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Optics Express

Optics Express

  • Editor: C. Martijn de Sterke
  • Vol. 20, Iss. 8 — Apr. 9, 2012
  • pp: 9090–9098
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Simultaneous measurement of quality factor and wavelength shift by phase shift microcavity ring down spectroscopy

M. Imran Cheema, Simin Mehrabani, Ahmad A. Hayat, Yves-Alain Peter, Andrea M. Armani, and Andrew G. Kirk  »View Author Affiliations


Optics Express, Vol. 20, Issue 8, pp. 9090-9098 (2012)
http://dx.doi.org/10.1364/OE.20.009090


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Abstract

Optical resonant microcavities with ultra high quality factors are widely used for biosensing. Until now, the primary method of detection has been based upon tracking the resonant wavelength shift as a function of biodetection events. One of the sources of noise in all resonant-wavelength shift measurements is the noise due to intensity fluctuations of the laser source. An alternative approach is to track the change in the quality factor of the optical cavity by using phase shift cavity ring down spectroscopy, a technique which is insensitive to the intensity fluctuations of the laser source. Here, using biotinylated microtoroid resonant cavities, we show simultaneous measurement of the quality factor and the wavelength shift by using phase shift cavity ring down spectroscopy. These measurements were performed for disassociation phase of biotin-streptavidin reaction. We found that the disassociation curves are in good agreement with the previously published results. Hence, we demonstrate not only the application of phase shift cavity ring down spectroscopy to microcavities in the liquid phase but also simultaneous measurement of the quality factor and the wavelength shift for the microcavity biosensors in the application of kinetics measurements.

© 2012 OSA

1. Introduction

The last two decades have seen tremendous progress towards the development of real time, label free and miniature optical biosensors. Researchers have demonstrated numerous techniques based on the surface plasmon resonance, interferometers, waveguides, microcavities, optical fibers, and photonic crystals [1

1. X. Fan, I. M. White, S. I. Shopoua, H. Zhu, J. D. Suter, and Y. Sun, “Sensitive optical biosensors for unlabeled targets: a review,” Anal. Chim. Acta 620, 8–26 (2008). [CrossRef] [PubMed]

]. Among these different approaches, the large photon lifetime (Quality factor of 106 – 109) of microcavities makes them a strong candidate for ultrasensitive biosensing, as the circulating photons will sample a biodetection event many times. The first microcavity biosensor was demonstrated by Vollmer et. al [2

2. F. Vollmer, D. Braun, A. Libchaber, M. Khoshsima, I. Teraoka, and S. Arnold, “Protein detection by optical shift of a resonant microcavity,” Appl. Phys. Lett. 80, 4057–4059 (2002). [CrossRef]

] in 2002, in which they detected proteins by measuring change of the resonant wavelength of a microsphere as a function of the binding event. Since then researchers have transitioned the microcavity-based sensors towards diagnostics platforms and protein behavior detection [3

3. A. L. Washburn and R. C. Bailey, “Photonics-on-a-chip: recent advances in integrated waveguides as enabling detection elements for real-world, lab-on-a-chip biosensing applications,” Analyst 136, 227 (2011). [CrossRef]

, 4

4. C. E. Soteropulos, H. K. Hunt, and A. M. Armani, “Determination of binding kinetics using whispering gallery mode microcavities,” Appl. Phys. Lett. 99, 103703 (2011). [CrossRef] [PubMed]

].

Until now, the majority of work using microcavity biosensors focused on correlating the change in the resonant wavelength to a biodetection event on the surface of the microcavity. However, the binding event will also influence the photon lifetime or the ring down time (and hence quality factor) of the microcavity [5

5. M. I. Cheema and A. G. Kirk, “Application of ring down measurement approach to microcavities for bio-sensing applications,” Proc. SPIE 7888, 788808 (2011) [CrossRef]

]. Apart from few instances, where quality factors have been determined based upon linewidth measurements [6

6. V. S. Ilchenko and L. Maleki, “High-Q whispering-gallery mode sensor in liquids,” Proc. SPIE 4629, 72 (2002).

, 7

7. A. M. Armani and K. J. Vahala, “Heavy water detection using ultra-high-q microcavities,” Opt. Lett. 31, 1896–1898 (2006). [CrossRef] [PubMed]

