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# Oxygen sensing ability of positronium atom for tumor hypoxia imaging

## Abstract

Positronium (Ps), a hydrogen-like atom consisting of a positron and an electron, is efficiently formed in the human body during positron emission tomography (PET) examination, and its decay rate into gamma-ray photons is significantly influenced by the chemical environment, especially the dissolved oxygen concentration (pO2) due to the unpaired electrons. However, the functionality of PET has been underestimated by neglecting the specific information provided by Ps. By comparing the decay rates in O2-, N2-, and air-saturated waters, here we show that Ps probes the absolute value of pO2 with a good linearity and a resolution better than 10 mmHg. This is a sufficient sensitivity for discriminating a hypoxic region in a tumor at approximately 6 mmHg from healthy tissues at approximately 40 mmHg. This method depends only on the fundamental properties of Ps and is independent of specific radiopharmaceuticals. The applications of Ps spin states and reactions will greatly enhance PET functionalities in the next decade.

## Introduction

Positrons are widely used for medical imaging as in positron emission tomography (PET1,2) to investigate the spatial distribution of pharmaceuticals labeled with positron emitters in the human body. During a PET scan, a patient is surrounded by γ-ray detectors for annihilation photons emitted by the positron–electron pair annihilation. Conventional PET has been interested only in the annihilation photons about their detected positions, timings, and energies, but not in the life history of positron before the annihilation.

Some positrons annihilate after forming positronium (Ps), which is a hydrogen-like atom consisting of a positron and an electron, e.g.,

$${\mathrm{e}}^ + + {\mathrm{H}}_{\mathrm{2}}{\mathrm{O}} \to {\mathrm{Ps + H}}_{\mathrm{2}}{\mathrm{O}}^ + .$$
(1)

An energic positron is emitted from an isotope such as 11C, 13N, 15O, 18F, 22Na, 44Sc3,4, and it quickly loses its kinetic energy within a few millimeters and within a few picoseconds through successive interactions with surrounding molecules5. During this process, some positrons capture an electron from these molecules to form Ps6, and the others directly annihilate by colliding with an electron. The former ratio has been estimated to be 40% in the human body7,8. Ps is a transient by-product in a PET scan and decays into γ-ray photons in a short lifetime.

Recently, Moskal et al.7,8,9,10 have proposed a new PET concept utilizing Ps and named it Ps imaging. Here, we demonstrate the fact that the lifetime of Ps is sensitive to dissolved oxygen concentration (pO2) and that Ps can be used for probing hypoxic regions in the body. Hypoxia is often observed as an internal structure of tumors where angiogenesis cannot match the unregulated cell proliferation. For example, pO2 is reported as $$40.6 \pm 5.4$$ mmHg in healthy liver tissue11 and as $$6$$ mmHg in liver tumors12. A hypoxic tumor is often resistant to radiation therapy as well as chemotherapy13,14,15; therefore, knowledge of the pO2 distribution in these tumors can support better treatment for patients.

We can measure the pO2 distribution by using the spin properties of Ps, whose total spin ($$S$$) can be 1 or 0, as a positron and an electron each have 1/2 spin. The spin parallel state, $$S = 1$$, is termed as ortho-Ps (o-Ps), and the antiparallel state, $$S = 0$$, is termed as para-Ps (p-Ps). The creation ratio between p-Ps and o-Ps is 1:316. p-Ps spontaneously decays into two photons as follows:

$${\mathrm{p}}\, \text{-} {\mathrm{Ps}}\mathop{\longrightarrow}\limits^{{\lambda _{\mathrm{p}}}}2\gamma ,$$
(2)

where the decay rate is $$\lambda _{\mathrm{p}} = 7.9909 \times 10^3$$ µs−1 (lifetime $$\tau _{\mathrm{p}} = \lambda _{\mathrm{p}}^{ - 1} = 125.14\,{\mathrm{ps}}$$) in vacuo17. The radiation energy is distributed in a line spectrum at 511 keV corresponding to the rest mass of one positron/electron. In contrast, o-Ps spontaneously decays into three photons as follows:

$${\mathrm{o}} \, \text{-} {\mathrm{Ps}}\mathop{\longrightarrow}\limits^{{\lambda _{\mathrm{o}}}}3\gamma ,$$
(3)

where the rate is $$\lambda _{\mathrm{o}} = 7.0401$$ µs−1 ($$\tau _{\mathrm{o}} = \lambda _{\mathrm{o}}^{ - 1} = 142.04\,{\mathrm{ns}}$$) in vacuo18. The energy is distributed in a continuous spectrum ranging from 0 to 511 keV19. Each o-Ps possesses a short but important history before annihilation because $$\lambda _{\mathrm{o}}$$ is small enough to permit o-Ps interact with surrounding molecules repeatedly, and as a result, the lifetime of o-Ps in non-vacuum environments is reduced to less than $$\tau _{\mathrm{o}}$$. Thus, we can examine the surrounding molecules by measuring the o-Ps lifetime.

