- •Analysis and Application of Analog Electronic Circuits to Biomedical Instrumentation
- •Dedication
- •Preface
- •Reader Background
- •Rationale
- •Description of the Chapters
- •Features
- •The Author
- •Table of Contents
- •1.1 Introduction
- •1.2 Sources of Endogenous Bioelectric Signals
- •1.3 Nerve Action Potentials
- •1.4 Muscle Action Potentials
- •1.4.1 Introduction
- •1.4.2 The Origin of EMGs
- •1.5 The Electrocardiogram
- •1.5.1 Introduction
- •1.6 Other Biopotentials
- •1.6.1 Introduction
- •1.6.2 EEGs
- •1.6.3 Other Body Surface Potentials
- •1.7 Discussion
- •1.8 Electrical Properties of Bioelectrodes
- •1.9 Exogenous Bioelectric Signals
- •1.10 Chapter Summary
- •2.1 Introduction
- •2.2.1 Introduction
- •2.2.4 Schottky Diodes
- •2.3.1 Introduction
- •2.4.1 Introduction
- •2.5.1 Introduction
- •2.5.5 Broadbanding Strategies
- •2.6 Photons, Photodiodes, Photoconductors, LEDs, and Laser Diodes
- •2.6.1 Introduction
- •2.6.2 PIN Photodiodes
- •2.6.3 Avalanche Photodiodes
- •2.6.4 Signal Conditioning Circuits for Photodiodes
- •2.6.5 Photoconductors
- •2.6.6 LEDs
- •2.6.7 Laser Diodes
- •2.7 Chapter Summary
- •Home Problems
- •3.1 Introduction
- •3.2 DA Circuit Architecture
- •3.4 CM and DM Gain of Simple DA Stages at High Frequencies
- •3.4.1 Introduction
- •3.5 Input Resistance of Simple Transistor DAs
- •3.7 How Op Amps Can Be Used To Make DAs for Medical Applications
- •3.7.1 Introduction
- •3.8 Chapter Summary
- •Home Problems
- •4.1 Introduction
- •4.3 Some Effects of Negative Voltage Feedback
- •4.3.1 Reduction of Output Resistance
- •4.3.2 Reduction of Total Harmonic Distortion
- •4.3.4 Decrease in Gain Sensitivity
- •4.4 Effects of Negative Current Feedback
- •4.5 Positive Voltage Feedback
- •4.5.1 Introduction
- •4.6 Chapter Summary
- •Home Problems
- •5.1 Introduction
- •5.2.1 Introduction
- •5.2.2 Bode Plots
- •5.5.1 Introduction
- •5.5.3 The Wien Bridge Oscillator
- •5.6 Chapter Summary
- •Home Problems
- •6.1 Ideal Op Amps
- •6.1.1 Introduction
- •6.1.2 Properties of Ideal OP Amps
- •6.1.3 Some Examples of OP Amp Circuits Analyzed Using IOAs
- •6.2 Practical Op Amps
- •6.2.1 Introduction
- •6.2.2 Functional Categories of Real Op Amps
- •6.3.1 The GBWP of an Inverting Summer
- •6.4.3 Limitations of CFOAs
- •6.5 Voltage Comparators
- •6.5.1 Introduction
- •6.5.2. Applications of Voltage Comparators
- •6.5.3 Discussion
- •6.6 Some Applications of Op Amps in Biomedicine
- •6.6.1 Introduction
- •6.6.2 Analog Integrators and Differentiators
- •6.7 Chapter Summary
- •Home Problems
- •7.1 Introduction
- •7.2 Types of Analog Active Filters
- •7.2.1 Introduction
- •7.2.3 Biquad Active Filters
- •7.2.4 Generalized Impedance Converter AFs
- •7.3 Electronically Tunable AFs
- •7.3.1 Introduction
- •7.3.3 Use of Digitally Controlled Potentiometers To Tune a Sallen and Key LPF
- •7.5 Chapter Summary
- •7.5.1 Active Filters
- •7.5.2 Choice of AF Components
- •Home Problems
- •8.1 Introduction
- •8.2 Instrumentation Amps
- •8.3 Medical Isolation Amps
- •8.3.1 Introduction
- •8.3.3 A Prototype Magnetic IsoA
- •8.4.1 Introduction
- •8.6 Chapter Summary
- •9.1 Introduction
- •9.2 Descriptors of Random Noise in Biomedical Measurement Systems
- •9.2.1 Introduction
- •9.2.2 The Probability Density Function
- •9.2.3 The Power Density Spectrum
- •9.2.4 Sources of Random Noise in Signal Conditioning Systems
