The lifetime of fluorophore’s excited state is typically an intrinsic property of the fluorophore, determined by the quantum transition amplitude between the initial and final states. In many cases, interactions with the environment can shorten the unperturbed lifetime. This mechanism forms the basis for a wide range of fluorescent sensors applied to biological systems. A typical example is oxygen sensitive dyes.1, 2 These dyes can be excited into a triplet state, which has a relatively long lifetime due to the “forbidden” (spin-flip) nature of the relaxation to the ground state. However, intermolecular collisions with oxygen (in its triplet ground state) can quench the excited state. Measuring the excited state lifetime provides a quantitative measure of oxygen concentration in the environment. This enables tissue oxygenation imaging,3 an extremely valuable tool for cancer diagnostics, assessment of tumor aggressiveness, and treatment monitoring. Lifetime measurement was also utilized to measure intermolecular distances based on energy transfer between acceptor and donor molecules4 [fluorescence resonance energy transfer (FRET) pair]. Shorter donor excited state lifetimes are observed at short intermolecular distances, due to efficient quenching by the acceptor molecule. This “spectral ruler” technique also enables monitoring protein dynamics in living cells. In these applications, the lifetime is evaluated by measuring the decay of the fluorescent signal. Compared to fluorescent intensity measurements, lifetime measurements are much more robust and stable due to insensitivity to dye concentration, excitation intensity, and light absorption in tissue.
One of the major difficulties in applying these methods for clinical imaging is the loss of spatial information due to strong light scattering. We present here an alternative technique for local measurement of a dye’s excited state lifetime, one that does not require collection of the fluorescent emission but rather relies on photoacoustic probing.5, 6 The technique is based on a double-pulse illumination. A first pulse is used to excite the dye, and a second pulse is used to generate photoacoustic waves that provide information on the dye’s optical absorption. Since the optical absorption of the excited state is different than that of the ground state, the amplitude of the photoacoustic signal does reflect the relative population of the excited and ground states. By changing the time delay between the pulses, the decay of the excited state population can be monitored and the excited state lifetime can be extracted. The wavelengths of the two pulses are independently optimized to maximize contrast. A schematic illustration of the principle of operation is given in Fig. 1 . The method is well suited for tissue imaging because both the excitation and photoacoustic probing pulses are insensitive to light scattering, while the generated acoustic waves propagate with minimal scattering and provide useful information for image reconstruction.
To demonstrate the new method we have used a octaethylporphine (PtOEP: Frontier Scientific Inc.) oxygen sensitive dye. Its excited state has an intrinsically long lifetime ( in polystyrene medium7), however, it decreases in the presence of oxygen due to intermolecular collisions resulting in energy transfer to the oxygen molecule. Measuring the lifetime, therefore, yields a measure for the concentration of oxygen. The experimental system is described in Fig. 2 . It consists of a closed flow system for circulating the dye and controlling the concentration of dissolved oxygen, and two pulsed lasers for excitation and photoacoustic probing. The airtight closed flow circulation system includes -ID ( -OD) transparent plastic tubing (Tygon Lab R-3603, L/S13, Cole-Parmer), a compatible peristaltic pump (MasterFlex 7524-00, Cole-Parmer), and an air-sealed gas exchange cavity for controlling the level of dissolved oxygen in the dye by either bubbling or air, for low and high oxygen concentration, respectively. A doubled YAG laser (QuantaRay, , pulse , pulse , beam ) was used for excitation. A doubled YAG laser pumped OPO system [Surelite I-20, Surelite OPOplus, Continuum, , pulse energy with neutral density (ND) , pulse , beam ) was used for photoacoustic probing. The two laser beams were directed to overlap on a section of the circulating dye tubing. A focused ultrasound (US) transducer (Panametrics V311, , ), focused at the beam overlap position, was used to detect the photoacoustic signal. The signal was amplified by a amplifier (Panametrics 5072PR) and recorded by a digital oscilloscope (WaveSurfer 432, LeCroy Inc., bandwidth limited to , 20 averaging). The timing of the excitation and probing pulses was controlled by a programmable logic array that enables an accurate time delay in the range of to between the excitation and the probe pulses. The dye was first dissolved in toluene at a concentration of stock solution which was then diluted with ethanol to prepare a dye solution. An optical system for collecting the fluorescence light was added to enable simultaneous measurement of fluorescence and photoacoustic signals. The optical system includes a collecting lens ( , ), bandpass filter ( , Chroma,Technology Corp.), and a photodiode (FDS010 Si Photodiode, , Thorlabs Inc.).