Figure 1 shows an overview on the life history of positrons, and the reduction of their lifetime occurs via two types of reaction with molecules: one is pick-off annihilation and the other is a spin-exchange interaction. First, o-Ps has a parallel spin between the positron and the electron, and there are several other electrons with the antiparallel spin around it. This situation induces o-Ps to perform pick-off annihilation where the positron of Ps annihilates with a foreign electron in a molecule, e.g.,

$${\mathrm{o}} \, \text{-} {\mathrm{Ps}} (\uparrow _{\mathrm{p}} \uparrow _{\mathrm{e}}) + {\mathrm{H}}_{\mathrm{2}}{\mathrm{O}}(\downarrow _{\mathrm{e}}) \to 2\gamma + {\mathrm{e}}^ - ( \uparrow _{\mathrm{e}}) + {\mathrm{H}}_{\mathrm{2}}{\mathrm{O}}^ + ,$$
(4)

where up/down arrows indicate up/down spins with the index of p/e (positron/electron). This reaction occurs with any molecule in the body. Second, only when the surrounding molecules possess unpaired electron, a spin-conversion from o-Ps to p-Ps is induced through a spin-exchange interaction, e.g.,

$${\mathrm{o}} \, \text{-} {\mathrm{Ps(}} \!\!\uparrow _{\mathrm{p}} \uparrow _{\mathrm{e}}\!\!{\mathrm{) + O}}_2{\mathrm{(}} \!\!\downarrow _{\mathrm{e}}\!\!{\mathrm{)}} \to {\mathrm{p}} \, \text{-} {\mathrm{Ps + O}}_2{\mathrm{(}}\!\! \uparrow _{\mathrm{e}}\!\!{\mathrm{)}}\mathop{\longrightarrow}\limits^{{\lambda _{\mathrm{p}}}}2\gamma + {\mathrm{O}}_2{\mathrm{(}}\!\! \uparrow _{\mathrm{e}}\!\!{\mathrm{)}}{\mathrm{.}}$$
(5)

Since $$\lambda _{\mathrm{p}} \gg \lambda _{\mathrm{o}}$$, the o-Ps lifetime is reduced by this reaction. Moreover, the reaction rate of the spin exchange is around two orders of magnitude larger than that of the pick-off annihilation. Therefore, o-Ps lifetime is significantly reduced by interactions with paramagnetic molecules such as $${\mathrm{O}}_2$$20,21. Furthermore, there could be a resonant state between Ps and O2, i.e., PsO2, and the resonance could increase the pick-off annihilation rate and the spin-exchange interaction rate because of the longer contact time22.

For measuring o-Ps lifetime, two signals per annihilation event are required, i.e., start and stop signals. The start signal informs the time of the positron emission, and the stop signal informs the time of the positron/Ps annihilation. The latter is determined by monitoring the annihilation photons. The former can be determined by monitoring a prompt γ-ray that is emitted immediately after the positron emission from some isotopes3; here we used 22Na with 1.27 MeV prompt γ-ray.

Three samples were prepared and measured: $${\mathrm{O}}_2$$-saturated water, $${\mathrm{N}}_2$$-saturated water, and air-saturated water. Each sample contained [22Na]-NaCl of 190 kBq (5 µCi) and monitored by two scintillation detectors for γ-ray photons23. The coincidental events between the start and top signals were recorded, and the waveforms were analyzed posteriori to determine the time lag. The time-lag histogram was created with the bin width of 20 ps, and the total counts for $${\mathrm{O}}_2$$-, $${\mathrm{N}}_2$$-, and air-saturated samples were $$4.3 \times 10^7$$, $$4.9 \times 10^7$$, and $$5.9 \times 10^7$$, respectively. The effective count rate was $$120\,{\mathrm{s}}^{ - 1}$$. All preparations and measurements were conducted at a temperature of $$19.0 \pm 1.0\,^\circ {\mathrm{C}}$$.