- •9.2.4.1 Noise from Resistors
- •9.2.4.3 Noise in JFETs
- •9.2.4.4 Noise in BJTs
- •9.3 Propagation of Noise through LTI Filters
- •9.4.2 Spot Noise Factor and Figure
- •9.5.1 Introduction
- •9.6.1 Introduction
- •9.7 Effect of Feedback on Noise
- •9.7.1 Introduction
- •9.8.1 Introduction
- •9.8.2 Calculation of the Minimum Resolvable AC Input Voltage to a Noisy Op Amp
- •9.8.5.1 Introduction
- •9.8.5.2 Bridge Sensitivity Calculations
- •9.8.7.1 Introduction
- •9.8.7.2 Analysis of SNR Improvement by Averaging
- •9.8.7.3 Discussion
- •9.10.1 Introduction
- •9.11 Chapter Summary
- •Home Problems
- •10.1 Introduction
- •10.2 Aliasing and the Sampling Theorem
- •10.2.1 Introduction
- •10.2.2 The Sampling Theorem
- •10.3 Digital-to-Analog Converters (DACs)
- •10.3.1 Introduction
- •10.3.2 DAC Designs
- •10.3.3 Static and Dynamic Characteristics of DACs
- •10.4 Hold Circuits
- •10.5 Analog-to-Digital Converters (ADCs)
- •10.5.1 Introduction
- •10.5.2 The Tracking (Servo) ADC
- •10.5.3 The Successive Approximation ADC
- •10.5.4 Integrating Converters
- •10.5.5 Flash Converters
- •10.6 Quantization Noise
- •10.7 Chapter Summary
- •Home Problems
- •11.1 Introduction
- •11.2 Modulation of a Sinusoidal Carrier Viewed in the Frequency Domain
- •11.3 Implementation of AM
- •11.3.1 Introduction
- •11.3.2 Some Amplitude Modulation Circuits
- •11.4 Generation of Phase and Frequency Modulation
- •11.4.1 Introduction
- •11.4.3 Integral Pulse Frequency Modulation as a Means of Frequency Modulation
- •11.5 Demodulation of Modulated Sinusoidal Carriers
- •11.5.1 Introduction
- •11.5.2 Detection of AM
- •11.5.3 Detection of FM Signals
- •11.5.4 Demodulation of DSBSCM Signals
- •11.6 Modulation and Demodulation of Digital Carriers
- •11.6.1 Introduction
- •11.6.2 Delta Modulation
- •11.7 Chapter Summary
- •Home Problems
- •12.1 Introduction
- •12.2.1 Introduction
- •12.2.2 The Analog Multiplier/LPF PSR
- •12.2.3 The Switched Op Amp PSR
- •12.2.4 The Chopper PSR
- •12.2.5 The Balanced Diode Bridge PSR
- •12.3 Phase Detectors
- •12.3.1 Introduction
- •12.3.2 The Analog Multiplier Phase Detector
- •12.3.3 Digital Phase Detectors
- •12.4 Voltage and Current-Controlled Oscillators
- •12.4.1 Introduction
- •12.4.2 An Analog VCO
- •12.4.3 Switched Integrating Capacitor VCOs
- •12.4.6 Summary
- •12.5 Phase-Locked Loops
- •12.5.1 Introduction
- •12.5.2 PLL Components
- •12.5.3 PLL Applications in Biomedicine
- •12.5.4 Discussion
- •12.6 True RMS Converters
- •12.6.1 Introduction
- •12.6.2 True RMS Circuits
- •12.7 IC Thermometers
- •12.7.1 Introduction
- •12.7.2 IC Temperature Transducers
- •12.8 Instrumentation Systems
- •12.8.1 Introduction
- •12.8.5 Respiratory Acoustic Impedance Measurement System
- •12.9 Chapter Summary
- •References
Models for Semiconductor Devices Used in Analog Electronic Systems |
97 |
Note the trade-off between closed-loop gain and bandwidth; the lower the mid-band gain magnitude is, −RF/Rs, the higher the break frequency,
ω = |
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The choice of transistor for a high-frequency amplifier design is paramount. BJTs must be chosen to have high fT s, and FETs to have high fmax. Although it may never be necessary to design a discrete or an IC multistage amplifier, the factors described earlier that go into the design of broadband amplifiers should appreciated.
