair on Smart Medical Devices
PolySTIM Neurotechnology LaboratoryDept. of Elec. Eng., École Polytechnique de Montréal
PART I
IEEE CASS DLPJanuary 2004
w Introductionn Purpose and motivation
w Microelectronics activitiesn Design, construction & test of smart medical devices (SMDs)n Typical architecture of an SMD
Focus on two main case studiesn Neurostimulation to recuperate the bladder functionsn Intracortical neurostimulation to create vision for the blind
Required biocircuits & biosystemsResearch team and collaborationsConclusions
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Biomedical circuits and systems to recuperateneuromuscular functions
OUTLINE
M. Sawan3
w 1947, transistor allows circuit designs suitable for implants.
w 1952, first external pacemaker which was the size of a tableradio of the time and was powered by 110 VAC.
w 1957, electrical stimulation in the inner ear of the acousticnerve in a totally deaf human was reported.
w 1960, totally implanted pacemaker (Buffalo).
w 1961, peroneal nerve stimulator for foot drop in hemiplegics.w 1968, implantation of an electrodes array on the visual cortex.
w 1980, first microchip was used to design small pacemakers.
w 1984, FDA approved the first cochlear implant for adultsw 1991, recording of neural activities
w 1992+, FES is widely used in several applications.
Main technological breakthroughof FES based SMDs
M. Sawan
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w Pacemaker: More than 350,000 pacemakers annually;
w Defibrillator: More than 50,000 implants annually;w Cochlear implant: More than 50,000 people worldwide;
w Functional stimulation: Recuperate hands and legsmovements of paralyzed patients;
w Stimulation for the treatment of Parkinson, respiration,pains, scleroses, etc;
w Automatic liberation of insuline in diabetics;
w Neuronal activities recording for better control;
w Devices for vision: Creation of adequate vision for blinds;w Other implantable microsystems.
Main technological breakthrough(Cont’d)
M. Sawan 5
Features:
Modulator
Demodulator
Receiver
Powersupply
Measurementand
digitalizationcircuitry
Stimuli generator
Current sources
Physio-logicalstimuli
Teststimuli
Clk
Pardata
MUX
DEMUX
Backtelemetry
Stimulation signals
Returned informations
- ETC impedance measurement- Charge per phase estimation- ETC voltage monitoring- Neural signal recording
Bi-directionalRF link
elec-trodes
Implant
Dataprocessing
Skin
Externalcontroller
Main
controller
Smart medical devices Proposed topology
M. Sawan6
Global view
Proposed SMD topology(cont’d)
C1
L1 L2 C2 C3
VoltageRegulator
Load ShiftKey (LSK)
DataDemodulator
ADCEncoder MUX
Controller/Stimulator
Charge Pump 1
Charge Pump 2
Charge Pump 3
Charge Pump 4
Vdd1
Vdd2
Vdd3
Vdd4
Vdd
Analogfrontend 1
Analogfrontend n
Electrodes
Start-upCircuit
ProtectionCircuit
Clock GeneratorCircuit
SwitchingRegulator
ASK Demodulator /DAC/Decoder
DataModulator
PowerAmplifier
Battery
Vdd
SignalProcessor
ClockGenerator
External Controller
Implant Circuit
Off-Chip On-Chip
M. Sawan
regulatorrectifierrflinktotal hhhh ⋅⋅=
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Power Transfern Efficiency and safety.
Data transmissionn Manchester based codecn PSK based codec: BPSK
Demodulator (COSTASLoop)
Link features
RF LINK to Transfer Power & Data(cont’d)
Without Feedback: 12.03%With Feedback: 22.04%
• Full duplex mode• Transfer rate:
-LSK: 200Kb/s-BPSK: 1Mb/s
• PSK demodulator consumes only529 mW.•QPSK may double the data rate.
M. Sawan
VCO Low Pass Filter
Data Out
Data In
PhaseShifter
90
I branch
Q branch
Low Pass Filter
Low Pass Filter
)sin()( 1 1 qw +ttm
)sin(2 2 1 qw +t
)cos(2 2 1 qw +t)sin()( 2 1 qq -tm
)(2sin2)( 2 1 qq -tm
)cos()( 2 1 qq -tm
• Recover thecarrier and thedata in the sameloop
regulatorrectifierrflinktotal hhhh ⋅⋅=
The bladder controller: Dual-stimulator
• Lower urinary tract deficiency followinga spinal-cord injury;- Incontinence and/or retention.