Here, we show that the Ps decay rate into γ-ray photons in water indicates the pO2 by means of comparing the decay rates in the three pO2-controlled samples. As the pO2 increases from 0 to 1400 µmol L−1, the decay rate linearly increases from 520 to 548 µs−1. This linearity makes it possible to indicate the absolute value of pO2 with a resolution of ≤10 mmHg by measuring the Ps decay rate. Because the Ps atoms are efficiently created in the human body during PET procedure, this indicator can be used for imaging the distribution of pO2 to examine hypoxia regions formed by unregulated cell proliferation inside the tumors.

## Results

### The time-lag histogram and the fit for the o-Ps lifetime

The time-lag histogram for the air-saturated sample is shown in Fig. 2a on a semilog scale with the following three major structures: (i) a prompt peak near time-zero primarily due to p-Ps annihilation and positron–electron direct annihilation, (ii) a single-exponential slope after 5.8 ns due to o-Ps annihilation including the pick-off annihilation and the spin-exchange interaction, and (iii) a flat background level due to random coincidences with no time correlation. The slope was fitted with a single-exponential function to determine the o-Ps lifetime and its reciprocal thereof, the decay rate ($${\Gamma}$$), as depicted in Fig. 2a–c.

### Contributions of gas molecules to o-Ps decay rate

The o-Ps lifetimes were determined to be $$\tau _{{\mathrm{O}}_{\mathrm{2}}} =$$ 1.8239(36) ns in O2-saturated water, $$\tau _{{\mathrm{N}}_{\mathrm{2}}} =$$ 1.9215(32) ns in N2-saturated water, and $$\tau _{{\mathrm{Air}}} =$$ 1.9040(29) ns in air-saturated water. Then, we obtained simultaneous equations as follows:

$$\left\{ \begin{array}{l}\lambda _{\mathrm{o}} + \lambda _{{\mathrm{H}}_{\mathrm{2}}{\mathrm{O}}} + 1396.4\left( {14} \right)\kappa _{{\mathrm{O}}_{\mathrm{2}}} = 1/\tau _{{\mathrm{O}}_{\mathrm{2}}} = 548.3(11)\ \mu {\mathrm{s}}^{ - 1}\hfill\\ \lambda _{\mathrm{o}} + \lambda _{{\mathrm{H}}_{\mathrm{2}}{\mathrm{O}}} + 705.1(7)\kappa _{{\mathrm{N}}_{\mathrm{2}}} = 1/\tau _{{\mathrm{N}}_{\mathrm{2}}} = 520.4(9)\ \mu {\mathrm{s}}^{ - 1}\hfill\\ \lambda _{\mathrm{o}} + \lambda _{{\mathrm{H}}_{\mathrm{2}}{\mathrm{O}}} + 296.0(3)\kappa _{{\mathrm{O}}_{\mathrm{2}}} + 556.1(5)\kappa _{{\mathrm{N}}_{\mathrm{2}}} = 1/\tau _{{\mathrm{Air}}} = 525.2(8)\ \mu {\mathrm{s}}^{ - 1}\hfill\\ \lambda _{\mathrm{o}} = 7.04\ \mu {\mathrm{s}}^{ - 1}\hfill\end{array} \right.,$$
(6)

where $$\lambda _{{\mathrm{H}}_{\mathrm{2}}{\mathrm{O}}}$$ is the annihilation rate due to the pick-off annihilation with water molecules, $$\kappa _{{\mathrm{N}}_{\mathrm{2}}}$$ is the annihilation rate, normalized by the number density of dissolved N2, due to the pick-off annihilation with the molecules, and $$\kappa _{{\mathrm{O}}_{\mathrm{2}}}$$ is that due to both the pick-off annihilation and the spin-exchange interaction with dissolved O2 molecules [Eqs. (4) and (5)]. The coefficients of $$\kappa$$’s are the solute number density in the unit of µmol L−1 taking into account the partial pressures and the temperature at the time of sealing of the vial, and their uncertainties arise from an aneroid barometer. The effects of Ar and CO2 molecules in the air are ignored because their contributions are estimated to be $$\le 0.06\%$$. Table 1 shows the general atmospheric components and their partial pressures, their solubility in water at the partial pressures24, the normalized o-Ps quenching rate in gas phase (1Zeff25) to estimate their contributions to o-Ps quenching, and the coefficients for converting the pressure unit from mmHg to µmol  L−1 at 19.0 °C.