2.6Photons, Photodiodes, Photoconductors, LEDs, and Laser Diodes
2.6.1Introduction
This section examines the properties of semiconductor devices that sense photon energy and others that emit photon energy. Photons are an alternate way to describe electromagnetic (EM) radiation generally having wavelengths from 1 ∞ 10−4 m to less than 3 ∞ 10−12 m. These wavelengths include infrared (IR); visible light; ultraviolet (UV); x-rays; and gamma rays. The photon is a quantum EM “particle” used to describe physical interactions of low-power EMR with molecules, atoms, and subatomic particles, such as atomic shell electrons. The electromagnetic wave characterization of EM energy is used throughout the EM spectrum and finds application in describing the operation of antennas, transmission lines, fiber optic cables, and optical elements such as lenses, prisms, and mirrors used in IR, visible, and UV wavelengths. Maxwell’s equations for EM wave propagation are also useful in describing such phenomena as diffraction, refraction, and polarization of light (Balanis, 1989; Hecht, 1987).
A photon has essentially zero mass; it moves at the speed of light in a medium and has an individual energy of ε = hc/λ = hν joules, where h is Planck’s constant (6.6253 ∞ 10−34 joule-second); c is the speed of light in the supporting medium (c = 2.998 ∞ 108 m/sec in vacuo); λ is the wavelength of the EM radiation in meters; and ν is the Hertz frequency of the EMR (ν of visible light is approximately 1014 Hz). Photon energy is also given in electronvolts (eV). To obtain the energy of a photon in eV, divide its energy in joules by 1.602 ∞ 10−19. (1.602 ∞ 10−19 is the magnitude of the charge on an electron.) For example, a photon of blue light with a wavelength of λ = 450 nm has an energy of e = (6.626 ∞ 10−34 J s)(3 ∞ 108 m/s)/(450 ∞ 10−9 m) = 4.41 ∞ 10−19 J or 2.76 eV. Similarly, a photon of λ = 700 nm (red light) has an energy of 2.84 ∞ 10−19 J or 1.77 eV. Figure 2.55 illustrates the EM spectrum.
© 2004 by CRC Press LLC
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ν Hz |
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Wavelength |
Photon |
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1021 |
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in vacuo |
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energy, eV |
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Gamma rays |
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1020 |
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3X10−12 |
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1019 |
X-rays |
3X10−11 |
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1018 |
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3X10−10 |
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4.13X103 |
1017 |
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3X10−9 |
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4.13X102 |
1016 |
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UV |
3X10−8 |
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4.13X101 |
1015 |
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3X10−7 |
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Visible |
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1014 |
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3X10−6 |
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LIR |
3X10−5 |
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FIR |
3X10−4 |
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1011 |
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3X10−3 |
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FIGURE 2.55
The electromagnetic spectrum.
Many sensors are used to measure EM energy in biomedical applications. These include, but are not limited to, photodiodes; phototransistors; photoconductors; pyroelectric IR sensors; photomultiplier tubes (PMTs); scintillation crystals + PMTs; etc. (Northrop, 2002).
Next, pn junction photon sensors, photoconductors and certain solid-state photon sources will be considered. It will be demonstrated that the interaction of photons in a certain energy range with a semiconductor pn junction can cause the generation of a photovoltaic EMF; this EMF is the basis for
© 2004 by CRC Press LLC
Models for Semiconductor Devices Used in Analog Electronic Systems |
99 |
photodiode behavior and the solar cell as an energy transducer (photons to electrical current flow) capable of doing work. Photodiodes and solar cells can be used to measure incident EM radiation intensity. Also treated in the following sections are the generation of photon energy by special semiconductor diode structures, the light-emitting diode (LED) and the laser diode. Both types of photon-emissive devices have found wide application in biomedical instrumentation (Northrop, 2002).
2.6.2PIN Photodiodes
Photodiodes are used as sensors for EMR ranging from near infrared (NIR) to near ultraviolet (UVA). Even a standard small-signal silicon pn junction diode with a transparent glass envelope will respond to incident EMR of appropriate wavelength, as will a reverse-biased LED. However, photodiodes used for photonic measurements have specialized junction structures that maximize the area over which incident photons are absorbed. Photodiodes are used in a broad range of biomedical instruments, including blood pulse oximeters; finger-tip heart-rate sensors; single-drop blood glucose meters; fiber-optic-based spectrophotometers (used to sense analytes in blood, urine, etc.); spectrophotometric detection of tumors using endoscopes; etc.