], researchers have not sought to measure this property, and thus important information about the biodetection event is lost. Moreover, in all configurations of the microcavity biosensors used so far, random intensity fluctuations of the laser source add noise into the final measurement and hence the overall performance of the biosensor is degraded [8

8. I. M. White and X. Fan, “On the performance quantification of resonant refractive index sensors,” Opt. Express 16, 1020–1028 (2008). [CrossRef] [PubMed]

, 9

9. J. Hu, X. Sun, A. Agarwal, and L. C. Kimerling, “Design guidelines for optical resonator biochemical sensors,” J. Opt. Soc. Am. B 26, 1032–1041 (2009). [CrossRef]

]. These issues can be overcome by using the microcavity as the key component in a phase shift cavity ring down spectroscopy (PS-CRDS) measurement.

With the success of CRDS in gaseous phase, the technique is also emerging as a new way for performing absorption measurements in the liquid phase [16

16. L. van der Sneppen, “Liquid-phase cavity ring-down spectroscopy for improved analytical detection sensitivity,” Ph.D. thesis, Vrije University, Amsterdam (2008).

] and for biosensing [17

17. T. Peter and K. K. Lehmann, “Cavity ring Down biosensing,” Optical Biosensors: Today and Tomorrow (Elsevier B.V, 2008), pp. 403–418.

]. The first application of CRDS biosensing involved a resonator made of an optical fiber with couplers at its ends[18

18. P. Tarsa, A. Wist, P. Rabinowitz, and K. K. Lehmann, “Single-cell detection by cavity ring-down spectroscopy,” Appl. Phys. Lett. 85, 4523–4525 (2004). [CrossRef]

]. In this work, the researchers used taper section of the fiber as a sensing medium where the evanescent tail of the cavity modes interacted with the analyte molecules. An alternative, inexpensive design is the use of fiber in a loop with a gap between the two ends for the insertion of a micro-fluidic chip. Loock et. al. applied PS-CRDS to the fiber loops to detect μM concentrations of chemicals in liquid samples [19

19. Z. Tong, A. Wright, T. McCormick, R. Li, R. D. Oleschuk, and H.-P. Loock, “Phase-shift fiber-loop ring-down spectroscopy,” Anal. Chem. 76, 6594–6599 (2004). [CrossRef] [PubMed]

]. However, fiber loop cavities have significantly lower quality factors than silica spheres or toroidal microcavities, resulting in significantly shorter photon lifetimes. Thus, by combining the advantages of PS-CRDS with an ultra-high-Q microcavity transducer, this sensing modality will be greatly improved. With this motivation, Barnes et.al [20

20. J. Barnes, B. Carver, J. M. Fraser, G. Gagliardi, H. P. Loock, Z. Tian, M. W. B. Wilson, S. Yam, and O. Yastrubshak, “Loss determination in microsphere resonators by phase-shift cavity ring-down measurements,” Opt. Express 16, 13158–13167 (2008). [CrossRef] [PubMed]

] applied PS-CRDS to silica microspheres for determining their losses in air. To determine the ring down times, they did linear curve fitting of phase change as a function of modulation frequency. Such a measurement requires the use of a small angle approximation of Eq. (9) (see section 2.1) and will be marginally correct for only small phase changes. The experimental scheme that was employed is not well-suited for biosensing application as it is not possible for that setup to track the quality factor or the resonant wavelength, as a function of a biodetection event, at multiple modulation frequencies. Therefore, the goal of our research is to show, 1) the application of PS-CRDS to microcavities in the liquid phase, and 2) to simultaneously track changes in the quality factor (ring down time) and the resonant wavelength shift as function of a biodetection event by PS-CRDS in a microcavity biosensor.

In our work, we used a bioconjugated [21

21. H. K. Hunt, C. Soteropulos, and A. M. Armani, “Bioconjugation strategies for microtoroidal optical resonators,” Sensors 10, 9317–9336 (2010). [CrossRef] [PubMed]

] microtoroid optical resonator [22

22. D. K. Armani, T. J. Kippenberg, S. M. Spillane, and K. J. Vahala, “Ultra-high-Q toroid microcavity on a chip,” Nature 421 (2003). [CrossRef] [PubMed]

] to specifically detect unbinding of streptavidin (Fig. 1). We tracked both change in the Q and the resonant wavelength by using PS-CRDS and we found that the disassociation curves of biotin-streptavidin are in good agreement with the previously published results.