We measured the photoacoustic response for a set of excitation-probe time delays in the range of 0 to . This set of measurements was repeated after 120 minutes of bubbling (low oxygen state) and after of air bubbling (high oxygen state). A reference signal with no excitation pulse, which corresponds to ground state constant absorption at the probe wavelength , was also recorded for each oxygen state. The reference signal was subtracted from the measured photoacoustic signals at different delays to extract the contribution of transient absorption to the photoacoustic signals. An example of transient absorption phtoacoustic signals at three different time delays and a low oxygen state is shown in Fig. 3 . To measure the amplitude of the signals we calculated the square root of the signal energy in a time window containing the first peak (see Fig. 3). The photoacoustic signal amplitudes, of both low and high oxygen states, as a function of the excitation-probe delay time are shown in Fig. 4 . To compare the excited state lifetime based on the photoacoustic measurements with fluorescence lifetime, the fluorescence emission was collected. The photoacoustic and fluorescence lifetimes were measured by fitting an exponential decay function to data in the range of 4 to . A close agreement was found between lifetimes measured in both methods. The results are summarized in Table 1 . The results for the high oxygen state show significant deviation from a simple exponential decay. This deviation is primarily due to lack of dynamic range in the PA measurement.
Lifetimes measured by fitting an exponential decay function to photoacoustic (PA) and fluorescence (FL) decay data.
A constant term was first subtracted from the data before fitting. For the photoacoustic data, the constant was determined from photoacoustic signals measured with no excitation pulse. For the fluorescence data, the constant was extracted from the photodetector signal at long delay (100ms) after excitation.
To conclude, we presented a new technique for quantifying the excited state lifetime of a dye, based on PA probing. The technique was demonstrated by measuring different lifetimes of an oxygen sensitive dye that was subjected to different oxygen concentrations. The results obtained by the PA method were verified by an independent measurement of the lifetimes by conventional time-dependent FL.
The single position measurement technique can be extended to lifetime imaging by replacing the single US transducer with an ultrasonic array receiver and acquisition system.8 PA lifetime imaging has a number of significant advantages over FL lifetime imaging:
1. Penetration is deeper in tissue since the excitation pulse and the PA probe pulse only traverse a single path to the target, while FL measurement requires two way light propagation. The typical penetration depth for PA imaging,9 at a wavelength of , exceeds . However, effective dye excitation imposes an additional limitation on the penetration depth. In the near IR (NIR) region this would correspond to a depth of 2 to .
2. Submillimeter resolution is maintained up to the full penetration depth.
3. 3-D imaging (with 2-D receiver arrays) is possible.
In the work reported here we used green light to excite the dye, which has very shallow tissue penetration (less than ). To translate the method to medical applications it is essential to replace the dye with a red or NIR excitable dye. A potential candidate is Pd-tetra-(4-carboxyphenyl) tetrabenzoporphyrin dendrimer (PdTBP) (Oxygen Enterprises Ltd., Philadelphia, Pennsylvania), which can be excited10 at . To estimate the effective penetration depth in tissue we first calculate the optical fluence required for saturated absorption as , where is Planck’s constant, is the optical frequency, and is the single-molecule cross section for absorption. For PdTBP dye, this requirement yields a value of . Considering tissue-effective attenuation at a wavelength of , and assuming surface illumination of (complying with ANSI Z136.1 laser safety standard), efficient excitation would be achieved up to a depth of .
Another improvement of the technique would be to use a long excitation pulse, but one that is still shorter than the resolution required for lifetime measurement. In our example, a excitation pulse could be used to measure the long lifetime (10 to ) of PtOEP dye. Using a relatively long excitation pulse would enable efficient rejection of the unwanted photoacoustic signals generated by the pump pulse, by utilizing a high-pass filter, thus leaving the PA signals of the probe pulse free of interferences.
Developing the technique for clinical tissue imaging could provide a valuable tool for cancer diagnostics, staging, and treatment monitoring. Note that over the past decade, studies have demonstrated high correlations of hypoxia with tumor aggressiveness and tumor resistance to therapy.11 Delivering the dye to tumor in vivo is a challenging task. One of the promising ways to accomplish it, is using12, 13 dye nanoencapsulation technology such as PEBBLE (Probing Explorers for Bioanalysis with Biologically Localized Embedding). This enables specific tissue targeting by biocompatible nanoparticles embedded with the sensor dye.
Our specific implementation of the PA lifetime measurement relied on the fact that the lifetime is in the order of of microseconds, much longer than the laser pulse width. However, most fluorophores in biological systems (or those used to probe biological systems) have lifetimes shorter than the laser pulse width.14, 15 In principle, the method can be scaled to measure shorter lifetimes by using laser pulse widths that are shorter than the required lifetime measurement resolution (e.g., picosecond lasers). In this case, the resulting PA signal would combine contributions from the excitation pulse and the delayed probe pulse (transient absorption). The decay of the PA signal amplitude as a function of the excitation-probe delay time would still reflect the transient absorption. However, penetration depth would be compromised due to lower pulse energy in picosecond lasers, lower efficiency for PA generation, and reduced contrast due to large constant absorption term. In spite of these difficulties, we believe that PA probing of excited state decay in the nanoseconds range of endogenous species (e.g., hemoglobin) and functional exogenous molecular probes would open up a range of new applications for medical molecular imaging.