Photodiodes fall into two broad categories: (1) three-layer, PIN diodes (“I” stands for intrinsic semiconductor) and (2) avalanche photodiodes (APDs), which are basically four-layer structures (P+IPN). Figure 2.56 illustrates schematic cross sections through two types of PIN devices. Note that to improve the efficiency of photon capture, a thin, λ/4 layer of antireflective (AR) coating is used on the surface of the PD, similar to the AR coatings commonly used on binocular and camera lenses. Assume an incident photon with the appropriate energy passes through the AR coating, enters the P+ diffusion layer, and interacts (collides) with a valence-band electron. If the electron gains energy greater than the band-gap energy, Eg, it is pulled up into the conduction band, leaving a hole in the valence band.
These electron–hole pairs are formed throughout the P+ layer, the depletion layer, and the N-layer materials. In the depletion layer, the E-field accelerates these photoelectrons toward the N-layer and the holes toward the P-layer. Electrons from the electron–hole pairs generated by photons in the N-layer, along with electrons that have arrived from the P-layer, are left in the N-layer conduction band. Meanwhile the holes diffuse through the N-layer up to the depletion layer while being accelerated and are collected in the P-layer valence band. By these mechanisms, electron–hole pairs, which are generated in proportion to the amount of incident light, are collected in the N- and P-layers of the PD. This results in a positive charge in the P-layer and a negative charge in the N-layer.
When an external circuit is connected between the P- and N-layers, photocurrent electrons will flow away from the N-layer and holes will flow away from the P-layer, toward the opposite electrode. The PIN PD and the external
© 2004 by CRC Press LLC
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Analysis and Application of Analog Electronic Circuits |
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FIGURE 2.56
(A) Layer cake schematic of a three-layer PIN Si photodiode. (B) Layer cake schematic of a three layer, NIP Si photodiode. The AR coating minimizes reflection (and thus maximizes photon absorption) in the range of wavelengths in which the PD is designed to work. The guard ring minimizes dark current.
circuit are shown in Figure 2.56(A). Note that in normal operation of the PD, it is reverse-biased, so the photocurrent is a reverse current flowing in the same direction as the thermally generated leakage current that flows in a reverse-biased pn diode.
© 2004 by CRC Press LLC
Models for Semiconductor Devices Used in Analog Electronic Systems |
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FIGURE 2.57
Top: simple series circuit for PIN PD. Bottom: iD vs. vD curves as a function of absorbed photon power, Pi. The load line is determined by the Thevenin equivalent circuit that the PD “sees.” Note that the PD’s photocurrent, IP, flows in the reverse direction. Vo across the load resistor can be determined graphically by the intersection of the iD = f(Pi) line with the load line.
Figure 2.57 illustrates typical PIN PD volt–ampere curves. The load line represents a graphical solution of the PD’s (nonlinear) volt–ampere curves with the (linear) Thevenin circuit “seen” by the PD. The zero-current intercept of the load line on the VD axis is at −Thevenin open-circuit voltage; the zero-voltage intercept is −Thevenin short-circuit current. The load line permits a graphical solution of:
iD (vD ) |
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The slope of the load line is easily seen to be −1/R and depends only on the Thevenin model parameters. Most PDs are operated in the third quadrant, either with a reverse-bias OCV or under short-circuit conditions (vD = 0). PD signal-conditioning circuits will be described later.
© 2004 by CRC Press LLC
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Analysis and Application of Analog Electronic Circuits |
The total PD current can be modeled by:
iD = Irs [exp(vD VT )− 1]− IP |
(2.186) |
where the photocurrent, IP, flows in the reverse direction and is given by:
IP |
= |
ηq Pi |
λ |
amperes |
(2.187) |
hc |
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where Pi is the total photon power incident on the PD active surface in watts; VT = kT/q, η is the capture efficiency (approximately 0.8); and Irs is the reverse saturation current. Irs is very temperature dependent; it can be approximated by (Navon, 1975; Millman, 1979):
Irs (T) = Irs (To )2(T−To )10
or
rs |
rs |
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where T is the Kelvin temperature; To is the Kelvin reference temperature; φ is the silicon energy gap (1.15 eV); and k is Boltzmann’s constant (1.380 ∞ 10−23 J/K). The simple PD model given by Equation 2.186 does not include the ohmic leakage of the reverse-biased PD. Such leakage can be an appreciable portion of the reverse dark iD for large reverse vD.