By solving Eq. (6) simultaneously, we obtain the breakdowns as follows:

$$\lambda _{{\mathrm{H}}_{\mathrm{2}}{\mathrm{O}}} = \, 512.8(16)\ \mu {\mathrm{s}}^{ - 1}\\ \kappa _{{\mathrm{O}}_{\mathrm{2}}} = \, 0.0204(8)\ \mu {\mathrm{s}}^{ - 1}\mu {\mathrm{mol}}^{ - 1}{\mathop{\rm{L}}\nolimits} \\ \kappa _{{\mathrm{N}}_{\mathrm{2}}} = \, 0.0015(25)\ \mu {\mathrm{s}}^{ - 1}\mu {\mathrm{mol}}^{ - 1}{\mathop{\rm{L}}\nolimits} .$$
(7)

This confirms that not only Ar and CO2, but also N2 molecules contribute below the detection limit, and this fact is consistent with Fig. 3, where a pure linearity between o-Ps decay rate and pO2 within the error bars is obvious despite ignoring N2 contributions. This tendency has been reported by Lee and Celitans26 and Stepanov et al.27; however, the linearity has been unclear because of the large uncertainties in water as shown in Fig. 3. The linearity was confirmed here on a practical level with sufficiently small uncertainties and the slope seemed consistent with those of Lee and Celitans26 and Stepanov et al.27

### Conversion from the o-Ps decay rate to absolute pO2

We elucidated how to convert the measured o-Ps decay rate ($${\Gamma}$$ in the unit of µs−1) into pO2 as follows:

$${\rm{pO}}_{2}/{\rm{\mu mol}}\,{\rm{L}}^{ - 1} = \frac{{{\Gamma} - \lambda _{\mathrm{o}} - \lambda _{{\mathrm{H}}_{\mathrm{2}}{\mathrm{O}}}}}{{\kappa _{{\mathrm{O}}_{\mathrm{2}}}}},$$
(8)

and the more practical form was as follows:

$${\rm{pO}}_{2}/{\rm{mmHg}} = 26.3(11) \times \left[ {{\Gamma} - 519.9(16)} \right]$$
(9)

by substituting Eq. (7) and the solubility in Table 1. The uncertainties (one standard deviation) can be reduced by increasing the total counts as discussed in the next section.

## Discussion

Now, we have the quantitative question of whether we can discriminate a hypoxic region at a pO2 of 6 mmHg from control regions at a pO2 of 40 mmHg using Eqs. (8) or (9). The answer can be found in Fig. 4, showing the relationship between the total counts ($$N$$) in the histogram and the resolution in pO2; the points are measured using the air-saturated sample, and those at $$N \ge 10^7$$ follow a line approximately according to $$1/\sqrt N$$. This implies a Poisson distribution nature, and the extrapolation indicates that we need $$N \ge 3 \times 10^8$$ acquisition from the region of interest (ROI) to achieve the pO2 resolutions of 10 mmHg and $$N \ge 1 \times 10^9$$ acquisition to achieve that of 5 mmHg. A resolution of 11 mmHg can discriminate the 6-mmHg region from the 40-mmHg regions with a reliability better than 99.7% due to a difference of greater than three standard deviations (3σ).

This is a practically sufficient sensitivity as the following order estimation. One of our laboratory PET scanners28 currently has a triple-coincidence sensitivity of 0.001% for 44Sc (half-life: 4.02 h) whose $$\beta ^ +$$ decay primarily provides one prompt-γ-ray photon (1.16 MeV) and two annihilation γ-ray photons (511 keV) per event4, when the energy window for the start signal accepts both the full-energy absorption events and the Compton scattering events. Subsequently, the required acquisition time would be 0.5 h for $$N = 3 \times 10^8$$ and 1.5 h for $$N = 1 \times 10^9$$, respectively, assuming a possible activity of 6-MBq 44Sc in ROI, which would be a few percent of a typical injection dose. It is worth noting that this method is independent of how the radiopharmaceutical is delivered to the ROI; it may be delivered physiologically in the same way as the conventional PET radiopharmaceuticals or delivered physically using a microsyringe directly to a tumor especially for small animals.