Fig. 1 (a) Experimental Setup, FG - Function Generator (b) Magnified view of the microacquarium. A cover slip is placed 2mm (approx.) above the microcavity chip holder with a spacer to form the microacquarium. (c) Scanning electron microscope (SEM) image of the microtoroidal cavity

2. Phase shift cavity ring down spectroscopy (PS-CRDS)

2.1. Theory

Following the similar procedure as outlined in [12

12. E. G. Berden and R. Engeln, Cavity Ring-Down Specroscopy: Techniques and Applications (Wiley, 2009).

, 15

15. R. Engeln, G. VonHelden, G. Berden, and G. Meijer, “Phase shift cavity ring down absorption spectroscopy,” Chem. Phys. Lett. 262, 105–109 (1996). [CrossRef]

] for free space optical cavities, PS-CRDS equations for a microcavity coupled with a tapered optical fiber can be developed. The intensity modulated light entering the fiber can be represented by :
Iin put=Io(1+αin put sin ωt)
(1)
where α is the modulation depth and ω is the modulation frequency.

Depending upon the coupling regime [23

23. S. Spillane, “Fiber-coupled ultra-high-q microresonators for nonlinear and quantum optics,” Ph.D. thesis, California Inst. of Technol. (2004).

], a fraction of light will be coupled to the microcavity. If I1 represents the uncoupled light and I2 represents the coupled light, then the modulated light entering into the microcavity can be written as:
Icavity=I2(1+αin put sin ωt)
(2)
If τ represents the ring down time of the microcavity, then its impulse response will be:
h(t)=C exp (tτ)
(3)
Therefore intensity at the fiber output will be
Iout put(t)=I1(1+αin put sin ωt)+Icavity*h(t)
(4)
=I1(1+αin put sin ωt)+CtI2(1+αin put sin ωt´) exp (tt´τ) dt´
(5)
where t́ is dummy variable for performing convolution. Under steady state conditions [23

23. S. Spillane, “Fiber-coupled ultra-high-q microresonators for nonlinear and quantum optics,” Ph.D. thesis, California Inst. of Technol. (2004).

] for a microcavity coupled with a tapered fiber, the value of C can be found by applying the principle of conservation of energy, i.e. total intensity coupled to the cavity in a time interval must be equal to the intensity coupled out in that time interval i.e.
CtI2exp (tt´τ) dt´=I2
(6)
C=1τ
(7)
Therefore,
Iout put(t)=I1(1+αin put sin ωt)+I2(1+αout put sin (ωt+ϕ))
(8)
where,
tan ϕ=ωτ
(9)
αout put=αin put1+ω2τ2
(10)
Hence, the ring down time (τ) of the microcavity can be found by taking the ratio of in phase and out of phase sinusoidal components at the fiber output. The quality factor then can easily be extracted by the following relation:
Q=2πcτλresonant
(11)
where λresonant is the resonant wavelength of the microcavity.

2.2. Experimental Setup

In the conventional PS-CRDS experiments with the free space cavities, a locking technique, such as Pound-Drever-Hall [24

24. R. W. P. Drever, J. L. Hall, F. V. Kowalski, J. Hough, G. M. Ford, A. J. Munley, and H. Ward, “Laser phase and frequency stabilization using an optical resonator,” Appl. Phys. B 31, 97–105 (1983). [CrossRef]

] technique, is used for locking the laser frequency to the cavity mode. Such locking techniques can also be applied to microcavities [25

25. A. Schliesser and T. J. Kippenberg, “Cavity Optomechanics with Whispering-Gallery Mode Optical Micro-Resonators,” Advances in Atomic Molecular and Optical Physics (Elsevier Inc., 2010), Vol. 58, pp. 207–323. [CrossRef]

]. However, locking the laser to the microcavity for biosensing means that information about the shift in resonant wavelength will not be measured; at the same time, if the locking technique is not used, then the ring down time can not be measured because the microcavity resonance wavelength will shift due to the biodetection event. We have developed a novel experimental setup to overcome these difficulties. The experimental setup is shown in Fig. 1.