If the PIN PD is operated at zero iD, photon power produces an opencircuit voltage given by:
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q ηλ P ˘ |
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vDoc |
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i |
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Silicon PIN PDs are useful over a wavelength band covering approximately 200 to 1100 nm; their spectral sensitivity rises slowly to a peak at approximately 800 nm, then falls off rapidly. Sensitivity is given by the PD’s responsivity in amps per watt; R(λ) = iD(0)/Pi. R(λ) peaks at approximately 0.55 A/W at approximately 850 nm. Figure 2.58 shows a “typical” Si PIN PD responsivity plot. PDs can also be fabricated using germanium (Ge) and InGaAs. The former material responds from approximately 300 to 1600 nm and the latter composition has a spectral responsivity range from approximately 800 to 2600 nm. Depending on operating conditions, PIN PDs are useful over a range of picowatts to milliwatts of optical power.
© 2004 by CRC Press LLC
Models for Semiconductor Devices Used in Analog Electronic Systems |
103 |
R(λ) (A/ W) 0.7
0.6
0.5
0.4
0.3
0.2
0.1
λ, nm
0.0
200 400 600 800 1000 1200
FIGURE 2.58
A typical responsivity plot for a Si PIN PD. See text for discussion.
Figures of merit for PDs include the responsivity R(λ), described previously; the noise-equivalent (optical) power (NEP); and the detectivity (D*). The NEP is the incident Pi at λ required to generate a short-circuit response current, IP, equal to the RMS noise current of the detector system (unity output signal-to-noise ratio.) NEP is a measure of the minimum detectable noise power at a given wavelength and bandwidth. In other words,
NEP(λ) = |
rms noise current |
Watts |
(2.190) |
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responsivity @ λ |
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The noise generated by a PD operating under reverse bias is due to shot noise generated in the dark leakage current and Johnson (thermal) noise generated in the equivalent shunt resistance of the PD. Shot and thermal noises are broadband and considered to have flat white power density spectra (See Chapter 9). The mean-squared shot noise can be shown to be given by:
i 2 |
= 2 q I |
DL |
B msA |
(2.191) |
sn |
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where q is the magnitude of the electron charge; IDL is the dark leakage current in amperes (IDL is zero for a zero-biased PD); and B is the equivalent
© 2004 by CRC Press LLC
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Analysis and Application of Analog Electronic Circuits |
Hertz noise bandwidth over which the noise current is measured. The meansquared thermal noise can be shown to be given by:
i 2 |
= 4 k T GB msA |
(2.192) |
tn |
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where k = Boltzmann’s constant (1.38 ∞ 10−38 J/K); T = Kelvin temperature of PD; B = equivalent Hertz noise bandwidth; and G = net thermal noise producing resistance. The total MS diode noise current is found by adding the two MS current noises:
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= i 2 |
+ i 2 |
msA |
(2.193) |
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n |
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sn |
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tn |
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Thus the total RMS diode noise is:
in = in2 = (2 q IDL + 4 k T G) B rmsA |
(2.194) |
Johnson noise dominates as the dark current 0. Note that NEP depends on λ, IDL (thus the PD operating circuit), the noise bandwidth B, T, and the net (Norton) conductance, G, in parallel with the photocurrent and noise current sources. The NEP for Si PIN PDs ranges from approximately 10–14 W/ Hz for small-area (A = 1 mm2) low-noise PDs, to over 2 ∞ 10–13 W/ Hz for very large area cells (A = 100 mm2). Obviously, the NEP is desired to be as small as possible. Note that manufacturers give NEP independent of the noise Hertz bandwidth, B. NEP must be multiplied by the
B to get the actual NEP in watts.
Often the input light power, Pi, is chopped; that is, the beam is periodically interrupted by a chopper wheel, effectively modulating the beam by multiplying it by a 0,1 square wave. The chopping rate is generally at audio frequencies (e.g., 1 kHz) and the bandwidth of the associated band-pass filter used to condition the PD output determines B. Chopping is used to avoid the excess 1/f diode noise present at DC and very low frequencies.
Figure 2.59 illustrates the equivalent model for a reverse-biased Si PIN PD, showing signal, noise, and dark current sources, the diode small-signal capacitance, Cd, which is a depletion capacitance that depends on −vDQ, and diode semiconductor doping and geometry. Note that the DC reverse leakage current has two components: a constant small Irs and a voltage-dependent dark current, IDL. (IDL + Irs) are used to calculate isn. Normally, RL R, so the thermal noise current is found using the external load resistor, R (1/R = G). The junction depletion capacitance, Cd, decreases as vDQ goes more negative. Large Cd is deleterious to PD high-frequency response because it shunts IP(jω) to ground. Note that Cd increases with illumination and is smallest in the dark
(using the circuit of Figure 2.57). Cd is on the order of picofarads. For example, one Si PIN PD with 1 mm2 active area and a vDQ = −10 V has a Cd 4 pF.
© 2004 by CRC Press LLC