To achieve a high resolution such as 5 mmHg, one must avoid the systematic drift caused by temperature fluctuations and other factors that facilitate deviation from the Poisson nature. The present system has been stable for several days because we have used the analog circuits only for making the trigger, and the time lag has been calculated from the digitized waveforms (“Methods” section).

Next, we must discuss some systematic uncertainties in this method. The first uncertainty is due to the measurement system and the method of data analysis. Even when the samples were simple solid materials such as fused silica and polycarbonate, there was a 1.7% systematic uncertainty in the o-Ps lifetimes among 12 laboratories in Japan, although it was 0.6% in the host laboratory of the study in 200829. Therefore, it will be more appropriate to use the relative difference in $${\Gamma}$$ between the ROI and the control regions rather than using their absolute values. The relative value is also beneficial for the second aspect, i.e., the effect of solutes other than gases. According to Green and Bell30, however, the effects of diamagnetic ions have been slightly observed in the count number belonging to the slope in Fig. 2a (not in the gradient of the slope, i.e., $${\Gamma}$$) at fairly high concentrations of 2–10 mol L−1. In contrast, the major ionic concentrations inside or outside of cells are less than these concentrations by one or two orders of magnitude, i.e., $${\mathrm{K}}^{\mathrm{ + }}$$ (0.16 mol L−1) and $${\mathrm{HPO}}{}_4^{2 - }$$ (0.06 mol L−1) in the intracellular solution and $${\mathrm{Na}}^{\mathrm{ + }}$$ (0.14 mol L−1) and $${\mathrm{Cl}}^ -$$ (0.10 mol L−1) in plasma31. In any case, the small effects that are common to the two regions are canceled out by each other if the relative values are used.

Finally, we mention the 3γ annihilation ratio ($$R_3$$)7,32, in other words, the ratio of the self-annihilation of o-Ps into 3γ photons unless quenched into 2γ photons through the pick-off annihilation or the spin-exchange interaction. $$R_3$$ is also expected to be sensitive to pO2 and can be described as

$$R_3 = \frac{{\lambda _{\mathrm{o}}}}{{\Gamma} } = \frac{{\lambda _{\mathrm{o}}}}{{\lambda _{\mathrm{o}} + \lambda _{{\mathrm{H}}_{\mathrm{2}}{\mathrm{O}}} + n_{{\mathrm{O}}_{\mathrm{2}}}\kappa _{{\mathrm{O}}_{\mathrm{2}}}}},$$
(10)

where $$n_{{\mathrm{O}}_{\mathrm{2}}}$$ is the number density of O2 molecules (in the unit of µmol L−1) in water. We made an indirect test for $$R_3$$ by comparing the energy spectra measured by the stop detector, i.e., the LaBr3(Ce) scintillator. Figure 5 shows the spectra obtained using O2- and N2-saturated samples with their counts normalized at the high-energy tails between 600 and 700 keV (Fig. 5a) where the events are primarily attributed to the 1.27-MeV photons and are free from $$R_3$$. Two structures are attributed to 2γ events: one is the full-energy peak at 511 keV (Fig. 5b) and other is the Compton edge at around 340 keV (Fig. 5c). In both structures, the intensity from the O2-saturated sample is larger than that from the N2-saturated sample. On the other hand, it is smaller at the valley between the two structures, from 340 to 420 keV (Fig. 5c), and at below the backscattering peak at 170 keV (Fig. 6). These facts indicate that o-Ps in the O2-saturated sample is more frequently quenched into 2γ photons through the spin-exchange interaction. Therefore, $$R_3$$ (Eq. (10)) would also be sensitive to pO2. Some laboratory-based PET scanners have already measured 3γ events directly33 for obtaining the spatial distribution of radiopharmaceuticals (not for Ps imaging).

The method based on Eq. (9) has become feasible due to recent instrumental improvements that enable a time resolution in a PET scanner better than 300 ps34,35. Furthermore, a new image reconstruction technique based on the Compton camera has been investigated to obtain pinpoint spatial information28,36. This technique would enhance the accuracy of the present method by informing whether the event comes from inside or outside of the ROI. In addition, since the present method would be sensitive to free radicals other than O237, we intend to study other chemically active species such as the hydroxyl radical (•HO), hydrogen peroxide (H2O2), and hydrated electrons (eaq) with regard to radiotherapy14,15 in a future research.