• Multiples complications at severallevels (Sphincter, bladder and kidneys)due to repetitive catheterizations;
• Bladder hyperreflexia (hypertrophy or atrophy) hardly curable with traditional medicine;
• Electrical stimulation of the detrusor muscle allows partlyvoiding and may induce kidney complication.
8M. Sawan
• Conventional electrical neural stimulation (ENS)induces contraction on both detrusor and sphincter,thus preventing from complete voiding;
• Conventional ENS combined with nerve rhizothomy isnot accepted by patients;
• Early ENS tends to reduce the hyperreflexia phase,while limiting damage in the whole urinary system;
• Selective neural stimulation proposed by ourteam allows efficient voiding of the bladder;
• Permanent low frequency combined withselective stimulation are proposed by ourteam to improve bladder function.
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The bladder controller: Dual-stimulator
M. Sawan
2
• Selective stimulation allows improvement in voiding;• This technique diplexes high and low frequency stimuli
to activate both categories of sacral nerve fibres:
- HF stimuli for somatic fibres which innervate the sphincter.
- LF stimuli for parasympathetic fibres which innervate thedetrusor.
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The bladder controller: Dual-stimulatorSelective neural stimulation
M. Sawan
l First selective stimulator includes :‡ Implant of 3.5 cm of diameter built around field programmable
devices (FPD) and other discrete components;‡ Shape Memory Alloy (SMA) based cuff electrodes to facilitate
connecting to sacral roots;‡ User friendly external controller based on FPD and other
discrete components.
SMA Electrode CuffSelective Implantable Stimulator
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The bladder controller: Dual-stimulatorSelective neural stimulation
M. Sawan
l Proposed dual-stimulator includes :-Permanent LF stimulation : Low amplitude train:
- Prevent the bladder hyperreflexia- Maintain the bladder shape- Selective stimulation.
l The system includes:- Battery to power thepermanent stimulator;- RF link for the selectivestimulation.
Amp
PW
1/Freq
Ton Toff
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The bladder controller: Dual-stimulatorPermanent/Selective stimulations
M. Sawan
Lesion
Bladder
Bipolar cuff Electrode
Dual-stimulator Implant User Interface RF Emitter
Data
Param Stim #530Hz 175us
0.9mA
Skin
Power
External Controller
Decoder
DACCurrent
CommutatorCurrentSource
Controller#1
(FPGA)
Controller#2
(PIC)
Bus Controller
DSR
SYS_ON
DSR READY
READY
Z_CTRL
DIN/SCLK/CS
UP/DOWN
3
2
DIN/SCLK/CS
UP/DOWN
Switch#1
SYS_ON
SYS_ON
SYS_OFF
RF_PWR_EN
BAT_PWR_EN
BAT_PWR_EN
RF_PWR_EN
AmDemodulator
RF_PWR
DATA_IN
Switch#2
BAT_PWR
Switch#3
PIC_PWR
PIC_PWR
SYS_OFF
Nerve
DIN/SCLK/CS
UP/DOWN
SWT_PWR
SWT_PWR
Antenna
Battery
3
2
32G_CLOCKMANCH_IN
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The bladder controller: Dual-stimulatorImplant description
M. Sawan
• External controller• Subcutaneous Implant (~ 2.5cm)• One cuff electrode pair
Bladder dual neurostimulation: Results
l Intravesical and intraurethral pressures measurements andElectromyographic (EMG) recording of the pelvic floor muscles wereperformed.
Voiding by selective stimulation
31%
88%
34%
69%
12%
66%
cathcath0 ml
100 ml
200 ml
50 ml
150 ml
250 ml
MeanBladderVolume
Residual
Voided
LF LFLF+HF+permanent
14M. Sawan 15
w 1960s, few groups began to investigate the possibilities ofexploiting the phenomenon of creating points of lights;
w 1990s, Researchers at NIH demonstrate that intra cortexstimulation allows to generate phosphenes;
w Progress in microelectronics and microfabrication motivateresearchers to explore several approaches;
w Dobelle institute, New York, early in 2000 presented a patientholding a PC which drives a percutaneous connector towardthe skull to extracortical visual region;
w We start this project in 1996n Early 2000, a prototype has been completed to prove the
feasibility of a visual cortical stimulatorn Miniaturized implant version is being achieved.
The visual cortical stimulator Evolution
M. Sawan
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The visual cortical stimulator Approaches
Researchers worldwide are developing solutions Several approaches are being explored:n Artificial retina;n Cuff electrodes around the optic nerves;n Tongue stimulation;n Surface stimulation of the visual cortex;n Intracortical stimulation of the visual cortex.