A function generator (FG1) with triangular wave output (100mHz, 1V peak-to-peak) continuously modulates the wavelength of a tunable laser (New Focus, Velocity Scan 633nm tunable laser) to generate the resonant peaks as shown in Fig. 2a. The peaks are labelled as Forward Scanning Peaks (FSP), and Backward Scanning Peaks (BSP). After locating a resonant peak, a second function generator (FG2) is switched on (13MHz, 4V peak-to-peak) to provide sinusoidal modulation of the laser intensity. After switching on both of the function generators, the phase shift between a reference sinusoid (sinusoidal modulated intensity of the laser before coupling) and the sinusoid at the fiber output is continuously recorded. In such a scan, there will be phase shifts only at the resonant peaks (Fig. 3). The same values of the phase shifts at the FSP and BSP indicate that there is no difference in the FWHM widths of the two peaks and hence any nonlinear effects are negligible [27

27. V. S. Ilchenko and M. L. Gorodetskii, “Thermal nonlinear effects in optical whispering gallery microresonators,” Laser Phys. 2, 1004–1009 (1992).

], an important consideration for the biosensing experiments. The values of the peaks are the phase shifts which correspond to the ring down time (and hence Q) and positions of the peaks correspond to the resonant wavelength. Both of them can easily be extracted by further signal processing of the captured data.

Fig. 2 Two types of measurements (a) Minimum of one of the resonant peak is tracked as function of the biodetection event (b) Phase shift experienced by the sinusoid coming out of the microcavity is tracked as a function of the biodetection event. With reference to Fig. (a), black sinusoid is extracted at the resonant peak.
Fig. 3 Full scan with zoom in view of FSP and BSP (a) Continuous monitoring of phase as function of disassociation of the streptavidin from the biotin (b) Due to limitations of the computer speed, two FSPs and BSPs are separated by 5s respectively.

3. Results and discussion

The binding kinetics of the biotin-streptavidin system in association and disassociation phase can be approximated by an exponential curve for the resonant wavelength [28

28. S. Zhao and W. M. Reichert, “Influence of biotin lipid surface density and accessibility on avidin binding to the tip of an optical fiber sensor,” Langmuir 8, 2785–2791 (1992). [CrossRef]

]. During the association phase, the resonant wavelength shifts towards the red and in the disassociation phase it shifts towards the blue [4

4. C. E. Soteropulos, H. K. Hunt, and A. M. Armani, “Determination of binding kinetics using whispering gallery mode microcavities,” Appl. Phys. Lett. 99, 103703 (2011). [CrossRef] [PubMed]

]. The change in resonant wavelength during the disassociation of the streptavidin from the biotin are shown in Fig. 4 which is in excellent agreement with [4

4. C. E. Soteropulos, H. K. Hunt, and A. M. Armani, “Determination of binding kinetics using whispering gallery mode microcavities,” Appl. Phys. Lett. 99, 103703 (2011). [CrossRef] [PubMed]

]. The change in Q during the disassociation phase is also shown which is following an increasing trend which makes sense as the binding and unbinding of the streptavidin will decrease and increase the overall quality factor of the microtoroid respectively. The error signal, which is recorded with the tapered optical fiber alone, is also shown in Fig. 5. The noise shown in Fig. 5 is significantly smaller than the signal shown in Fig. 3 with the minimum and maximum signal to noise ratios of 12dB and 15.8dB respectively.

Fig. 4 Experimental parameters. The curves are not smooth because each data point is 5s apart on each curve, a limitation of the computer used in the experiment. In (b), negative values signify that the resonant wavelength is shifting towards blue
Fig. 5 A typical error signal, recorded by moving the taper far away from the microcavity. Mean: ±0.2662°, Variance: 0.1076°, mode: ±0.3387°. Based upon the detected signals, (SignalNoise)min=12dB, and (SignalNoise)max=15.8dB

The results indicate successful proof of the concept for the application of PS-CRDS to microcavities for biosensing. The PS-CRDS biosensor simultaneously tracks the Q and the resonant wavelength as a function of the biodetection event as opposed to its frequency domain counterpart which can only track the resonant wavelength. In our current setup, only tracking of the Q is free from noise due to the intensity fluctuations. However, the performance of the sensor can be improved by employing a lock-in amplifier which will reduce the error signal to 0.01° and hence the minimum and maximum signal to noise ratios will be improved to 27dB and 30dB respectively. In conventional wavelength shift based microcavity biosensors, minimum of the resonant wavelength is tracked by software. On the other hand, by use of lock-in ampli-fier in PS-CRDS biosensor, accuracy of tracking of the resonant wavelength will be improved as compared to the frequency domain biosensor.