Some recent studies have focused on other oxygen sensing methods using phosphorescence or fluorescence38,39. An advantage of annihilation photons beyond the visible and infrared photons is their strong transmission from deep inside the human body even through the skull in a noninvasive manner. A disadvantage may be the acquisition time for obtaining sufficient N, which is as long as that of PET diagnosis, up to several dozen minutes.

Collaborations with established PET hypoxia markers, such as [18F]-FMISO, [18F]-FAZA, and Cu-ATSM40, would be interesting because the absolute pO2 value (in mmHg) obtained by our method could provide higher accuracy and wider applications for them. The proposed methodology would describe self-multi-modality between Ps imaging and conventional PET imaging. Most PET markers accumulate physiologically, and the radioactive concentrations are attributed to metabolism. However, the Ps imaging is often independent of how the radiopharmaceuticals are delivered to the ROI; for example, they may be directly injected into a tumor using a microsyringe, especially for small animals.

In brief, we have proposed a methodology for converting the o-Ps decay rate into the absolute value of pO2 and demonstrated the linearity with a resolution of better than 10 mmHg, which would be sufficient for discriminating a hypoxic region in a tumor at less than 6 mmHg from control regions at approximately 40 mmHg. We anticipate that this methodology can be used in a wide range of oncological PET applications to extend the biological and clinical functionalities as it is based on the fundamental properties of Ps and is independent of any specific radiopharmaceuticals. The synergy between this methodology and these radiopharmaceuticals would improve our understanding and treatment of cancers for patients. We believe that now is the time for PET to enter a new stage utilizing information from the spin states and reactions of Ps and that the Ps imaging is the next axis of PET research.

## Methods

### Sample preparation

The samples were prepared as follows. Distilled water was degassed by freeze-pump-thaw three times and was saturated with $${\mathrm{O}}_2$$ gas by bubbling for 1 h in a glove box with the air replaced with 100% $${\mathrm{O}}_2$$ gas at a barometric pressure of 750.1 mmHg (1000 hPa) and at a temperature of $$19.0\,^\circ {\mathrm{C}}$$. This method of gas-saturation is based on the one used for Fricke dosimeter. The $${\mathrm{O}}_2$$-saturated water, approximately 50 mL, and 190 kBq (5 µCi) [22Na]–NaCl were sealed in a 50-mL vial that had been ultrasonically washed in a dilute NaOH aqueous solution and dried. A small amount of $${\mathrm{O}}_2$$ gas remained between the water surface and the cap. Then, the sealed vial and 100% $${\mathrm{O}}_2$$ gas were again sealed in a 200-mL screw bottle. In addition to this O2-saturated sample, a N2-saturated sample (751.6 mmHg (1002 hPa), 18.8 °C) and an air-saturated sample (759.1 mmHg (1012 hPa), 18.6 $$^\circ {\mathrm{C}}$$) were prepared in the same manner. An oxygen scavenger was also sealed in the 200-mL crew bottle for the $${\mathrm{N}}_2$$-saturated sample. The degassing step was omitted for the air-saturated sample. The partial pressures and the temperature at the time of sealing were considered in the coefficients of Eq. (6).

### Measurement system

The measurement system was primarily composed of the following instruments: two γ-ray detectors, two discriminators, a coincidence unit, and a digital oscilloscope. The sample bottle was monitored by the two γ-ray detectors for the start and stop signals. The former was a photo-multiplier tube (PMT, H3378, Hamamatsu, Japan) equipped with a BaF2 scintillator crystal and a supplied voltage of −2200 V. The PMT used a fused silica window because of the ultraviolet scintillation photons. The latter was a PMT equipped with a LaBr3(Ce) scintillator crystal and a supplied voltage of −1570 V. The crystal was sealed in an airtight package because of the deliquescence, and it was used as delivered (Saint-Gobain, France). This detected one of the two or three annihilation photons per event. Both crystals were cylindrical in shape with a size of $$\phi 50\,{\mathrm{mm}} \times {\mathrm{30}}\,{\mathrm{mm}}$$, which was selected for sensitivity rather than time resolution. The distance between the sample and detectors were ca. 5 cm. The output of each PMT was divided into two lines, of which one was for recording using a digital oscilloscope and the other was for making a trigger for the oscilloscope. The trigger was generated by a coincidence unit when it received two signals within 100 ns from the two discriminators; one was for the start PMT with a discrimination level of ca. 750 keV, and the other was for the stop PMT with a discrimination level of ca. 300 keV. Thus, the coincidental events were selectively recorded using the oscilloscope at a sampling interval of 100 ps, and the digitized waveforms were analyzed posteriori using a PC to determine the time lag between the two signals. The effective coincidental count rate was $$120\,{\mathrm{s}}^{ - 1}$$ (11 megacounts per day), which was limited by the processing speed of the oscilloscope. Further details of the system have been described in our previous studies41,42,43.