Intracortical stimulation does not depend on the health ofthe eye or optic nerve; also, it requires stimuli at low currentlevel. It can be the predominant one:n Artificial retina requires functional retina and optic nerve;
n Surface stimulation of the visual cortex is imprecise;n Other techniques only allow sensory substitution .
M. Sawan 17
Artificial retina / Extracorticalstimulation
Experimentationn Stable, non flickering phosphenes;n Able to distinguish shapes;n Lower threshold in macular region;n Resolution restricted by electrode shapen Mechanical properties challenges.
Extracortical surface stimulationn Images feed from a digital camera to a belt-
mounted processor;n commands send through the skull, and into
the visual cortex
Optic nerve stimulationn Fixed, stable phosphenesn Many phosphenes with few electrodesn Phosphene characteristics widely variable.
Tongue stimulation, and auditory ortactile input.
M. Sawan 18
Intracortical stimulation
Intra-cortical stimulationn Better resolution
n Better control on phosphenes
n Lower power
n Lower chances of seizure.
Subject: 38 year old womann Parameters affect brightness, not position
n Elicits stable phosphenes
n Threshold ~15 µA (as low as 1.9 µA)
n Short term accommodation.
Experiments in Monkey at IITn Recently, report good news.
M. Sawan
3
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The visual cortical stimulator The whole proposed system
StimulatorChips
InputImage
Camera
1
2
Image Processor & Power source
3
WirelessTransmitter
4
ControllerChip
6
7
5Antenna
Cortex
The system includes 4 main components:n Camera mounted onto a pair of glasses;n External controller to process the images and commands;n Bidirectional data & energy transmitted by RF link;n Implant to stimulate the region of the cortex controlling vision.
M. Sawan 20
The visual cortical stimulatorUndertaken research projects
Front-end(Camera& DSP)
Front-end(Camera& DSP)
RxRx InterfaceInterfaceTxTx
RF Data and PowerRF Data and Power
StimulatorStimulator
System level optimization:n Front-end for efficient image processing;n Tx / Rx for power efficiency and data rate;n Power consumption, size, safety, biocompatibility;n Interface for shape and surface.
System level optimization:n Front-end for efficient image processing;n Tx / Rx for power efficiency and data rate;n Power consumption, size, safety, biocompatibility;n Interface for shape and surface.
Timing HardwareTiming Hardware StimulatorStimulator InterfaceInterface
ExternalComponents
ExternalComponents
ImplantedComponents
ImplantedComponents
IsolationIsolation
1011000101
&&Development
board
Computer Matrixof
electrodes
M. Sawan
Prototype (VCS)
PVCS emulatinga 16x16 matrix
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VDB source
Inverse Stim. Site to PVC Mapping
Display
Imageacquisi-
tion
Program-ming GUI
Imagefitting
External components
Implantablecomponents
Skin
VisuotopicMapImage
enhance-ment
InterfaceModule
Stim.Module
Stim.Module
Trans-mitter
Encoding& timing
PVC toSSA
mappingOrdering
Low levelPulse
sequencing
Visual FieldEmulator
Display
ArtificialVisuotopicMap gen.
Data collected fromexperimentation
SSA toPVC
mapping
...
......
Electrodes
Config.
Direct Mapping
Inputs
Low LevelData Manag. Implant
The visual cortical stimulator Integrated smart devices
•• Block diagram
M. Sawan
22
Components of Multi-modulesn Stimulator Modules (SMs)w Multi-channel stimulationw Electrode-tissue and
stimulator monitoring
n Interface Module (IM)w Bidirectional wireless
Communicationw Implant controlw Power recovery / management
w A/D Conversion of monitoring data
The visual cortical stimulatorImplant architecture
M. Sawan23
Implant architectureStimulator Module
Features (flexibility/safety)n Current Constant Stimulation
w Monopolar, Bipolarw Single/Multiple paths
n Configurable Comm.protocolw One to 25 bits per pulse.