Since absorption of analytes influences the quality factor of the microtoroid, the PS-CRDS biosensor can also conduct such measurements in a faster (electronics) and an intensity noise free manner. On the other hand, absorption measurements [7

7. A. M. Armani and K. J. Vahala, “Heavy water detection using ultra-high-q microcavities,” Opt. Lett. 31, 1896–1898 (2006). [CrossRef] [PubMed]

, 29

29. A. T. Rosenberger, “Analysis of whispering-gallery microcavity-enhanced chemical absorption sensors,” Opt. Express 15, 12959–12964 (2007). [CrossRef] [PubMed]

] in the wavelength shift based microcavity sensors are slow (software) and carry noise not only due to the intensity fluctuations but also due to fitting of Lorentzian curves to the resonant peaks. Moreover, other noise mechanisms that are present in the wavelength shift based microcavity sensors, such as laser frequency jitter, conversion of FG1 voltage to the wavelength [30

30. T. Lu, H. Lee, T. Chen, S. Herchak, J.-H. Kim, S. E. Fraser, R. C. Flagan, and K. Vahala, “High sensitivity nanoparticle detection using optical microcavities,” Proc. Natl. Acad. Sci. U.S.A. 108, 5976–5979 (2011). [CrossRef] [PubMed]

], and shift in the resonant wavelength due to thermal fluctuations [31

31. J. D. Swaim, J. Knittel, and W. P. Bowen, “Detection limits in whispering gallery biosensors with plasmonic enhancement,” Appl. Phys. Lett. 99, 243109 (2011). [CrossRef]

] are also minimized in the Q measurements. This observation is clear from the fact that these noise mechanisms will effect the location of the resonant peak whereas the Q measurements are independent of the peak’s position (see Fig. 2b along with its caption, Eq. (9), and Eq. (11)).

CRDS with free space cavities is an emerging technique for liquid phase applications such as liquid chromatography [32

32. K. L. Snyder and R. N. Zare, “Cavity ring-down spectroscopy as a detector for liquid chromatography,” Anal. Chem. 75, 3086–3091 (2003). [CrossRef] [PubMed]

, 33

33. B. Bahnev, L. van der Sneppen, A. E. Wiskerke, F. Ariese, C. Gooijer, and W. Ubachs, “Miniaturized cavity ring-down detection in a liquid flow cell,” Anal. Chem. 77, 1188–1191 (2005). [CrossRef] [PubMed]

]. However, such devices suffer from scattering and reflection losses due to the placement of the liquid sample inside the cavity. In some cases [33

33. B. Bahnev, L. van der Sneppen, A. E. Wiskerke, F. Ariese, C. Gooijer, and W. Ubachs, “Miniaturized cavity ring-down detection in a liquid flow cell,” Anal. Chem. 77, 1188–1191 (2005). [CrossRef] [PubMed]

], liquid is in contact with the mirrors which degrades the mirrors over a period of time. Moreover, different mirrors need to be employed to meet wavelength requirements in an experiment. The PS-CRDS sensor demonstrated in this work can overcome the above mentioned difficulties and has potential to offer a compact and sensitive solution for the liquid chromatography applications.

4. Conclusions

In summary, we have combined the advantages of CRDS (high noise immunity) and microcavities (high Q, low cost and compact) to develop a sensor that can simultaneously track the Q and the resonant wavelength as a function of a biodetection event. The sensor can also provide faster results for absorption measurements than its frequency domain counterpart. This work is also the first demonstration of applying PS-CRDS to microcavities for liquid phase applications. This PS-CRDS microcavity sensor has potential of finding wide applications not only in biosensing but also in analytical chemistry, pharmaceutical and agriculture sectors.

Acknowledgments

This work was supported by the NSERC-CREATE training program in integrated sensor systems, McGill institute of advanced materials, Montreal, Canada and the National Science Foundation [ 085281]. The authors would also like to thank Raja Abdullah and Jason Gamba for useful discussions.

References and links

1.

X. Fan, I. M. White, S. I. Shopoua, H. Zhu, J. D. Suter, and Y. Sun, “Sensitive optical biosensors for unlabeled targets: a review,” Anal. Chim. Acta 620, 8–26 (2008). [CrossRef] [PubMed]

2.