### Waveform analysis

The digitally recorded signals from the two detectors were analyzed using a PC as follows. First, the smoothed waveforms ($$b_n$$) were created from the recorded waveforms ($$a_n$$) for filtering high frequency noises as follows: $$b_n = a_n + 2a_{n - 1} + 2a_{n - 2} + a_{n - 3}$$. Second, the energy was determined by the integration of the waveform between 1.5 ns before the peak and 2.5 ns after the peak for the start signal from the BaF2 scintillator to obtain a relative energy resolution of 31% for 1.27 MeV full-energy peak, and between 8.0 ns before the peak and 22.0 ns after the peak for the stop signal from the LaBr3(Ce) scintillator to obtain a relative energy resolution of 6.4% for 511 keV full-energy peak. Only events that satisfy the both energy windows were sent to the next process, i.e., from 0.87 to 1.67 MeV for the start signal and from 450 to 570 keV for the stop signal. Third, the timing was determined as the position where the rising part of the waveform reached 7.5% of the peak intensity. Finally, the time lag was determined by comparing the two positions and was classified into the histogram with a bin width of 20.0 ps. The systematic time resolution for the coincidence between the 1.27-MeV photon and the 511-keV photon was 249 ps41. The abnormal waveforms having plural peaks or pile-up peaks were rejected by checking the peak width and the ratio between the peak height and the integrated peak area.

### Curve fitting

The slope of the time-lag histogram was fitted with a single-exponential function as follows. First, the background level was determined by a delayed time window from 40.0 to 60.0 ns where no true counts were expected (Fig. 2a). Second, the slope was fitted with a single-exponential function by a weighted-least-squares method. The weight was the square root of the number of counts in each bin including the background. The end of the fit range was set at 25.0 ns, which was not critical to the result, whereas the start of the fit range was carefully set at 5.8 ns with reference to the literature44. A too-early start was affected by the prompt component, whereas a too-late start was statistically disadvantageous. It is worth noting that some software tools are available to fit the time-lag histogram with multi-exponential function including the prompt peak, e.g., LT-1045 and PALSfit346. According to Jasinska et al.47, the prompt peak for human tissues can be divided into two components, and the contribution of a third component (i.e., the long-lifetime component) accounts for approximately 20% of the total annihilation.

### Energy spectra

The energy spectra shown in Figs. 5 and 6 were measured with some changes in the measurement system as follows. The detector for the start signal and the coincidence unit were not used. The discrimination level for the stop signal was lowered to be at ca. 70 keV to measure the structure of the Compton edge at ca. 340 keV and other structures below it. The count rate was 450 s−1 and the distance between the stop detector and a sample was 80 cm.

## Data availability

The data supporting the findings of this study are available from the corresponding author upon reasonable request.

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## Acknowledgements

We would like to thank Dr. H. Tashima with the National Institute of Radiological Sciences for providing information on PET image reconstruction and Mr. T. Takizawa and Ms. A. Inamasu with the University of Tokyo for their supports on radiation safety. This work was partially supported by the Japan Society for the Promotion of Science (JSPS) KAKENHI Grant nos. 20H00671 and 20H05667.

## Author information

Authors

### Contributions

K.S. and T.Y. designed the experiments. F.N. and M.T. prepared the samples, operated the measurement systems, and collected the data. H.S. and K.S. created the computing programs and analyzed the data. K.S. and T.Y. created the figures and wrote the paper with input from all other authors. All authors approved the final version submitted.

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### Competing interests

The authors declare no competing interests.

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Shibuya, K., Saito, H., Nishikido, F. et al. Oxygen sensing ability of positronium atom for tumor hypoxia imaging. Commun Phys 3, 173 (2020). https://doi.org/10.1038/s42005-020-00440-z

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