Enables the use of a LF Clkw System power saving
n Voltage Monitoring
n RAM Configured Parametercontinuous error checkingw Disables stimulation in case of
Parameter corruption
Serial inclk
ElectrodeSwitchMatrixC
o ntr
o lle r
DAC#0
DAC#1
DAC#2
DAC#3
Analogout
LS
R2R
LSLS
Band-GapBias
REF
n Compatible with electrodematrix dimensionsw 4 x 4 electrodes (prototype)
M. Sawan24
Power supplyn External Coil, Rectifiers
Communicationn Downlink
w ASK: keep OOK for its simplicity(Tx/Rx), but need higher data rate
w «All digital» Demodulatorn Uplink
w Manchester LSK
System Controln Power managementn Communication Error
detection/correctionn Stimulator Instructions Dispatching
Monitoringn Actual Stimulating Currentn Voltage at every stimulation site
err flgcvtFSM
in / out reg
in/outFSM
errordetec. err
ctrl / status reg
clkLskclk
clkdata
LSKout
adc
o ut adc c lk a dc c vt
data(1)
data(N)
clk(1)
clk(N)
(to in/out FSM andctrl / status reg)Manch.
decod.envIn Envelop
detect.
PWRdata(1), clk(1)Vmon(1)err(1)
ASK in
LSK out
Monit.
Controller
...
PWRdata(N), clk(N)Vmon(N)err(N)
REF MREF
LSKmod
Env.det.
ClkDataext.
Regul
Clk
Data
Implant architectureInterface Module
M. Sawan
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Coil Voltage
ASK in
VDDDownlink Tradeoffn High Q > Best efficiency, but
w Envelop transition speedlimited by Q-factor of receiver whenrectifier diodes voltage is reversed.
n … Limited Data Ratew Manchester encoding does not allow more
than ~500 kbps @ 13.56 MHz.
w Enhance Data Rate & Power Transfer
by reducing carrier OFF period.
n Digital decoderw Based on carrier signal attenuation
w Toggling of attenuated carrier detected byextra toggling of direct carrier.
Downlink CommunicationPower Efficiency vs Data Rate
Direct Coil
V -SS V j
V +DD Vj
Att. Coil VthL
VthH
Dig. I nDir
Dig. Att In
M. Sawan26
Monitoring & Data uplink
V / I monitoringV / I monitoringn Sampling at any programmable time
n Voltage measurementw Any stimulation site during normal stimulation
n Current monitoringw Actual stimulation current measurement.
Normal Stim.
Hi-Z
ADC
+-
enable
adc out
adc clkadc cvt
FromCtrler
ToCtrler
REF
I monit
Voltage Monit.
Co n
t ro l l
e rC
on t
ro l l
er
REF
REF
VD
DV
SS
DACDAC
DACDAC
R2R
R2R
Anal
og
Mon
it. B
us
REF
Hi-Z
Hi-Z
Current Monit.
M. Sawan27
Cortical stimulationStimulus mode/type
Anodic/CathodicStimulation
Anodic/CathodicStimulation
BipolarBipolarMonopolarMonopolar
Distant
reference
Distant
referenceDistributed
reference
Distributed
reference
Current
sink
Current
sinkCurrent
sink/source
Current
sink/source
Current
source
Current
source
– Flexibility• Modular: Variable number of stimulation sites
• Stimulation modes: Mono / Bipolar, Single / distributed return terminal
– Safety• Electrical Isolation: Allows stimulation current / voltage monitoring.
M. Sawan
4
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Implementation Results
Stimulation Module (Stimulation Module (4 x 4 Matrix)• CMOS 0.18 µm, ~60 000 Gates
DownlinkDownlinknn > 1 Mbps @ 13.56 MHz, Duty Cycle = 67%> 1 Mbps @ 13.56 MHz, Duty Cycle = 67%nn 500 kbps @ 13.56 MHz, Duty Cycle > 85%500 kbps @ 13.56 MHz, Duty Cycle > 85%
Uplink : 200 kb/sUplink : 200 kb/s
Power: <1mW/SM @ 1MHzPower: <1mW/SM @ 1MHznn > 100 mW load capability; P (err) < 10> 100 mW load capability; P (err) < 10-6-6
Sufficient for 1000 stimulation sitesSufficient for 1000 stimulation sitesnn 256 stimulation patterns @ 50 Hz.256 stimulation patterns @ 50 Hz.
DownlinkImplantM. Sawan
CTRL
TEST structures
MONITORINGR2R AMP
ELECTRODESCONN / CTRL
DACs
BIAS
400 um400 um
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Cortical stimulationImplant assembly
Modularn One controller &
several stimulationUnits
Flexible substrate
Power/data linkn Wireless
Data rate >1 Mb/sn Max. Stim. Freq. :> 1 kHz @ 500 Elec.
I / V Monitoring
Assemblyn Stim. Units.
Modularn One controller &
several stimulationUnits
Flexible substrate
Power/data linkn Wireless
Data rate >1 Mb/sn Max. Stim. Freq. :> 1 kHz @ 500 Elec.