F. Vollmer, D. Braun, A. Libchaber, M. Khoshsima, I. Teraoka, and S. Arnold, “Protein detection by optical shift of a resonant microcavity,” Appl. Phys. Lett. 80, 4057–4059 (2002). [CrossRef]

3.

A. L. Washburn and R. C. Bailey, “Photonics-on-a-chip: recent advances in integrated waveguides as enabling detection elements for real-world, lab-on-a-chip biosensing applications,” Analyst 136, 227 (2011). [CrossRef]

4.

C. E. Soteropulos, H. K. Hunt, and A. M. Armani, “Determination of binding kinetics using whispering gallery mode microcavities,” Appl. Phys. Lett. 99, 103703 (2011). [CrossRef] [PubMed]

5.

M. I. Cheema and A. G. Kirk, “Application of ring down measurement approach to microcavities for bio-sensing applications,” Proc. SPIE 7888, 788808 (2011) [CrossRef]

6.

V. S. Ilchenko and L. Maleki, “High-Q whispering-gallery mode sensor in liquids,” Proc. SPIE 4629, 72 (2002).

7.

A. M. Armani and K. J. Vahala, “Heavy water detection using ultra-high-q microcavities,” Opt. Lett. 31, 1896–1898 (2006). [CrossRef] [PubMed]

8.

I. M. White and X. Fan, “On the performance quantification of resonant refractive index sensors,” Opt. Express 16, 1020–1028 (2008). [CrossRef] [PubMed]

9.

J. Hu, X. Sun, A. Agarwal, and L. C. Kimerling, “Design guidelines for optical resonator biochemical sensors,” J. Opt. Soc. Am. B 26, 1032–1041 (2009). [CrossRef]

10.

D. Anderson, J. Frisch, and C. Masser, “Mirror reflectometer based on optical cavity decay time,” Appl. Opt. 23, 1238–1245 (1984). [CrossRef] [PubMed]

11.

A. Okeefe and D. Deacon, “Cavity ring-down optical spectrometer for absorption-measurements using pulsed laser sources,” Rev. Sci. Instrum. 59, 2544–2551 (1988). [CrossRef]

12.

E. G. Berden and R. Engeln, Cavity Ring-Down Specroscopy: Techniques and Applications (Wiley, 2009).

13.

K. K. Lehmann and H. Huang, “Optimal Signal Processing in Cavity Ring-Down Spectroscopy,” Frontiers of Molecular Spectroscopy (Elsevier, 2009), pp. 623–658. [CrossRef]

14.

J. M. Herbelin, J. A. McKay, M. A. Kwok, R. H. Ueunten, D. S. Urevig, D. J. Spencer, and D. J. Benard, “Sensitive measurement of photon lifetime and true reflectances in an optical cavity by a phase-shift method,” Appl. Opt. 19, 144–147 (1980). [CrossRef] [PubMed]

15.

R. Engeln, G. VonHelden, G. Berden, and G. Meijer, “Phase shift cavity ring down absorption spectroscopy,” Chem. Phys. Lett. 262, 105–109 (1996). [CrossRef]

16.

L. van der Sneppen, “Liquid-phase cavity ring-down spectroscopy for improved analytical detection sensitivity,” Ph.D. thesis, Vrije University, Amsterdam (2008).

17.

T. Peter and K. K. Lehmann, “Cavity ring Down biosensing,” Optical Biosensors: Today and Tomorrow (Elsevier B.V, 2008), pp. 403–418.

18.

P. Tarsa, A. Wist, P. Rabinowitz, and K. K. Lehmann, “Single-cell detection by cavity ring-down spectroscopy,” Appl. Phys. Lett. 85, 4523–4525 (2004). [CrossRef]

19.

Z. Tong, A. Wright, T. McCormick, R. Li, R. D. Oleschuk, and H.-P. Loock, “Phase-shift fiber-loop ring-down spectroscopy,” Anal. Chem. 76, 6594–6599 (2004). [CrossRef] [PubMed]

20.

J. Barnes, B. Carver, J. M. Fraser, G. Gagliardi, H. P. Loock, Z. Tian, M. W. B. Wilson, S. Yam, and O. Yastrubshak, “Loss determination in microsphere resonators by phase-shift cavity ring-down measurements,” Opt. Express 16, 13158–13167 (2008). [CrossRef] [PubMed]

21.

H. K. Hunt, C. Soteropulos, and A. M. Armani, “Bioconjugation strategies for microtoroidal optical resonators,” Sensors 10, 9317–9336 (2010). [CrossRef] [PubMed]

22.

D. K. Armani, T. J. Kippenberg, S. M. Spillane, and K. J. Vahala, “Ultra-high-Q toroid microcavity on a chip,” Nature 421 (2003). [CrossRef] [PubMed]

23.

S. Spillane, “Fiber-coupled ultra-high-q microresonators for nonlinear and quantum optics,” Ph.D. thesis, California Inst. of Technol. (2004).

24.

R. W. P. Drever, J. L. Hall, F. V. Kowalski, J. Hough, G. M. Ford, A. J. Munley, and H. Ward, “Laser phase and frequency stabilization using an optical resonator,” Appl. Phys. B 31, 97–105 (1983). [CrossRef]

25.

A. Schliesser and T. J. Kippenberg, “Cavity Optomechanics with Whispering-Gallery Mode Optical Micro-Resonators,” Advances in Atomic Molecular and Optical Physics (Elsevier Inc., 2010), Vol. 58, pp. 207–323. [CrossRef]

26.

J. C. Knight, G. Cheung, F. Jacques, and T. A. Birks, “Phase-matched excitation of whispering-gallery-mode resonances by a fiber taper,” Opt. Lett. 22, 1129–1131 (1997). [CrossRef] [PubMed]

27.

V. S. Ilchenko and M. L. Gorodetskii, “Thermal nonlinear effects in optical whispering gallery microresonators,” Laser Phys. 2, 1004–1009 (1992).

28.

S. Zhao and W. M. Reichert, “Influence of biotin lipid surface density and accessibility on avidin binding to the tip of an optical fiber sensor,” Langmuir 8, 2785–2791 (1992). [CrossRef]

29.

A. T. Rosenberger, “Analysis of whispering-gallery microcavity-enhanced chemical absorption sensors,” Opt. Express 15, 12959–12964 (2007). [CrossRef] [PubMed]

30.

T. Lu, H. Lee, T. Chen, S. Herchak, J.-H. Kim, S. E. Fraser, R. C. Flagan, and K. Vahala, “High sensitivity nanoparticle detection using optical microcavities,” Proc. Natl. Acad. Sci. U.S.A. 108, 5976–5979 (2011). [CrossRef] [PubMed]

31.

J. D. Swaim, J. Knittel, and W. P. Bowen, “Detection limits in whispering gallery biosensors with plasmonic enhancement,” Appl. Phys. Lett. 99, 243109 (2011). [CrossRef]

32.

K. L. Snyder and R. N. Zare, “Cavity ring-down spectroscopy as a detector for liquid chromatography,” Anal. Chem. 75, 3086–3091 (2003). [CrossRef] [PubMed]

33.

B. Bahnev, L. van der Sneppen, A. E. Wiskerke, F. Ariese, C. Gooijer, and W. Ubachs, “Miniaturized cavity ring-down detection in a liquid flow cell,” Anal. Chem. 77, 1188–1191 (2005). [CrossRef] [PubMed]

OCIS Codes
(280.1415) Remote sensing and sensors : Biological sensing and sensors
(280.1545) Remote sensing and sensors : Chemical analysis
(140.3945) Lasers and laser optics : Microcavities
(140.3948) Lasers and laser optics : Microcavity devices
(280.4788) Remote sensing and sensors : Optical sensing and sensors

ToC Category:
Sensors

History
Original Manuscript: March 2, 2012
Revised Manuscript: March 23, 2012
Manuscript Accepted: March 27, 2012
Published: April 3, 2012

Virtual Issues
Vol. 7, Iss. 6 Virtual Journal for Biomedical Optics

Citation
M. Imran Cheema, Simin Mehrabani, Ahmad A. Hayat, Yves-Alain Peter, Andrea M. Armani, and Andrew G. Kirk, "Simultaneous measurement of quality factor and wavelength shift by phase shift microcavity ring down spectroscopy," Opt. Express 20, 9090-9098 (2012)
http://www.opticsinfobase.org/oe/abstract.cfm?URI=oe-20-8-9090


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References

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