I / V Monitoring
Assemblyn Stim. Units.
Physical Dimensionsn SM’s area : 3.5x3.5 mm2
n Substrate : 50 µm
n Stim Assembly: 1 mm thick
n Electrode Length: 2 mm
n IM’s Area : ~ 2 x 2 cm2
n Ctrler thickness : ~ 3 mm.
Physical Dimensionsn SM’s area : 3.5x3.5 mm2
n Substrate : 50 µm
n Stim Assembly: 1 mm thick
n Electrode Length: 2 mm
n IM’s Area : ~ 2 x 2 cm2
n Ctrler thickness : ~ 3 mm.
IM
SMs
M. Sawan 30
In vivo testingCollaboration with the INM
Subject
(Monkey)
Subject
(Monkey)
TimingTiming
PWR Data
Isolation
PWR Data
Isolation
StimulatorStimulator
OscilloscopeOscilloscopeComputer
Developmentboard
ParametersAmplitude, Pulse width,Inter-phase delay,Direction of first pulse,Pulse frequency, Pulsetrain duration, and Inter-train delay.
Only electrodes insubject; Configurablehardware; “Large” outputvoltage swing.
ParametersAmplitude, Pulse width,Inter-phase delay,Direction of first pulse,Pulse frequency, Pulsetrain duration, and Inter-train delay.
Only electrodes insubject; Configurablehardware; “Large” outputvoltage swing.
M. Sawan
Electrode matrix400 µm spacin;Platinum tips; Parylene-C coating, LowImpedance.
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Acquired ImageAcquired Image
Image acquisition/processing
Challenges and Need for Optimizationn Stimulator
w Physical Properties Placement flexibility, wiringw Safety Chronic usagew Data rate High number of stimulation sitesw Stimulation Flexibility Prototypew Power efficiency High parallelism
n External Controlw Relevance of Data Low resolution
Actual Perceived ImageActual Perceived Image(Direct Fit)(Direct Fit)
Controlon phospheneparameters
Irregular- Density- Size- Sensitivity- …
M. Sawan32
Dedicated image processorn Allow to transform images over visuotopic maps;n Follow a bottom-up approach until percepts are understandable;n Must deal with every image encountered in real world;n Be safe for patient.
Required processingn Present image as the patient would see it;n Hardware implementation of processing algorithms;n Low power consumption topologies.
Minimize power consumption with other techniques than circuitoptimization approaches.
Image acquisition/processingMain specifications
M. Sawan33
Image acquisition/processingElectrically invoked phosphenes
w Visuotopic Mapsn Experimental determinationn Creation of random maps :
w Investigation of representation needed for a VCS.Original
Zones
EdgesM. Sawan
Constructed from experiments or fromVisual Data Base Generatorn Realistic Visuotopic Map
w Set of Phosphene Visual Field Coordinatesw Generated from probabilistic parameters
weighted with Schwartz retinotopic relationshipand estimated electrode placement.
n Probabilistic weighted PVFCvariations and phospheneparameters:w Sensitivity, Size, Brightness, etc.
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Image acquisition/processingVisual Data Base (cont(cont’’d)d)
Enhancement/mappingn Image has to be enhanced for
clarity, then mapped to theavailable PVFCs.
n The Visual Field Emulator allowsperception prediction / evaluationfrom the research team.
Fit
Fitting example
M. Sawan
FoveaHorizontal Angle
Ver
tical
Ang
le
Sample Visuotopic Map
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Image acquisition/processing
Power Optimization
average
average
With large electrode arrays, stimulation current represents a major partof power consumptionn Predetermined image scanning results in large current variations
n Adaptive scanning method regulates current demandw Equalize the required power and reduce the peak demands
Required stimulation current for 1 sample frame
Total stimulation current
Min. Current
Max. Current
AdaptiveScan
FixedScan
t
M. Sawan36
SummaryTypical topology of inductively coupled implantable electronic devicesDual-stimulator to recuperate the bladder functionsMain issues of a visual cortical stimulatorn Stimulation in the visual cortex may soon permit true artificial visionn Other undertaken research topics:
w Design of dedicated image sensorw High voltage stimulation techniquesw Modeling, simulation and in vivo validationw Measurement techniques of neuronal activitiesw Assembly several arrays
n 128, 500, and 1000+ microelectrodes.
Nanoelectronics will allow the design of additional devices.Microelectrodes & power sources are among the major works.Such medical devices include validation and involve physicians,engineers, health care professionals, families, etc.
M. Sawan